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PHOTOPOLYMERIZATION OF 2 HYDROXYETHYL
METHACRYLATE IN THE DEVELOPMENT OF
GLASS-IONOMER CEMENTS
SYED MUHAMMAD KEFI IQBAL
B.D.S. (KU), M. Sc. (London)
A thesis submitted to the Baqai Medical University for the degree of
Doctor of Philosophy
Department of Dental Material Sciences
Faculty of Medicine and Dentistry
Baqai Medical University
Karachi, Pakistan
June, 2011
iii
CERTIFICATE
This is to certify that the work presented in this thesis entitled “Photopolymerization
of 2-Hydroxyethyl Methacrylate in the Development of Glass-Ionomer Cements” is
original and has been conducted by Mr. Kefi Iqbal under my supervision as fulfillment
of the requirement of Ph.D. degree from the Faculty of Medicine and Dentistry, Baqai
Medical University, Karachi.
Professor Dr. Iqbal Ahmad
Faculty of Pharmaceutical Sciences,
Baqai Medical University, Karachi.
iv
ABSTRACT
The present investigation is based on a comparative study of the
polymerization reactions of 2-hydroxyethyl methacrylate (HEMA) using riboflavin
(RF), camphorquinone (CQ) and safranin T (ST) as photoinitiators and
triethanolamine (TEOHA) as a co-initiator in aqueous and organic solvents. HEMA is
involved in photoinitiated polymerization reactions occurring in glass-ionomer
cements (GICs). The above photoinitiators are stable on exposure to a 15 W lamp
emitting in the visible region during the irradiation period. A UV spectrophotometric
method has been developed to determine the concentration of HEMA in polymerized
solutions at low conversion, i.e., about 5% concentration change in the monomer. The
effect of pH, solvent characteristics and HEMA / TEOHA concentration on the rate of
polymerization reactions has been evaluated. The rates of the reactions have been
found to increase with pH probably as a result of the deprotonation of TEOHA and
the presence of a labile proton on the hydroxyl group of HEMA. The steady-state
assumption of the rate of initiation being equal to the rate of termination is considered
valid only at a low conversion of the monomer. Under these conditions the
polymerization reactions have been found to follow pseudo first-order kinetics
(within about 5 % change in HEMA concentration) and the determined apparent first-
order rate constants (kobs) range from 5.44–7.63×10–4
s–1
at pH 6.0–9.0 using 0.01M
TEOHA. The polymerization reactions of HEMA are affected by the dielectric
constant and viscosity of the medium. There is a linear relation between the rate
constants and the solvent dielectric constant indicating the involvement of a polar
intermediate in the reaction. The observation of a linear relation between the rate
v
constants and the inverse of solvent viscosity indicates the effect of viscosity on the
diffusional processes of reacting species and hence the decrease in rates with an
increase in the viscosity of the medium. For all the photoinitiators used the
polymerization reaction is dependent on the TEOHA concentration and the second-
order rate constants for the interaction of HEMA (1–3M) and TEOHA 0.0025–
0.01M) range from 1.79–8.87×10–2
M–1
s–1
at pH 6.0–9.0. The reactivity of the
photoinitiators appears to depend on the energy of the excited triplet state, and its
degree of interaction with the amine to form a radical ion pair, its dissociation and
further interaction of amine radicals with HEMA to undergo polymerization. In the
present work, the reactivity of the photoinitiators has been found to be in the order:
RF > CQ > ST. The irradiation wavelength of the photoinitiators also increases in the
same order resulting in decreased energy and, therefore, it may influence the efficacy
of the photoinitiator. The polymerization of HEMA photoinitiated by the three
compounds is faster in aqueous solution compared with the organic solvent under
identical conditions. The results indicate that the reactivity of the photoinitiators
depends upon their structural features, ionization behavior, spectral characteristics,
triplet energy and solvent characteristics. It appears that the photoinitiators absorbing
in the lower visible region are more efficient (RF 445 nm, CQ 468 nm) in causing
polymerization of HEMA compared to those absorbing in the relatively higher visible
region (ST 520 nm), as indicated by their absorption maxima. Therefore, the use of
RF as a photoinitiator in glass ionomer cements would require a relatively less curing
time for the setting of resin restorative materials and it appears to be the most
efficient photoinitiator in the polymerization process under the conditions studied.
vi
ACKNOWLEDGEMENTS
All praise to Allah Who is the most Beneficent and the most Merciful.
I am extremely grateful to my supervisor, Prof. Dr. Iqbal Ahmad,
Department of Pharmaceutical Chemistry, Faculty of Pharmaceutical Sciences, for his
guidance, keen interest, cheerful support and healthy criticism throughout this study.
Without his help and encouragement through the various phases of this work, the
project would have never reached fruition.
I would also like to thank my co-supervisor Prof. Dr. Aminuddin,
Department of Pharmaceutical Chemistry, for his advice, inspiration and support
during this study.
I pay gratitude to Prof. Lt. Gen. (R) Dr. Syed Azhar Ahmed, Vice
Chancellor, Baqai Medical University, for his interest, encouragement and support.
His keen interest in the promotion of research activities in the University is highly
appreciated.
I would like to express my grateful thanks to Dr. Muhammad Ali Sheraz and
Dr. Sofia Ahmed of the Department of Pharmaceutics for their continued support,
and help during the study.
I consider myself lucky to have met and worked with the staff of the Faculty
of Pharmaceutical Sciences.
My appreciation and thanks go to all my colleagues in the Department of
Dental Material Sciences. I would particularly like to thank Dr. Maria, Dr. Adel, Dr.
Sana, Dr. Afreen and Mr. Altaf for their help and support throughout this study.
vii
I would also like to thank my students, colleagues and friends for their
kindness and support during the period of this study.
I don’t have words to thank Mrs. Prof. Dr. Iqbal Ahmad for her kindness,
love and support.
Finally I am highly indebted to my family who provided me enormous
support, love and understanding at every step of my path to this achievement.
K. I.
viii
Dedicated
to my sweet mother for her endless love and
care
ix
ABBREVIATIONS
AA Acrylic acid
ATR-FT-IR Attenuated total refraction Fourier transform infrared
bis-GMA Bisphenol glycidyl dimethacrylate
BP Benzophenone
BPO Benzoyl peroxide
CQ
Camphorquinone
DEGDMA Diethylene glycol dimethacrylate
DHEPTI Di-hydroxyethyl-p-toluidine
DMAEMA Dimethylaminoethyl methacrylate
EGDMA Ethylene glycol dimethacrylate
FTIR Fourier transform infrared spectroscopy
GIC Glass-ionomer cement
GMA
Glycidyl methacrylate
HEMA Hydroxyethyl methacrylate
IA Itaconic acid
ICP–ES Inductively coupled plasma emission spectroscopy
IR infrared spectroscopy
MA Maleic acid
NMR
Nuclear Magnetic Resonance
NVP
N-vinyl pyrrolidone
PMMA
Polymethyl methacrylate
x
RF Riboflavin
RMGICs Resin-modified glass-ionomer cements
SEM
Scanning electron microscopy
ST Safranin T
TAS
Transient absorption spectroscopy
TEOHA Triethanolamine
TLC Thin-layer chromatography
UDMA Urethane dimethacrylate
UV Ultraviolet
XPS X-Ray photoelectron spectroscopy
xi
CONTENTS Chapter Page
ABSTRACT iv
ACKNOWLEDGEMENTS
ABBREVIATIONS
vi
ix
I INTRODUCTION 1
1.1 Glass-Ionomer Cements 2
1.1.1 Composition of GICs 3
1.1.2 Water Settable Cement 5
1.1.3 Powder: Liquid Ratio 5
1.1.4 Working and Setting Times 7
1.1.5 Variations in Basic Glass Composition 8
1.1.6 Role of Glasses in GICs 8
1.1.7 Effect of Glass Particles Size on GICs 10
1.1.8 Role of Aluminum in Glasses 10
1.1.9 Phases in Glass Structure 12
1.1.10 Role of Liquid in GICs 12
1.1.11 Role of Polymer on Setting Time 14
1.1.12 Role of Tartaric Acid in Setting Time 14
1.1.13 Setting Reaction 15
1.1.14 Leaching Behaviour of Glasses During the Setting Reaction 17
1.1.15 Structure of Set Cement 18
1.1.16 Solubility and Disintegration 18
xii
1.1.17 Adhesive Characteristics 18
1.1.18 Surface Treatment of Glass Particles and Their Effect on the Setting Reaction 19
1.1.19 Participation of Glasses During Cement Formation 21
1.1.20 Types of Glass Ionomer Cements 21
1.1.21 Physical Properties of GICs 23
1.1.22 Literature on Glass Ionomer Cements 28
II CHEMISTRY OF POLYMERIZATION 29
2.1 Introduction 30
2.2 Polymerization Reactions 32
2.2.1 Condensation Polymerization 32
2.2.2 Addition Polymerization 33
2.3 Free-radical Polymerization 34
2.4 Polymerization Process 37
2.4.1 Activation 37
2.4.2 Initiation 37
2.4.3 Propagation 39
2.4.4 Termination 39
2.5 Activation of Resin Materials 40
2.6 Photopolymerization 42
2.6.1 Photoinitiated Free Radical Polymerization 42
2.6.2 Photoinitiated Cationic Polymerization 43
2.6.3 Photoinitiated “Living” Polymerization 43
2.7 Photophysical Process in Photoreactions 46
2.8 Photochemical Reactions of Riboflavin 48
xiii
2.8.1 Introduction 48
2.8.2 Spectral Properties 49
2.8.3 Redox and Protolytic Equilibria 52
2.8.4 Photochemical Reactions 52
2.8.4.1 Intramolecular photoreduction 53
2.8.4.2 Intermolecular photoreduction 54
2.8.4.3 Photosensitized reactions 56
III APPLICATIONS OF LASER FLASH PHOTOLYSIS, SPECTROSCOPY AND ELECTRON MICROSCOPY IN
PHOTOPOLYMERIZATION
58
3.1 Introduction 59
3.2 Spectral and Photophysical Properties of Riboflavin 60
3.3 Applications to Polymerization of 2-Hydroxyethyl methacrylate 61
3.4 Spectroscopic Techniques 63
3.4.1 UV and Visible Spectroscopy (UV/VIS) 63
3.4.2 Transient Absorption Spectroscopy (TAS) 64
3.4.3 Infrared Spectroscopy (IR) 64
3.4.4 Fourier Transform Infrared Spectroscopy (FTIR) 66
3.4.5 Raman Spectroscopy 68
3.4.6 Nuclear Magnetic Resonance Spectroscopy (NMR) 69
3.4.7 Magic Angle Spinning Nuclear Magnetic Resonance Spectroscopy (MAS-
NMR)
70
3.4.8 Time-of-Flight Secondary Ion Mass Spectroscopy (TOF–SIMS) 71
3.4.9 Fluorimetry 71
3.4.10 Atomic Absorption Spectroscopy (AAS) 71
3.4.11 Inductively Coupled Plasma Emission Spectroscopy (ICP–ES) 72
3.4.12 X-Ray Photoelectron Spectroscopy (XPS) 72
xiv
3.5 Electron Microscopy 73
3.5.1 Scanning Electron Microscopy (SEM) 73
3.5.2 Transmission Electron Microscopy (TEM) 75
OBJECT OF PRESENT INVESTIGATION 76
IV EXPERIMENTAL WORK 80
4.1 Materials 81
4.2 Methods 84
4.2.1 Thin-Layer Chromatography (TLC) 84
4.2.2 pH Measurements 84
4.2.3 Ultraviolet and Visible Spectrophotometry 85
4.2.4 Fluorescence Spectroscopy 85
4.2.5 Light Intensity Measurement 86
4.2.5.1 Procedure 87
4.2.5.2 Calculations 89
4.2.6 Polymerization of 2-Hydroxyethyl methacrylate (HEMA) 91
4.2.6.1 Radiation source 91
4.2.6.2 Method 91
RESULTS AND DISCUSSION 93
V POLYMERIZATION OF HEMA IN AQUEOUS SOLUTION 94
5.1 Riboflavin as Photoinitiator 98
5.1.1 Spectral Characteristics of RF Solutions 98
5.1.2 Photoproducts of Riboflavin 100
5.1.3 Assay of HEMA 101
5.1.4 Kinetics of Photopolymerization of HEMA 104
5.1.5 Effect of pH 104
xv
5.1.6 Effect of Viscosity 113
5.1.7 Effect of TEOHA Concentration 116
5.1.8 Mechanism of HEMA Polymerization 116
5.2 Camphorquinone as Photoinitiator 126
5.2.1 Spectral Characteristics of CQ Solutions 126
5.2.2 Assay of HEMA 128
5.2.3 Kinetics of Polymerization 128
5.2.4 Effect of pH 138
5.2.5 Effect of Viscosity 140
5.2.6 Effect of TEOHA Concentration 140
5.2.7 Mechanism of HEMA Polymerization 149
5.3 Safranin T as Photoinitiator 151
5.3.1 Spectral Characteristics of ST Solutions 151
5.3.2 Assay of HEMA 153
5.3.3 Kinetics of Photopolymerization 153
5.3.4 Effect of pH 163
5.3.5 Effect of Viscosity 163
5.3.6 Effect of TEOHA Concentration 165
5.3.7 Mechanism of HEMA Polymerization 174
VI POLYMERIZATION OF HEMA IN NONAQUEOUS SOLUTION 176
6.1 Types of Bimolecular Reactions 177
6.2 Solvent Effect on Polymerization Reactions 179
6.3 Photoinduced Electron Transfer 181
6.3.1 Long-distance Electron Transfer 181
6.4 Photoinitiated Polymerization 182
6.5 Effect of Dielectric Constant 184
xvi
6.5.1 Riboflavin as Photoinitiator 184
6.5.2 Camphorquinone as Photoinitiator 190
6.5.3 Safranin T as Photoinitiator 194
6.6 Effect of Viscosity 197
6.6.1 Riboflavin as Photoinitiator 197
6.6.2 Camphorquinone as Photoinitiator 198
6.6.3 Safranin T as Photoinitiator 202
6.7 Spectral and Structural Characteristics of Photoinitiators 202
6.8 Mechanism of Polymerization 203
CONCLUSIONS AND SUGGESTIONS 206
REFERENCES 211
AUTHOR’S PUBLICATIONS 254
CHAPTER I
INTRODUCTION
2
1.1. Glass-Ionomer Cements
The term ‘glass-ionomer cement’ (GIC) is used for an acid-decomposable glass
and a water-soluble acid, i.e., a polyelectrolyte such as polyacrylic acid, which is set by an
acid–base or neutralization reaction. It was first reported by Wilson and Kent (1971). GICs
were developed to incorporate the favourable properties of both silicate and
polycarboxylate cements (Wilson and McLean, 1988). The concept was to produce a
cement with characteristics of both the silicate cements and the polycarboxylate cements
(ability to bond chemically with tooth structure and friendly to pulp). The zinc
polycarboxylate cement came along during sixty’s (Smith, 1968). It was the first metal
polycarboxylate cement of practical purpose to be used in dentistry. The characteristic
properties of these cements are shown in Fig.1.
These materials have proven good adhesion with enamel and dentine and are
widely used in a variety of clinical applications. The main property of the GICs is releasing
fluoride over a long period of time, along with the adhesive characteristic of these
materials; it has an aesthetic quality as well.
The synonyms used for ionomer cements are as follows:
(1) Poly (alkenoate) cement, (2) glass ionomer cement (Millett and McCabe, 1996), (3)
acronym of alumino-silicate polyacrylic acid (ASPA) (Nagaraja and Kishore, 2005).
All these cements are available as: (i) Powder/liquid in bottles, (ii) Powder/distilled water
(water settable cement), (iii) Pre-proportioned powder/liquid in capsules (McCabe and
Walls, 2008).
3
1.1.1. Composition of GICs
In the composition of powder and liquid, the powder consists of sodium
alumino silicate glass with about twenty percent calcium fluoride. The composition is
similar to that used in a silicate material but has higher alumina-silica ratio (McCabe and
Walls, 2008; McLean, and Gasser, 1985a). This increases the reactivity of the glass with the
weak poly (acrylic acid) as compared to that of the phosphoric acid used in the silicate
glasses. These glasses contain more fluoride as compared to GICs (McCabe and Walls,
2008) (Fig. 2).
The earlier liquid used in a GIC was fifty percent aqueous solution of
polyacrylic acid. The problem with this solution was that it was very viscous and had a
tendency to gel. This problem can be overcome by using copolymers instead of
homopolymers by creating the steric hindrance to stop the hydrogen bonding, or vacuum
drying the polyacrylic acid (McCabe and Walls, 2008).
In the most current cements, the liquid contains polyacrylic acid in the form of
copolymer with itaconic acid, maleic acid and tricarballylic acid by using the aqueous
solution of polymers derived from the unsaturated alpha, beta-dicarboxylic acid. These
acids have four or five carbon atoms in a liquid to form dental cement which exhibits an
excellent setting performance, good strength, good physiological compatibility and
acceptable aesthetics (Schmitt et al., 1982). The copolymer has an average molecular
weight of less than 20,000, and a solution having a viscosity of less than 50 poise (Crisp et
al., 1977). Copolymerisation of all these acids tends to increase the reactivity of the liquid,
decreases the viscosity and reduce the tendency for gelation.
4
Fig. 1. Characteristic properties of glass ionomer cements.
Fig. 2. Glass-ionomer glass powder composition.
Silicate Cement
Fluoride release
Tooth colour
Translucency
Polycarboxylate
Adhesion to tooth structure
Glass Ionomer Cement
Glass Composition
Area
SiO2
CaF3 Al2O3
5
The various types of carboxylic acid units used in GIC liquid (Wilson and
McLean, 1988) are shown in Fig. 3. Tartaric acid added to the liquid component of GIC
improves the handling characteristics, which increases the working time and shortens the
setting time (Nicholson et al., 1988).
Water is the most important constituent of the GIC liquid and is responsible for
the acid- base reaction, it is the medium for reaction and it hydrates the reaction products.
The quantity of the water present in the liquid is very critical in the composition of GICs.
Mishandling during the operating procedures may affect the properties of the cement. Too
much water results in weak cement, whereas too little water is insufficient for the setting
reaction to go to completion (Anusavice, 2003). Therefore a proper proportion of water is
required for the setting of GICs.
1.1.2. Water Settable Cement
In this form of cement the poly (acrylic acid) copolymer is freeze dried, and
mixed with the glass ionomer powder. The liquid is water or water containing tartaric acid.
When the water is mixed with powder, the poly (acrylic acid) partly goes into the solution
to form the liquid acid. Then the chemical reaction takes place as mentioned for powder and
liquid. This cement is known as water settable cement (McCabe and Walls, 2008).
1.1.3. Powder: Liquid Ratio
The powder / liquid ratio should be high in order to optimize the strength and
lower solubility of the cement. The dentists should always follow the manufacturer’s
recommended ratio for optimum performance. An increase in powder / liquid ratio leads to
6
Fig. 3. Types of carboxylic acid units used in GIC liquid.
7
an increase in stiffness of mix, setting rate, compressive strength, superficial hardness and
resistance to acid attack (Crisp et al., 1976). For restorative purpose the recommended
powder:liquid ratio is 6.8:1. At this ratio the compressive strength is 195 MPa and diametral
strength is 16.0 MPa (Billington et al., 1990). The mechanical properties of GICs are
affected as the powder: liquid ratio decreases. At the ratio of 5:1 the compressive strength
and diametral strength are around 103 MPa and 7.5 MPa, respectively (Billington et al.,
1990).
The reduced porosity levels in the cement mass and extended working and
setting time occur when the powder / liquid is used below the manufacturers’ recommended
ratio. Since it causes reduction in the cement’s load bearing capacity, it fails at lower
compressive stress levels in the posterior region of the mouth (Fleming et al., 2003).
1.1.4. Working and Setting Times
The oscillating rheometer is used to observe continuous changes in viscosity
during the setting cycle. Pearson (1991) has determined the working and setting times of
different commercially available restorative GIC as 1.5 minutes and 5-6 minutes,
respectively.
According to ISO standard (9917) the setting time of restorative cement is a
minimum of 2 minutes and maximum of 6 minutes, whereas minimum setting time for
luting cement is 2.5 minutes and maximum is 8 minutes. For lining / base cement the
minimum and maximum setting time is 2 minute and 6 minutes, respectively (McCabe and
Walls, 2008).
8
1.1.5. Variations in Basic Glass Composition
Typical glasses for cement formation are calcium alumino-silicates with
variable composition. Calcium may be replaced wholly by strontium which has a similar
ion radius (Sr2+
=1.13A°, Ca2+
= 0.99A°). Strontium has a capability to replace calcium
without disrupting the glass structure and translucency and provide greater radiopacity
(Wilson and McLean, 1988).
Barium and lanthanum can partly replace colour, they are alkaline earth metal
and have a radio-opaque property but they do not perform the same role as strontium
because of greater ionic radii (Wilson and McLean, 1988).
1.1.6. Role of Glasses in GICs
Glasses are based on SiO2 - AlO3 - CaF2- AlPO4- Na3AlF6 composition. The
ratio of AlO3 / SiO2 is 1:2 or more and fluoride content is around 23% but commercially
available glasses have more sodium and less fluoride content (Wilson and McLean, 1988;
McLean and Gasser, 1985a).
The powder used in glass ionomer cements has similar composition as that of
the dental silicate cement. Glasses contain different metals like strontium, barium and zinc.
These powders are combined and fused at high temperatures, typically in the range of 1200
to 1550° C. After fusion of the constituent materials, the molten glasses can either be
poured onto a cool metal plate and then into water, or poured directly into the water. This
will form a coarse frit which is further ground, usually by dry milling in a rotatory ball mill,
until the glass powder will pass through a 45µm sieve (for a filling purpose) or a 15µm
sieve (fine grained particles for luting cement) (Hill and Wilson, 1988).
9
The modification of the basic glasses can increase the working time and
decrease the water sensitivity by partially removing the outer surface of the glass particles
around 10-100 µm with the help of acid (Schmitt et al, 1983). The glass component has
many functions in the cement. It acts as a source of ions for the initial cross-linking
reaction, and also provides an inorganic substance such as silicate for the post-hardening
maturation process. It also controls the setting rate and assists in the development of
translucency (Wilson, 1996a).
Fluoride also plays an important role in the composition of glasses. These
powder are combined and fused (at high temperature) with the fluoride flux which is
responsible for lowering the fusion temperatures (Wilson and McLean, 1988). Fluoride also
improves the handling characteristics of the cement paste and enhances the strength of the
set cement. It also has the therapeutic effect in the mouth. However, the optimum fluoride
release level of GIC against dental caries is not yet known due to the fact that the leaching
of fluoride from glass ionomer is a complex process that is not yet well understood.
In a previous study, it has been suggested that the elution of fluoride, which is
loosely bound in the GIC, originates from the initial acid-base reaction between the glass
and the polyacid (De Maeyer et al., 1998). Fluoride facilitates a refractive index match of
the glass to the formed inorganic-organic matrix, allowing translucent cements to be
produced. Fluoride ions also help to produce an amorphous phase separation of glass-
ionomer to give a very reactive glass droplet phase and less reactive matrix phase
(Culbertson, 2001). Acid treatment can modify the properties of glasses such as the
working time. It is responsible for the removal of ions from the surface of the glass particles
10
and reduced soluble fluoride. However, the presence of mildly acidic water increases the
soluble fluoride (Williams et al., 2002).
It is thought that the droplet phase provides cations for generating the salt-
bridges between the polymeric acid chains (Fig.4). The matrix phase also acts as filler,
forming a stable interface to which the polymeric acid chains can bond (Culbertson, 2001).
The other types of glasses have developed high strength hydrolytically stable cements based
on alumino-zinc-silicate glasses (Darling and Hill, 1994). Metal powder may also be
blended with the glass particles by sintering a mixture of the glass and the precious metal at
a temperature greater than 600° C to improve the wear resistance of the glasses (McLean et
al., 1985).
1.1.7. Effect of Glass Particles Size on GICs
Different sizes of the glass particles are used according to the clinical
application but they have some effect on the setting reaction as well. The particle size for
the restorative purpose is around 50 µm in diameter, while that for the luting and lining
materials is reduced to less than 20 µm (Noort, 2002). The setting reaction will be faster by
using fine particle size because they will increase the specific surface of the glass powder
(Wilson and McLean, 1988).
1.1.8. Role of Aluminium in Glasses
The structure of the silicate glass is very difficult to decompose by acid,
because it is a highly cross linked network of connected silicon and oxygen atoms and it
does not carry the electrical charges which make it free to acid attack. Aluminium is
incorporated into silica network by replacing silicon, thus producing the negative charge on
the network, which becomes more basic and more susceptible to acid attack (Wilson and
11
Fig. 4. Possible inter- and intramolecular Ca2+
or Al3+
carboxylates (salt-bridges or
molecular structures) on cured glass-ionomer cement, where X represent
OH or F anions.
12
McLean, 1988; Griffin and Hill, 1999). It may act as either a network former or network
modifier and depends on their co-ordination. If aluminium received four-fold co-ordination
in an oxygen polyhedron it act as a network former, or it may adopt six fold co-ordinations
so as to act as a network modifier. The glass component not only acts as a source of ions for
initial crosslinking, but also provides the inorganic substance for post hardening
(Lowenstein, 1954).
1.1.9. Phases in Glass Structure
The property and behaviour of ions may be modified by change in the structure.
In spinodal type of structure with continuously interlocking phases, the calcium is more
susceptible to acid attack as compared to the other phases (Wasson and Nicholson, 1990).
The flexural strength of the cement may be increased by inducing the disperse droplet
phase.
1.1.10. Role of Liquid in GICs
The main acids used in glass ionomer cements are polymers with carboxylic
acid functional groups. The liquid is an aqueous solution of polymers and copolymers of
acrylic acid with maleic acid and itaconic acid (Crisp and Wilson, 1977). Other monomers
have been used to make copolymers with acrylic acid for experimental glass ionomer
cements, such as 3-butene-1, 2, 3-tricarboxylic acid (Wilson and Nicholson, 1993). Itaconic
acid promotes reactivity between the glass and the liquid. It also prevents gelation of the
liquid which can result from hydrogen bonding between two polyacrylic acid chains
(Wilson and Nicholson, 1993). These polyelectrolytes used in glass-ionomer cement
(Culbertson, 2001) are shown in Fig 5. Polymaleic acid is a stronger acid than polyacrylic
acid and causes the cement to harden and lose its moisture sensitivity faster. This is due to
13
Fig. 5. Polyelectrolytes used in glass-ionomer formulations.
14
the number of carboxyl (COOH) groups, more carboxyl groups lead to more rapid
crosslinking (Wilson and McLean, 1988). The polyacid is typically concentrated to the
range 40-50 % for use, it may be either in the form of aqueous solution or blended vacuum
dried with the glass powder when the system is activated by mixing with either water or an
aqueous solution of tartaric acid.
1.1.11. Role of Polymer on Setting Time
Polymers affect the setting characteristic of the cement. The proportion of the
aqueous solution is very important in the setting time. Decreasing the proportion of aqueous
polymer solution it may reduce the setting time but at the same time it enhances the
compressive strength of the set cement (Crisp and Wilson, 1977). The molecular weights of
the poly acid affects setting rate, toughness, fracture toughness, wear and erosion resistance.
The polyacid chain is very important regarding the formation of the cement, the higher the
molecular weight, the better properties achievable. However, the higher molecular weight is
not practical due to its high viscosity (Wilson et al., 1989).
1.1.12. Role of Tartaric Acid in Setting Time
Tartaric acid is an extremely important ingredient of GICs. An isomer of
tartaric acid is unique in both prolonging the working time and increasing the setting rate It
acts to extend the working time and shortens the setting time by removing the ion from the
glass particles; it then complexes with the ions, preventing them from crosslinking the
polymer chain until the chains become more linear when crosslinking can occur more
readily (Cook, 1983b; Nicholson et al., 1988). Tartaric acid modifies the setting
characteristics of glass ionomer cements. It sharpens the setting time and also increases the
compressive strength, without effecting the working time.
15
1.1.13. Setting Reaction
The setting of glass ionomer cement is complex and may vary with the
composition. On mixing the component of the cement (either aqueous solution of polymer
with the glass powder or polymer / glass powder mixed with water), hydrogen ions are
released and attack the glass particles, converting there peripheries into silica-based
hydrogels and responsible the release of silicic acid and aluminium, calcium, sodium and
fluoride ions (Anusavice, 2003).
In the second phase, these ions migrate out of the hydrogel and into the aqueous
cement phase where they precipitate out as the pH increases. The resulting calcium and
aluminium polycarboxylates ionically crosslink the polymer chains to form the basic
cement matrix (Wilson and Nicholson, 1993). Initial setting (gelation) is due to the chain
entanglement as well as weak ionic cross linking which correspond with the viscoelastic
behaviour of the freshly set cement. The final maturation increases the mechanical
properties of the cement gradually with time (Wilson and Nicholson, 1993) (Fig. 6). A
number of different factors which affect the speed of the setting reaction and the final
strength of the glass-ionomer cement (Prosser et al., 1986; Hill et al., 1989) are as follows:
• The types of polymers or copolymers used in the formulation, which also consider
the concentration of water, ratio of powder/liquid and their molecular weight.
• Type of tartaric acid, either (+)-or meso tartaric acid, which effect on their setting
time and compressive strength of the cured cement.
• The choice of the type of CaFAlSi glass powder and additives
• The ratio of the polymeric acid / CaFAlSi glass powder (Prosser et al., 1986)
16
Fig. 6. Setting reactions of glass ionomer cement.
17
1.1.14. Leaching Behaviour of Glasses During Setting Reaction
During the setting reaction of GIC, the leaching of different cations and anions
from the cements take place. Cook (1983a) showed by atomic absorption spectroscopy that
aluminium was present in the matrix during the early stage of the setting reaction by
dissolving freshly prepared cement in a 3% percent potassium hydroxide solution. It was
concluded that both calcium and aluminium ions were present in the initial setting reaction.
Another study by Wasson and Nicholson (1990) showed the release of aluminium and
calcium by washing the cement with aqueous solution of acetic acid. Following acid
washing the solutions were analysed by Inductively Coupled Plasma Optical Emission
Spectroscopy (ICP-OES). Two glasses including the single phase oxide glass (MP4) and a
complex phase separated glass (G338) were studied. Very little changes were observed in
MP4 and indicated that acid attacks uniformly at the surface of the glass. In G338 glass,
aluminium was found to be released under all condition of time of washing and acid
concentration. However, the ratio was different in Al:Ca and Ca:Si. This result showed that
acid attack occurs preferentially at calcium rich site. The same results were observed by
Barry et al. (1979). They also indicated that the acid attack was at the calcium rich site.
Another concept for setting the glass ionomer cement was the micro structural
study by Hatton and Brook (1992). In this study the set glass-ionomer cements were
sectioned with a diamond knife and examined in the transmission electron microscope by
using a probe to see the behaviour of the ions release from the core to the depleted zone and
matrix. It was found that the ions released from core into the matrix, as well as in the glass
and in ion depleted zone around the individual glass particles. The silicon and phosphorus
was present throughout the matrix as well as in the depleted zone around the individual
18
glass particles. Another study by Wilson (1996b) showed that silicate and phosphate are the
main matrix formers. Two glasses including phosphate-containing and the other phosphate-
free were used and mixed with 40% aqueous solution of acetic acid. ICP analysis showed
after several days that the phosphate-free glass gave rise to aluminium and silicon, whereas
phosphate-containing glass gave a product having phosphorus and forms a mixed silicate /
phosphate structure.
1.1.15. Structure of Set Cement
The set cement consists of agglomerates of unreacted powder particles
surrounded by silica gel embedded in an amorphous matrix of hydrated calcium and
aluminium polysalt (Anusavice, 2003).
1.1.16. Solubility and Disintegration
The initial solubility and early moisture sensitivity of GICs is very high. The
best setting condition for GIC is a high humidity environment approximately (80%), but not
wet and should not be desiccated either, otherwise the cracking or crazing occurs due to
loosely bound water. The complete setting reaction take place in 24 hrs, therefore, the
cement should be protected from saliva in the mouth during this period.
1.1.17. Adhesive Characteristics
One of the basic properties of the glass ionomer is their adhesiveness. It
provides good adhesion to enamel and dentine. The exact mechanism has not been fully
understood, there may be a chelating of carboxyl groups of the polyacid with the calcium in
the apatite of enamel and dentine. The bond to enamel is always higher than that to dentine,
probably due to the greater inorganic content of enamel (McCabe and Walls, 2008) (Fig. 7).
Shear bond strength was about 4-10 MPa to both enamel and dentine without using any
19
conditioner. This shear bond strength was increased when using the conditioner or etchant
on the tooth surface (McCabe, 1998). The glass ionomers are relatively brittle, having a
flexural strength of only 15-20 MPa whereas the tensile strength of the cement itself is only
around 12 MPa (McCabe and Walls, 2008).
Another method used by manufacturers that apply the conditioner and primer on
the enamel and dentine before the placement of restorative materials, primer has capability
to partly demineralise the tooth surface and increase the wettability to enhance the shear
bond strength around 8-24 MPa (McCabe, 1998).
1.1.18. Surface Treatment of Glass Particles and Their Effect on the Setting Reaction
Different types of treatment applied to modify the surface of the glasses include
properties such as setting and working time. One of surface treatment is to apply complex
fluoride salt like Na3AlF6 or K3AlF6 which improved the physical properties of the glass
powder and the fluidity of the mixed cement. Another method to sharpen the setting time of
GIC is to induce a surface reaction of tartaric acid with the surface of the glass particles. To
adjust the working and the setting time of the GIC can be achieved by different method.
Heat treatment is one of these; however, the disadvantage of such thermal treatment is to
prolonged the setting time as well as the working time. Snap setting of these materials is
clinically important (Gasser, 1994).
Another approach to increase the working time is washing the reactive glass
particles with an acid to reduce the reactivity of the glasses and therefore, increasing the
working time of the cement (Schmitt et al., 1983).
20
Fig. 7. One possible mechanism of bonding to tooth substance for GIC.
CO-2 CO
-2 CO
-2 CO
-2
Polyacid chain
Tooth structure
Ca2+ Ca
2+
21
This has little or no effect on the setting time. The acid washing results in a
partial leaching of the outer surface of the glass particles; therefore, it produces the delay to
start of set and controls the initial acid reactivity in order to achieve the proper setting and
working time (De Maeyer et al., 1998).
1.1.19. Participation of Glasses During Cement Formation
The composition and structure of the glasses used in GICs are very important
regarding the performance of the final set cement. Working time, initial solubility, speed of
set, strength and cariostatic properties are largely determined by the glasses used, In
addition, they control radiopacity and optical characteristics such as translucency. In the
chemical reaction of GIC the hydrogen ions are formed from the ionization of the poly
(acrylic acid) in water and formation of the silica-based hydrogels around the involved
glass particles. Calcium and Aluminium ions migrate from silica hydrogel into the aqueous
cement phase where, as the pH increases, they precipitate out as polysalts. They ionically
crosslink the polyanion chain and cause the cement to harden. During setting reaction, ions
released from the glasses and an involved in the matrix formation but it is not known how
much the particle size and weights are affected (McCabe and Walls, 2008).
1.1.20. Types of Glass Ionomer Cements
A classification of different types of GICs according to their applications is: I -
luting cements, II - restorative esthetics, III - restorative reinforced cements, IV - lining
cements (Wilson and McLean, 1988). These types are described as follows.
(i) Type 1 Luting Cements
Dental luting agents provide the link between a fixed prosthesis and the
supporting prepared tooth structure; GICs have been in use for many years for luting
purpose. Traditionally, zinc phosphate cement is still used as a luting material, despite its
22
well documented disadvantages, like solubility and lack of adhesion. GICs have some
advantages over zinc phosphate cement such as better flow and lower solubility (Pluim et
al., 1984) along with the fluoride release which helps to prevent the recurrent caries even
though this is very minimal (Scoville et al., 1990). GICs were shown to have the highest
retentive value among the luting cements (McComb, 1982; Young et al., 1985
(ii) Type II Restorative Esthetics
This is slow setting cement and needs to be more in isolation from the oral
environment for up to 24 hours in order to produce better physical properties and
translucency (Mount, 1990). Polishing and contouring of the restoration should always be
performed under air-water spray using a very fine diamond to begin with and finishing
with aluminum oxide discs (McKinney et al., 1987; Mount, 1991).
(iii) Type III Restorative Reinforced Cements
Due to the short setting time of this cement, e.g. Ketac silver, it can be
finished five minutes after the start of mix. This can be used only in areas where esthetics
is of no concern due to lack of translucency and esthetic appeal (McLean and Gasser,
1985b). This type has improved physical properties as compared to the conventional glass
ionomer cement, such as higher compressive strength, (Murray et al., 1986), higher
compressive fatigue limit (Walls et al., 1987) and better wear resistance (Moore et al.,
1985). Fracture resistance is similar to the unreinforced type (Osman et al., 1986). This
reinforced GICs have a number of clinical applications such as for cavity base, (Kanca,
1988; Scherer et al., 1990) restorations (class V, minimal class II., e.g. tunnel preparation
(McLean, 1990) and primary teeth (Croll et al.,1988; Croll, 1989, 1990), sealants, repairs
of castings (McLean, 1990) and temporary or emergency procedures (Burke, 1990). These
23
cements are commonly used for core buildups and the area where a moderate strength and
cariostatic effects are required. However, the tensile strength is not high, therefore, this
requires a considerable support from remaining tooth structure (Mount, 1991).
(iv) Type IV Lining Cements
These types of cements are used for conventional lining or as a base under
restorations and a dentin substitute (Kanca, 1988; Scherer et al., 1990; McLean et al.,
1985; Godoy et al., 1998; Holton et al., 1990). We need a low powder/liquid ratio if used
as conventional lining agent in order to make it flow easily over the pulpal floor. This type
of GIC has both the chemically and light activated forms (Tyas, 1989). The light activated
glass ionomer cements that contain polyalkenoic acid may be superior in strength to the
hand mixed cements (Tay and Lynch, 1990). Due to lack of fracture resistance, this
cement is not recommended for use in high stress bearing areas, where other restorative
materials like composite resin or dental amalgam are recommended. These are placed over
the glass ionomer cement and are responsible to bear the major stresses of the occlusal
forces (Kanca, 1988; Scherer et al., 1990; McLean et al., 1985).
1.1.21. Physical Properties of GICs
It is well known that GICs possess certain unique properties, such as direct
adhesion to the moist tooth structure and base metals due to capability of crosslinking with
calcium ions in tooth or metal ions in base metals (Wilson and Kent, 1971; Wilson and
McLean, 1988; Crisp et al., 1975; Katsuyama et al., 1993), anticariogenic properties due
to fluoride release (Wilson and Nicholson, 1993), minimized microleakage at the tooth–
enamel interface due to low shrinkage, thermal compatibility with tooth enamel and dentin
because of low coefficient of thermal expansion similar to that of the tooth structure
24
(Davidson, 1999; Mount, 1994), biologically compatible and low cytotoxic effect which
make them useful as a restorative material (McLean et al., 1994; Wilson and Kent, 1972;
Wilson, 1989). However, the problem associated with the existing conventional
formulation of GIC in which the materials set sluggishly, showed relatively prolonged
sensitivity to moisture, opacity, brittleness and low mechanical properties which make the
cement unsuitable for use in high stress bearing areas. Therefore, efforts for improvement
have been made in several ways to enhance their physical properties to overcome these
problems (Wilson and Kent, 1971; Wilson and McLean, 1988; Crisp et al., 1975;
Katsuyama et al., 1993; Wilson and Nicholson, 1993; Davidson, 1999; Mount, 1994;
McLean et al., 1994; Wilson and Kent, 1972; Wilson, 1989; Smith, 1999; Nicholson,
1998). These properties have been improved by several changes to the cement system,
either by bringing the changes in basic glass powder preparations or in the chemical
composition of polyacid which are responsible to form the organic matrix (Culbertson,
2001). Since these early materials, numerous modifications have been made to improve
their properties. They are:
(i) Different kinds of polymers, such as acrylic acid–maleic acid
(AA-MA), and acrylic acid-itaconic acid (AA-IA) as the polyacid component.
(ii) The use of dried polymer powders blended with the glass, and activated by the
addition of water (Prosser et al., 1984).
(iii) The development of cermet-containing cements, in which the filler consists of a
cermet (i.e. a ceramic-metal hybrid, in this case being calcium fluoroaluminosilicate glass
fused to silver) rather than a pure glass (McLean and Gasser, 1985b). These cermets are
used in areas where radiopacity is required, and for core build-up under crowns.
25
(iv) Metal-reinforced cements, where a metal, such as silver-tin alloy (Simmons,
1983) or stainless steel (Williams et al., 1992) is added to an otherwise conventional
glass-ionomer in an attempt to reinforce the set cement.
(v) Resin-modified cements, in which the conventional acid-base reactions are
involved with monomers and the initiator is responsible for photochemical polymerization
(Nicholson, 1998).
In order to improve toughness, speed of setting and resistance to dehydration,
hybrid types of materials were introduced in the late 1980s, in which some of the water
content was replaced by water-soluble polymers or monomer in order to achieve greater
early strength and speed up the initial set. These materials are known as resin-modified
glass-ionomer cements (RMGICs), these cement are responsible for combining the acid-
base cross-linking reaction of the metal ion-polyacid with the cross-linking polymerization
of a monomer system (Antonucci et al., 1988; Mitra, 1988). The RMGICs contain not
only the components of the glass-ionomer cement; polyacid, acid-degradable glass and
water, but also contain a water-loving monomer usually 2-hydroxyethyl methacrylate
(HEMA) along with the compatible polymerization initiators. RMGICs have two possible
setting mechanisms, the acid–base reaction of the conventional glass-ionomer cement and
a free-radical addition polymerization of the monomer. The resin-modification was
intended to provide a material with improved mechanical properties and a command cure
facility while still maintaining the clinical advantages of the conventional GICs, such as
adhesion and fluoride release offering some protection against caries. In essence, the
RMGICs are glass-ionomer cements with the incorporation of a small quantity of
monomers as well as initiators involved in the polymerization reaction (Sidhu, 2010). The
26
influence of HEMA plays a role on the optical properties of HEMA-added dental glass
ionomer (HAGI), incorporation of 30–40% HEMA is recommended when formulating
HAGI (Lim et al., 2009).
It has been shown that due to steric hindrance, a very close attachment of
carboxylic acid groups to the polymeric backbone of PAA resulted in a very rigid matrix
(Culbertson, 2001, 2006; Xie et al., 1998). Subsequently, not all the carboxylic acid
groups will convert to carboxylate groups and very little polysalt bridge (Ca+2 di- and
Al+3 tricarboxylate complexes) are formed. Recent studies have shown that this problem
may be overcome by the incorporation of different monomers, such as N-vinylpyrrolidone
(NVP), and amino acid derivatives as spacers between the carboxylic acid groups, which
is responsible to make the polymeric backbone more flexible (Culbertson, 2001; Xie et al.,
2006a, 2006b) and provide the greater chance for the acid–base reaction (allowing greater
freedom of COOH groups to react with Al and Ca ions), resulting in more complete
polysalt bridge formation by improved filler–polymer interaction. This approach was
found to improve the mechanical strength of GICs (Wilson and Kent, 1971; Wilson and
McLean, 1988; Crisp et al., 1975; Katsuyama et al., 1993; Wilson and Nicholson, 1993;
Davidson, 1999; Mount, 1994; McLean et al., 1994; Wilson and Kent, 1972; Wilson,
1989; Smith, 1999; Nicholson, 1998; Culbertson, 2001, 2006).
It has been found that amino acid polyelectrolytes are promising additives to
GIC polyacids (Culbertson, 2001, 2006; Xie et al., 1998; 2006a, 2006b). Amino acid
additives play an important role in both acid–base reactions in the cement matrix and
adhesion to the tooth structure. It has the capability to enhance the mechanical properties
and bond strength to the dentin due to the presence of amine groups and more carboxylic
27
acid groups in the structure of the final set cement. Kao et al. (1996) were the first
research group to report the use of N-acryloyl-substituted amino acid monomers and
evaluated their physical properties in the preparation of GIC. The incorporation of amino
acid in GICs is responsible to make better mechanical and working properties (Kao et al.,
1996). Wu et al. (2003) synthesized the amino acid derivatives (methacryloyl and
acryloyl) and incorporated in the formulations of conventional glass ionomers. These
amino acid modification (amino acid-modified GICs) showed higher compressive strength
(193–236 MPa) and significantly higher flexural strength (55–71 MPa) in comparison to
the commercial Fuji II glass ionomer (compressive strength 191 MPa and flexural strength
16 MPa). Xie et al. (2006a) reported that the resin-modified glass ionomer has increased
its mechanical strength by the incorporation of amino acid derivatives, in which the
compressive strength (20%), diametral tensile strength (70%) and flexural strength (93%)
(Xie et al., 2004a, 2004b). With the different molar ratios of acrylic acid (AA)–itaconic
acid (IA)–NVP polymers may be responsible to enhance their mechanical properties of the
GICs (Culbertson, 2001, 2006; Xie et al., 1998). Some other study reported that AA–MA–
NVP (MA: Maleic Acid) polymer resulted in modified GICs with higher compressive
strength and diametral tensile strength in comparison to Fuji IX commercial GIC
(Yamazaki et al., 2005).
Since the developments of GICs more than thirty years ago, these materials
have involved many different applications in clinical dentistry. The merits and demerits of
GICs system have proved by different clinical experiences. This has resulted in improved
formulations and more controlled techniques. It is difficult to produce an ideal material, but
with continuous development it may be possible.
28
1.1.22. Literature on Glass Ionomer Cements
A. Chapters
Andreasen et al. (2006), Anusavice (2003), Bhat and Nandish (2006), Cahn et
al. (1992), Eliades et al. (2003), Ferracane (2001), Ingle et al. (2008), Ireland (2006),
McCabe and Walls (2008), Nicholson (2002), O′Brien (2002), Phinney and Halstead
(2008), Power and Sakaguchi (2006), Roberson et al. (2006), Schmalz and Arenholt
(2009), Smith et al. (1996), Soratur (2002), Subbarao (2007), Van Noort (2002).
B. Books
Chuin (1983), Combe (2006), Darling (1993), Davidson (1999), Gillingham
(2004), Katsuyama et al. (1993), Kilpatrick (1993), Mount (1994), Mount (2002),
Nicholson (1991), Oen et al. (1990), Wilson and McLean (1988).
C. Reviews:
AI-Badry and Kamel (1994), Buck (2002), Cho and Cheng (1999), Croll and
Nicholson (2002), Culbertson (2001), D’Alpino et al. (2006), Kovarik et al. (2005),
Kramer and Frankenberger (2007), Millett and McCabe (1996), Nicholson (1998),
Nicholson (2007), Nicholson and Beata (2009), Ngo (2010), Rosenstiel et al. (1998),
Simonsen (1996), Walls (1986).
D. Specifications
ANSI/ADA (1989), American National Standards Institute / American Dental
Association; BSI (1981), British Standards Institution Specification; ISO (1986),
International Standards Organization; ISTC (1991), International Standard Technical
Committee.
CHAPTER II
CHEMISTRY OF
POLYMERIZATION
30
2.1. Introduction
A polymer is a long chain organic molecule that is made up of many units
(mer = unit) and the oligomer is a short polymer composed of two, three or four mer
units. When many identical, small molecules chemically react, adding together like
beads on a string, they produce a long chain of many mers, or a polymer (Ferracane,
2001; O′Brien, 2002). If the reactions occur between two different but compatible
monomers, the polymeric product is called a copolymer. This copolymer may be
either random (mers do not appear in specific order) or block (large numbers of one
type of mer appear arranged in sequence). Atoms along the length of any polymer are
joined together through strong, primary covalent bond (O′Brien, 2002). The ability to
add many different types of monomers together to make copolymers gives the
polymer chemist a tremendous ability to “tailor- make” molecules for specific
applications. For example a patient who cannot tolerate a hard denture base made
from poly(methyl methacrylate) (PMMA) requires a soft liner to be placed on the
tissue surface of the dentures. There are many rubber-like polymers compatible with
the PMMA, but they would be too flexible and have limited durability for dentures. A
copolymer can be produced, however, by having the molecules that produce the hard
denture base react with the rubbery material, resulting in the liner with properties
intermediate between the two, i.e., not too soft or too hard. Polymers of different
types are used in dentistry as denture bases and artificial teeth, denture liners or
tissues conditioners, composite restorative and pit and fissure sealants, impression
materials, custom trays for impression, temporary restoratives, mouth guards,
maxillofacial prostheses, space maintainers, veneers cements, and adhesives. They
31
can be processed in the laboratory, in the office, or in the cavity, and they can be
produced with nearly ideal esthetics (Ferracane, 2001; Van Noort, 2002; Power and
Sakaguchi, 2006).
The molecular weight of polymers plays an important role in determining its
physical properties. Chemically, polymers are long-chain molecules of very high
molecular weight. For example the hard denture base resins have been reported to
have viscosity average molecular weight ranging from 150 000 to 600 000 (Cahn et
al., 1992). However, improving the physical properties by increasing the molecular
weight which is responsible to increase the degree of polymerization until a certain
molecular weight is reached (Subbarao, 2007; Soratur, 2002). Polymers may exist in
the crystalline form or in an amorphous state. Many polymers crystallize, and the
size, shape, and organization of the crystals depend on how the polymer was
crystallized. These polymers are not wholly crystalline solids, but are composed of a
large number of small crystalline regions in close proximity to one another, in an
amorphous matrix (Van Noort, 2002). Other polymers are amorphous, often because
their chains are too irregular to permit regular packing. The onset of chain molecular
motion heralds the glass transition and softening of the polymer from the glassy
(plastic) state to the rubbery state. Mechanical behavior includes such basic aspects as
modulus, stress relaxation, and elongation to break (Sperling, 2006).
Degradation of the resin matrix material is influenced by the degree of cure.
An increased degree of cure influences degradation at the filler surface by increasing
the resin density and decreasing the diffusion rate through the matrix material. When
32
a resin composite is placed in ethanol, monomer is leached during a shorter time
interval than if it were placed in water. When monomer molecules leach into alcohol,
alcohol molecules diffuse into the resin. During this process, matrix will swell and
retain alcohol molecules within the resin network. Because of the space alcohol
molecules occupy, they will increase the distance between the polymer chains. Due to
increase in chain spacing results in weaker polar interaction between the separated
chains, which results in a softer and more wear-susceptible matrix (Eliades et al.,
2003).
2.2. Polymerization Reactions
Monomers react to forms polymers by a chemical reaction called
polymerization. Most polymerization reactions are of two types: condensation and
addition polymerization and are described as follows.
2.2.1. Condensation Polymerization
Condensation polymers are any kind of polymers formed through
a condensation reaction, releasing small molecules or low molecular weight as by-
products such as water or methanol, as opposed to addition polymers which involve
the reaction of unsaturated monomers. The type of end product resulting from a
condensation polymerization is dependent on the number of functional end groups of
the monomer which can react. Generally condensation polymers
include polyamides, polyacetals and polyesters and the most commonly known
condensation polymers are proteins, fabrics such as nylon, silk, or polyester
(Ferracane, 2001). Materials that set by the condensation mechanism use for taking
the impression of some dental prosthesis, for example, the dental crown and dental
33
bridges including polysulphide rubber and silicone rubber impression materials
(O′Brien, 2002; Anusavice, 2003; Roberson et al., 2006).
2.2.2. Addition Polymerization
Most dental resins are polymerized by a mechanism in which monomers add
sequentially to the end of a growing chain. Addition polymerization starts from an
active center, adding one monomer at time to rapidly from a chain. In theory the
chain can grow indefinitely until the entire monomer is exhausted. The process is
simple, but it is not easy to control (Anusavice, 2003). Addition reactions usually
involve monomers containing carbon–carbon double bonds (C=C). The C=C bond is
of high energy and is relatively unstable, so it reacts rather easily with other
molecules (Ferracane, 2001). The reactive species which is involved in the addition
reaction may be ionic in nature or it may be a free radical. Although most addition
polymerizations processes in dental materials may be characterized as free radicals
processes, other mechanisms involving the growth of chains through ionic species
such as anions and cations are also used. Cationic ring opening reactions involving
imine and oxirane groups may be used to produce addition polymers. This ring
opening polymerization of imines is employed in the setting of certain impression
materials whilst the ring opening polymerization of oxiranes are closely related
sioloranes and are being used in newly developed resin matrix composite materials. A
key feature of the ring opening process is that it produces a slight expansion, which
reduces the overall contraction resulting from the conversion of monomer molecules
to polymers (McCabe and Walls, 2008). Materials that sets by this reaction include
34
poly(methyl methacrylate), used in the construction of dentures, and bisphenol
glycidyl dimethacrylate (bis-GMA), a common component of the matrix of resin
composites (Cahn et al., 1992; O′Brien, 2002).
2.3. Free-radical Polymerization
Free-radical polymerization reaction usually occurs with unsaturated
molecules containing double bonds (Power and Sakaguchi, 2006). The activator can
be light, heat, or a chemical (peroxide), and all are used in dentistry (O′Brien, 2002).
The first step in the polymerization is to break down or activate the initiator and cause
it to initiate the reaction by joining with a monomer and making it reactive. When the
monomer is attacked by the initiator, the C=C double bond splits, leaving the
molecule with C-C single bond and a free, unpaired electron (Anusavice, 2003;
Power and Sakaguchi, 2006; Sperling, 2006; Ferracane, 2001). This type of reaction
begins at many sites throughout the mixture of monomers, one molecule at a time is
added and a chain rapidly builds up, which can grow almost indefinitely as long as
the supply of the building block is available, finally as fewer monomers remain and
the viscosity of the mixture increases, the reaction enters the final stage where it
stops, or terminates, by the combination of the remaining free radicals (McCabe and
Walls, 2008; Sperling, 2006).
Two more important points are always to be considered during the reaction of
addition type polymerization. First every time C=C bond is broken, heat is evolved.
Second, as each monomer reacts, the entire mass of polymer shrinks. This follows
from the facts that two molecules held together by a primary chemical bond, such as a
covalent C=C linkage, occupy less total volume than they did when they were next
35
to another is an overall shrinkage of polymers used as dental restoratives or
prosthetics devices (Ferracane, 2001; Anusavice, 2003).
Free radical polymerization reactions can be inhibited by the presence of any
material that will react with a free radical, thus decreasing the rate of initiation and
increasing the rate of termination. Decreasing the rate of initiation retards the
polymerization reaction, and increasing the rate of termination decreases the degree
of polymerization or the molecular weight of the final polymer. Such materials as
hydroquinone, eugenol, or large amounts of oxygen will inhibit or retard the
polymerization. Small amounts of hydroquinone are used to protect the
methylmethacrylate monomer from premature polymerization, which prolongs the
shelf life of the monomer (Power and Sakaguchi, 2006).
The majority of monomers which can be polymerized by a free radical
addition mechanism are of the alkenes type. That is, they contain a C=C double bond.
These monomers can be represented by the general formula and some of the familiar
monomers which can be obtained by substituting for X and Y are given in Table 1.
36
Table 1
General formula for alkene molecules which are capable of polymerizing to form
polymers. Example of some specific monomers are given as under:
X Y Monomer Polymer
H H Ethylene Polyethylene
H Cl Vinyl chloride Polyvinyl chloride
H Phenyl Styrene Polystyrene
H –CH=CH2 Butadiene Polybutadiene
H –CO2CH3 Methylacrylates Polymethylacrylate
CH3 –CO2CH3 Methylmethacrylate Polymethylmethacrylate
37
2.4. Polymerization Process
The polymerization process follows a well documented pattern which consists
of four main stages-activation, initiation, propagation and termination (Soratur, 2002;
Van Noort, 2002; Anusavice, 2003; Power and Sakaguchi, 2006; Sperling, 2006;
Subbarao, 2007; McCabe and Walls, 2008).
2.4.1. Activation
This involves the production of free radicals by decomposition of the peroxide
initiator using either thermal activation (heat), chemical activators or radiation of a
suitable wavelength if a radiation activated initiator is present. In simplified, general
terms it may be expressed as follows
2.4.2. Initiation
Initiation is a step in which free radicals, formed on activation, react with
monomer units to create the initial end of a polymer chain. This is illustrated for the
specific case of the benzoyl peroxide radical (RO .) and the methacrylates monomer
(M) (it should be pointed out that hydrogen peroxide undergoes the same reaction on
a wound, giving a burning sensation as the free radicals “kill the germs.”) (Sperling,
2006) in Fig. 8. The reaction may be given in simplified general terms as follows
38
Fig. 8. The reaction of a benzoyl peroxide radical with methylmethacrylate to
form a new species. This is the initiation reaction in free radical
polymerization of methylmethacrylate (McCabe and Walls, 2008).
39
Where the symbol M represents one molecule of the monomer. It can be seen from
the above equation and Fig 1 that the initiation reaction is an addition reaction
producing another active free radical reaction species which is capable of further
reaction.
2.4.3. Propagation
Following initiation, the new free radicals are capable of reacting with further
monomer molecules to form the growing chain. Each stage of the reaction produces a
new reactive species capable of further reaction as illustrated in the following
equation
A general equation for the propagation reaction may be written as follows
Where the value of n defines the number of monomer added and hence the length of
the chain and the molecular weight (McCabe and Walls, 2008).
2.4.4. Termination
Termination is the conclusion of the process as a result of steric hindrance,
lack of monomer molecules or other problems. Other examples of termination involve
the reaction of growing chains with molecules of initiators, dead polymer, impurity or
40
solvent, if present. One example of termination is the combination of two growing
chains to form one dead chain as follows
Light intensity plays an important role for the activation of the materials. Increased
light intensity increases the probability of effective activation whereas low light
intensity does not cause activation (Anusavice, 2003; Power and Sakaguchi, 2006;
McCabe and Walls, 2008). Activation and initiation do occur happen quickly, early
propagation rates involve 100,000 to 1 million monomer reactions per second
(Roberson et al., 2006).
2.5. Activation of Resin Materials
For the early resin composites, polymerization was initiated by the mixing of
two pastes. One paste contained an activator, such as a tertiary amine, most
commonly di-hydroxyethyl-p-toluidine (DHEPTI), which was used to split the
initiator, usually benzoyl peroxide, found in the second paste (Cahn et al., 1992). The
UV light, with a wavelength of approximately 365 nm, splits benzoin methyl ether
into free radicals, without the presence of tertiary amines, thus starting the
polymerization. In this way, only one paste of composite was necessary and
polymerization would not start until it was activated by the UV light (McCabe and
Walls, 2008). Unfortunately, there were some serious drawbacks attached to the UV
light-curing systems. Because of the spectral distribution of UV light it may cause
damage to the eye and soft tissue burns (Xu et al., 2008). The depth of cure achieved
with UV light-curing units was limited due to high light absorption in the resin
composite. However, the benefits of having one paste resin composite, which sets on
41
demand by the curing light, gave rise to the development of visible light activated
resin composites. Dart et al. (1978) at ICI in London, received a patent for the visible
light curing of resins. In modern light-cured resin composites, the most common
photoinitiator is camphorquinone (CQ). This CQ can itself photoinitiate
polymerization, however, only at a low rate. In order to accelerate the polymerization,
amines are used as coinitiators (Jakubiak et al., 2003). CQ is an α diketone that
feature is a conjugated dicarbonilic group and also sensitive to visible range of
spectrum with a wavelength in the blue range, approximately 420 to 490 nm with a
peak at 470 nm (Alvim et al., 2007). After irradiation, it works as a source of free
radicals for the curing process. The absorption of visible light by CQ raises the
molecule to an excited state, known as the “triplet-state”, with very short half-life
(Tsai and Charney, 1969). If the excited CQ interacts with an amine molecule, it
results in an excited state complex, called “exciplex” (Stansbury, 2000). In this state,
CQ can abstract a hydrogen atom from the tertiary amine, resulting in the formation
of a free Radical (Jakubiak et al., 2007; Schneider et al., 2009). CQ is a solid yellow
compound with an unbleachable chromophore group, so that large amounts of CQ in
resin formulations lead to an undesirable yellow color, affecting the final aesthetic
appearance of the cured material (Rueggeberg et al., 1997; Shin and Rawls, 2009).
The concentration of CQ photosensitizer is in the range 0.17–1.03 mass% of the resin
phase and that of dimethylaminoethyl methacrylate (DMAEMA) reducing agent is
0.86–1.39 mass% (Taira et al., 1988).
42
2.6. Photopolymerization
The formation of polymers by photoinitiated polymerization is the basis for
the majority of the commercial applications of photopolymer technology (Peiffer,
1997). Radiation curing, ultraviolet (UV) curing, light (visible) curing, laser curing
and photocuring became very attractive phenomena with the development of new
technologies in 1990s. The word “curing” refers, in this case, to the use of a luminous
“radiation as an energy source to induce the rapid conversion of specially formulated
100% liquid to solids”. Curing can also be achieved with electron beams, x-rays,
plasmas, and microwaves (Fouassier, 1995). Photoinitiated polymerization can result
in a number of different reaction schemes including free radical, cationic, and living
polymerizations (Reiser, 1989; Fouassier, 1995).
2.6.1. Photoinitiated Free Radical Polymerizations
The most common type of photoinitiated polymerization is free radical
polymerization. The basic components of this reaction usually include acrylate or
methacrylic monomers or oligomers, along with a free-radical generating
photoinitiator (Reiser, 1989; Fouassier, 1995).
The polymerization begins with the formation of a free radical species through
the absorption of light by the photoinitiators, then proceeds by a typical chain-growth
mechanism or crosslinking (Fouassier, 1995; Kindernay et al., 2002). In order to gain
a better understanding of the effect of chain-length-dependent termination and chain
transfer agents in photoinitiated polymerizations, Bowman and coworkers have
studied the photoinitiated polymerizations of 2-hydroxyethyl methacrylate (HEMA)
lightly crosslinked with diethylene glycol dimethacrylate (DEGDMA) (Hacioglua et
43
al., 2002). The photoinitiator used in the polymerization of HEMA by various
workers are listed in Table 2.
2.6.2. Photoinitiated Cationic Polymerizations
As previously mentioned, airborne free radical polymerizations can be
inhibited by the presence of oxygen. The use of cationic mechanisms circumvent this
problem since cationic photopolymerizations are insensitive to oxygen, minimal
sensitivity to water, low shrinkage during curing and dark curing behaviour (Decker
and Bendaikha, 1998; Li et al., 2010). Onium salts were generally employed as
photoinitiators for cationic polymerization (Gomez et al., 2007).
2.6.3. Photoinitiated “Living” Polymerizations
Bowman and coworkers have experimented with the living
photopolymerization of methacrylates (Kannurpatti et al., 1997; Lovell et al., 2001;
Hutchison et al., 2002). By using an iniferter such as 2,2-dimethoxy-2-
phenylacetophonone in combination with tetraethylthiuram disulfide, this group
synthesized polymers with narrow molecular weight distributions and no trapped
radicals. An iniferter is a compound that can initiate, chain transfer and terminate
radical polymerizations. The polymerization proceeds in a stepwise fashion with
reversible radical termination by tetraethylthiuram disulfide. Bowman (2008) has
photopolymerized 2-hydroxyethyl methacrylate (HEMA), diethylene glycol
dimethacrylate, and triethyleneglycol dimethacrylate using this or a similar method.
Bowman’s group has also performed living polymerizations to graft acrylic acid onto
polypropylene (PP) membranes (Ma et al., 2000).
44
Table 2
Photoinitiators used in the polymerization of 2-hydroxyethyl methacrylate (HEMA)
45
46
In biomaterial application, photoinitiated free-radical polymerization was used to
create an adhesive and an insulating material for autonomic nerve activity recording
(Toru et al., 2002).
2.7. Photophysical Processes in Photoreactions
The photophysical processes involved in photoreactions have been explained
by Moore (1996) and are expressed by an energy level diagram (Fig. 9) and through
the following equations.
A UV or visible light-induced chemical process starts with the excitation of a
molecule from their ground state (Do) to the reactive excited states, by the absorption
of photons of particular wavelengths. The molecule, Do, in the ground, upon the
absorption of radiation state is excited to a higher energy level, 1D (excited-singlet
state) (2.8). The excited-singlet state is deactivated on dissipating energy by a variety
of competing physical processes. The energy dissipation may be either by internal
conversion (1C) (2.9) (a non-radiative transition between states of like multiplicity) or
by photon emission (fluorescence) resulting in return to Do (2.10). Even if the
excitation of a molecule occurs to an excited state higher than the first, 1C will
always convert molecule to the 1D level (within picoseconds) before the occurrence
47
Fig. 9. Energy level of molecules, showing electronic transitions involving
fluorescence, phosphorescence, internal conversion (IC) and intersystem
crossing (ISC) (Moore, 1996).
48
of fluorescence. Thus the emission wavelength of fluorescence is the same,
irrespective of the wavelength of excitation. Any excess energy within a particular
electronic state is dissipated as heat on collision with the neighboring molecules. This
has been referred to as vibrational relaxation (VR). In the excited-singlet state (life-
time in nanosecond), the ionization potential of the molecule is reduced, and the
excited electron is more easily removed than it is from the ground state molecule
(2.11). This process is more likely to occur if high energy UV is used (i.e. < 300 nm)
and if the molecule is in the anionic state. Alternatively, intersystem crossing (ISC)
may occur from the excited-singlet state to a metastable excited-triplet state, 3D, in
which the electron spin is parallel (2.12). The excited-triplet state, because of its
longer life-time (microsecond to second or even longer), could diffuse to a significant
distance in fluid media and therefore has a much higher probability of interaction
with neighboring molecules. If no interaction occurs, it decays back to the ground
state by a further ISC process (2.13), or by the emission of fluorescence (2.14).
2.8. Photochemical Reactions of Riboflavin
2.8.1. Introduction
In view of the importance of riboflavin (vitamin B2) (1) as a photoinitiator in
the polymerization of acrylamide (Oster et al., 1957) and 2-hydroxyethylmeth-
acrylate (Bertolotti et al., 1999; Orellana et al., 1999; Encinas et al., 2001; Encinas
and Previtali, 2006), and its high photosensitivity to visible light, it is necessary to
consider the photochemical reactions of riboflavin. The photochemistry of riboflavin
has been reviewed by a number of workers (Oster et al., 1962; Holmstrom, 1964a;
Penzer, 1970; Penzer and Radda, 1967, 1971; Song, 1971; Hemmerich, 1976; Muller,
49
1981; Heelis, 1982, 1991; Fasihullah, 1988; Tollin, 1995; Ahmad and Vaid, 2006;
Ahmed, 2009; Ahmad et al., 2010a; Encinas and Previtali, 2006; Silva and Edwards,
2006; Silva and Quina, 2006; Garcia et al., 2006).
2.8.2. Spectral Properties
Riboflavin exhibits absorption in the ultraviolet and visible region with
maxima at 223, 267 (Є 32500 M−1
cm−1
), 374 (Є 10600 M−1
cm−1
) and 444 nm (Є
12500 M−1
cm−1
) in aqueous solution (British Pharmacopoeia, 2009; Du et al., 1998;
Dawson et al., 1986). The molar absorptivity of riboflavin at the maxima are greater
than 104 M
−1 cm
−1 indicating the π-π* electronic transition. The positions of the
absorption maxima and the molar absorptivities of flavin chromophore are influenced
by the solvent and pH (Ahmad et al., 2004b, 2006b; Ahmad and Vaid, 2006).
Riboflavin gives an intense yellow green fluorescence at 520 nm in aqueous solution
(Weber, 1950). The fluorescence of riboflavin is due to the neutral form of the
molecule where as the ionized forms (cation and anion) are non-fluorescent (Drossler
et al., 2002). The quantum yield of riboflavin is affected by the polarity of the
medium, e.g., 0.26 (water), 0.30 (ethanol), 0.36 (pyridine) (Koziol, 1966a).
Riboflavin is highly photolabile is less polar solvents (Koziol, 1966b). The
spectroscopic and photophysical properties of riboflavin and analogues in aqueous
and organic solvents have been reviewed by Muller (1981), Heelis (1991) and Ahmad
and Vaid (2006). The spectroscopic properties of the excited singlet-state and excited-
triplet state are given in Table 3 and 4, respectively.
50
Table 3
Spectroscopic and photophysical properties of the excited-singlet state of selected flavins*.
51
Table 4
Spectroscopic and photophysical properties of the excited-triplet state of lumiflavin
and lumichromes*.
52
2.8.3. Redox and Protolytic Equilibria
The redox and protolytic equilibria of the ground and excited states of flavins
(Muller, 1983) are as follows.
Thus the flavin can exist in the cationic, neutral and anionic forms in the ground and
excited states and can undergo one and two electron reductions in the ionized forms.
2.8.4. Photochemical Reactions
Riboflavin is highly photosensitive and is degraded by several photochemical
reactions including intramolecular photoreduction and Intramolecular photoaddition
(Heelis, 1981, 1991; Ahmad and Vaid, 2006). The nature and rates of these reactions
is affected by factors such as pH of the medium (Cairns and Metzler, 1971; Schuman
53
Jorns et al., 1975; Ahmad and Rapson, 1990; Ahmad et al., 2004a; Hozler et
al.,2005), polarity of the medium (Song, 1971; Moore and Ireton, 1977; Schmidt,
1982; Ahmad and Tollin, 1981a; Ahmad et al., 2006b), buffer type and concentration
(Holmstrom and Oster, 1961; Holmstrom 1964b; Schuman Jorns et al., 1975; Ahmad
et al 2004a, 2005, 2008, 2010b), ionic strength (Sato et al., 1984), oxygen content
(Treadwell et al., 1968; Schuman Jorns et al., 1975; Ahmad et al., 2004b),
complexation (Ahmad et al., 2008; 2009) and light intensity and wavelengths (Sato et
al., 1982; Ahmad and Rapson, 1990; Ahmad et al., 2006a). The photolysis of
riboflavin is mediated by both excited-singlet and excited-triplet states and occurs
through several pathways (Song, 1971; Cairns and Metzler, 1971; Schuman Jorns et
al., 1975; Ahmad and Tollin, 1981b; Ahmad and Vaid, 2006). The life-time of the
flavin excited-singlet (1Fl) is approximately 5 ns (Wahl et al., 1974) and that of the
flavin excited-triplet state (3Fl) is 1 ns (Namen and Tegner, 1986). The
Intramolecular and intermolecular photoreduction of riboflavin or other flavins is of
interest in the present studies.
2.8.4.1. Intramolecular photoreduction
This is the normal pathway of riboflavin photolysis in aqueous and organic
solvents. It has been suggested that the intramolecular photoreduction occurs through
dehydrogenation of the N(10)-ribityl side chain in the excited state to give ketonic or
aldehydic functions and simultaneous reduction of the flavin (isoalloxazine) ring.
This is followed by the oxidation of the side-chain to give formylmethylflavin (2).
This compound is an intermediate in the photolysis sequence of riboflavin (Moore et
al., 1963; Smith and Metzler, 1963; Cairns and Metzler, 1971; Ahmad and Vaid,
54
2006; Ahmad et al., 2006b) and is reported to hydrolyse to lumichrome (3) and
lumiflavin (4) (Song et al., 1965; Ahmad et al., 1980; 2006a;) and is oxidized to
carboxymethylflavin (5), (Fukumachi and Sakurai 1954; Treadwell et al., 1968;
Ahmad et al., 2006b). The chemical structures of riboflavin and photoproducts are
shown in Fig.10. The primary process involved in the photolysis of riboflavin
requires the abstraction of a hydrogen atom from the α-CH group of the ribityl side-
chain to give a biradical intermediate (Heelis, 1991) that disproportinates leading to
the formation of the reduced 2′-keto flavin. This is oxidized to give
formylmethylflavin or similar compounds (Fig.10).
2.8.4.2. Intermolecular photoreduction
The biological oxidation-reduction reactions of riboflavin occur through
participation of certain enzymes including FMN and FAD, the prosthetic group of
which is riboflavin. The intermolecular photoreduction of flavins involves the
addition of two electrons from external donors to give a fully reduced flavin (6)
A number of compounds such as amino acids, thiols and aldehydes are known as
electron donors in these reactions. Molecular oxygen can oxidize the reduced flavins
back to the oxidized form under favourable conditions (Heelis, 1982, 1991).
• The intermolecular photoreduction of flavins occurs through a one-electron
transfer from a donor to the flavin triplet state (3Fl) to produce a semiquinone
radical (FlH) followed by dismutation of the radical to form the fully reduced
flavin.
55
Riboflavin (1) Formylmethylflavin (2)
Lumichrome (3) Lumiflavin (4)
Carboxymethylflavin (5) 1,5- Dihydroflavin (6)
Fig. 10. Chemical structure of riboflavin and photoproducts.
56
The technique of laser flash photolysis has been used to understand the mechanism of
intermolecular electron transfer reactions involving flavins (Tollin, 1995).
2.8.4.3. Photosensitized reactions
Photosensitization is a process by which a photophysical alteration occurs in
one molecular entity as a result of initial absorption of radiation by another molecular
entity called a photosensitizer. In the presence of air and light riboflavin can initiate
photosensitized reactions involving a number of electron donors (substrates) (Heelis,
1991; Silva and Edwards, 1996; Ahmad and Vaid, 2006; Encinas and Pervitali, 2006;
Silva and Quina, 2006; Garcia et al., 2006; Rivlin, 2007). The photosensitized
oxidation reactions involve Type I or Type II, mechanisms (Taylor and Radda, 1971;
Silva et al., 1994; Karlsen, 1996).
In Type I mechanism, the substrate reacts with the sensitizer excited state
(either singlet or triplet) to give radicals or radical ions, respectively, by hydrogen
atom abstraction or electron transfer to oxygenated products. In Type II mechanism,
the excited sensitizer reacts with triplet oxygen (3O ) to form singlet molecular oxygen
(1O ) which then reacts with substrate to form the products (Tonnesen, 1996). The
type I and type II mechanisms of the photosensitized oxidation reactions (Silva and
Quina, 2006) may be expressed as follows.
2
2
57
Type I mechanism (in presence of low oxygen concentration)
Type II mechanism (in presence of high oxygen concentration)
RF, 1RF and
3RF represent riboflavin in the ground state, singlet state and triplet state,
respectively, RF•−
, RFH• and RFH2 are the radical anion, the semiquinone radical and
the reduced form of riboflavin; SH is the reduced substrate and SH•+
, S• and
1O2 are
the radical cation, the radical and singlet oxygen, respectively.
The riboflavin-senstized photoreactions include photooxidation,
photodecarboxylation, photoisomerization, photomonomerization,
photopolymerization, photodegradation, photoinitiation, photoinactivation,
photoinduction and photomodification (Ahmad and Vaid, 2006; Silva and Quina,
2006; Garcia et al., 2006; Encinas and Pervitali, 2006; Ahmed, 2009).
CHAPTER III
APPLICATIONS OF LASER
FLASH PHOTOLYSIS,
SPECTROSCOPY AND
ELECTRON MICROSCOPY IN
PHOTOPOLYMERIZATION
59
3.1. Introduction
The glass ionomer cement (GIC) or glass polyalkenoate cement (GPC) was
developed by Wilson and Kent (1971, 1972) and is used in dentistry as restorative
material. It is also used as an adhesive, fissure sealant and tooth filling material. GIC
is formed by the acid-base reaction of an ion leachable fluoro-alumino-silicate glass
with an acidic polyelectrolyte usually poly (acrylic acid) (Wilson, 1978; Zainuddin et
al., 2008). The setting reaction of the GICs involves gelation of the polyacid by cross-
linking of the carboxyl groups with cations liberated from the glass to form a polysalt
matrix (Crisp and Wilson, 1974a, 1974b; Crisp et al., 1974). In addition to this, the
setting mechanism in the resin-modified glass ionomer cements (RMGICs) involves a
free-radical polymerization reaction leading to the formation of a polymer network
(Wilson, 1990). The photoinitiated polymerization of vinyl monomers such as
hydroxyethyl methacrylate (HEMA) by riboflavin (RF) has been studied by laser
flash photolysis and transient absorption spectroscopy. The object of this study is to
highlight the applications of: 1) laser flash photolysis in the photoinitiated
polymerization processes of GICs; 2) spectroscopic techniques in the structural
characterization of GICs components; and 3) electron microscopy in the study of
surface properties of GICs.
The photoinitiated polymerization of vinyl monomers has been the subject of
extensive study over the past fifty years (Oster and Yang, 1968; Slifkin, 1971; Eaton,
1986; Paczrkowski et al., 1999) and the application of laser flash photolysis has
facilitated the understanding of the excited state interactions of photoinitiators and the
monomers (Previtali et al., 1994; Bertolotti et al., 1999; Encinas and Previtali, 2006)
60
leading to the polymerization process. RF has widely been used as a photoinitiator in
vinyl polymerization and its photochemistry has been reviewed by many workers
(Penzer and Radda, 1971; Song, 1971; Hemmerich, 1976; Muller, 1981; Heelis, 1982,
1991; Tollin, 1995; Holzer et al., 2005; Ahmad and Vaid, 2006).
The earlier applications of laser flash photolysis to flavin photochemistry has
played a significant role in the understanding of the flavin-mediated electron transfer
reactions (Schreider et al., 1975; Heelis, et al., 1980, 1981, 1985; Ahmad and Tollin,
1981a, 1981b; Ahmad and Vaid, 2006; Ahmad et al., 1981, 1982; Traber et al., 1981;
Karen et al., 1983; Hazzard et al., 1987; Tollin, 1995; Tollin, et al., 1993). Further
studies have been carried out on the photoinitiated free radical polymerization
electron-transfer reactions (Seigalski and Paczkowski, 2005), excited state interaction
of flavins with amines (Encinas and Previtali, 2006), and fluorescence quenching
mechanisms of flavins (Karen et al., 1983). These electron transfer reactions
constitute the basis of photoinitiated polymerization processes involved in GICs.
3.2. Spectral and Photophysical Properties of Riboflavin
In view of the importance of RF as a major photoinitiator in polymerization
processes of GICs, a knowledge of the spectral and photophysical properties of RF is
necessary for the understanding of laser flash photolysis studies. The UV and visible
absorption spectra of RF in aqueous and organic solvents have been reported by
Koziol (1966a), Heelis (1982, 1991), Ahmad and Rapson (1990), Du et al. (1998),
Sikorska et al. (2005) and Ahmad et al. (2006a). It exhibits peaks around 220, 265,
375 and 445 nm in aqueous solution and all the absorption maxima possess high
molar absorptivities (>104 M
–1 cm
–1), corresponding to π–π* transitions. RF emits an
61
intense yellow-green fluorescence at 520–530 nm in aqueous and organic solvents
with a quantum yield of 0.26–0.30. The cationic and anionic forms of the molecule
are non-fluorescent (Sun et al., 1972; Heelis, 1982; Visser and Muller, 1979; Drossler
et al., 2002).
3.3. Applications to Polymerization of 2-Hydroxyethyl methacrylate
Laser flash photolysis has been applied to study the polymerization of 2-
hydroxyethyl methacrylate (HEMA) in a methanolic solution using safranin T as the
photoinitiator in the presence of tertiary aliphatic amines. The polymerization rate is
increased with the amine concentration to a maximum and then decreased slowly.
Safranin T in the presence of amines yields the triplet species 3SH
+, 3
S+ and the
unprotonated semireduced radical, SH•. The polymerization involves the interaction
of the excited triplet state of safranin with the added amine (Previtali et al., 1994).
A detailed investigation of the polymerization of HEMA in methanol,
photoinitiated by riboflavin in the presence of triethanolamine (TEOHA), has been
conducted by laser flash photolysis (Bertolotti et al., 1999). The transient absorption
spectrum of photolysed solutions is ascribed to the triplet–triplet absorption of RF.
The triplet decay is accompanied by the appearance of a long-lived absorption band
in the 500–600 nm region due to the formation of the semireduced RF radical and is
shortened at 670 nm in the presence of TEOHA. The results indicated that the triplet
quenching by TEOHA (bimolecular quenching rate constant 8 × 108
M–1
s–1
) is due to
the electron transfer from the amine to the triplet of RF with the formation of
semireduced flavin (RF•−
) and semioxidised amine (Am•+
). The protonation of the RF
62
radical anion by proton transfer from the amine radical cation produces the RF neutral
radical.
3RF + Am → (RF
• − + Am
• +) → RF H• + Am (−H)• (3.1)
The interaction of triplet excited state of RF with the amine results in the
polymerization of HEMA. In the light of the previous work and further studies a
photoinitiation mechanism of HEMA polymerization by RF/ TEOHA in aqueous
solution has been proposed (Orellana et al., 1999). It has been suggested that the free
radicals produced in the photoinduced electron transfer from TEOHA to excited RF
lead to the polymerization of HEMA. The polymerization rates increase with the
amine concentration and are maximum at an amine concentration of 0.01 M. Based
on the time-resolved photolysis studies a scheme of the photochemical behavior RF in
the presence of amine (Am) and monomer (HEMA) in aqueous solution at pH 9 has
been presented (Orellana et al., 1999). It has been proposed that the interaction
between the RF triplet state and HEMA does not lead to polymerization. The process
involves RF triplet quenching by the amine to produce radicals initiating the
polymerization reaction.
The RF initiated photopolymerization rates of HEMA have been determined
using amines of different chemical structure as co-initiators (Encinas et al., 2001).
The results have been explained in terms of the dependence of the production of
amine radicals and their reactivity towards the monomer double bonds with the
structural features of the amines. Photochemical studies of 4-2 (2-hydroxy-3-
trimethylammoniumpropoxy) thioxanthone (TXA) in water (pH 9.5) using laser flash
63
photolysis indicated the dependence of the polymerization rate of HEMA on the
amine concentration. This has been explained in term of the interaction of the excited
state of TXA with the amine in different media. The excited singlet and triplet states
are quenched by electron transfer from the amine to TXA forming a charge transfer
intermediate. This is followed by rapid proton transfer from the amine radical cation
to the TXA radical anion to give the ketyl and amine neutral radicals:
TXA* + Am → (TXA
• − + Am
• +) → TXAH• + Am (−H)• (3.2)
↓
TXA + Am
The amine radical [Am (−H)•] originating from the interaction between TXA
triplet state and the co-initiator is involved in the initiation of the polymerization of
vinyls monomers (Valdebenito and Encinas, 2003).
3.4. Spectroscopic Techniques
3.4.1. UV and Visible Spectroscopy (UV/VIS)
The UV and visible absorption characteristics of RF have been reviewed in
Section 3.2. Spectral changes occurring in the UV and visible region on the
photolysis of aqueous solutions of RF (Ahmad and Vaid, 2006; Ahmad et al., 2004a,
2008; Holzer et al., 2005) and formylmethylflavin (Ahmad et al., 1980, 2006b) have
been studied. Variations in the UV and visible spectra of lumichrome in the presence
of various concentration of butylamine (Encinas et al., 2002), of 2-hydroxyethyl
methacrylate (HEMA) / hydroxytelechelic polybutadiene (HTBP) / 2,2-dimethyl-2-
hydroxyacetophenone (Darocur 1173) mixture (Desilles et al., 2005) and of the
absorption coefficient of a dental resin as a function of wavelength at different
64
illumination times (Chen et al., 2007) have been reported. The visible absorption
spectra of methylene blue and thionine in aqueous solutions and in poly-2-
hydroxyethyl methacrylate hydrogel (PHEMA) matrix in the presence of surfactant
(SDS and TAB) have been studied (Ghanadzadeh Gilani et al., 2008).
3.4.2. Transient Absorption Spectroscopy (TAS)
Several studies have been reported on transient absorption measurement in the
UV and visible region on the excited state interactions of flavins in the initiation of
vinyl polymerization (Encinas and Previtali, 2006). The technique has been useful in
the identification of the excited state species and in the understanding of their role in
the mechanism of the reaction.
The measurements of transient absorption spectra of excited state species
include those of the monoprotonated safranin triplet state, 3SH
+ (λmax 830 nm),
unprotonated safranin triplet state, 3S (λmax 420 nm) (Previtali et al., 1994), riboflavin
triplet state, 3RF (λmax 670 nm), semireduced riboflavin radical, RFH•
(λ max 500–
600 nm) (Bertolotti et al., 1999), lumichrome triplet state, 3LC (λmax 370 nm),
semireduced lumichrome radical, LCH• (λmax 450 nm) (Encinas et al., 2002) and 4-(2-
hydroxy-3-trimethylammoniumpropoxy)thioxanthane triplet state, 3TXA (λmax 580
nm) (Valdebenito and Encinas, 2003).
3.4.3. Infrared Spectroscopy (IR)
The application of IR spectroscopy in the study of the acid-base reaction in
GICs is of qualitative nature. IR has been used to study the interaction between
cations and carboxylate groups in various media. The IR spectra exhibit C=O peak at
1700 cm–1
as a result of the acid neutralization (Crisp et al., 1974). An IR
65
spectroscopic study of the formation of cements between metal oxides and aqueous
solutions of poly (acrylic acid) indicates that oxides of divalent metals form cement
gels more readily than the oxides of trivalent metals. Structural information can be
obtained from the observed frequency shift of the absorption band of the carboxylate
groups (~1700 cm–1
) in the metal poly (acrylate) gel relative to those of the purely
ionic form (Crisp et al., 1976). The IR spectra during hardening of GICs show a shift
of the characteristic band of the silicate network (1000 cm–1
) towards high frequency,
with time (Matsuya et al., 1996).
The setting of a hybrid cement composed of ethyl cyanoacrylate and a glass
ionomer cement (ECGIC) has been studied by mid-IR spectroscopy. In the spectrum
of ECGIC, both the acid-base reaction (of the GIC components) and the
cyanoacrylate polymerization have been identified by their characteristic peaks. The
spectrum indicates that the cyanoacrylate polymerization is complete within 6–7 min,
while the acid-base reaction continues 45 min after mixing. IR spectroscopy is
particularly valuable in the development of dental materials, where correct setting is
of fundamental importance to achieve the desired mechanical properties (Tomlinson
et al., 2007). The photoinduced polymerization of poly (ethylene glycol)
dimethacrylate and poly (ethylene glycol) monomethacrylate in imidazolium-based
ionic liquids (ILS) has been studied by IR. An interaction between the monomer
carbonyl group and C2–H of the imidazolium ring is indicated by a shift of the IR
absorption peaks of the two groups. The relative strength of polar interactions
depends on the position of the C=O absorption. The polymerization rates are directly
66
related to the magnitude of the monomer/IL interaction (Andrezejewska et al., 2009;
Woecht et al., 2008).
3.4.4. Fourier Transform Infrared Spectroscopy (FTIR)
FTIR spectroscopy has been used to study the role of certain ingredients in the
setting of GICs. It has been confirmed that (+)-tartaric acid incorporated into GICs to
control the setting characteristics, reacts more readily with the glass than poly(acrylic
acid), resulting in the delay of the setting of the cement. (+)-Tartaric acid not only
reacts rapidly to yield calcium tartrate (1385 cm–1
), but also enhances the rate of
formation of aluminum polyacrylate (1600 and 1460 cm–1
) within the cement. FTIR
is capable of showing distinct differences between the rates at which the various
bands appear in different formulations, of demonstrating the relative ease of tartrate
formation, and of showing the corresponding suppression of polyacrylate formation
(Nicholson et al., 1988).
A FTIR study on the free radical setting mechanism of resin modified GICs
(RMGICs) has shown that the curing efficiency is reduced in commercial products
immediately after irradiation. Non-irradiated specimens after the dark storage
demonstrated higher carboxylate yields compared to their irradiated analogs.
Photopolymerization seems to greatly reduce the acid-base reaction during the early
setting stages of RMGICs (Kakaboura et al., 1996). FTIR and Raman studies indicate
different peak shifts for the polyacid neutralization and polymerization reactions
(Wan et al., 1999). The physical and chemical changes of aesthetic restorative
materials in artificial saliva have been investigated using FTIR spectroscopy. The
spectra show major chemical changes in a GIC in P–NH2 group bonding (900–1000
67
cm–1
) which may be responsible for increase in microhardness after immersion in the
artificial saliva solution. A direct correlation between the surface roughness and
spectral changes of the tested material has not been observed (Yip and To, 2005).
These authors have summarized the FTIR studies of the reaction mechanism and
chemical changes of GICs conducted by Lee et al. (1995a, 1995b), Papagiannoulis et
al. (1997), Eliades et al. (1998) and DeMaeyer et al. (2002). FTIR spectroscopy has
been applied to the structural study of ethylhydroxymethylacrylate (EHMA), an
isomeric analogue of HEMA (Antonucci et al., 2000) and to determine the effect of
water on the polymerization of HEMA (Jafarzada Kashi et al., 2007). The degree of
conversion of HEMA is decreased by increasing the water content in HEMA solution.
A new diamond attenuated total reflectance Fourier transform infrared (ATR FTIR)
method has been developed to quantify the process taking place in a RMGIC at 1 mm
depth from the cement/water interface. Various spectral changes have been observed
due to 90% polymerization within 1 min after 20 s exposure to a dental light. On the
completion of polymerization further IR peak shifts (1300 and 1322 cm–1
), with time,
are observed. A comparison of the spectral changes in RMGIC during setting with
those of the conventional GIC indicates that these could be assigned to water sorption
and / or polyacid neutralization. Such behavior suggests two separate diffusion
mechanism for acid neutralization (Young, 2002). The technique has been used to
quantify polyacid neutralization and light-catalyzed polymerization rates in various
GICs, RMGICs and compomers. At 150 s after light exposure, levels of methacrylate
polymerization (1730 cm–1
) on the lower surface of 1 mm thick specimens are 97–
98% for the GICs and RMGICs and 47% for the compomers. After light exposure,
68
polymerization rates for compomers decrease linearly with inverse time. Reaction
mechanisms have been discussed and used to interpret the mechanical properties,
fluoride release and adhesion to tooth structure (Young et al., 2004). FTIR data
confirm that RMGIC Vitrebond (VB) exhibits the carboxylate cross linking reactions
of a true glass ionomer (Mitra et al., 2009).
3.4.5. Raman Spectroscopy
The Raman spectrum of poly (acrylic acid) and the various peak assignments
have been reported by Dong et al. (1997). Raman spectra of various combinations of
GIC components have been compared with those of the reactants and the salts of poly
(acrylic) and tartaric acids. The components consisted of a fast-setting acid-
degradable dental glass, poly (acrylic acid) and /or tartaric acid. The spectra obtained
on the addition of water to the glass and tartaric acid indicates the loss of acid and
formation of tartarates within a few seconds of mixing. After about 1 h, Raman peaks
associated with the ionized species disappear. Raman spectra show changes during
the reaction between a very fast setting fluoro-alumino-silicate glass, poly (acrylic
acid), tartaric acid and water at various acid and water ratios (Young et al., 2000).
The degree of polymerization of HEMA in the presence of camphorquinone as
photoinitiator has been measured using micro-Raman spectroscopy (Wang et al.,
2006).
Raman spectroscopic methods have been developed for characterizing the
rates of both the polyacid glass (GIC) reaction and the light-catalyzed polymerization
process in hybrid materials. These methods have been applied to commercial
RMGICs and the acid modified composite (compomer). Several Raman and FTIR
69
peaks have been identified that can be used to quantify any polymerization process.
The C=C stretching peak at1634 cm–1
of the methylacrylate group is one of the most
intense in the Raman spectra. It is well removed from any other intense peak in
RMGI and its height can be used for quantitative analysis. It has been observed that
after 20 s of cure this peak height is 10% of that observed before cure. Raman
scattering intensity is generally proportioned to the concentration (Young et al.,
2009).
3.4.6. Nuclear Magnetic Resonance Spectroscopy (NMR)
The structural changes during hardening of GICs and the role of the silica
phase in the hardening of the cement have been investigated by the application of
solid state NMR spectroscopy. The 27
Al NMR analysis of the cement samples after
the comprehensive strength measurements shows that Al3+
ion is tetrahedrally
coordinated by oxygen in the original glass but a part of the Al3+
ion is octahedrally
coordinated after hardening to form Al polyacrylate gel. The chemical shift of Si in
the 29
Si NMR spectra also changes during hardening. The variation in the chemical
shift indicates the structural changes in the silicate network (Matsuya et al., 1996).
The quantitation of five-and six-coordinated Al3+
ions in aluminosilicate and fluoride-
containing glass has been achieved by high field, high resolution 27
Al NMR (Stebbins
et al., 2000). NMR has also been used to study the setting mechanisms of GICs
(Maeda et al., 1993; Pires et al., 2004). The polymerization efficacy of self-etching
dental adhesives in different solvent evaporation conditions have been studied by
NMR spectroscopy. Temperature increase after the photopolymerization reaction is
dominant towards the effect of the drying step for solvent evaporation. Attempts to
70
remove the solvents did not increase the extent of polymerization (Numes et al.,
2006).
3.4.7. Magic Angle Spinning Nuclear Magnetic Resonance Spectroscopy (MAS–
NMR)
MAS–NMR has been used for the structural characterization of various GICs.
The 29
Si NMR spectra are consistent with Q4 (3Al) and Q
4 (4Al) units being present
and agree with the low non-bridging oxygen contents. The 27
Al NMR spectra
typically exhibit three distinct sites at 45-60, 20 and 0 ppm, attributed to Al (IV), Al
(V) and Al (VI) coordinate aluminium.
The 31
P NMR spectra show a chemical shift between –8 and –23 ppm
indicating a PO4 tetrahydra surrounded by 1–4 Al moieties. The 19
F NMR spectra
indicate the presence of Al-F-Ca (n) and Al-F-Sr (n) in different glasses. A peak
corresponding to Al-F-Na (n) is present in all glasses. The intensity of the peak is
approximately proportional to the sodium content (Stamboulis et al., 2004). Similar
studies on the structural characterization of fluorine containing glass by 19
F, 27
Al,
27Al,
29Si and
31P MAS–NMR have been reported (Kiczenski et al., 2004; Stamboulis
et al., 2005; Matsuya et al., 2007).
A 27
Al MAS–NMR study on the setting reaction of GIC has clearly shown the
formation of six coordinate, aluminium Al (VI) cross-linking to carboxyl groups in
the poly(acrylic acid). It has been found that the composition of original glass exerts a
substantial effect on the setting behaviour of the cements and the presence of
phosphorus has a strong influence in the setting reaction (Zainuddin et al., 2008).
71
3.4.8. Time-of-Flight Secondary Ion Mass Spectroscopy (TOF–SIMS)
An application of TOF–SIMS to the study of the adsorption of monomers to
hydroxyapatite (HA) has been reported (Smith, 1998). The technique indicates that
increased hydrophobicity and reduced chain flexibility and mobility in functional
monomers and polymers reduce intrinsic bonding to HA on adsorption.
3.4.9. Fluorimetry
The fluorescence decay profiles of RF in HEMA / water (1:2), water, pH 9
(λex 440 nm, λem 525 nm) (Orellana et al., 1999) and in HEMA / methanol in the
absence and presence of triethylamine (TEA) (Encinas et al., 2001) and of TXA in
water pH 9.5, HEMA / water (1:4), HEMA / acetonitride (1:1) (λex 382–392 nm, λem
382–472 nm) (Valdebenito and Encinas, 2003) have been determined. Stern-Volmer
plot for the fluorescence quenching of lumichrome singlet state (1LC) (λex 450 nm,
λem 550 nm) (Encinas et al., 2002), and Rehm-Weller plot for the quenching of the
fluorescence of neutral red and thionine dyes (Buchwieser et al., 1991) have been
reported. The fluorescence quantum yield of riboflavin in neutral water (pH 7) is ≈
0.26. The cationic form (pH –1.09) is non-fluorescent and the quantum yield of the
anionic form (pH 13.35) is ≈ 0.001155 (Drossler et al., 2002).
3.4.10. Atomic Absorption Spectroscopy (AAS)
AAS has been used to determine the elements involved in the setting process
of GICs. In freshly prepared cements (dissolved in 3% potassium hydroxide solution),
the sequence of release of elements shows aluminium to be the first in the setting
matrix (Cook, 1983a). The analysis of different cations such as potassium and
72
rubidium on their interaction with GICs and uptake from aqueous solution has been
carried out by this technique (Hadley et al., 2001).
3.4.11. Inductively Coupled Plasma Emission Spectroscopy (ICP–ES)
In a comparative study of the composition of mineral trioxide aggregate
(MTA) and Portland cement, ICP–ES has been used to evaluate the chemical
elements present. The results show similarities between the materials, except that
there is no detectable quantity of bismuth in Portland cement. It has been concluded
that there is no significant difference between the other elements in both Portland and
MTA and Portland cement may be used as an option to MTA in dental practice
(Funteas et al., 2003). ES has been used to study the conventional RMGICs by
monitoring the peak intensities of chromium ions in the aluminium oxide matrix as a
function of the reaction time (due to poly-salt formation). Emission spectra have been
used to compare the different setting reactions with and without light irradiation. The
differences of the setting reactions are based on the formation of the polymer network
due to light–induced polymerization (Jin, 2000).
3.4.12. X-Ray Photoelectron Spectroscopy (XPS)
In spectroscopic studies of the stability of the chemisorption of monomers on
clean sintered hydroxyapatite (HA) surfaces, the C peaks in the energy spectrum of
HA shows evidence of C–H bonding at 285 eV together with several minor peaks for
oxygenated components indicative of the ubiquitous presence of C contaminants. A
characteristic peak for –COOH group (209 eV) was present in another specimen
having a layer of poly (acrylic acid) adsorbed from solution and dried. XPS shows
that considerable amounts of poly (acrylic acid) remain adsorbed to HA even after
73
boiling the HA specimens in water for 2 h (Smith, 1998). On the basis of XPS of a
self-cured GIC, it has been proposed that an ion exchange layer is formed by the
reciprocal diffusion of the different elements forming the GIC and dentine, with the
exception of collagen (Tanumiharaja et al., 2001). XPS studies have shown that the
methacrylated copolyalkenoic acid component present in RMGIC VB and VBP are
chemically bonded to the calcium in HA (Mitra et al., 2009).
3.5. Electron Microscopy
3.5.1. Scanning Electron Microscopy (SEM)
A detailed study of the working and setting times of GICs after mixing by the
measurement of scanning electron micrographs at different time intervals has been
conducted (Pearson, 1991). It has been found that the surface of the GICs at 10 min
finish causes some disturbance to the structure of the restoration and produces fault
lines. These lines are not apparent on the specimen finish after 24 h. The effect of
etching the GICs at 10–60 s immediately after mixing shows that longer the etch
time, the more damage caused to the subsurface. The enamel surfaces exposed to
different orthodontic bonding systems have been evaluated by SEM. The bonding
system with self-etching primers or conditioners with poly (acrylic acid) might offer
potential benefits compared with the conventional acid etching and priming because
of fewer irreversible changes to the enamel surface (Fjeld and Ogaard, 2006).
The strengthening of GIC by compounding short fibers with CaO–P2O5–
SiO2–Al2O3 (CPSA) glass has been investigated to observe the microstructure of the
fractured surface (after diametral tensile strength measurement) of the set cement.
CPSA glass short fibers are more effective in the strengthening of GIC than the
74
electric glass fibers (Kobayashi et al., 2000). The fractured surface of commercial
GICs has been examined using SEM to ascertain the relationship between the
mechanical properties and the microstructures of the cements (Xie et al., 2000). The
mechanical properties and morphology of polycarbonate/ethylene-1-octylene
copolymer (PC/POE) binary blends and PC/POE/ ionomer ternary blends have been
studied by SEM of fractured surfaces. The tensile strength and elongation at break of
the PC/POE blends decrease with increasing the POE content. The PC/POE weight
ratio has a greater effect on the morphology of PC/POE blends (Li et al., 2003).
Twelve specimens of mineral trioxide aggregate (MTA) and Portland cement material
have been examined for the percentage composition of chemical elements. In spite of
chemical similarity, a difference in the texture and particles of each material is
observed by SEM (Oliveira et al., 2007).
Field-emission electron microscopy (FE–SEM) has been applied to the
evaluation of GIC-dentine interface morphology after using different surface
conditioners. All the GICs tested demonstrate intimate adaptation to the dentine
surface whether it is conditioned or not (Tanumiharja et al., 2001). A high resolution
SEM study in conjunction with tensile bond strength analysis has been used to
correlate the morphologic findings to the bonding potential of a restorative system.
The binding procedure shows favorable results at ultra-structural level when the
compomer is applied to both the enamel and dentine surface for 30 s (Breschi et al.,
2001). SEM images show evidence of micromechanical bonding at the interface
between VBP and the tooth (Mitra et al., 2009).
75
Electron probe microanalysis has been employed to study the ion exchange of
selected elements (e.g., Ca, P) between dentine and GICs. The element penetration
into the tooth structure and GIC exceeds beyond the “ion exchange layer” as observed
in SEM studies (Knight et al., 2007).
3.5.2. Transmission Electron Microscopy (TEM)
The ultrastructure of the hardened GIC has been observed by TEM in
conjunction with an energy-dispersive X–ray microanalyser. The existence of a
metal-ion-depleted and Si-rich layer (siliceous hydrogel) on the glass surface in the
hardened cement has been confirmed (Hatton and Brook, 1992).
The existence of the glass ionomer phase in a conventional GIC, a RMGIC, a
giomer, a compomer and a composite, before and after water uptake, has been studied
by TEM. The variable extent of glass ionomer phase is determined by differences in
resin composition of the restoratives. Based on the ultrastructural manifestation of the
glass ionomer phase, the compomer is very similar to a resin composite. Unlike a
compomer, a giomer containing a pre-reacted glass-ionomer phase behaves more like
a RMGIC. It may occupy a position between the two materials within the spectrum of
hybrid tooth-colored restoratives (Tay et al., 2001).
A review on the applications of laser flash photolysis, spectroscopy and
electron microscopy in photopolymerization reactions and development of glass
ionomer dental cements has been presented by Ahmad et al. (2011).
76
OBJECT OF PRESENT INVESTIGATION
The polymerization of acrylic acid derivatives is being investigated since
1950s. The use of photoinitiators has facilitated the polymerization reactions
involving a radical mechanism. Several workers have studied the polymerization of 2-
hydroxyethyl methacrylate (HEMA), a widely used material in glass ionomer
cements, using different photoinitiators. So far a comparative study of the reactivity
of photoinitiators in the polymerization of HEMA has not been reported. In view of
this fact, the present study has been designed to evaluate the comparative reactivity of
the different photoinitiators such as riboflavin, camphorquinone and safranin T,
alongwith triethanolamine as a co-initiator, in the polymerization of HEMA in both
aqueous and organic solvents is to be carried out. It is intended to develop a simple
analytical method for the determination of HEMA in polymerized solutions during
the initial stages of the reactions (~5% concentration change) to avoid any volume
changes in the solution due to further reactions. It has been assumed that the rate of
initiation is equal to the rate of termination at low conversion of HEMA using a low
intensity radiation source. Under these conditions the reaction may follow an apparent
first-order kinetics. The rates of polymerization reactions in the presence of these
photoinitiators would be determined at various pH values to observe any effect with a
change in pH. The effect of a change in HEMA concentration on the reaction rate
would also be studied. An important aspect of the work would be to make a
comparison of the rates of polymerization in aqueous and organic solvents and to
evaluate the effect of solvent parameters such as dielectric constant (a measure of
77
polarity) and viscosity (a measure of rheological behavior) of the medium. It is also
intended to ascertain the effect of triethanolamine concentration on the rate of
polymerization and to determine the bimolecular rate constant for the interaction of
HEMA and triethanolamine during the reactions. The kinetic data may provide useful
information on the reactivity of the photoinitiators and their efficacy in the
polymerization of HEMA in aqueous and organic solvents. The variations in rates for
different photoinitiators may throw light on the mode of these reactions and hence the
choice of the best medium to achieve optimum polymerization.
78
PROPOSED PLAN OF WORK
An outline of proposed plan of work on the polymerization of 2-hydroxyethyl
methacrylate (HEMA) is presented as follows.
1. Development of an analytical method for the assay of HEMA during the
initial stages of the polymerization reactions under specified conditions.
2. Performance of polymerization reactions on HEMA in aqueous solutions
in neutral and alkaline region using different photoinitiators, e.g.,
riboflavin, camphorquinone and safranin T, in the presence of
triethanolamine (TEOHA) as a co-initiator.
3. Study of the kinetics of polymerization reactions at various pH values
within about 5% change of HEMA concentration using a low intensity
radiation source.
4. Study of the effect of variation in HEMA concentration on the rates of
polymerization reactions at various pH values.
5. Performance of polymerization reactions on HEMA in organic solvents in
the presence of different photoinitiators as described under 2.
6. Study of the effect of solvent characteristics such as dielectric constant
and viscosity and development of correlations between the polymerization
rate constants and solvent parameters.
79
7. Study of the effect of TEOHA concentration on the rate of polymerization
in aqueous and organic solvents and determination of the bimolecular rate
constants for the interaction of HEMA and TEOHA during the reactions.
8. Comparison of the reactivity and efficacy of the photoinitiators used on
the basis of the kinetic data and to throw light on the mode of
polymerization reactions of HEMA in various media.
CHAPTER IV
EXPERIMENTAL
WORK
81
4.1. Materials
2-Hydroxyethyl methacrylate (HEMA) ≥99+% Aldrich
Synonym: 1, 2-Ethanediol mono(2-methylpropenoate)
Linear formula: CH2=C (CH3) COOCH2CH2OH Mr 130.14
Density: 1.073g/ml at 25˚C
It was distilled under reduced pressure and was stored in a refrigerator at 2-8˚C.
Triethanolamine ≥99% Merck
Density: 1.124 g/ml at 20˚C
Empirical formula: C6 H15 NO3 Mr 149.19
It was distilled under reduced pressure before use.
Camphorquinone 97% Aldrich
Synonym: 2,3 Bornanedione,
Empirical formula: C10 H14 O2 Mr 166.22
It was stored in the dark in a desiccator.
Safranin T Fluka
Synonym: Basic Red 2, Safranin O, 3,7-Diamino-2,8-dimethyl-5
phenylphenazinium chloride
Empirical formula: C20H19ClN4 Mr 350.84
Storage: It was stored in the dark in a desiccator.
82
Riboflavin: (3,10-dihydro-7,8-dimethyl-10-[(2S,3S,4R)-2,3,4,5-tetrahydroxypentyl]
benzopetridine-2,4-dione) Merck
Empirical formula: C17 H2ON4O6 Mr 376.4
It was found to be chromatographically pure and was stored in the dark in a
desiccator.
Lumiflavin (7,8,10-trimethylisoalloxazine) Sigma
Empirical formula: C13H12N4O2 Mr 256.3
It was stored in a light resistant container in the desiccator below O˚C.
Lumichrome (7,8-dimethylalloxazine) Sigma
Empirical formula: C12H10N4O2 Mr 242.3
It was stored in the dark in a desiccator.
Formylmethylflavin (7,8-dimethyl-10-formylmethylisalloxazine)
Empirical formula: C14H12N4O3 Mr 284.3
It was synthesized according to the method of Fall and Petering (1956) by the
periodic acid oxidation of riboflavin. The material was recrystallized from absolute
methanol, dried in vacuo and stored in the dark in a refrigerator.
Potassium Ferrioxalate
Empirical formula: K3Fe(C2O4)3.3H2O Mr 491.2
Potassium ferrioxalate was prepared by the method of Hatchard and Parker (1956) by
mixing three volume of 1.5 M potassium oxalate with one volume of 1.5 M ferric
83
chloride with vigorous stirring. The yellow green precipitated compound was
recrystallized twice from water, dried at 45˚C and stored in the dark in a desiccator.
Buffer Solutions
The following buffer solutions were used:
Phosphate buffer, pH 6.0-8.0; Borate buffer, Na2B4O7-HCl, pH 9.0.
The ionic strength was kept constant in each case (0.02 M).
Reagent/Solvents
All reagents and solvents were of analytical grade or of the purest form available
from BDH//Merck.
Water
Water was purified using a Milli-Q-system.
84
4.2. Methods
4.2.1. Thin-Layer Chromatography (TLC)
The following TLC conditions were used for the separation and identification
of riboflavin and photoproducts.
Adsorbent: a) Silica gel GF 254 (Merck precoated plates)
b) Microgranular CC 41 cellular powder, 10-20 micron
(Whatman) 30g /150 ml distilled water
Layer thickness: 250-µm
Solvent systems: I1; 1-butanol-acetic acid-water (4:1:5, v/v, organic phase) / silica
gel (Treadwell et al., 1968).
I2; 1-butanol-1-propanol-acetic acid-water (50:30:2:18, v/v) /
cellulose powder (Ahmad et al., 1980).
Temperature: 25-27 ˚C
Location of spots: UV light, 254 and 365nm (Unitec lamp, UK)
4.2.2. pH Measurements
An Elmerton LCD display pH meter (model-CP 501, sensitivity ± 0.01 pH
unit, Poland) with appropriate electrodes was used for pH measurements.
The electrodes were calibrated at 25˚C using the following buffers:
Phosphate (0.2 M) = pH 6.86
Disodium tetraborate (0.2 M) = pH 9.18
85
4.2.3. Ultraviolet and Visible Spectrometry
All absorbance and spectral measurements were performed on a Shimadzu
UV visible recording spectrophotometer (model UV-1601) using matched silica cells
of 1cm path length and appropriate control solutions in the reference beam. The base
line correction was made automatically by the built-in baseline memory at the
initializing period. The auto-zero adjustment was performed by one-touch operation.
The instrument calibration was periodically carried out using the following standards.
Wavelength scale: Automatic at the initializing period.
Absorbance scale: 0.050 g/l of K2Cr2O7 in 0.005 M H2SO4
Absorbance at 257 nm = 0.725
350 nm = 0.539 ± 0.005 (Rand, 1969)
Riboflavin solution, pH 4.0 (acetate buffer)
A (1%, 1cm) at 444 nm = 328
(British Pharmacopoeia, 2009).
4.2.4. Fluorescence Spectroscopy
Fluorescence measurements of RF in various HEMA solutions (aqueous and
organic solvent) were carried out at room temperature (~25 ºC) using a Spectramax 5
fluorimeter ( Molecular Devices, USA) in the end point mode using λex = 374 nm and
λem = 520 nm (Song and Metzler, 1967). The fluorescence was recorded at relative
fluorescence unit using a pure 0.05 mM RF solution as standard. The solutions were
86
protected from light with aluminum foil to prevent photolysis of riboflavin during
handling.
4.2.5. Light Intensity Measurement
The potassium ferrioxalate actinometer (Parker, 1953; Hatchard and Parker,
1956) has been found as the most useful solution phase actinometer and may be used
over a wide range of wavelengths in the UV and visible region (254–577 nm). It has
been used by Holmstrom and Oster (1961), Byrom and Turnbull (1967), McBride and
Moore (1967), Ahmad (1968) and Ahmad et al., (2004a, 2004b, 2005, 2006a, 2006b,
2008, 2009, 2010a) for the measurement of light intensity in the photolysis of
riboflavin and analogues. This actinometer has been employed for light intensity
measurements of the radiation source employed in this study.
In the actinometer the solutions of potassium ferrioxalate in sulphuric acid are
irradiated. This results in the reduction of ferric ion to ferrous:
On the completion of irradiation the amount of Fe2+ ions produced may be measured
spectrometrically by the formation of the red ferrous-phenanthroline complex and the
determination of its absorbance at 510 nm.
It is important to ensure that the actinometer solution completely absorbs the
radiation during the period of the measurement. The actinometry is performed before
87
and after irradiation and the lamp assumed to maintain the mean during the
experiment.
4.2.5.1. Procedure:
An oxygen free 0.006 M solution of potassium ferrioxalate (2.947 g/1) in 0.05
M H2SO4 is placed in the reaction vessel and irradiated with a General Electrics 15 W
fluorescent lamp (emission in the visible region) used for the photolysis. The
irradiation of this solution is carried out under nitrogen (90–120 bubbles/minute). The
temperature of the reaction vessel is maintained at 25 ± 1˚C by circulating water from
a thermostat cooling unit.
An aliquot of the photolysed solution of potassium ferrioxalate (1–2 ml) is
pipetted out at appropriate intervals (upto 15 minutes) into a 20 ml volumetric flask,
to which 1.8 ml of 0.5 M H2SO4 + 2 ml of 0.1% 1:10-phenanthroline + 1 ml of buffer
(60 ml M CH3COONa + 36 ml 0.5 M H2SO4) are added. The flask is made upto the
mark with distilled water (final pH 3.5), well shaken to mix and allowed to stand for
one hour in the dark to develop the coloured complex. The absorbance of the
phenanthroline-ferrous complex is measured in a 1 cm cell at 510 nm using the
appropriate solution in the blank. The amount of Fe2+ ions formed is determined from
the calibration graph. The calibration graph is constructed in a similar manner using
several dilutions of 1× 10−6 M/ml of Fe2+ in 0.05 M H2SO4 using a standardized 0.1
M FeSO4 in 0.05 M H2SO4 (Fig.11). The value of the molar absorptivity of Fe2+
complex, as determined from the slope of the calibration graph, is equal to
88
0.0
0.2
0.4
0.6
0.8
1.0
1.2
0 2 4 6 8 10 12
Concentration of Fe++
× 105 M
Ab
sorb
an
ce a
t 51
0 n
m
Fig. 11. Calibration graph for the determination of K3Fe(C2O4)3.
89
1.11×104 M−1 cm1 and is in agreement with the value reported by Parker (1953).
Employing the known values of the quantum yield for ferrioxalate actinometer at
various wavelengths (Hatchard and Parker, 1956), the number of Fe2+ ions formed
during the photolysis, the time of exposure and the fraction of the light absorbed by
the length of the actinometer solution, the light intensity incident just inside the front
window of the photolysis cell can be calculated. In the present case it has been
assumed that total absorption of the light takes place.
4.2.5.2. Calculations:
The number of Fe2+ ions formed during photolysis (nFe2+) is given by the
equation:
where V1 = volume of the actinometer solution irradiated (ml),
V2 = volume of the aliquot taken for analysis (ml),
V3 = final volume to which the aliquot V2 is diluted (ml),
1 = path length of the spectrophotometer cell used (1cm),
A = measured absorbance of the final solution at 510 nm,
ε = molar absorptivity of the Fe2+ complex (1.11 × 104 M−1 cm−1)
90
The number of quanta of the radiation source absorbed by the actinometer solution,
nabs, can be determined as follows:
where Φ = quantum yield for the Fe2+ formation at the desired wavelength (Hatchard
and Parker, 1956).
Considering t as the irradiation time of the actinometer in seconds, the number of
quanta per second per cell, nabs, is determined by the equation:
The average intensity of the lamp used has been determined as 2.1±0.2×1016quanta
s−1.
91
4.2.6. Polymerization of 2-Hydroxyethyl methacrylate (HEMA)
4.2.6.1. Radiation source
The choice of the radiation source for a photochemical reaction is an
important factor for the desired reaction to occur and depends on the chemical nature
and absorption characteristics of the reactants and the duration of the required change
in the reactants. It also depends on the total output of energy and the spectral and
relative energy distribution of the source. Since riboflavin (RF), camphorquinone
(CQ) and safranin T (ST) have been used as photoinitiators in this reaction, a General
Electrics 15 W fluorescent lamp (emission in the visible region) was used for the
photochemical work. The visible radiations are absorbed by all the photoinitiators
used in this work (absorption maxima: RF 445 nm (Heelis, 1982); CQ 468 nm
(Jakubiak et al., 2003); ST 520 nm (Previtali et al., 1994). The low intensity radiation
source has been used to determine the chemical change during the initial stages of the
reactions for kinetic purposes.
4.2.6.2. Method
A 1-3 M solution of 2-hydroxyethyl methacrylate (HEMA) containing
appropriate concentrations of the photoinitiators and triethanolamine (absorbance of
all the solutions at the absorption maxima of the photoinitiators is ~ 0.125 to avoid
inhomogenous free radical distribution (Alverez et al., 1998)) and 0.0025-0.01 M
triethanolamine (TEOHA) in water (pH 6.0-9.0 maintained with 0.02 M buffer) or in
organic solvents, was placed in a 10 ml volumetric flask and immersed in a water
bath maintained at 25±1˚C. The solution was degassed with nitrogen for 20 minutes
92
and then irradiated with the 15 W lamp (emission in the visible region) fixed
horizontally at a distance of 30 cm from the centre of the flask in a radiation chamber.
A gentle stream of nitrogen gas was continuously bubbled into the solution during
irradiation. An appropriate volume of the aliquot of the irradiated solution was
pipetted out at various intervals for spectrometric assay of HEMA.
Aqueous solutions of the photoinitiators (RF, CQ, ST) containing the same
concentration as used during the polymerization of HEMA were also irradiated under
identical conditions to determine any loss of the photoinitiator and formation of
photoproducts during irradiation. Spectral measurements and thin-layer
chromatography of the irradiated solutions were carried out to detect any
photodegradation of the photoinitiators.
RESULTS
AND
DISCUSSION
CHAPTER V
POLYMERIZATION OF
HEMA IN AQUEOUS
SOLUTIONS
95
Acrylic acid derivatives including 2-hydroxyethyl methacrylate monomer
(HEMA) (Mitra, 1991), urethane dimethylacrylate monomer (Atai et al., 2007),
proline modified acrylic acid copolymer
(Moshaverinia et al., 2009a),
N-
vinylcaprolactam-containing acrylic acid terpolymer (Moshaverinia et al., 2009b), N-
vinylpyrrolidone modified acrylic acid copolymer (Moshaverinia et al., 2008), and
polyurethane acrylate monomer (Yaobin et al., 2006) have been synthesized for
dental cement applications. These derivatives are intended to undergo polymerization
on exposure to light and form a hardened mass (cement). Among these derivatives,
HEMA is widely used in glass ionomer cements (GICs) that are employed as
restorative materials (Smith, 1998). Various types of GICs containing HEMA have
been developed as light cure restorative materials (Lee et al., 2010).
The photoinitiated polymerization of vinyl polymers has been studied since
1950s (Oster et al., 1957, 1958; Eaton, 1986; Lissi and Encinas, 1991; Paczkowski et
al., 1999; Encinas and Previtali, 2006). The process involves the participation of
photoinitiators that absorb in the visible region. The kinetics of photopolymerization
reactions has been discussed by several workers (Encinas and Previtali, 2006; Encinas
et al., 1996; Watts and Cash, 1991; Watts et al., 2003; Watts, 2005; Andrezejewska,
2001). The medium characteristics, ionization behavior of reacting species and
efficiency of the photoinitiators are among the major factors that influence the rate of
polymerization reactions (Alvarez et al., 1996). In most cases the
photopolymerization rates of HEMA have been determined dilatometrically
(Bertolotti et al., 1999; Orellana et al., 1999; Encinas et al., 2001). This method has
been used to study the effect of solvent on the rates of polymerization of HEMA
96
photoinitiated by azo compounds, (Alvarez et al., 1996; Valdebenito and Encinas,
2003) camphorquinone, (Wang et al., 2006) and pyrene derivatives (Encinas et al.,
1993). The light activated composite for restorative purpose are one-paste system
which contain a photoinitiator that is sensitive to blue light (470 nm). The curing of
composite resins in this case is initiated by the use of special dental curing lamps that
emit light at 470 nm with a light intensity of 500 Wm–3
(Watts et al., 1984). The
polyacid-modified composite resins are light activated and cured by free-radical
reactions using a photoinitiator and subsequently made to set by a dental curing lamp
that emits at 470 nm in the same way as the true composite resins (Nicholson, 2002).
The present studies are concerned with the polymerization of HEMA using
riboflavin, camphorquinone and safranin T as photoinitiator and triethanolamine
(TEOHA) as a co-initiator in aqueous and organic solvents. The chemical structure of
HEMA and photoinitiators are given in Fig.12. The chemical structure of riboflavin is
shown in Fig. 10. It is intended to conduct a comparative study of the reactivity of
these photoinitiators on the basis of the kinetic data obtained on the polymerization of
HEMA in the pH range of 6.0–9.0 and to throw light on the interaction of HEMA and
TEOHA resulting in the polymerization process. An important aspect of this work is
to study the effect of solvent characteristics such as dielectric constant and viscosity
on the rate of polymerization reactions. These parameters may influence the reactivity
of the photoinitiators in a particular medium (i.e. degree of polarity), depending upon
the nature and life-times of the radicals formed and the extent of their interactions
with HMEA. In addition to this the viscosity of the medium would determine the
magnitude of diffusional processes of the species involved and hence the rate of the
97
Fig. 12. The chemical structures of HEMA, TEOHA and photoinitiators.
98
reactions. The study would provide information on the photoinitiated reactions and
interactions of HEMA with excited species in the pH range 6.0–9.0 and in organic
solvents. It would facilitate the understanding of polymerization processes in light-
cure GIC systems. The nature and mechanisms of polymerization reactions using a
photoinitiator have been discussed in Section 6.2–6.4. The polymerization reactions
of HEMA involving different photoinitiators in aqueous medium and the effect of pH
and viscosity on these reactions are presented in the following sections.
5.1. Riboflavin as Photoinitiator
Riboflavin (RF) has been used as a photoinitiator in the polymerization of
HEMA along with triethanolamine (TEOHA) as a co-initiator to form a redox pair
involved in the process (Bertolotti et al., 1999; Orellana et al., 1999; Encinas et al.,
2001; Porcal et al., 2003). RF is an efficient electron acceptor and meditates in
numerous photochemical and biological electron transfer reactions (Ahmad and
Tollin, 1981a, 1981b; Ahmad et al., 1981, 1982; Ahmad and Vaid, 2006; Heelis,
1982, 1991; Tollin, 1995; Tollin et al., 1993; Scigalski and Paczkowski, 2005).
5.1.1. Spectral Characteristics of RF Solutions
RF exhibits an absorption maximum at 444 nm (ε = 12500 M-1
cm-1
) (Ahmad
et al., 2004a) in the visible region. The absorption spectrum of RF (pH 7.0) is shown
in Fig. 13. A concentration of 1 × 10-5
M (absorbance at 444 nm = 0.125) was used
as a photoinitiator along with 0.0025–0.01 M TEOHA in the polymerization of
HEMA solutions to avoid inhomogenous free radical distribution (Alvarez et al.,
99
Fig. 13. Absorption spectrum of riboflavin at pH 7.0.
100
1998). The spectral characteristics of the photolysed solutions of RF (pH 9.0) during
irradiation (5 min) showed a minor loss of absorbance at 444 nm in the visible region
indicating the formation of LC as the major final photoproduct through FMF as an
intermediate in this reaction (Ahmad and Vaid, 2006; Ahmad et al., 1980; Ahmad et
al., 2006b). Since RF solutions are used at a low concentration (1×10–5
M) in the
polymerization reactions (Bertolotti et al., 1999), any minor spectral changes during
the reaction would not affect the efficacy of RF as a photoinitiator.
5.1.2. Photoproducts of Riboflavin
RF is highly sensitive to light (DeRitter, 1982) and may undergo
photodegradation during irradiation with the visible light. It was felt necessary to
irradiate RF solution and to examine the photoproducts formed in this reaction which,
to some extent, would cause a loss in RF concentration and hence its efficacy as a
photoinitiator. The TLC of the photolysed solutions of RF (1×10–5
M), in the presence
of HEMA, using solvents systems (a) and (b) (Section 4.2.1), indicated the presence
of trace amounts of FMF, LC and LF at pH 9.0 only. In the alkaline solutions the
photodegradation of RF is much greater than that in the acid region (Ahmad and
Vaid, 2006), however, under the present irradiation conditions (~1 min), there would
be negligible loss in RF concentration. The photoproducts of RF observed are known
and have previously been reported (Ahmad and Vaid, 2006; DeRitter, 1982; Ahmad
and Rapson, 1990).
101
5.1.3. Assay of HEMA
A UV spectophotometric method has been used for the assay of HEMA at 208
nm during the photopolymerization reactions. This wavelength corresponds to the
absorption maximum of HEMA (Table 5) and on appropriate dilution would give the
concentration of HEMA monomer during the reaction. The validity of Beer’s Law
was confirmed in the desired concentration range prior to the assay and the content of
HEMA in photopolymerized solutions was determined using 7980 M–1
cm–1
as the
value of molar absorptivity at the analytical wavelength (Table 5). The reproducibility
of the method was confirmed by the assay of known amounts of HEMA in the
concentration range likely to be found in photopolymerized solutions. The values of
RSD for the assay indicate the precision of the method within ± 3%. The results of a
typical assay of HEMA in photopolymerized solutions at pH 9.0 are reported in Table
6. This is a new method for the determination of HEMA in photopolymerized
solutions since most of the previous workers have used dilatometric method for this
purpose (Bertolotti et al., 1999; Orellana et al., 1999; Encinas et al., 2001). In some
cases the rates of polymerization of HEMA have been measured using gas
chromatography (Beers et al., 1999), Raman spectroscopy (Wang et al., 2006), ATR-
FTIR spectroscopy (Guo et al., 2008) and differential scanning calorimetry (Jakubiak
et al., 2003; Anderzejewska et al., 2009). The assay of HEMA has been carried out
during the initial stages of the reaction assuming that a negligible change in volume
occurs in the medium during which does not affect the accuracy of the assay method.
102
Under the Assay conditions of HEMA, on the dilution of photolysed
solutions, the maximum TEOHA concentration used (0.01 M) would be of the order
of 10×-6 M. It would probably be too low to undergo complexation with HEMA in a
molar ratio. The UV spectra of HEMA at such a dilution did not show any change in
UV absorption in the presence of TEOHA. This suggest that no possibility of
interaction between these compounds to effect the rate constant.
The error on the Assay of HEMA was determined to be within ± 3%. In the
Assay of HEMA in photolysed solutions, the analytical error would remain the same
but the magnitude of Assay values would be affected by other factors such as the
variations in light intensity, changes in volume of HEMA, overall analytical errors in
measurement etc. Therefore, the error in the measurement of rate constants may
exceed the 3 % limit as indicated with the rate constants (Table 7-9). Under these
conditions the values of rate constant may be considered as statistically meaningful.
Table 5. Calibration data for HEMA showing linear regression analysis.a
λ max 208 nm
Concentration range 0.1–1.0 × 10–4
M
Slope 7980
SE (±) of slope 0.0112
Intercept 0.0010
Correlation coefficient 0.9995
Molar absorptivity (ε) 7980 M–1
cm–1
a values represent a mean of five determinations.
103
Table 6. Polymerization of HEMA (1 M) at pH 9.0 in presence of RF as
photoinitiator at various TEOHA concentrations.
TEOHA Concentration (M) Time
(sec) 0.0025 0.005 0.0075 0.01
0 1.000 1.000 1.000 1.000
10 0.997 0.996 0.993 0.992
20 0.994 0.991 0.988 0.985
30 0.992 0.988 0.983 0.975
40 0.990 0.983 0.975 0.968
50 0.987 0.976 0.967 0.959
60 0.985 0.971 0.963 0.947
104
5.1.4. Kinetics of Photopolymerization of HEMA
The kinetics of photopolymerization at low conversion of HEMA has been
studied by UV spectrometry as described above. The assay data on HEMA during the
reactions were subjected to kinetic treatment and the photolysis of HEMA (a measure
of photopolymerization) was found to follow pseudo first-order kinetics in the initial
stage of the reaction at 0.01 M TEOHA concentrations (Orellana et al.,1999) at pH
6.0–9.0 (Fig. 14–18). The apparent first-order rate constant (kobs) for the
polymerization of HEMA at 1–3 M in the presence of various concentrations of
TEOHA are reported in Table 7–9, respectively. The polymerization of HEMA at low
conversion remains homogenous since the polymer remains soluble in monomer-rich
aqueous solutions (Encinas et al., 1996). The steady-state assumption of the rate of
initiation being equal to the rate of termination is considered valid only at a low
conversion of monomer (Jakuubiak et al., 2003) and has been observed in the present
study. The value of kobs reported represents the rate of initiation in this case. During
the initial stages of the reaction (within ~5% change), the average degree of
polymerization as well as the viscoelastic properties of HEMA would almost be
constant on changing the co-initiator concentration (0.0025–0.01 M). Under these
conditions, the shrinkage properties of the polymerized solution would largely remain
unaffected.
5.1.5. Effect of pH
The apparent first-order rate constants (kobs) for the photopolymerization of
HEMA indicate that the rate of reaction is enhanced with an increase in pH from 6.0–
105
R2 = 0.993
R2 = 0.995
R2 = 0.993
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 10 20 30 40 50 60 70 80 90 100
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 14. First-order plots for the polymerization of HEMA in the presence of RF at
pH 6.0. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
106
R2 = 0.991
R2 = 0.991
R2 = 0.990
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 10 20 30 40 50 60 70 80
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 15. First-order plots for the polymerization of HEMA in the presence of RF at
pH 7.0. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
107
R2 = 0.989
R2 = 0.996
R2 = 0.989
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 10 20 30 40 50 60 70 80Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 16. First-order plots for the polymerization of HEMA in the presence of RF at
pH 7.5. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
108
R2 = 0.995
R2 = 0.991
R2 = 0.990
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 10 20 30 40 50 60 70
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 17. First-order plots for the polymerization of HEMA in the presence of RF at
pH 8.0. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
109
R2 = 0.992
R2 = 0.993
R2 = 0.991
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 10 20 30 40 50 60
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 18. First-order plots for the polymerization of HEMA in the presence of RF at
pH 9.0. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
110
Table 7. The apparent first-order rate constant (kobs) for polymerization of HEMA (1
M) at pH 6.0–9.0 in presence of RF as photoinitiator at various TEOHA
concentrations.
kobs × 104 s
–1
pH 0.0025 M 0.0050 M 0.0075 M 0.010 M
6.0 1.05±0.084 1.66±0.099 2.97±0.14 3.70±0.15
7.0 1.61±0.080 2.42±0.12 4.03±0.16 5.05±0.19
7.5 1.97±0.098 3.13±0.15 5.07±0.20 6.32±0.16
8.0 2.49±0.12 3.83±0.14 5.72±0.25 7.89±0.25
9.0 2.48±0.10 4.89±0.16 6.41±0.22 8.87±0.28
111
Table 8. The apparent first-order rate constant (kobs) for polymerization of HEMA (2
M) at pH 6.0–9.0 in presence of RF as photoinitiator at various TEOHA
concentrations.
kobs × 104 s
–1
pH 0.0025 M 0.0050 M 0.0075 M 0.010 M
6.0 0.93±0.061 1.45±0.075 2.32±0.092 2.84±0.12
7.0 1.18±0.058 2.24±0.091 3.31±0.12 3.98±0.15
7.5 1.38±0.069 2.86±0.11 4.28±0.15 5.18±0.21
8.0 1.92±0.086 3.23±0.099 5.32±0.20 6.44±0.26
9.0 2.17±0.11 3.57±0.13 5.98±0.18 7.63±0.22
112
Table 9. The apparent first-order rate constant (kobs) for polymerization of HEMA (3
M) at pH 6.0–9.0 in presence of RF as photoinitiator at various TEOHA
concentrations.
kobs × 104 s
–1
pH 0.0025 M 0.0050 M 0.0075 M 0.010 M
6.0 0.86±0.052 1.25±0.085 1.94±0.12 2.45±0.14
7.0 1.03±0.050 1.98±0.011 2.82±0.15 3.43±0.12
7.5 1.13±0.068 2.45±0.13 3.60±0.12 4.38±0.21
8.0 1.62±0.11 2.77±0.16 4.56±0.23 5.61±0.25
9.0 2.01±0.099 3.28±0.14 5.39±0.21 6.68±0.22
113
9.0. Since the photopolymerization of HEMA has been carried out in the presence of
TEOHA, a decrease in the ionization of TEOHA (pKa 7.82) (Albert and Serjeant,
1962) from 98.5–6.1% at pH 6.0–9.0 would affect the rate of photopolymerization
since it would facilitate electron transfer from TEOHA to RF triplet state (Orellana et
al., 1999), ultimately resulting in the polymerization of HEMA. The rate-pH profiles
for the photopolymerization of HEMA at 1–3 M concentrations are shown in Fig. 19.
These profiles represent sigmoid type curves as a consequence of an acid / base
dissociation of HEMA molecule. The profiles indicate a great enhancement in the
rate, with pH, in the range of 6.0–9.0, as observed earlier by Valdebenito and Encinas
(2003). An increase in the rate of polymerization, with pH, is attributed to the
presence of a labile proton on the hydroxyl group of HEMA (Jakubiak et al., 2003).
The relative decrease in the rate of polymerization of HEMA (6.0–9.0) from 1–3 M
appears largely to be due to the viscosity effect as discussed below.
5.1.6. Effect of Viscosity
It has been observed that the rate of photopolymerization of HEMA in
aqueous solution (pH 6.0–9.0) is affected by a change in the viscosity of the medium
on increasing the HEMA concentration (1–3 M). The plots of kobs at different HEMA
concentrations versus the inverse of viscosity of the solutions in the pH range 6.0–9.0
are linear (Fig. 20), indicating that an increase in viscosity leads to a decrease in the
rate of polymerization of HEMA probably as a result of flavin triplet quenching
(Ahmad and Tollin, 1981b). In addition to this the rate is controlled by solute
diffusion and would be affected by an increase in the viscosity of the medium. A
114
1 M
2 M
3 M
0.0
2.0
4.0
6.0
8.0
10.0
4.0 5.0 6.0 7.0 8.0 9.0 10.0
pH
ko
bs
× 1
04
(s–
1)
Fig. 19. Rate-pH profile for polymerization of HEMA (1–3 M) in presence of RF and
0.01 M TEOHA.
115
Fig. 20. Plots of kobs for polymerization of HEMA in presence of RF and 0.01 M
TEOHA versus inverse of solution viscosity. HEMA: (●) 1.0 M, (■) 2.0 M,
(▲) 3.0 M.
pH 6.0
pH 7.0
pH 7.5
pH 8.0
pH 9.0
0.0
2.0
4.0
6.0
8.0
10.0
0.4 0.5 0.6 0.7 0.8 0.9 1.0
Viscosity (mPa.s)–1
ko
bs
× 1
04
(s–
1)
116
small change in the viscosity of HEMA solutions with an increase in pH has been
reported (Valdebenito and Encinas, 2003). Thus the HEMA concentration appears to
be one of the controlling factors in the rate of polymerization.
5.1.7. Effect of TEOHA Concentration
TEOHA plays an important role in the polymerization of HEMA and the
reaction does not occur in the absence of the co-initiator. RF radicals interact with
TEOHA to cause the polymerization reaction. It has been reported that the rate of
photopolymerization of HEMA is maximum in the presence of 0.01 M TEOHA
(Orellana et al., 1999). In order to observe the effect of TEOHA concentration
(0.0025–0.01 M) and its interaction with HEMA (1–3 M) in the initial stages of
polymerization, the kobs values were determined for the reactions carried out at
various TEOHA concentrations (Fig. 21–25). The plots of kobs versus TEOHA
concentrations were found to be linear (Fig. 26) and the slopes yielded the second-
order rate constant (k2) for the interaction of TEOHA with HEMA. The k2 values
(Table 10) have been found to increase with an increase in pH as explained above for
the polymerization reactions at pH 6.0–9.0. Thus the rate of polymerization is
dependent on the fate of amine radical produced during the reaction and their
interaction with HEMA.
5.1.8. Mechanism of HEMA Polymerization
A photoinitiation mechanism of HEMA polymerization by RF / TEOHA
system in aqueous solution has been proposed by Orellana et al. (1999). Based on the
117
R2 = 0.987
R2 = 0.990
R2 = 0.992
R2 = 0.993
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.992
R2 = 0.993
R2 = 0.992
R2 = 0.995
0.280
0.290
0.300
0.310
log
co
nce
ntr
ati
on
(M
)
R2 = 0.989
R2 = 0.992
R2 = 0.991
R2 = 0.993
0.460
0.464
0.468
0.472
0.476
0.480
0 20 40 60 80 100
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 21. First-order plots for the polymerization of HEMA (1–3 M) in presence of RF
as photoinitiator at different TEOHA concentrations (pH 6.0). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
2M
3M
1M
118
R2 = 0.994
R2 = 0.991
R2 = 0.992
R2 = 0.991
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.993
R2 = 0.992
R2 = 0.990
R2 = 0.991
0.280
0.290
0.300
0.310
log
co
nce
ntr
ati
on
(M
)
R2 = 0.990
R2 = 0.992
R2 = 0.992
R2 = 0.990
0.460
0.464
0.468
0.472
0.476
0.480
0 10 20 30 40 50 60 70 80
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 22. First-order plots for the polymerization of HEMA (1–3 M) in presence of RF
as photoinitiator at different TEOHA concentrations (pH 7.0). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
119
R2 = 0.990
R2 = 0.991
R2 = 0.990
R2 = 0.993
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.990
R2 = 0.992
R2 = 0.993
R2 = 0.996
0.275
0.285
0.295
0.305
log
co
nce
ntr
ati
on
(M
)
R2 = 0.992
R2 = 0.991
R2 = 0.992
R2 = 0.989
0.450
0.460
0.470
0.480
0 10 20 30 40 50 60 70 80
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 23. First-order plots for the polymerization of HEMA (1–3 M) in presence of RF
as photoinitiator at different TEOHA concentrations (pH 7.5). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
120
R2 = 0.993
R2 = 0.990
R2 = 0.992
R2 = 0.996
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.993
R2 = 0.995
R2 = 0.991
R2 = 0.990
0.260
0.280
0.300
0.320
log
co
nce
ntr
ati
on
(M
)
R2 = 0.989
R2 = 0.991
R2 = 0.994
R2 = 0.992
0.450
0.460
0.470
0.480
0 10 20 30 40 50 60 70
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 24. First-order plots for the polymerization of HEMA (1–3 M) in presence of RF
as photoinitiator at different TEOHA concentrations (pH 8.0). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
121
R2 = 0.993
R2 = 0.989
R2 = 0.993
R2 = 0.994
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.992
R2 = 0.992
R2 = 0.988
R2 = 0.993
0.260
0.280
0.300
0.320
log
co
nce
ntr
ati
on
(M
)
R2 = 0.991
R2 = 0.991
R2 = 0.992
R2 = 0.990
0.450
0.460
0.470
0.480
0 10 20 30 40 50 60
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 25. First-order plots for the polymerization of HEMA (1–3 M) in presence of RF
as photoinitiator at different TEOHA concentrations (pH 9.0). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
122
R2 = 0.990
R2 = 0.991
R2 = 0.993
R2 = 0.993
R2 = 0.994
0.0
2.0
4.0
6.0
8.0
10.0
ko
bs
× 1
04
(s–
1)
R2 = 0.991
R2 = 0.992
R2 = 0.994
R2 = 0.992
R2 = 0.995
0.0
2.0
4.0
6.0
8.0
10.0
ko
bs
× 1
04
(s–
1)
R2 = 0.989
R2 = 0.991
R2 = 0.993
R2 = 0.994
R2 = 0.994
0.0
2.0
4.0
6.0
8.0
10.0
0.000 0.002 0.004 0.006 0.008 0.010
TEOHA concentration (M)
ko
bs
× 1
04
(s–
1)
Fig. 26. Second-order plots for polymerization of HEMA (1–3 M) in presence of RF
at various TEOHA concentrations (0.0025–0.01 M). pH: (●) 6.0, (■) 7.0,
(▲) 7.5, (♦) 8.0, (*) 9.0.
1M
2M
3M
123
Table 10. Second-order rate constants (k′) for the interaction of TEOHA (0.0100 M)
with HEMA (1–3 M) at pH 6.0–9.0 in the presence of RF.
k'×102 M
–1 s
–1
pH Monomer:
water
ratio
(1.21:10)
Correlation
coefficient
Monomer:
water
ratio
(2.42:10)
Correlation
coefficient
Monomer:
water
ratio
(3.63:10)
Correlation
coefficient
6.0 3.70 0.993 2.84 0.995 2.45 0.993
7.0 5.05 0.991 3.98 0.991 3.43 0.990
7.5 6.32 0.993 5.18 0.996 4.38 0.989
8.0 7.89 0.996 6.44 0.990 5.61 0.992
9.0 8.87 0.994 7.63 0.993 6.68 0.990
124
time-resolved photolysis studies a scheme of the photochemical behavior of RF in the
presence of amine and monomer in aqueous solution has been presented (Scheme 1).
The process involves RF triplet quenching by the amine to produce radicals initiating
the polymerization reaction. It has been suggested that the free radicals produced in
the photoinduced electron transfer from TEOHA to excited RF form a radical pair
which ultimately leads to the polymerization of HEMA. The various steps involved in
the photopolymerization process are shown in the scheme. The free radicals may also
be produced from other photoinitiators such as ketones and add to HEMA to initiate
polymerization of the monomer (Dutta and Bhat, 1996). The use of camphorquinone
and safranin T as photoinitiators in the polymerization of HEMA is described in the
following sections.
125
Scheme 1. Photopolymerization of HEMA in presence of RF and TEOHA.
126
5.2. Camphorquinone as Photoinitiator
The results of the reactivity of RF as a photoinitiator in RF / TEOHA system
in the polymerization of HEMA have been presented in Section 5.1. Camphorquinone
(CQ) has previously been used as a photoinitiator in this reaction by several workers
(Corrales et al., 2003; Jakubiak et al., 2003; Wang et al., 2006; Chen et al., 2007;
Guo et al., 2008). It has been used as a photoinitiator alongwith TEOHA in the
polymerization of HEMA in these studies. CQ has been employed as a photoinitiator
in the polymerization of HEMA in both aqueous and organic solvents. In the present
work CQ / TEOHA system has been used for the polymerization of 1–3 M HEMA at
pH 6.0–9.0 to compare the kinetic data with those of RF. The CQ / amine
photoinitiator system is widely used for the polymerization of dental restorative
materials (Watts, 2005).
5.2.1. Spectral Characteristics of CQ Solutions
CQ possesses an absorption maximum at 468 nm (ε = 46 ± 2 M–1
cm–1
) (Chen
et al., 2007) in the visible region (Fig. 27). This is similar to that of RF (445 nm),
however, the value of molar absorptivity of CQ at the absorption maximum is much
lower than that of RF and this may affect its reactivity as a photoinitiator compared to
that of RF. In order to maintain the same absorbance (0.125 as that of RF in the
HEMA solution, a 2.7×10–3
M concentration of CQ was used during the reaction. The
low absorbance of the photoinitiators is necessary to avoid inhomogenous free radical
distribution (Alvarez et al., 1998). The spectra of the photolysed solutions of CQ
alone at various pH values during irradiation (5 min) did not show any change in
127
Fig. 27. Absorption spectra of camphorquinone at pH 7.0.
128
absorbance at 468 nm in the visible region. This may be due to the use of a low
intensity irradiation source (15 W lamp) which does not produce any change in the
molecule during the short period of exposure to light. It may be concluded that
aqueous solutions of CQ are less sensitive to light compared to RF and would remain
stable during the polymerization reactions.
5.2.2. Assay of HEMA
The concentrations of HEMA (1–3 M) in aqueous solutions polymerized in
the presence of CQ as a photoinitiator were determined by measurement of
absorbance at 208 nm as in the case of RF (Section 5.1.3). The result of a typical
assay of HEMA during the reactions at pH 9.0 is presented in Table 11. The values
show a gradual loss in the concentration of HEMA, with time, indicating the
conversion of the monomer. The loss of HEMA has been found to increase with pH
suggesting that the polymerization reaction is facilitated in the alkaline medium. The
analytical data have only been obtained at low conversion of HEMA.
5.2.3. Kinetics of Polymerization
The kinetics of polymerization of HEMA in the presence of CQ has been
studied in the initial stages of the reaction (~5% change) for reasons stated in the case
of RF as a photoinitiator. The assay data at various pH values were found to comply
with pseudo first-order kinetics (log concentration versus time plots are linear) and
the apparent first-order rate constants (kobs) (Table 12–14) were determined from the
slopes of the straight lines (Fig. 28–32). The plots were found to be linear only within
129
Table 11. Polymerization of HEMA (1 M) at pH 9.0 in presence of CQ as
photoinitiator at various TEOHA concentrations.
TEOHA Concentration (M) Time
(sec) 0.0025 0.005 0.0075 0.01
0 1.000 1.000 1.000 1.000
10 0.997 0.995 0.992 0.990
20 0.995 0.989 0.987 0.983
30 0.992 0.985 0.981 0.974
50 0.988 0.978 0.970 0.959
70 0.984 0.971 0.962 0.947
130
Table 12. The apparent first-order rate constant (kobs) for polymerization of HEMA (1
M) at pH 6.0–9.0 in presence of CQ as photoinitiator at various TEOHA
concentrations.
kobs × 104 s
–1
pH 0.0025 M 0.0050 M 0.0075 M 0.010 M
6.0 1.01±0.072 1.84±0.095 2.80±0.17 3.35±0.15
7.0 1.32±0.081 2.34±0.097 3.31±0.15 4.04±0.16
7.5 1.79±0.099 3.12±0.11 4.03±0.16 5.54±0.21
8.0 1.81±0.092 4.07±0.13 5.14±0.18 6.97±0.19
9.0 2.28±0.11 4.15±0.15 5.49±0.21 7.78±0.27
131
Table 13. The apparent first-order rate constant (kobs) for polymerization of HEMA (2
M) at pH 6.0–9.0 in presence of CQ as photoinitiator at various TEOHA
concentrations.
kobs × 104 s
–1
pH 0.0025 M 0.0050 M 0.0075 M 0.010 M
6.0 0.87±0.051 1.38±0.062 2.18±0.11 2.72±0.17
7.0 0.98±0.062 1.56±0.069 2.73±0.14 3.51±0.16
7.5 0.72±0.044 2.03±0.082 3.47±0.12 4.65±0.21
8.0 1.38±0.062 3.10±0.15 3.97±0.21 5.89±0.25
9.0 1.55±0.075 2.82±0.13 5.29±0.24 6.78±0.27
132
Table 14. The apparent first-order rate constant (kobs) for polymerization of HEMA (3
M) at pH 6.0–9.0 in presence of CQ as photoinitiator at various TEOHA
concentrations.
kobs × 104 s
–1
pH 0.0025 M 0.0050 M 0.0075 M 0.010 M
6.0 0.45±0.020 1.06±0.039 1.92±0.15 2.33±0.12
7.0 0.90±0.042 1.38±0.068 2.02±0.11 2.86±0.15
7.5 0.76±0.036 1.70±0.081 2.68±0.14 4.01±0.18
8.0 1.09±0.042 2.26±0.098 4.14±0.22 5.12±0.24
9.0 1.62±0.084 3.17±0.14 4.13±0.20 5.89±0.26
133
R2 = 0.987
R2 = 0.989
R2 = 0.989
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 25 50 75 100 125
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 28. First-order plots for the polymerization of HEMA in the presence of CQ at
pH 6.0. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
134
R2 = 0.989
R2 = 0.989
R2 = 0.990
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 20 40 60 80 100
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 29. First-order plots for the polymerization of HEMA in the presence of CQ at
pH 7.0. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
135
R2 = 0.993
R2 = 0.988
R2 = 0.987
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 20 40 60 80 100
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 30. First-order plots for the polymerization of HEMA in the presence of CQ at
pH 7.5. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
136
R2 = 0.994
R2 = 0.992
R2 = 0.989
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 20 40 60 80
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 31. First-order plots for the polymerization of HEMA in the presence of CQ at
pH 8.0. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
137
R2 = 0.995
R2 = 0.990
R2 = 0.990
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 10 20 30 40 50 60 70
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 32. First-order plots for the polymerization of HEMA in the presence of CQ at
pH 9.0. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
138
5% concentration loss of HEMA, i.e. low conversion of the monomer (Jakubiak et al.,
2003). Above this level, the reaction is complicated resulting in volume changes and
non-linear behavior. In the majority of cases dilatometric method has been used to
study the polymerization of HEMA to account for any change in the volume of the
solutions (Bertolotti et al., 1999; Orellana et al., 1999; Encinas et al., 2001). In the
present case the UV spectrometric method has been found to be satisfactory for
kinetic purposes in the concentration range involving low conversion of HEMA.
5.2.4. Effect of pH
The present study of the polymerization of HEMA using CQ as a
photoinitiator has been carried out in the pH range of 6.0–9.0 as in the case of RF.
The values of apparent first-order rate constants (kobs) for the reactions (Table 12–14)
have been found to gradually increase with pH showing a relatively fast change
between pH 7.0–8.0. This is probably due to the deprotonation of TEOHA (pKa 7.82)
(Albert and Serjeant, 1962) and consequently the ease in electron transfer from
TEOHA to RF triplet state. It is followed by the interaction of amine radicals with
HEMA to undergo polymerization. The rate is highest at pH 9.0 probably due to the
basic nature of the neutral amine radical. This behavior has already been explained in
the case of the reactivity of RF as a photoinitiator in this reaction (Section 5.1.5). The
rate-pH profiles for the polymerization reaction of HEMA carried out at 1–3 M
concentrations are shown in Fig. 33. An explanation for the increase in the rate of
reactions on increasing the pH from 6.0–9.0 is based on the availability of a labile
proton on the molecule (Beers et al., 1999) and has been discussed in the case of RF
139
1 M
2 M
3 M
0.0
2.0
4.0
6.0
8.0
10.0
4.0 5.0 6.0 7.0 8.0 9.0 10.0
pH
ko
bs
× 1
04
(s–
1)
Fig. 33. Rate-pH profile for polymerization of HEMA (1–3 M) in presence of CQ and
0.01 M TEOHA.
140
earlier (Section 5.1.5).
5.2.5. Effect of Viscosity
The effect of viscosity on the rate of polymerization of HEMA on changing
the concentration from 1–3 M in the presence of CQ is prominent (Fig. 34) and is
similar to that observed in the case of RF. However, the apparent first-order rate
constants obtained in the presence of CQ are considerably lower than those of RF
under the same conditions (Table 12–14). This appears to be due to a difference in the
reactivity of the triplet states of the two photoinitiators. The increase in the viscosity
of HEMA solutions would cause quenching of the triplet state and hence a decrease in
the rate of interaction between the CQ triplet state and the amine leading to the
formation of a radical ion pair and further reactions. Furthermore, the solute diffusion
processes would also be affected by the viscosity of the medium and thus would
influence the rate of polymerization of HEMA. It is, therefore, necessary to take into
consideration the effect of viscosity on the rate of polymerization of HEMA and
consequently on the yield of the polymer.
5.2.6. Effect of TEOHA Concentration
In order to compare the effect of TEOHA concentration on the rate of
polymerization of HEMA in the presence of CQ, with that of RF, the reactions were
carried out at 0.0025–0.01 M TEOHA concentrations (Fig. 35–39). The second-order
rate constants for the interaction of HEMA and TEOHA under these conditions (Fig.
40) are reported in Table 15. These rate constants are lower than those obtained
141
pH 6.0
pH 7.0
pH 7.5
pH 8.0
pH 9.0
0.0
2.0
4.0
6.0
8.0
10.0
0.4 0.5 0.6 0.7 0.8 0.9 1.0
Viscosity (mPa.s)–1
ko
bs
× 1
04
(s–
1)
Fig. 34. Plots of kobs for polymerization of HEMA in presence of CQ and 0.01 M
TEOHA versus inverse of solution viscosity. HEMA: (●) 1.0 M, (■) 2.0 M,
(▲) 3.0 M.
142
R2 = 0.986
R2 = 0.988
R2 = 0.989
R2 = 0.987
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.990
R2 = 0.987
R2 = 0.989
R2 = 0.989
0.280
0.290
0.300
0.310
log
co
nce
ntr
ati
on
(M
)
R2 = 0.985
R2 = 0.991
R2 = 0.989
R2 = 0.989
0.460
0.464
0.468
0.472
0.476
0.480
0 25 50 75 100 125
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 35. First-order plots for the polymerization of HEMA (1–3 M) in presence of CQ
as photoinitiator at different TEOHA concentrations (pH 6.0). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
143
R2 = 0.989
R2 = 0.992
R2 = 0.992
R2 = 0.989
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.986
R2 = 0.990
R2 = 0.992
R2 = 0.989
0.280
0.290
0.300
0.310
log
co
nce
ntr
ati
on
(M
)
R2 = 0.987
R2 = 0.986
R2 = 0.989
R2 = 0.990
0.460
0.464
0.468
0.472
0.476
0.480
0 20 40 60 80 100
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 36. First-order plots for the polymerization of HEMA (1–3 M) in presence of CQ
as photoinitiator at different TEOHA concentrations (pH 7.0). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
144
R2 = 0.991
R2 = 0.993
R2 = 0.991
R2 = 0.993
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.992
R2 = 0.990
R2 = 0.987
R2 = 0.988
0.275
0.285
0.295
0.305
log
co
nce
ntr
ati
on
(M
)
R2 = 0.988
R2 = 0.988
R2 = 0.990
R2 = 0.987
0.450
0.460
0.470
0.480
0 20 40 60 80 100
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 37. First-order plots for the polymerization of HEMA (1–3 M) in presence of CQ
as photoinitiator at different TEOHA concentrations (pH 7.5). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
145
R2 = 0.990
R2 = 0.991
R2 = 0.990
R2 = 0.994
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.988
R2 = 0.988
R2 = 0.992
R2 = 0.992
0.260
0.280
0.300
0.320
log
co
nce
ntr
ati
on
(M
)
R2 = 0.984
R2 = 0.991
R2 = 0.993
R2 = 0.989
0.450
0.460
0.470
0.480
0 20 40 60 80
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 38. First-order plots for the polymerization of HEMA (1–3 M) in presence of CQ
as photoinitiator at different TEOHA concentrations (pH 8.0). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
146
R2 = 0.991
R2 = 0.989
R2 = 0.992
R2 = 0.995
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.986
R2 = 0.991
R2 = 0.991
R2 = 0.990
0.260
0.280
0.300
0.320
log
co
nce
ntr
ati
on
(M
)
R2 = 0.991
R2 = 0.986
R2 = 0.987
R2 = 0.990
0.450
0.460
0.470
0.480
0 10 20 30 40 50 60 70
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 39. First-order plots for the polymerization of HEMA (1–3 M) in presence of CQ
as photoinitiator at different TEOHA concentrations (pH 9.0). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
147
R2 = 0.992
R2 = 0.989
R2 = 0.989
R2 = 0.990
R2 = 0.993
0.0
2.0
4.0
6.0
8.0
10.0
ko
bs
× 1
04
(s–
1)
R2 = 0.993
R2 = 0.992
R2 = 0.990
R2 = 0.991
R2 = 0.989
0.0
2.0
4.0
6.0
8.0
10.0
ko
bs
× 1
04
(s–
1)
R2 = 0.988
R2 = 0.991
R2 = 0.990
R2 = 0.990
R2 = 0.994
0.0
2.0
4.0
6.0
8.0
10.0
0.000 0.002 0.004 0.006 0.008 0.010
TEOHA concentration (M)
ko
bs
× 1
04
(s–
1)
Fig. 40. Second-order plots for polymerization of HEMA (1–3 M) in presence of CQ
at various TEOHA concentrations (0.0025–0.01 M). pH: (●) 6.0, (■) 7.0,
(▲) 7.5, (♦) 8.0, (*) 9.0.
1M
2M
3M
148
Table 15. Second-order rate constants (k′) for the interaction of TEOHA (0.0100 M)
with HEMA (1–3 M) at pH 6.0–9.0 in the presence of CQ.
k'×102 M
–1 s
–1
pH Monomer:
water
ratio
(1.21:10)
Correlation
coefficient
Monomer:
water
ratio
(2.42:10)
Correlation
coefficient
Monomer:
water
ratio
(3.63:10)
Correlation
coefficient
6.0 3.35 0.987 2.72 0.989 2.33 0.989
7.0 4.04 0.989 3.51 0.989 2.86 0.990
7.5 5.54 0.993 4.65 0.988 4.01 0.987
8.0 6.97 0.994 5.89 0.992 5.12 0.989
9.0 7.78 0.995 6.78 0.990 5.89 0.990
149
for the interaction of HEMA and TEOHA in the presence of RF and also decrease
with an increase in HEMA concentration at all pH values. However, these rate
constants also increase with an increase in pH suggesting a higher interaction of the
amine radicals with HEMA in the alkaline region. The degree of interaction of the
amine radicals with HEMA would depend upon the reactivity and radical formation
of the photoinitiator in this reaction.
5.2.7. Mechanism of HEMA Polymerization
The mechanism of HEMA polymerization using CQ as a photoinitiator is
similar to that suggested for the polymerization reaction in the presence of RF
(Orellana et al., 1999) and has been discussed by Jakubaik et al. (2003).
Photoinitiated CQ-amine polymerization has been suggested to occur through
electron / proton transfer. It involves the formation of reactive radicals that initiate the
polymerization, by hydrogen atom abstraction from the amine (AH) by the triplet
state of CQ, mediated by photoinduced electron transfer through a radical ion pairs.
The radicals thus formed attach the C=C bond of the monomer to initiate
polymerization (Stansbury, 2000). The efficiency of the polymerization depends not
only on the efficiency of the quenching of the triplet state of CQ by AH, but also on
the relative importance of processes leading to the formation of radicals that are able
to initiate the polymerization. The mechanism of the polymerization of HEMA
involving CQ / TEOHA system is similar to that of Orellana et al. (1999) as presented
in Scheme 2.
150
Scheme 2. Photopolymerization of HEMA in the presence of CQ and TEOHA.
151
5.3. Safranin T as Photoinitiator
The results of the reactivity of RF and CQ as photoinitiators in the
polymerization of HEMA and the effects of pH, viscosity and TEOHA concentration
on the rates of these reactions have been discussed in Sections 5.1 and 5.2,
respectively. In order to evaluate the reactivity of safranin T (ST) as a photoinitiator
in this reaction under the present condition and its comparison with that of RF and
CQ as photoinitiators, the polymerization of HEMA in the presence of ST / TEOHA
system at pH 6.0–9.0 has been studied. The use of ST as a photoinitiator in the
polymerization of HEMA in aqueous and organic solvents has previously been
reported by some workers (Previtale et al., 1994; Encinas et al., 1996; Gomez et al.,
2003). The present work focuses on the kinetic aspects of these reactions.
5.3.1. Spectral Characteristics of ST Solutions
ST exhibits an absorption maximum at 520 nm (ε = 2900 M–1
cm–1
) in the
visible region (Dutta and Bhat, 1996) (Fig. 41). It would have a lower energy of the
excited triplet state compared to that of the RF and CQ which have relatively lower
absorption maxima (445 and 468 nm, respectively). A 4.31×10–5
M ST concentration
in HEMA solutions (absorbance = 0.125) has been used for the polymerization
reactions. Similar ST solutions (pH 6.0–9.0) on irradiation for a period of 1–5 min did
not show any absorbance change at the maximum indicating that ST concentration
remains constant during the reactions and the photoinitiator is stable to light during
irradiation in the polymerization reactions.
152
Fig. 41. Absorption spectrum of safranin T at pH 7.0.
153
5.3.2. Assay of HEMA
The same UV spectrophotometric method has been used for the assay of
HEMA during the polymerization reactions carried out in the presence of ST as in the
case of RF and CQ. The concentration values of HEMA for the reactions at 1–3 M
concentration in the pH range of 6.0–9.0 are given in Table 16. The values decrease,
with time, as a result of the loss of HEMA during the initial stages of the reactions as
observed in the case of RF and CQ. However, the magnitude of change is lower,
probably due to a difference in the reactivity of ST. The increase in the loss of
HEMA, with pH, is in accordance with the polymerization behavior observed in the
presence of RF and CQ and may involve a similar mechanism.
5.3.3. Kinetics of Photopolymerization
The loss of HEMA during the polymerization reactions in the presence of ST
also follows pseudo first-order kinetics within 5% concentration change at all pH
values (Fig. 42–46) as observed in the case of RF (Section 5.1) and CQ (Section 5.2).
Beyond this level the data do not fit the first-order linear plot suggesting a change in
the nature and mode of the reaction. The values of apparent first-order rate constants
determined at 6.0–9.0 for the polymerization of 1–3 M HEMA are reported in Table
17–19. The values of the rate constants are affected by the pH and viscosity of the
solutions in a manner similar to that observed in the case of data obtained in the
presence of RF and CQ as photoinitiators. This kinetic behavior of HEMA
polymerization has been explained earlier for the reactions carried out in the presence
of RF and CQ. The apparent first-order rate constants (kobs) determined for the
154
Table 16. Polymerization of HEMA (1 M) at pH 9.0 in presence of ST as
photoinitiator at various TEOHA concentrations.
TEOHA Concentration (M) Time
(sec) 0.0025 0.005 0.0075 0.01
0 1.000 1.000 1.000 1.000
10 0.997 0.994 0.991 0.991
20 0.995 0.991 0.987 0.986
40 0.991 0.985 0.979 0.971
60 0.987 0.979 0.971 0.964
80 0.983 0.974 0.959 0.951
155
R2 = 0.991
R2 = 0.991
R2 = 0.990
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 30 60 90 120 150 180
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 42. First-order plots for the polymerization of HEMA in the presence of ST at
pH 6.0. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
156
R2 = 0.993
R2 = 0.988
R2 = 0.989
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 30 60 90 120 150
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 43. First-order plots for the polymerization of HEMA in the presence of ST at
pH 7.0. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
157
R2 = 0.989
R2 = 0.990
R2 = 0.990
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 30 60 90 120
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 44. First-order plots for the polymerization of HEMA in the presence of ST at
pH 7.5. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
158
R2 = 0.988
R2 = 0.991
R2 = 0.991
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 20 40 60 80 100
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 45. First-order plots for the polymerization of HEMA in the presence of ST at
pH 8.0. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
159
R2 = 0.990
R2 = 0.994
R2 = 0.991
-0.100
0.000
0.100
0.200
0.300
0.400
0.500
0 20 40 60 80
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 46. First-order plots for the polymerization of HEMA in the presence of ST at
pH 9.0. HEMA: (●) 1.0 M, (■) 2.0 M, (▲) 3.0 M.
160
Table 17. The apparent first-order rate constant (kobs) for polymerization of HEMA (1
M) at pH 6.0–9.0 in presence of ST as photoinitiator at various TEOHA
concentrations.
kobs × 104 s
–1
pH 0.0025 M 0.0050 M 0.0075 M 0.010 M
6.0 0.78±0.045 1.36±0.060 2.03±0.095 2.57±0.13
7.0 1.00±0.052 1.53±0.072 2.32±0.12 2.98±0.14
7.5 1.47±0.061 2.49±0.11 3.64±0.16 4.45±0.22
8.0 1.57±0.068 3.01±0.15 3.98±0.20 5.45±0.21
9.0 2.09±0.099 3.17±0.15 4.85±0.24 6.08±0.27
161
Table 18. The apparent first-order rate constant (kobs) for polymerization of HEMA (2
M) at pH 6.0–9.0 in presence of ST as photoinitiator at various TEOHA
concentrations.
kobs × 104 s
–1
pH 0.0025 M 0.0050 M 0.0075 M 0.010 M
6.0 0.51±0.026 0.90±0.042 1.47±0.068 2.14±0.096
7.0 0.59±0.024 1.05±0.048 1.88±0.085 2.50±0.12
7.5 0.64±0.031 1.63±0.072 2.60±0.12 3.79±0.17
8.0 1.34±0.060 2.58±0.12 3.38±0.17 4.73±0.22
9.0 1.56±0.081 2.87±0.14 3.87±0.18 5.44±0.25
162
Table 19. The apparent first-order rate constant (kobs) for polymerization of HEMA (3
M) at pH 6.0–9.0 in presence of ST as photoinitiator at various TEOHA
concentrations.
kobs × 104 s
–1
pH 0.0025 M 0.0050 M 0.0075 M 0.010 M
6.0 0.29±0.012 0.77±0.042 1.19±0.058 1.79±0.085
7.0 0.49±0.028 0.94±0.048 1.40±0.065 2.10±0.10
7.5 0.63±0.029 1.41±0.068 2.17±0.11 3.28±0.14
8.0 1.00±0.055 1.85±0.072 2.88±0.15 4.14±0.21
9.0 1.22±0.058 2.32±0.12 3.22±0.157 4.81±0.25
163
polymerization reactions in the presence of ST are slightly lower than those obtained
in the presence of CQ indicating similar reactivities of the two compounds.
5.3.4. Effect of pH
Similar to the study of the polymerization reactions of HEMA carried out in
the presence of RF and CQ, the present work is also based on the reactions conducted
in the pH range of 6.0–9.0 to compare the reactivities of these photoinitiators. The
values of the apparent first-order rate constants (kobs) are close to those obtained in the
presence of CQ and increase with pH, for similar reason as stated in the case of RF
and CQ. On the basis of the values of these rate constants, the reactivity of ST
appears to be lower than that of RF and CQ. The rate-pH profiles for the
polymerization reactions in the presence of ST (Fig. 47) are similar to those of RF
and CQ, indicating a similar mechanism involved in these reactions. However, the
difference in the magnitude of rate constants is due to the differences in the reactivity
and radical formation of the photoinitiators. Thus the highest rate of polymerization
of HEMA also appears to be at pH 9.0 in this case or above as observed by
Valdebenito and Encinas (2003).
5.3.5. Effect of Viscosity
The photochemical reactions involving free radical or radical ion pairs are
generally affected by the viscosity of the medium (Turro et al., 2010). This has also
been observed in the polymerization reactions of HEMA carried out at 1–3 M
concentrations using RF and CQ as photoinitiators. In a similar manner the rate
constants for the polymerization reactions in the presence of ST have been found to
164
1 M
2 M
3 M
0.0
2.0
4.0
6.0
8.0
10.0
4.0 5.0 6.0 7.0 8.0 9.0 10.0
pH
ko
bs
× 1
04
(s–
1)
Fig. 47. Rate-pH profile for polymerization of HEMA (1–3 M) in presence of ST and
0.01 M TEOHA.
165
decrease with an increase in the viscosity of the medium (Table 17–19). A gradual
decrease in rates for the reactions carried out at 1–3 M HEMA concentrations have
been observed (Fig. 48). As explained earlier in the case of RF (Section 5.1.6) and
CQ (Section 5.2.5), the decrease in the rate constant in viscous media is probably a
result of triplet state quenching and changes in diffusional processes of the species
involved. This would result in a relatively low rate of interaction of the excited state
species and consequently a low rate of polymerization compared to that of RF and
CQ. These results indicate that it may be necessary to keep into consideration the
effect of viscosity on the rate of polymerization reactions and ultimately the yield of
the polymer.
5.3.6. Effect of TEOHA Concentration
The rates of polymerization reactions of HEMA in the presence of a fixed
concentration of ST and variable concentrations of TEOHA at pH 6.0–9.0 (Fig. 49–
53) are lower than those of RF and CQ indicating a lower reactivity of ST compared
with that of the other two photoinitiators. This would suggest a lower rate of
formation and interaction of the amine radicals and HEMA in the presence of ST
compared to that of RF and CQ. The second-order rate constants for the interaction of
HEMA (1–3 M) and TEOHA (0.0025–0.01 M) (Fig. 54) are reported in Table 20 and
are similar to those obtained in the presence of CQ under the same conditions.
However, the values are considerably lower than those obtained in the presence of
RF. Thus the photochemical behavior of ST in the polymerization reaction of HEMA
is similar to RF and CQ but its reactivity is lower than the two photoinitiators. This is
166
pH 6.0
pH 7.0
pH 7.5
pH 8.0
pH 9.0
0.0
2.0
4.0
6.0
8.0
10.0
0.4 0.5 0.6 0.7 0.8 0.9 1.0
Viscosity (mPa.s)–1
ko
bs
× 1
04
(s–
1)
Fig. 48. Plots of kobs for polymerization of HEMA in presence of CQ and 0.01 M
TEOHA versus inverse of solution viscosity. HEMA: (●) 1.0 M, (■) 2.0 M,
(▲) 3.0 M.
167
R2 = 0.992
R2 = 0.993
R2 = 0.988
R2 = 0.991
-0.030
-0.020
-0.010
0.000
0 30 60 90 120 150 180
log
co
nce
ntr
ati
on
(M
)
R2 = 0.986
R2 = 0.991
R2 = 0.987
R2 = 0.991
0.280
0.290
0.300
0.310
0 30 60 90 120 150 180
log
co
nce
ntr
ati
on
(M
)
R2 = 0.987
R2 = 0.993
R2 = 0.992
R2 = 0.990
0.460
0.464
0.468
0.472
0.476
0.480
0 30 60 90 120 150 180
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 49. First-order plots for the polymerization of HEMA (1–3 M) in presence of ST
as photoinitiator at different TEOHA concentrations (pH 6.0). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
168
R2 = 0.987
R2 = 0.992
R2 = 0.994
R2 = 0.993
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.990
R2 = 0.992
R2 = 0.990
R2 = 0.988
0.280
0.290
0.300
0.310
log
co
nce
ntr
ati
on
(M
)
R2 = 0.989
R2 = 0.988
R2 = 0.988
R2 = 0.989
0.460
0.464
0.468
0.472
0.476
0.480
0 40 80 120 160
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 50. First-order plots for the polymerization of HEMA (1–3 M) in presence of ST
as photoinitiator at different TEOHA concentrations (pH 7.0). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
169
R2 = 0.990
R2 = 0.991
R2 = 0.994
R2 = 0.989
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.987
R2 = 0.994
R2 = 0.992
R2 = 0.990
0.275
0.285
0.295
0.305
log
co
nce
ntr
ati
on
(M
)
R2 = 0.989
R2 = 0.989
R2 = 0.991
R2 = 0.990
0.450
0.460
0.470
0.480
0 30 60 90 120
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 51. First-order plots for the polymerization of HEMA (1–3 M) in presence of ST
as photoinitiator at different TEOHA concentrations (pH 7.5). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
170
R2 = 0.985
R2 = 0.989
R2 = 0.987
R2 = 0.988
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.987
R2 = 0.990
R2 = 0.988
R2 = 0.991
0.260
0.280
0.300
0.320
log
co
nce
ntr
ati
on
(M
)
R2 = 0.985
R2 = 0.990
R2 = 0.995
R2 = 0.991
0.450
0.460
0.470
0.480
0 20 40 60 80 100
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 52. First-order plots for the polymerization of HEMA (1–3 M) in presence of ST
as photoinitiator at different TEOHA concentrations (pH 8.0). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
171
R2 = 0.994
R2 = 0.987
R2 = 0.987
R2 = 0.990
-0.030
-0.020
-0.010
0.000
log
co
nce
ntr
ati
on
(M
)
R2 = 0.994
R2 = 0.987
R2 = 0.989
R2 = 0.994
0.260
0.280
0.300
0.320
log
co
nce
ntr
ati
on
(M
)
R2 = 0.988
R2 = 0.990
R2 = 0.990
R2 = 0.991
0.450
0.460
0.470
0.480
0 20 40 60 80
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 53. First-order plots for the polymerization of HEMA (1–3 M) in presence of ST
as photoinitiator at different TEOHA concentrations (pH 9.0). (×) 0.0025 M,
(■) 0.005 M, (▲) 0.0075 M, (●) 0.01 M TEOHA.
1M
2M
3M
172
R2 = 0.996
R2 = 0.992
R2 = 0.991
R2 = 0.995
R2 = 0.990
0.0
2.0
4.0
6.0
8.0
10.0
0.000 0.002 0.004 0.006 0.008 0.010
ko
bs
× 1
04
(s–
1)
R2 = 0.991
R2 = 0.992
R2 = 0.990
R2 = 0.994
R2 = 0.995
0.0
2.0
4.0
6.0
8.0
10.0
0.000 0.002 0.004 0.006 0.008 0.010
ko
bs
× 1
04
(s–
1)
R2 = 0.987
R2 = 0.992
R2 = 0.989
R2 = 0.995
R2 = 0.993
0.0
2.0
4.0
6.0
8.0
10.0
0.000 0.002 0.004 0.006 0.008 0.010
TEOHA concentration (M)
ko
bs
× 1
04
(s–
1)
Fig. 54. Second-order plots for polymerization of HEMA (1–3 M) in presence of ST
at various TEOHA concentrations (0.0025–0.01 M). pH: (●) 6.0, (■) 7.0,
(▲) 7.5, (♦) 8.0, (*) 9.0.
1M
2M
3M
173
Table 20. Second-order rate constants (k′) for the interaction of TEOHA (0.0100 M)
with HEMA (1–3 M) at pH 6.0–9.0 in the presence of ST.
k'×102 M
–1 s
–1
pH Monomer:
water
ratio
(1.21:10)
Correlation
coefficient
Monomer:
water
ratio
(2.42:10)
Correlation
coefficient
Monomer:
water
ratio
(3.63:10)
Correlation
coefficient
6.0 2.57 0.991 2.14 0.991 1.79 0.990
7.0 2.98 0.993 2.50 0.988 2.10 0.989
7.5 4.45 0.989 3.79 0.990 3.28 0.990
8.0 5.45 0.988 4.73 0.991 4.14 0.991
9.0 6.08 0.990 5.44 0.994 4.81 0.991
174
due to a lower energy of the wavelength of irradiation (520 nm) compared with those
of RF (445 nm) and CQ (468 nm). These rate constants are affected by the pH and
viscosity of the medium and are a function of the concentration of TEOHA used in
the reactions. The rates of polymerization are increased with an increase in TEOHA
concentration. It has been reported that the rate of polymerization of HEMA is
maximum in the presence of 0.01 M TEOHA (Orellana et al., 1999). In the present
case also the maximum concentration of TEOHA used in the polymerization reaction
is 0.01 M and its interaction with HEMA has been studied.
5.3.7. Mechanism of HEMA Polymerization
The kinetic behavior of the polymerization reactions of HEMA using RF, CQ
and ST as photoinitiators is similar with respect to pH, viscosity and TEOHA
concentration suggesting a similarity in the mechanism of these reactions. However,
the difference in the rates of polymerization in the presence of these photoinitiators is
probably due to variation in the reactivity of the individual photoinitiators and its role
in the process. The primary reaction in the polymerization process involves the
formation of the photoinitiator (e.g. RF) and amine radicals and subsequently the
interaction of amine radicals with HEMA to undergo polymerization as presented in
Scheme 1 (Orellana et al., 1999). A similar mechanism for the polymerization of
HEMA in the presence of ST has earlier been suggested by Encians et al. (1996) and
is presented in Scheme 3. It describes only the formation of amine radicals and no
further reactions to proceed to the polymerization of HEMA. This step was later
included in the scheme of Orellana et al. (1999) as given in Scheme 1.
175
Scheme 3. Photopolymerization of HEMA in the presence of ST and TEOHA.
CHAPTER VI
POLYMERIZATION OF
HEMA IN NONAQUEOUS
SOLUTIONS
177
The influence of solvent on the rates and mechanism of chemical reactions is
of great importance and has been discussed by many workers (Amis and Hinton,
1973; Reichardt, 1988; Buncel et al., 2003; Sinko, 2006; Turro et al., 2010). The
majority of the chemical reactions occurring in solution media are affected by solvent
characteristics such as dielectric constant, viscosity and solvating power. These
properties play an important role in determining the rate as well as the equilibrium of
the reaction. The transition state theory may predict the effects of changes in solvent
polarity on the rates of chemical reactions. It can further predict the ability of the
solvent to interact with the solute and thus solvate charged species undergoing the
reaction.
6.1. Types of Bimolecular Reactions
The various types of bimolecular reactions in organic solvents occur as
follows.
a. Neutral nonpolar reactants giving neutral nonpolar products
In this case the transition state would also be nonpolar, and in such a case a
change in solvent polarity would have little effect on the rate of reaction.
b. Neutral reactants giving charged products
In these reactions the transition state would be more polar than the initial state.
This results from the partial charge separation in the transition state. In this
case an increase in solvent dielectric constant (polarity) would result in an
increase in the rate of the reaction. The following quaternization reaction is an
example of this type of behavior in bimolecular reaction (the transition-state
structure in this reaction is enclosed in brackets and the dashed lines signify
178
the bonds that are partially formed or broken). In the experimental approach
solvent polarity can be the changed by replacing one solvent by another (Eq.
6.1).
c. Neutral molecule-ion reactions
In these reactions the transition state would be less polar than the initial state.
This would occur because the same charge would be spread over a greater
volume in the transition state. Thus an increase in the polarity of the solvent
would result in a decrease in the rate of reaction. In some cases the results of
this type of reaction may be difficult to interpret because as a result of
alteration of the reaction medium, factors other than the polarity are also
changed. This behavior would complicate the interpretation of these reactions.
d. Ion-ion reactions
If the reactants are two ions of opposite charge, then the transition state would
have less or no charge and, therefore, less polar than the initial state. In this
reaction an increase in the polarity of solvent would tend to decrease the rate.
If the two ionic reactants have the same charge, the opposite would occur
(Connors et al., 1986).
The activation energy of a reaction is dependent on the type of the reaction. It
does not change rapidly from one solvent to the other. The entropy of activation is
always negative and changes with the nature of the solvent. It becomes more negative
179
with a decrease in solvent polarity. Thus the reactions that produce products more
polar than the reacting species proceed well in polar solvents (Amis and Hinton et al.,
1973).
6.2. Solvent Effect on Polymerization Reactions
In relevance to polymerization reactions, it is useful to examine a plausible
sequence of steps that might occur along a reaction coordinate as a donor approaches
the acceptor (for which either the donor or the acceptor is electronically excited). In
such a case the reaction concludes with the electron transfer to form a radical ion pair.
The separation of the radical ion pair into free radicals and their rate of interaction
with the monomer would depend upon the solvent characteristics including polarity
and viscosity. The reaction would include a number of possible intermediate that
might exist along the reaction coordinate (Eq. 6.2).
Assuming the donor as an electronically excited species (*D) and that *D
encounters A and this leads to the formation of an encounter complex (*DA)ex. This
then forms an exciplex with delocalized excitation, symbolized as *(D, A)ex. In the
next stage, electron transfer takes place in the exciplex which is converted to a
contact radical ion pair (CRIP, symbolized as D●+
, A●¯ ). This is followed by insertion
of one or more solvent molecules between the partners of the radical ion pair to form
180
a solvent separated radical ion pair (SSRIP, symbolized as D●+
(S) A●¯ ). Finally the
ions separate to become free radical ions (FRIs) in the bulk solvent (FRI, D●+
, A●¯ ).
At various stages, each step along this hypothetical pathway will compete with other
possible pathways, such as chemical reactions or back electron transfer. Thus, the
radical ion pairs, CRIP, SSRIP, and FRI appear to be similar chemical species, since
they both formally consist of a D●+
and A●¯ units. However, they may possess vastly
different rates for back electron transfer to form D + A because of the distance
dependence of electron transfer and the reorganization energies involved in a
particular solvent.
The energetic term associated with electron transfer have a strong dependence
on the distance between charges
where Sp refers to a rigid molecular framework that serves as a spacer and allows
electron transfer in liquids but prevent diffusion D and A.
From (Eq. 6.5), it could be conceived that nascent radical ion pairs may have different
initial structures (Eq. 6.6) depending on the nature of the reaction that generated them
and the solvent properties for stabilizing the development of charges. In certain cases
D and A may be able to form a ground-state electron-transfer stabilized complex and
electron transfer may occur directly following excitation of this complex (Eq. 6.6).
181
In this case, the partners of the initial radical ion pair (D●+
, A●¯ ) must be a
geminate CRIP, since they were in contact in order to form a ground-state CT
complex (GSCTC). In this way, the initial geminate radical ion pair (D●+
, A●¯ ) is
formed with no solvent molecules separating the partners of the pair (Turro et al.,
2010). This treatment may apply to polymerization reaction in solution media
depending upon the nature of the solvent in which the reaction is being carried out.
6.3. Photoinduced Electron Transfer
Miller and Closs (1984, 1986, 1988) have demonstrated the validity of the
fundamental principles of Marcus’ theory (Marcus, 1956, 1959, 1960) of electron
transfer for a nonphotochemical system. The principles of this theory have been
applied to explain the nature of photochemical reactions. In the majority of examples
for application of Marcus theory to photochemical reactions, the key electron-transfer
steps are frequently back electron transfers from “ground-state” D●+
, A●¯ radical ion
pairs produced by photoinduced electron transfer. The concepts of Marcus theory
influence the efficiency of charge separation and the yield of final products in a
photoreaction controlled by electron transfer energetics.
6.3.1. Long-distance Electron Transfer
This involves electron transfer reactions that occur over distances significantly
larger than the sum of the van der Walls radii and of the electron donor and the
182
acceptor. An understanding of these electron transfer reactions is fundamental for an
understanding of important electron-transfer processes such as photopolymerization
and photosynthesis. The understanding of the mechanism of these processes requires
a knowledge of factors such as how the electron-transfer rate depends on the distance
of separation from the electron donor and acceptor (RDA), on the relative orientation
of D and A (which determines the effective orbital overlap), and on the nature of
intervening medium (solvent, rigid spacer, flexible spacer, supramolecular medium)
that separate the electron donor and acceptor. The rate constants for electron transfer
depend on the electronic coupling between the donor (D) and acceptor (A) involved
in an electron-transfer reaction. The magnitude of electronic coupling depends on the
wave functions of D and A. The mechanism of long distance electron-transfer
reactions have been discussed by Turro et al. (2010) in detail.
6.4. Photoinitiated Polymerization
Great interest has been shown in the polymerization of vinyl monomers
induced by light and the subject has been reviewed by several workers (Oster and
Yang, 1968; Eaton, 1986; Paczkowski et al., 1999; Encinas and Previtali, 2006). The
kinetic of free-radical polymerization can be represented by classical scheme that
comprises the photochemical radical production, the initiation chain, the propagation
and the termination steps. A key in these processes is the involvement of the
photoinitiator, which produces radicals through the photochemical process and
ultimately leads to polymerization. Among the principle characteristics of a
photoinitiators is a high absorption in a visible region (e.g., riboflavin). The
photoinitiators that absorb in the visible light allow (i) to find spectral windows when
183
pigmented formulations have to be polymerized, (ii) the use of the sun light for a
curing of outdoor coationgs. (iii) to imply laser beams as light source. Also
photoinitiators that can be used in polymerization in aqueous media are of interest
because of their ecological advantages. Riboflavin (vitamin B2) absorbs in the 400-
500 nm region, and fulfils these requirements. It has been used as a photoinitiator in
the polymerization of hydroxyethyl methacrylate (HEMA) by Oster et al., 1957;
Bertolotti et al., 1999; Orellana et al., 1999 and Encinas, 2001, and in the present
study along with other photoinitiators (i.e., camphorquinone and safranin T).
The efficacy of photoinitiators in the polymerization of HEMA may be
affected by medium characteristics including the polarity and viscosity and the extent
of radical formation. Several studies have been carried out on the effect of solvent on
photopolymerization of HEMA using dilatometry (Encinas et al., 1996; Valdebenito
and Encinas, 2003), gas chromatography (Beers et al., 1999), Raman spectroscopy
(Wang et al., 2006), ATR-FTIR spectroscopy (Guo et al., 2008), and differential
scanning calorimetry (DSC) (Anderzejewska et al., 2009). The present work is based
on the study of the effect of solvent dielectric constant and viscosity on the rate of
photopolymerization of HEMA in aqueous and organic solvents using a UV
spectrophotometric method. Riboflavin (λmax = 445 nm) (Heelis, 1982),
camphorquinone (λmax = 468 nm) (Jakubiak et al., 2003), and safranin T ((λmax = 520
nm) (Dutta and Bhat, 1996) and triethanolamine as co-initiator (Encinas et al., 1996;
Valdebenito and Encinas, 2003; Encinas et al., 2009) in the reaction. The study
throws light on the effect of solvent characteristics, interactions and kinetics of
HEMA polymerization. A comparative study of the reactivity of different
184
photoinitiators in aqueous and organic solvents has been made to highlight the effect
of solvent parameters on the kinetics of these reactions.
6.5. Effect of Dielectric Constant
The rate of the reactions between dipolar molecules is dependent on the
dielectric constant, D, of the medium (Sinko, 2006).
ln k = ln k D =∞ − K (1/D) (6.7)
where kD=∞ is the rate constant in a medium of infinite dielectric constant. The
dielectric constant of the medium is approximately equal to the dielectric constant of
the solvent in dilute solutions. A decrease in dielectric constant of the medium tends
to decrease the rate of reaction, and conversely.
6.5.1. Riboflavin as Photoinitiator
The polymerization reactions of HEMA were carried out in aqueous and
organic solvents containing RF and 0.01 M TEOHA. The values of HEMA
concentrations in water, acetonitrile, methanol and ethanol determined during
photopolymerization are reported in Table 21. The values for the reactions in 1-
propanol and 1-butanol could not be obtained due to the insolubility of RF in these
solvents. The apparent first-order rate constants (kobs) for the polymerization of
HEMA in the presence of RF as photoinitiator and TEOHA as a co-initiator were
determined from the slopes of the straight lines of log concentration versus time plots
in water and organic solvents (Fig. 55) and are reported in Table 22. The
determination of kobs in this study is based on the steady-state assumption that the rate
of initiation being equal to the rate of termination is considered valid only at a low
185
Table 21. Polymerization of HEMA in the presence of RF and TEOHA in aqueous
and organic solvents.
HEMA concentrations (M) Time
(sec) water acetonitrile methanol Ethanol
0 1.000 1.000 1.000 1.000
10 0.993 0.995 0.996 0.997
20 0.990 0.991 0.993 0.993
30 0.986 0.988 0.990 0.990
40 0.980 0.984 0.986 0.987
50 0.976 0.980 0.983 0.985
60 0.969 0.977 0.980 0.982
70 0.966 0.974 0.976 0.979
80 0.959 0.970 0.971 0.974
186
R2 = 0.994
R2 = 0.994
R2 = 0.996
R2 = 0.993
-0.030
-0.020
-0.010
0.000
0.010
0 10 20 30 40 50 60 70 80
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 55. First-order plots for the polymerization of HEMA in the presence of RF in
aqueous and organic solvents. (×) Water; (●) acetonitrile; (▲) methanol; (♦)
ethanol.
187
Table 22. Apparent first-order rate constants (kobs) for the polymerization of HEMA
in water and organic solvents. Effect of dielectric contants.
kobs × 104 (s
–1)a
Solvent
Dielectric
Constant
(25ºC) RF CQ ST
Water 78.5 5.05 4.04 2.98
Acetonitrile 37.5 3.71 3.02 2.10
Methanol 32.6 3.53 2.90 1.93
Ethanol 24.3 3.12 2.62 1.71
1-Propanol 20.1 – 2.45 1.56
1-Butanol 17.1 – 2.39 1.45
a The values of rate constants are relative and depend on specific experimental
conditions including light intensity.
188
conversion of monomer (Jakubaik et al., 2003). In the present case the values of kobs
have been determined from the analytical data obtained on HEMA assay during the
initial stages of the reaction (within ~5% change), on exposure to a low intensity
radiation source. Under these conditions the first-order plots have been found to be
linear in the desired range. In order to develop a correlation between kobs and
dielectric constant (D) of the medium, a plot of kobs versus dielectric constant of the
solvents was constructed (Fig. 56). It was observed that the rate of reaction is
dependent upon the solvent and is a linear function of the dielectric constant of the
medium, i.e. increasing with an increase in the solvent dielectric. Since RF is used as
a photoinitiator in this reaction, the behavior of RF could be explained on the basis of
the existence of a polar flavin (Fl) intermediate, which would facilitate the
polymerization reaction with an increase in the polarity of the medium. A strong
evidence for the presence of such an intermediate has been presented by Ahmad and
Tollin (1981a) who studied the solvent effect on flavin electron transfer reactions
using laser flash photolysis. According to these workers the reduction of flavin triplet
(3Fl) by the substrate (amine (AH) in this case) proceeds via a dipolar intermediate in
water and organic solvents and, therefore, the rate is increased with an increase in
solvent dielectric.
The extent of solvent interaction of the dipolar intermediate would determine the
degree to which it leads to the formation of separate radicals. In these reactions the
189
RF
CQ
ST
0.0
1.0
2.0
3.0
4.0
5.0
0 10 20 30 40 50 60 70 80
Dielectric constant
ko
bs ×
10
4 (
s–1)
Fig. 56. Plots of kobs for polymerization of HEMA against dielectric constant. (×)
Water; (●) acetonitrile; (▲) methanol; (♦) ethanol; (■) 1-propanol; (∗) 1-
butanol.
190
primary photochemical process is considered as being the electron transfer between
reactants. In such a case the transition state would be more polar than the reactant and
the rate of reaction would increase with the dielectric constant of the medium as
observed in the case of the photolysis of formylmethylflavin (Ahmad et al., 2006). It
needs to be emphasized that the flavin excited triplet state lifetimes vary depending
on the solvent characteristics (Ahmad and Tollin, 1981a) and this would affect the
rate of reaction. Thus the polarity of the medium in which the polymerization of
HEMA is being carried out would exert an effect on the rate of reaction depending
upon the polar character of the medium. Water, with the highest dielectric constant,
appears to be the best medium for carrying out the polymerization of HEMA to obtain
a greater yield than those of the organic solvents. The dependence of the
polymerization rate on the solvent may be due to changes in the initiation,
propagation and / or termination steps and has been discussed with reference to the
effect of azo compounds by Encinas et al. (1996).
It has been reported that the rates of polymerization of HEMA are decreased
with a decrease in medium polarity, i.e. from water to acetonitrile, as a result of
singlet quenching in organic solvents (Encinas et al., 1996; Valdebenito and Encinas,
2003). The present study is in agreement with the observations of these workers and a
decrease in the fluorescence of RF has been found in organic solvents (Section 6.6.1).
6.5.2. Camphorquinone as Photoinitiator
The results of the effect of solvent dielectric constant on the rate of
polymerization of HEMA in the presence of CQ as photoinitiator may be considered
191
on the basis of the data discussed above in the case of RF as a photoinitiator. The
CQ/amine photoinitiator system for generating radicals has been widely used for the
polymerization of dental restorative materials. In this system the absorption of light in
the visible region leads to the n–π* transition of the dicarbonyl group (Tsai and
Charney, 1969). The excited state interacts with TEOHA to form an exciplex. The
exciplex accepts an electron from TEOHA to produce a radical ion pair. This
abstracts a hydrogen atom from the TEOHA resulting in the formation of the primary
radical. This radical would attack the C=C bonds of the monomer (HEMA) to
undergo polymerization. The CQ radical may retard polymerization through
termination reaction (Stansbury, 2000). The theory of processes involved in
photopolymerization has been discussed in Section 6.2 and 6.3.
The assay of HEMA in aqueous and organic solvents in the presence of CQ is
reported in Table 23. The apparent first-order rate constants determined for the
polymerization reactions in the presence of CQ as a photoinitiator (Fig. 57) are given
in Table 22. The polymerization behavior of HEMA in aqueous and organic solvents
is similar to that observed in the presence of RF with respect to the effect of dielectric
constant (Fig. 56). However, the values of kobs in this case are lower than those
observed for RF and may be due to a lower reactivity of the excited state and
subsequent radical formation in this reaction. In view of the structural consideration
(C=O groups), the polar character of the radicals formed from CQ would be lower
than that of RF (a highly conjugated system), resulting in lower rate constants for the
reactants. The effectiveness of CQ / TEOHA system depends on the H-atom donor
ability of the amine in a particular environment, and the subsequent interaction of the
192
Table 23. Polymerization of HEMA in the presence of CQ and TEOHA in aqueous
and organic solvents.
HEMA concentrations (M) Time
(sec) Water acetonitrile methanol ethanol 1-propanol 1-butanol
0 1.000 1.000 1.000 1.000 1.000 1.000
20 0.992 0.993 0.995 0.995 0.996 0.997
40 0.985 0.985 0.990 0.991 0.991 0.993
60 0.978 0.982 0.985 0.986 0.985 0.988
80 0.967 0.976 0.980 0.981 0.982 0.984
100 0.962 0.970 0.974 0.976 0.978 0.979
120 0.953 0.964 0.966 0.969 0.971 0.972
140 0.945 0.957 0.960 0.964 0.966 0.968
193
R2 = 0.997
R2 = 0.995
R2 = 0.992
R2 = 0.995
R2 = 0.994
R2 = 0.991
-0.030
-0.020
-0.010
0.000
0 20 40 60 80 100 120 140
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 57. First-order plots for the polymerization of HEMA in the presence of CQ in
aqueous and organic solvents. (×) Water; (●) acetonitrile; (▲) methanol; (♦)
ethanol; (■) 1-propanol; (∗) 1-butanol.
194
photoinitiator excited species with the monomer (HEMA) to undergo polymerization
(Guo et al., 2008). The rates of the reaction would be affected by the nature and
polarity of the medium involved and the extent of radical formation.
6.5.3. Safranin T as Photoinitiator
The assay of HEMA in aqueous and organic solvents in the presence of CQ is
reported in Table 24. The apparent first-order rate constants for the polymerization of
HEMA in ST / TEOHA system in aqueous and organic solvent (Fig. 58) are reported
in Table 22. A plot of these rate constants (kobs) as a function of the solvent dielectric
constant is shown in Fig. 56. These results indicate that the reactivity of ST is lower
than that of RF and CQ as photoinitiators. Apart from a consideration of the excited
state polarization behavior of this molecule and subsequent polarity of the
intermediate involved in this reaction, the visible absorption maximum (520 nm) of
ST is higher than that of RF (445 nm) and CQ (468nm). This would provide a
relatively less energy for the activation of the molecule and would probably have a
lower efficiency compared with that of the other two photoinitiators. Thus the rates of
polymerization of HEMA in this case are lower than those obtained in the presence of
RF and CQ. The polymerization of HEMA in methanolic solutions using the
photoinitiator ST in the presence of tertiary aliphatic amines has been studied by
Previtali et al. (1994). The polymerization rates increase with the amine concentration
reaching a maximum, and further amine addition slowly reduces the polymerization
rate. The results indicate that the polymerization of HEMA involves the interaction of
the excited triplet state of ST with the amine and this would be affected by the solvent
characteristics.
195
Table 24. Polymerization of HEMA in the presence of ST and TEOHA in aqueous
and organic solvents.
HEMA concentrations (M) Time
(sec) Water acetonitrile methanol ethanol 1-propanol 1-butanol
0 1.000 1.000 1.000 1.000 1.000 1.000
30 0.992 0.993 0.994 0.994 0.995 0.996
60 0.984 0.985 0.987 0.988 0.990 0.993
90 0.972 0.978 0.980 0.982 0.987 0.989
120 0.964 0.973 0.975 0.977 0.980 0.985
150 0.958 0.968 0.970 0.974 0.976 0.979
180 0.948 0.963 0.967 0.970 0.973 0.974
196
R2 = 0.996
R2 = 0.991
R2 = 0.988
R2 = 0.987
R2 = 0.993
R2 = 0.988
-0.030
-0.020
-0.010
0.000
0 30 60 90 120 150 180
Time (seconds)
log
co
nce
ntr
ati
on
(M
)
Fig. 58. First-order plots for the polymerization of HEMA in the presence of ST in
aqueous and organic solvents. (×) Water; (●) acetonitrile; (▲) methanol; (♦)
ethanol; (■) 1-propanol; (∗) 1-butanol.
197
The slopes of the plots of kobs for the polymerization of HEMA versus
dielectric constants of the solvents used in the presence of different photoinitiators are
in the order:
RF > CQ > ST
indicating the magnitude of the solvent effect on the reactivity of these
photoinitiators in conducting the polymerization reaction. Thus RF appears to be the
best photoinitiators for HEMA polymerization.
6.6. Effect of Viscosity
6.6.1. Riboflavin as Photoinitiator
Another important factor that may influence the rate of a chemical reaction is
the viscosity of the medium. This appears to control the solute diffusion and hence
the rate of a reaction. A pervious study has shown that the flavin triplet (3Fl)
quenching by a substrate in proportional to the inverse of solvent viscosity as
expected for a diffusional process (Ahamd and Tollin, 1981a).
Polymerization reactions of HEMA in water at 1, 2, and 3 M concentrations
have shown that the rates are decreased with an increase in the viscosity of the
medium (Section 5.1.6, 5.2.5, 5.3.5) as observed by other workers (Anderzejewska et
al., 2009). A study of polymerization of HEMA in various solvents has shown that
the rates are affected by Hildebrand solubility parameters and the viscosities of the
solvent. The rates are faster in water compared to those determined in acetonitrile
(Encinas et al., 1996). In order to confirm the effect of medium viscosity on the rates
198
of these reactions, the values of kobs in organic solvents were plotted as a function of
the inverse of solvent viscosity (Table 25), and a linear relationship was observed as
expected (Fig. 59). These observations are supported by the data of rate constants
reported by Valdebenito and Encinas (2003) who reported a decrease in fluorescence
quantum yields of the photoinitiator with an increase in viscosity in organic solvents
compared to that obtained in aqueous medium. The decrease in fluorescence intensity
of RF in organic solvents (Table 26) indicates the effect of solvent viscosity (Fig. 59)
on the polymerization reaction. This may be explained on the basis of flavin excited
singlet quenching in organic solvents as a result of change in solvent viscosity. The
radical-radical reactions, as in the case of polymerization of HEMA, are sensitive to
solvent viscosity (Turro et al., 2010). The decrease in the rate of polymerization has
also been ascribed to the combination of a monomer viscosity effect (Biasutti et al.,
2003).
6.6.2. Camphorquinone as Photoinitiator
The effect of viscosity on the rate of polymerization of HEMA using CQ as a
photoinitiator shows a similar behavior as observed in the case of RF. A plot of kobs
versus the inverse of solvent viscosity shows a linear relationship and the rates tend to
decrease with an increase in the viscosity of the medium. This appears to be due to a
decrease in solute diffusional processes with an increase in solvent viscosity. The
slope of the plot (Fig. 59) indicates that viscosity exerts a lower effect on the rates in
the presence of CQ compared to that of RF.
199
Table 25. Apparent first-order rate constants (kobs) for the polymerization of HEMA
in water and organic solvents. Effect of viscosity.
kobs × 104 (s
–1)a
Solvent Viscosity
(mPa.s)–1
RF CQ ST
Water 1.000 5.05 4.04 2.98
Acetonitrile 2.898 3.71 3.02 2.10
Methanol 1.838 3.53 2.90 1.93
Ethanol 0.931 3.12 2.62 1.71
1-Propanol 0.514 – 2.45 1.56
1-Butanol 0.393 – 2.39 1.45
a The values of rate constants are relative and depend on specific experimental
conditions including light intensity.
200
RF
CQ
ST
0.0
1.0
2.0
3.0
4.0
0.0 0.5 1.0 1.5 2.0 2.5 3.0
Viscosity (mPa.s)–1
ko
bs
× 1
04
(s–
1)
Fig. 59. Plots of kobs for polymerization of HEMA against inverse of solvent
viscosity. (●) acetonitrile; (▲) methanol; (♦) ethanol; (■) 1-propanol; (∗)
1-butanol.
201
Table 26. Fluorescence intensity of 1×10–5
M RF in water and organic solvents.
Solvent Relative fluorescence intensity at 520 nm
Water 100.0
Ethanol 87.1
Methanol 86.7
Acetonitrile 84.1
202
6.6.3. Safranin T as Photoinitiator
The results obtained with ST as a photoinitiator in the polymerization of
HEMA are similar to those of RF and CQ. A plot of kobs versus inverse of solvent
viscosity shows a linear relationship (Fig. 59) and the rates are further lower than
those observed in the case of CQ. The effect of viscosity on the rates of
polymerization of HEMA using ST as a photoinitiator is lower than that observed in
the presence of RF and CQ. Thus viscosity appears to play a significant role in the
photopolymerization of HEMA. The results indicate that in the polymerization of
HEMA, the effect of solvent characteristics should be taken into consideration to
facilitate the reaction and to achieve greater yields of the polymer.
6.7. Spectral and Structural Characteristics of Photoinitiators
In order to provide further explanation of the reactivity of the three
photoinitiators (RF, CQ, ST) used in this study, a consideration of the structural
characteristics and ionization behavior of these compounds is necessary. The
chemical structures of these photoinitiators are shown in Fig. 10 and 12.
RF absorbs at 445 nm and undergoes π–π* transitions resulting in high molar
absorptivity. It is a highly conjugated polar compound (pKa 1.9, 10.2) and exists as a
dipolar molecule in aqueous solution. It compared with RF, CQ possesses weakly
ionizable C=O groups. The light absorption at 468 nm would lead to n– π* transition
of the dicarbonyl group in the molecule which has low molar absorptivity. Hence its
efficiency in water would be lower compared to that of RF as observed. ST (pKa 4.0)
is an ionizable compound and absorbs at 520 nm to undergo π–π* transition. All these
203
photoinitiators, on excitation, produce radicals which interact with the amine and thus
initiate the polymerization of HEMA. The degree of interaction of these
photoinitiators with TEOHA would depend on the yield of these radicals in aqueous
and organic solvents. The rate of the reaction would depend on the viability of the
radical ion pair in a specific medium leading to polymerization.
6.8. Mechanism of Polymerization
RF is known to produce a polar intermediate on light absorption which would
further proceed to form radicals (Ahmad and Tollin, 1981a), and then interact
efficiently with the amine to initiate polymerization. The efficiency of CQ and ST is
lower than that of RF as explained in this chapter. The mechanisms of photoinitiated
polymerization of HEMA using RF (Orellana et al., 1999), CQ (Jakubiak et al.,
2003), and ST (Valdebenito and Encinas, 2003) as initiators have been reported.
However, these mechanisms involve similar steps to produce the amine radicals that
interact with HEMA resulting in the polymerization as presented earlier in schemes
1_3. Based on these mechanisms, a general scheme for the polymerization of HEMA
in the presence of different photoinitiators and the amine in presented in Fig. 60.
The photoinitiator (PI) on the absorption of light is promoted to the excited
singlet state (1PI*), followed by intersystem crossing (isc) to the excited triplet state
(3PI*).
3PI* abstracts a hydrogen atom from the amine, mediated by photoinduced
electron transfer through the radical ion pair. The free radicals thus formed in the
reaction add to the double bonds of HEMA monomer and thus initiate the
polymerization process. The rates and the extent of polymerization would depend on
204
the polarity and viscosity of the solvent used. It would also depend on the reactivity
and the efficacy of the photoinitiator used since the radical produced and their degree
of interaction with HEMA would determine the yield of the polymer.
205
Fig. 60. A general scheme for the polymerization of HEMA in the presence
of photoinitiators and amine.
CONCLUSIONS
AND
SUGGESTIONS
207
CONCLUSIONS
The conclusions of the present study on the polymerization of HEMA may be
summarized as follows.
1. Identification of Photodegradation Products of Riboflavin (RF)
RF solution (1×10-5
M) undergoes minor photodegradation at pH 9.0 during
irradiation for 5 min with a low intensity lamp (15 W) emitting in the visible region.
The products detected by thin layer chromatography are formylmethylflavin,
lumichrome and lumiflavin. However, there is no detectable spectral change affecting
the absorbance of RF at the maximum at 445 nm (0.125) on irradiation for about 1
min, the time involved in polymerization reactions. Similarly no changes in the
intensity of absorption of camphorquinone (CQ) and safranin T (ST) solutions
(absorbance 0.125) have been observed at the maxima at 468 nm and 520 nm,
respectively, during irradiation for 1–2 min. These compounds have been used as
photoinitiators in the polymerizations reactions carried out in the present study.
2. Assay of HEMA in Polymerized Solutions
A UV spectrometric method has been developed for the assay of HEMA at
208 nm in polymerized solutions at various pH values. It has also been applied to the
determination of HEMA in organic solvents under the same conditions. The method
has been found to give satisfactory results within about 5% change in the monomer
concentration. This is necessary to avoid any changes in the volume / viscosity of
polymerized solutions.
208
3. Kinetics of Polymerization Reactions in Aqueous Solution
The polymerization of HEMA has been studied in aqueous solution in the
presence of RF, CQ and ST as photoinitiators and triethanolamine (TEOHA) as a co-
initiator and the apparent first-order rate constants (kobs) have been determined for the
initial stages of the reactions. Under the steady-state assumption, the rate of initiation
being equal to the rate of termination is considered valid only at a low conversion of
the monomer. It has been observed that during the initial stages (upto about 5%
change), the reaction follows an apparent first-order kinetics. The rates of the
reactions increase with pH in the range of 6.0-9.0 (kobs 5.44–7.63×10–4
s–1
) probably as
a result of the gradual deprotonation of the amine which may produce a higher yield
of radicals for interaction with HEMA to undergo polymerization. An increase in
TEOHA concentration in the range of 0.0025-0.01 M has been found to increase the
rate of polymerization reactions. The second-order rate constants for the interaction of
HEMA and the amine are of the order of 1.79–8.87×10–2
M–1
s–1
. These values are
also affected by pH and the rates of interaction increase with an increase in the pH of
the solutions. The rate of polymerization reactions is also affected by changes in the
viscosity of the solutions (1–3 M concentration) and is lowered with an increase in
the viscosity of the medium due to changes in the diffusional processes.
4. Kinetics of Polymerization Reactions in Organic Solvents
The polymerization reactions of HEMA carried out in organic solvents
(acetonitrile, methanol, ethanol, 1-propanol, 1-butanol) indicate the effect of solvent
dielectric constant and viscosity on the rate of the reactions. A linear relation has been
209
observed between kobs and the solvent dielectric constant suggesting the presence of a
polar intermediate in the reaction pathway to facilitate polymerization in polar
medium. Thus the polarity of the medium does influence the rate of polymerization
reactions. A linear relation has also been observed between kobs and the inverse of
solvent viscosity indicating that an increase in the viscosity of the medium results in a
decrease in the rate of the reaction. This could be due to a relatively low diffusion of
solute in the medium as well as the triplet state quenching of the photoinitiators. The
rates of polymerization reactions are lower in organic solvents compared to aqueous
solutions due to difference in the polarity and viscosity of the medium.
5. Mechanism of HEMA Polymerization
The kinetic data indicate a similarity in the mechanism of the polymerization
reactions in the presence of different photoinitiators (RF, CQ, ST). These reactions
basically involve the formation of photoinitiator and amine radicals by electron /
proton transfer followed by the interaction of amine radicals and HEMA to undergo
polymerization. Reactions scheme for the mechanism of the polymerization of
HEMA in the presence of RF, CQ, ST and amine have been presented by different
workers. In all these reactions the final step involves the interaction of amine radicals
and HEMA and the rate of reaction would depend on the formation and degree of
interaction of amine radicals with HEMA. However, the rate of the reaction and
radical yield would be affected by the medium characteristics. It has been found that
the reactivity of RF as a photoinitiator is greater than CQ and ST and water is the best
medium for the polymerization of HEMA.
210
SUGGESTIONS
The following suggestions can be made on the polymerization of HEMA on
the basis of the work presented in this study.
The present work has shown the reactivity of certain photoinitiators (RF, CQ,
ST) in the polymerization of HEMA in aqueous and organic solvents. Considering
water as the best medium for the polymerization of HEMA, further studies may be
conducted to evaluate the reactivity of these photoinitiators in the presence of other
amine derivatives as co-initiators to optimise the reaction. Similarly, it would be a
good idea to use other photoinitiators mentioned in the literature and ascertain
whether there reactivity and efficacy is greater than those used in this present study.
Attempts can be made to develop conditions to optimize the reactivity of selected
photoinitiators in the polymerization of HEMA. Under specified conditions the
maximum concentration of the amine needs to be established to achieve greater yields
in the polymerization reactions. Laser flash photolysis studies on these reactions may
throw light on the delicate mechanistic aspects and factors affecting radical formation
and interaction leading to polymerization.
REFERENCES
212
Ahmad, I. (1968). A Study of the Degradation of Riboflavin and Related Compounds,
Ph.D. Thesis, University of London, London.
Ahmad, I., Rapson, H.D.C. (1990). Multicomponent spectrophotometric assay of
riboflavin and photoproducts. J. Pharm. Biomed. Anal., 8, 217–223.
Ahmad, I., Tollin, G. (1981a). Solvent effect on flavin electron transfer reactions.
Biochemistry, 20, 5925–5928.
Ahmad, I., Tollin, G. (1981b). Flavin triplet quenching and semiquinane formation by
aliphatic α-substituted acetic acids: intermediates in flavin sensitized
photodecarboxylation. Photochem. Photobiol., 34, 441–445.
Ahmad, I., Vaid, F.H.M. (2006). Photochemistry of flavin in aqueous and organic
solvents. In: E. Silva. and A.M. Edwards (Eds.), Flavins Photochemistry and
Photobiology. The Royal Society of Chemistry, Cambridge, pp. 13–40.
Ahmad, I., Cusanovich, M.A., Tollin, G. (1981). Laser flash photolysis studies of
electron transfer between semiquinone and fully reduced free flavins and horse
heart cytochrome c. Proc. Natl. Acad. Sci. USA, 78, 6724–6728.
Ahmad, I., Cusanovich, M.A., Tollin, G. (1982). Laser flash photolysis studies of
electron transfer between semiquinone and fully reduced free flavins and the
cytochrome c-cytochrome oxidase complex. Biochemistry, 21, 3122–3128.
Ahmad, I., Fasihullah, Q., Vaid, F.H.M. (2004a). A study of simultaneous photolysis
and photoaddition reactions of riboflavin in aqueous solution. J. Photochem.
Photobiol. B: Biol., 75, 13–20.
213
Ahmad, I., Fasihullah, Q., Vaid, F.H.M. (2005). Effect of phosphate buffer on
photodegradation reactions of riboflavin in aqueous solution. J. Photochem.
Photobiol., B: Biol., 78, 229-234.
Ahmad, I., Fasihullah, Q., Vaid, F.H.M. (2006a). Effect of light intensity and
wavelengths on photodegradation reaction of riboflavin in aqueous solution. J.
Photochem. Photobiol. B: Biol., 82, 21–27.
Ahmad, I., Fasihullah, Q., Vaid, F.H.M. (2006b). Photolysis of formylmethylflavin in
aqueous and organic solvents. J. Photochem. Photobiol. Sci., 5, 680–685.
Ahmad, I., Ahmed, S., Sheraz, M.A., Vaid, F.H.M. (2008). Effect of borate buffer on
the photolysis of riboflavin in aqueous solution. J. Photochem. Photobiol. B:
Biol., 93, 82–87.
Ahmad, I., Kefi, I., Ahmed, S., Sheraz, M.A., Aminuddin, M. (2011). Applications of
laser flash photolysis, spectroscopy and electron microscopy in
photopolymerization and development of glass ionomer dental cements. Int. J.
Clin. Dent., 4, 57–73.
Ahmad, I., Vaid, F.H.M., Ahmed, S., Sheraz, M.A., Hasan, S. (2010a). Advances in
biochemical functions and photochemistry of flavins and flavoproteins. Int. J.
Chem. Anal. Sci., 1, 18–21.
Ahmad, I., Ahmed, S., Sheraz, M.A., Vaid, F.H.M., Ansari, I.A. (2010b). Effect of
divalent ions on photodegradation kinetics and pathways of riboflavin in aqueous
solution. Int. J. Pharm., 390, 174-182.
214
Ahmad, I., Ahmed, S., Sheraz, M.A., Aminuddin, M., Vaid, F.H.M. (2009). Effect of
caffeine complexation on the photolysis of riboflavin in aqueous solution: A
kinetic study. Chem. Pharm. Bull., 57, 1363–1370.
Ahmad, I., Rapson, H.D.C., Heelis, P.F., Phillips, G.O. (1980). Alkaline hydrolysis of
7,8-dimethyl-10-(formylmethyl) isoalloxazines. A kinetic study. J. Org. Chem.,
45, 731–733.
Ahmad, I., Fasihullah, Q., Noor, A., Ansari, I.A., Ali, Q.N.M. (2004b). Photolysis of
riboflavin in aqueous Solution: A kinetic study. Int. J. Pharm., 280, 199-208.
Ahmed, S. (2009). Effect of Complexing Agents on the Photodegradation of
Riboflavin in Aqueous Solution, Ph.D. Thesis, Baqai Medical University,
Karachi.
AI-Badry, I.A., Kamel, F.M. (1994). Clinical use of glass ionomer cement: A
Literature Review. The Saud. Dent. J., 6, 107-116.
Albert, A., Serjeant, E.P. (1962). Ionization Constants of Acids and Bases. Methuen
& Co Ltd: London, p. 140.
Al-Malik, M. (2003). Repairability of resin-modified glass-ionomer and polyacid-
modified resin composite cements. Saudi Dent. J., 15, 123-130.
Alvarez, J., Encinas, M.V., Lissi, E.A. (1999). Solvent effects on the rate of
polymerization of 2- hydroxyethyl methacrylate photoinitiated with aliphatic azo
compounds. Macromol. Chem. Phys., 200, 2411-2415.
Alvarez, J., Lissi, E.A., Encinas, M.V. (1998). Effect of the initiator absorbance on
the transition-metal complex photoinitiated polymerization. J. Polym. Sci. Polym.
Chem., 36, 207-208.
215
Alvim, H. H., Alecio, A. C., Vasconcellos, W. A., Furlan, M., De Oliveira, J. E.,
Saad, J. R.C. (2007). Analysis of camphorquinone in composite resins as a
function of shade. Dent. mater., 23, 1245–1249.
Amis, E.S., Hinton, J.F. (1973). Solvent Effects on Chemical Phenomena. Academic
Press, New York.
Andreasen, J.O., Andreasen, F.M., Andersson, L. (2006). Text Book and Colour
Atlas of Traumatic Injuries to the Teeth. 4th ed., Blackwell, Oxford, Chap. 10.
Andrezejewska, E. (2001). Photopolymerisation kinetics of multifunctional
monomers. Prog. Polym. Sci., 26, 605-665
Andrzejewska, E., Andrzejewski, M., Socha, E., Zych-Tomkowiak, D. (2003).
Effect of polyacid aqueous solutions on photocuring of polymerizable
components of resin-modified glass ionomer cements. Dent. Mater., 19, 501–509.
Andrzejewska, E., Podgorska-Golubska, M., Stepniak, I., Andrzejewski, M. (2009).
Photoinitiated polymerization in ionic liquids: kinetics and viscosity effects.
Polymer, 50, 2040–2047.
ANSI/ADA (1989). Dental Glass Ionomer Cements. American National Standards
Institute/American Dental Association, Council on Dental Materials and
Equipment, Chicago, IL, USA, No. 66.
Antonucci, J.M., McKinney, J.E., Stansbury, J.W. (1988). Resin modified glass-
ionomer dental cement.US Patent Application 7160 856.
Antonucci, J.M., Stansberry, J.W., Fowler, B.O. (2000). An improved synthesis of
ethylhydroxymethylacrylate, a unique mixture analog of HEMA. Polymer, 41,
1616–1617.
216
Anusavice, K. J. (2003). Phillips’ Science of Dental Materials. 11th ed., Saunders,
Elsevier Science, New York.
Atai, M., Ahmadi, M., Babanzadeh, S., Watts, D.C. (2007). Synthesis,
characterization, shrinkage and curing kinetics of a new low-shrinkage urethane
dimethacrylate monomer for dental applications. Dent. Mater., 23, 1030-1041.
Barry, T.I., Clinton, D.J., Willson, A.D. (1979). The structure of the glass ionomer
cement and its relationship to the setting process. J. Dent. Res., 58, 1072-1079.
Beers, K.L., Boo, S., Gaynor, S.G., Matyjaszewski, K. (1999). Atom transfer radical
polymerization of 2-hydroxyethyl methacrylate. Macromolecules, 32, 5772-5776.
Bertolotti, S.G., Previtali, C.M., Rufs, A.M., Encinas, M.V. (1999). Riboflavin /
triethanolamine as photoinitiator system of vinyl polymerization. A mechanistic
study by laser flash photolysis. Macromolecules, 32, 2920–2924.
Bhat, V.S., Nandish, B.T. (2006). Sciences of Dental Material (Clinical Application).
6th, ed., SBS Publishers, New Delhi, India, Chap. 8.
Biasutti, J.D., Roberts, G.E., Lucien, F.P., Heuts, J.P.A. (2003). Substituent effects in
the catalytic chain transfer polymerization of 2-hydroxyethyl methacrylate. Eur.
Polym. J., 39, 429-435.
Billington, R.W, Williams, J.A., Pearson, G.J. (1990). Variation in powder/liquid
ratio of restorative glass-ionomer cement used in dental practice. Br. Dent J.,
169, 164-167.
Bowen, R.L. (1962). Dental filling material comprising vinyl-silane treated fused
silica and a binder consisting of the reaction of bisphenol and glycidyl
methacrylate. US patent 3,066, 112.
217
Bowman, C.N., Kloxin, C.J. (2008). Towards an enhanced understanding and
implementation of photopolymerization reactions. AIChE J, 54, 2775-2795.
Breschi, L., Gobbi, P., Falconi, M., Ciavarelli, L., Teti, G., Mazzotti, G. (2001).
Evaluation of the F 2000 bonding procedure: a high resolution SEM study. J.
Dent., 29, 499–507.
British Pharmacopoeia (2009). Her Majesty’s Stationary Office, London, Electronic
version.
BSI (1981). Specification for dental glass ionomer cements. British Standards
Institution, London.
Buck, R.A. (2002). Glass ionomer endodontic sealers: a literature review. Gen. Dent.,
50, 365-368.
Buncel, E., Stairs, R.A, Wilson, H. (2003). The Role of the Solvent in Chemical
Reactions. Oxford University Press, New York.
Bushwieser, S.F., Gessner, F., Veterc, L.C., Neumann, M.G. (1991). Electron-transfer
quenching of the singlet state of protonated and unprotonated basic dyes. J. Braz.
Chem. Soc., 2, 74-79.
Burke, F.J.T. (1990). Cermet - an additional use, Dent. Update, 17, 214.
Byron, P., Turnbull, J.H. (1967). Excited states of flavin coenzymes. II, Anaerobic
oxidation of amino acids by excited riboflavin derivatives. Photochem.
Photobiol., 6, 125-131.
Cahn, R.W., Haasen, P., Kramer. E.J. (1992). Materials Science and Technology A
Comprehensive Treatment Medical and Dental Materials. vol. 14. VCH, New
York.
218
Cairns, W.L., Metzler, D.E. (1971). Photochemical degradation of flavins. VI. A new
photoproduct and its use in studying photolytic mechanism. J. Am. Chem. Soc.,
93, 2772-2777.
Chen, Y.C., Ferracane, J.L., Prahl, S.A. (2007). Quantum yield of conversion of the
photoinitiator of camphorquinone. Dent. Mater., 23, 655–664.
Cho, S.Y., Cheng, A.C. (1999). A review of glass ionomer restorations in the
primary dentition. J. Can. Dent. Assoc., 65,491-495.
Chuin, W.T.C. (1983). Glassionomer Cements: Strength, Flim, Thickness and Sem
Investigation. University of Sydney, Sydney.
Closs, G.L., Miller, J.R. (1988). Intermolecular long-distance electron transfer in
organic molecules. Science, 240, 440-447.
Closs, G.L., Calcaterra, L.T., Green, N.J., Penfield, K.W., Miller, J.R. (1986).
Distance, steroelectric effects, and the Marcus inverted region in intramolecular
electron transfer in organic radical anions. J. Phys. Chem., 90, 3673-3683.
Combe, E.C. (2006). Combe’s Notes on Dental Material. 7th ed., Unicorn Press
Pakistan, Pakistan, pp. 94-99.
Cook, W.D. (1983a). Degradative analysis of glass-ionomer polyelectrolyte cement.
J. Biomed. Mater. Res., 17, 1015–1017.
Cook, W.D. (1983b). Dental polyelectrolyte cements III. Effect of additives on their
rheology. Biomaterials, 4, 85-88.
Cook, W.D. (1992). Photopolymerization kinetics of dimethacrylates using the
camphorquinone / amine initiator system. Polymer, 33, 600-609.
219
Connors, K.A., Amidon, G.L., Stella, V.J. (1986). Chemical Stability of
Pharmaceuticals A Handbook for Pharmacists. 2nd ed., John Wiley, New York,
pp. 38-41
Corrales, T., Catalina, F., Peinado, C., Allen, N.S. (2003). Free radical
macrophotoinitiators: an overview on recent advances. J. Photochem. Photobiol.
A: Chem., 159, 103–114.
Coutinho, E., Cardoso, M.V., DeMunck, J., Neves, A.A., Van Landuyt, K.L.,
Poitevin, A., Peumans, M., Lambrechts, P., Van Meerbeek, B. (2009). Bonding
effectiveness and interfacial characterization of a nano-filled resin-modified glass-
ionomer. Dent. Mater., 25, 1347-1357.
Crisp, S., Wilson, A.D. (1974a). Reactions in glass-ionomer cements. 1.
Decomposition of the powder. J. Dent. Res., 53, 1408–1413.
Crisp, S., Wilson, A.D. (1974b). Reactions in glass-ionomer cements. The
precipitation reaction. J. Dent. Res., 53, 1420–1424.
Crisp, S., Wilson, A.D. (1977). Cement comprising acrylic acid / itaconic acid
copolymers and fluoroaluminosilicate glass powder. US Patent 4,016,124.
Crisp, S., Prosser, H.J., Wilson, A.D. (1976). An infrared spectroscopic study of
cement formation between metal oxides and aqueous solution of poly(acrylic
acid). J. Mater. Sci., 11, 36–48.
Crisp, S., Ferner, A.J., Lewis, B.G., Wilson, A.D. (1975). Properties of improved
glass- ionomer cement formulations. J. Dent., 3, 125–130.
220
Crisp, S., Pringuer, M.A., Wardleworth, D., Willson, A.D. (1974). Reaction in glass-
ionomer cements: II. An infrared spectroscopic study. J. Dent. Res., 53, 1414–
1419.
Croll, T.P. (1988). Glass ionomer-silver cermet class II tunnel-restorations for
primary molars. J. Dent. Child., 55, 177-182.
Croll, T.P. (1990). Glass ionomers for infants, children, and adolescents. J. Am. Dent.
Assoc., 120, 65-68.
Croll, T.P., Nicholson, J.W. (2002). Glass ionomer cements in pediatric dentistry:
review of the literature. Pediatr. Dent., 24, 423-429.
Croll, T.P., Risenberger, R.E., Miller, A.S. (1988). Clinical and histologic
observations of glass ionomer silver cermet restorations in six human primary
molars. Quintessence Int., 19, 911-919.
Culbertson, B.M. (2006). New polymeric materials for use in glass-ionomer cements.
J. Dent., 34, 556–565.
Culbertson, B.M. (2001). Glass ionomer dental restoratives. Prog. Polym. Sci., 26,
577-604.
D’Alpino, P.H.P., Pereira, J.C., Svizero, N.R., Rueggeberg, F.A., Pashley, D.H.
(2006). Use of fluorescent compounds in assessing bonded resin based
restorations: A literature review. J. Dent., 34, 623-634.
Darling, M., Hill, R.G. (1994). Novel polyalkenoate (glass ionomer) dental cement
based on zinc silicate glasses. Biomaterials, 15, 299-306.
Darling, M. (1993). The Design of Novel Glass-Ionomer Cements. University of
Greenwich, Greenwich.
221
Dart, E.C., Cantwell, J.B., Traynor, J.R., Franciszek, J.J., Nemeck, J. (1978). Method
of repairing teeth using a composition which is curable by irradiation with visible
light. US Patent 4,089,763.
Davidson, C.L. (1999). Advances in Glass-ionomer Cements. Quintessence
Publishing Co., Chicago.
Dawson, R.M.C., Elliott, D.C., Elliott, W.H., Jones, K.M. (1986). Data for
Biochemical Research. 3rd ed., Clarendon Press, Oxford, pp. 137-138.
Decker, C., Bendaikha, T. (1998). Interpenetrating polymer networks. II. Sunlight-
induced polymerization of multifunctional acrylates. J. App. Polym. Sci., 70,
2269-2282.
DeMaeyer, E.A.P., Verbeeck, R.M.H., Vercruysse, C.W.J. (1998). Reactivity of
fluoride containing calcium aluminosilicate glass used in dental GICs. J. Dent.
Res., 77, 2005- 2011.
DeMaeyer, E.A., Verbeeck, R.M.H., Vercruysse, C.W. (2002). Infrared spectrometric
study of the acid-degradable glasses. J. Dent. Res., 81, 552–555.
DeRitter, E. (1982). Vitamins in pharmaceutical formulations. J. Pharm. Sci., 71,
1073-1096.
Dessilles, N., Gautrelet, C., Lecamp, L., Lebaudy, P., Bunel, C. (2005). Effect of UV
light scattering during photopolymerization on UV spectroscopy measurements.
Eur. Polym. J., 41, 1296–1303.
Dong, J., Qzaki, Y., Nakashima, K. (1997). Raman IR and NIR spectroscopic
evidence for the coexistence of various hydrogen bond forms in PAA.
Macromolecules, 30, 1111–1117.
222
Drossler, P., Holzer, W., Penzkofer, A., Hegemann, P. (2002). pH dependence of the
absorption and emission behavior of riboflavin in aqueous solution. Chem. Phys.,
282, 429–439.
Drossler, P., Holzer, W., Penzkofer, A., Hegemann, P. (2003). Fluorescence
quenching of riboflavin in aqueous solution by methionin and cystein. Chem.
Phys., 286, 409-420.
Du, H., Fuh, R.A., Li, J., Corkan, A., Lindsey, J.S. (1998). PhotochemCAD: A
computer aided design and research tool in photochemistry. Photochem.
Photobiol., 68, 141–142.
Dutta, R.K., Bhat, S.N. (1996). Interaction of phenazinium dyes and methyl orange
with micelles of various charge types. Colloids and Surfaces, A: Physicochem.
Engin. Asp., 106, 127-134.
Eaton, D.F. (1986). Dye-sensitized photopolymerization. In: D. Volman, K. Gollnick
and G.S. Hammand (Eds.), Advances in Photochemistry. vol. 13, Wiley, New
York, Chap. 4.
Eliades, G., Kakaboura, A., Palaghias, G. (1998). Acid-base reaction and fluoride
release profiles in visible light-cured polyacid-modified composite restoratives
(compomers). Dent. Meter., 14, 57–63.
Eliades, G., Eliades, T., Brantley, W.A., Watts, D.C. (2003). Dental Materials In Vivo
Aging and Related Phenomena. Quintessence Publishing Co, Inc. Kimberly
Drive, UK.
Encinas, M.V., Previtali, C.M. (2006). Excited states interactions of flavins with
amines: application to the interaction of vinyl polymerization. In: E. Silva and
223
A.M. Edwards (Eds.), Flavins Photochemistry and Photobiology. The Royal
Society of Chemistry, Cambridge, pp. 41-59.
Encinas, M.V., Lissi, E.A., Martimez, C. (1996). Polymerization of 2-hydroxyethyl
methacrylate induced by azo compounds: Solvent effects. Eur. Polym. J., 32,
1151-1154.
Encinas, M.V., Lissi, E.A., Majmud, C., Cosa, J.J. (1993). Photopolymerization in
aqueous solutions initiated by the interaction of excited pyrene derivatives with
aliphatic amines. Macromolecules, 26, 6284-6288.
Encinas, M.V., Rufs, A.M., Bertolotti, S.G., Previtali, C.M. (2001). Free radical
polymerization photoinitiated by riboflavin / amines. Effect of the amine
structure. Macromolecules, 34, 2845-2847.
Encinas, M.V., Rufs, A.M., Bertolotti, S.G., Previtali, C.M. (2002). The interaction of
ground and excited states of lumichrome with aliphatic and aromatic amines in
methanol. Helv. Chim. Acta, 85, 1427-1438.
Encinas, M.V., Rufs, A.M., Bertolotti, S.G., Previtali, C.M. (2009). Xanthene
dyes/amine as photoinitiators of radical polymerization:A comparative and
photochemical study in aqueous medium. Polymer, 50, 2762-2767.
Encinas, M.V., Rufs, A.M., Neumann, M.G., Previtali, C.M. (1996). Photoinitiated
vinyl polymerization by safranine T/triethanolamine in aqueous solution.
Polymer, 8, 1395-1398.
Fall, H.H., Petering, H.G. (1956). Metabolic inhibitors. 1. 6,7-dimethyl-9-
formylmethylisoalloxazine,6,7-dimethyl-9-(2-hydroxyethyl)-isoalloxazine and
derivatives. J. Am. Chem. Soc., 78, 377-381.
224
Fasihullah, Q. (1988). Photolysis of Flavins in Aqueous and Organic Solvents, Ph.D.
Thesis, University of Karachi, Karachi.
Ferracane, J.L. (2001). Materials in Dentistry Principles and Application. 2nd ed.,
Lippincott Williams &Wilkins, Philadelphia, PA.
Fleming, G.J.P, Farooq, A.A., Barralet, J.E. (2003). Influence of powder/liquid
mixing ratio on the performance of restorative glass-ionomer dental cement.
Biomaterials, 24, 4173- 4179.
Fjeld, M., Ogaard, B. (2006). Scanning electron microscopic evaluation of enamel
surfaces exposed to 3 orthodontic bonding systems. Am. J. Orthod. Dentofacial
Orthop., 130, 575-581.
Fouassier, J.P. (1995). Photoinitiation, Photopolymerization, and Photocuring
Fundamentals and Applications. Hanser Gardner, NewYork.
Funteas, U.R., Wallace, J.A., Fochtman, E.W. (2003). A comparative analysis of
mineral trioxide aggregate and portland cement. Aust. Endod. J., 29, 43-44.
Fukumachi, C., Sakurai, Y. (1954). Vitamin B2 photolysis. V. The photolytic
formation of 6,7-dimethylflavin-9-acetic acid ester from riboflavin. Vitamins
(Kyoto), 7, 939-943.
Garcia, N.A., Criado, S.N., Massad, W.A. (2006). Riboflavin as a visible-light-
sensitizer in the aerobic photodegradation of ophthalmic and sympathomimetic
drugs, In: Silva, E., Edwards, A.M., (Ed.), Flavin Photochemistry and
Photobiology. The Royal Society of Chemistry, Cambridge, Chap. 4.
Gasser, O. (1994). Evolution of the Glass System. Glass Ionomer: The Next
Generation, 2nd International Symposium on Glass Ionomer, Philadelphia, PA.
225
Gillingham, K. H. (2004). Novel Glass Ionomer Cements for Biomedical
Applications. University of Sheffield, Sheffield.
Godoy, F.G., Draheim, R.N., Titus, H.W. (1998). Shear bond strength of a posterior
composite resin to glass ionomer bases. Quintessence Int., 19, 357-359.
Gomez, M.L., Previtali, C.M., Montejano, H.A. (2007). Phenylonium salts as third
component of the photoinitiator system safranine O/triethanolamine: A
comparative study in aqueous media. Polymer, 48, 2355-2361.
Gomez, M.L., Avila, V., Monteljano, H.A., Previtali, C.M. (2003). A mechanistic and
laser flash photolysis investigation of acrylamide polymerization photoinitiated by
the three component system safranine-T/triethanolamine/diphenyliodonium
chloride. Polymer, 44, 2875-2881.
Gomez, M.L., Fasce, D.P., William, R.J.J., Erra-Balsells, R., Fatema, M.K., Nonamo,
H. (2008). Silsesquioxane functionalized with methacrylate and amine groups as a
crosslinker/co-initiator for the synthesis of hydrogels by visible light
photopolymerization. Polymer, 49, 3648-3653.
Ghanadzadeh Gilani, A., Tajalli, H., Zakerhamidi, M.S. (2008). Photophysical
behavior of thiazine dyes with or without surfactants into poly-HEMA
hydrophilic gel matrix. J. Mol. Liq., 143, 81-88.
Griffin, S.G., Hill, R.G. (1999). Influence of glass composition on the properties of
glass polyalkenoate cements. Part I: influence of aluminum to silicon ratio.
Biomaterials, 20, 1579-1586.
226
Grodowski, M.S., Veyret, B., Weiss, K. (1977). Photochemistry of flavins-II.
Photophysical properties of alloxazines and isoalloxazines. Photochem.
Photobiol., 26, 341-352.
Guo, X., Wang, Y., Spencer, P., Ye, Q., Yao, X. (2008). Effects of water content and
initiator composition on photopolymerization of a model BisGMA/HEMA resin.
Dent. Mater., 24, 824-831.
Hacioglua, B., Berchtolda, K.A., Lovella, L.G., Niea, J., Bowman, C. N. (2002).
Polymerization kinetics of HEMA/DEGDMA: using changes in initiation and
chain transfer rates to explore the effects of chain-length-dependent termination.
Biomaterials, 23, 4057-4064.
Hadley, P.C., Billington, R.W., Williams, J.A., Pearson, G.J. (2001). Interactions
between glass ionomer cement and alkali metal fluoride solutions: the effect of
different cations. Biomaterials, 22, 3133-3138.
Hatchard, C.G., Parker, C.A. (1956). A new sensitive chemical actinometer. II.
potassium ferrioxalate as a standard chemical actinometer. Proc. R. Soc. (Lond.),
A235, 518-536.
Hatton, P.V., Brook, I.M. (1992). Characterization of the ultrastructure of glass-
ionomer (poly-alkenoate) cement. Br. Dent. J., 123, 275-277.
Hazzard, J.T., Poulas, T.A., Tollin, G. (1987). Kinetics of reduction by free flavin
semiquinones of the components of the cytochrome c-cytochrome c-peroxidase
complex and intracomplex electron transfer. Biochemsitry, 26, 2836-2848.
Heelis, P.F. (1982). The photophysical and photochemical properties of flavins
(isoalloxazines). Chem. Soc. Rev., 11, 15-39.
227
Heelis, P.F. (1991). The photochemistry of flavins. In: F. Muller, (Ed.), Chemistry
and Biochemistry of Flavins. vol.1. CRC Press, Boca Raton, FL, pp. 171-193.
Heelis, P.F., Phillips, G.O. (1985). A laser flash photolysis study of the triplet states
of lumichrome. J. Phys. Chem., 89, 770-774.
Heelis, P.F., De la Rosa, M.A., Phillips, G.O. (1985). A laser flash photolysis study of
the photoreduction of the lumiflavin triplet state. Photobiochem. Photobiophys., 1,
57-63.
Heelis, P.F., Parsons, B.J., Phillips, G.O., McKeller, J.F. (1981). The flavins-
sensitized photooxidation of ascorbic acid. A continuous and flash photolysis
study. Photochem. Photobiol., 33, 7-13.
Heelis, P.F., Phillips, G.O., Ahmad, I., Rapson, H.D.C. (1980). The Photodegradation
of formylmethylflavin-a steady state and laser flash photolysis study.
Photobiochem. Photobiophys., 1, 125-130.
Hemmerich, P. (1976). The present status of flavin and flavocoenzyme chemistry.
Fortsch. Chem. Org. Naturst., 33, 451-527.
Hill, R.G., Wilson, A.D. (1988). Some structural aspect of the glasses used in the
ionomer cements. Glass Technol., 29, 150-158.
Hill, R.G., Wilson, A.D., Warren, C.P. (1989). The influence of poly (acrylic acid)
molecular weight on the fracture toughness of glass ionomer cements. J. Mater.
Sci., 24, 363-371.
Holton, J.R., Nystrom, G.P., Douglas, W.H., Phelps, R.A. (1990). Microleakage and
marginal placement of glass ionomer liner. Quintessence Int., 21, 117-122.
228
Holzer, W., Shirdel, J., Zirak, P., Penzkofer, A., Hegemann, P., Dentzmann, R.,
Hochmuth, E. (2005). Photo-induced degradation of some flavins in aqueous
solution. Chem. Phys., 308, 69-78.
Holmstrom, B. (1964a). Mechanism of the photoreduction of riboflavin. Arkiv. Kemi,
22, 329-346.
Holmstrom, B. (1964b). Spectral studies of the photobleaching of riboflavin
phosphate. Arkiv. Kemi, 22, 281-301.
Holmstrom, B., Oster, G. (1961). Riboflavin as an electron donor in photochemical
reactions. J. Am. Chem. Soc., 83, 1867-1871.
Hu, M-Xin., Yang, Q., Xu, Z-Kang. (2006). Enhancing the hydrophilicity of
polypropylene microporous membranes by the grafting of 2-hydroxyethyl
methacrylate via a synergistic effect of photoinitiators. J. Membr. Sci., 285, 196-
205.
Hutchison, J.B., Haraldsson, K.T., Hawker, C.J., Bowman, C.N., Anseth, K. S.
(2002). Modification of polymeric components. ACS PMSE, 87, 162.
Ingle, J.I., Bakland, L.K., Baumgartner, J.C. (2008). Ingles’ Endodontics. 3rd ed., BC
Decker Inc, Hamilton, Canada, Chap. 12.
Insinska-Rak, M., Sikorska, E., Herance, J.R., Bourdelande, J.I., Khmelinskii, I.V.,
Kubicki, M., Prukala, W., Machado, I.F., Komasa, A., Ferreira, L.F.V., Sikorski,
M. (2005). Spectroscopy and photophysics of flavin-related compounds: 3-
benzyllumiflavin. Photochem. Photobiol., Sci. 4, 463-468.
Insinska-Rak, M., Sikorska, E., Bourdelande, J.L., Khmelinskii, I.V., Prukała, W.,
Dobek. K., Karolczak, J., Machado, I.F., Ferreira, L.F.V., Dulewicz, E., Komasa,
229
A., Worrall, D.R., Kubicki, M., Sikorski, M. (2007). New photochemically stable
riboflavin analogue-3-methyl-riboflavin tetraacetate. J. Photochem, Photobiol, A:
Chem., 186, 14-23.
ISO (1986). International standards for glass ionomer cements. International
Standards Organization, Central Secretariat, Switzerland, ISO 7489.
ISTC (1991). Specification for dental water-based cements. International Standard
Technical Committee, International Organization for Standardization, Geneve,
Switzerland, ISO 9917.
Ireland, R. (2006). Clinical Textbook of Dental Hygiene and Therapy. Blackwell,
Oxford, Chap. 9.
Jafarzada Kashi, T.S., Erfan, M., Watts, D.C. (2007). Effect of water on HEMA
conversion by FTIR spectroscopy. J. Dent. (Tehran Univer. Med. Sci.), 4, 123-
129.
Jakubiak, J., Wrzyszczyn´ ski, A., Linden, L.Å., Rabek, J.F. (2007). The role of
amines in the camphorquinone photoinitiated polymerization of multifunctional
monomer. J. Macromol. Sci. A., 44, 239-242.
Jakubiak, J., Allonas, X., Fouassier, J.P., Sionkowska, A., Anderzejewska, E.,
Linden, L.A., Rabek, J.F. (2003). Camphorquinone–amines photoinitiating
systems for the initiation of free radical polymerization. Polymer, 44, 5219-5226.
Jin, Y. (2000). Spectroscopic Investigations of New Glass-Ionomer Dental Cements.
M.S. Thesis, West Virginia University, Morgantown, West Virginia.
230
Kakaboura, A., Eliades, G., Palaghias, G. (1996). An FTIR study on the setting
mechanism of resin-modified glass ionomer restoratives. Dent. Mater., 12, 173-
178.
Kanca, J. (1988). The functional posterior restoration. Quintessence Int., 19, 659-662.
Kannurpatti, A.R., Goodner, M.D., Lee, H.R., Bowman, C.N. (1997). Reaction
behavior and kinetic modeling studies of living radical photopolymerizations,
In: American Chemical Society Symposium Series, Photopolymerization:
Fundamentals and Applications, A.B. American Chemical Society, Washington,
D.C, 673, 51.
Kao, E.C., Culbertson, B.M., Xie, D. (1996). Preparation of glass ionomer cement
using N-acryloyl-substituted amino acid monomers–evaluation of physical
properties. Dent. Mater., 12, 44-51.
Karen, A., Ikeda, N., Mataga, N., Tanaka, F. (1983). Picosecond laser flash photolysis
studies of fluorescence quenching mechanisms of flavins. A direct observation of
indole-flavin singlet charge transfer state formation in solutions and
flavoenzymes. Photochem. Photobiol., 37, 495-502.
Karlsen, J. (1996). Light-activated drugs and drug formulations in drug targeting, In:
Tonnesen, H.H., The Photostability of Drugs and Drug Formulations. Taylor and
Francis, London, pp. 174-177.
Katsuyama, S., Ishikawa, T., Fujii, B. (1993). Glassionomer Cements: The Material
and Their Clinical Uses. Ishiyaku EuroAmerica, University of Michigan,
Michigan, MI.
231
Kiczenski, T.J., Du, L.-S., Stebbins, J.F. (2004). F–19 NMR study of the ordering of
high field strength cations at fluoride sites in silicate and aluminosilicate glasses.
J. Non-Cryst. Solids, 337, 142-149.
Kilpatrick, N.M. (1993). Glass Ionomer Cements: Factors Influencing Their
Duarability. University of Newcastle upon Tyne, New Castle, UK.
Kindernay, J., Blazkova, A., Ruda, J., Jancovicova, V., Jakubikova, Z. (2002). Effect
of UV light source intensity and spectral distribution on the photopolymerisation
reactions of a multifunctional acrylated monomer. J. Photochem, Photobiol. A:
Chem., 151, 229-236.
Knight, G.M., McIntyre, J.M., Craig, G.G., Mulyani. (2007). Electron probe
microanalysis of ion exchange of selected elements between dentine and adhesive
restorative materials. Aust. Dent. J., 52, 128-132.
Kobayashi, M., Kon, M., Miyai, K., Asaoka, K. (2000). Strengthening of glass-
ionomer cement by compounding short fibers with CaO-P2O5-SiO2-Al2O3 glass.
Biomaterials, 21, 2051-2058.
Kovarik, R.E., Haubenreich, J.E., Gore. D. (2005). Glass Ionomer Cements: A review
of composition, chemistry, and biocompatibility as a dental and medical implant
material. J. Long Term Eff. Med. Implants, 15, 655-671.
Koziol, J. (1966a). Studies on flavins in organic solvents-I. Spectral characteristics of
riboflavin, riboflavin tetrabutyrate and lumichrome. Photochem. Photobiol., 5, 41-
54.
Koziol, J. (1966b). Studies on flavins in organic solvents-II. Photodecomposition of
riboflavin in the presence of oxygen. Photochem. Photobiol., 5, 55-62.
232
Kramer, N., Frankenberger, R. (2007). Compomers in restorative therapy of children:
a literature review. Int. J. Pediatr. Dent., 17, 2-9.
Lee, S.Y., Greener, E.H., Menis, D.L. (1995b). Detection of leached moieties from
dental composites in fluid simulating food and saliva. Dent. Mater., 11, 348-353.
Lee, S.Y., Greener, E.H., Muller, H.J. (1995a). Effect of food and oral simulating
fluids on structure of adhesive composite system. J. Dent., 23, 27-35.
Lee, Y-K., YU, B., Zhao, G-F., Lim, J.I. (2010). Effects of aging and HEMA content
on the translucency, fluorescence, and opalescence properties of experimental
HEMA added glass ionomers. Dent. Mater., 29, 9-14.
Li, C., Zhang, Y., Zhang, Y., Zhang, C. (2003). Blends of polycarbonate and
ethylene-1-octylene copolymer. Eur. J. Polym., 39, 305-311.
Li, M., Chen, Y., Zhang, H., Wang, T. (2010). A novel ferrocenium salt as visible
light photoinitiator for cationic and radical photopolymerization. Prog. in Org.
Coat., 68, 234-239.
Lim, Ho-Nam., Bin Y.u., Lim, J.I., Ahn, Jin-Soo., Lee, Yong-Keun. (2009). Influence
of 2-hydroxyethyl methacrylate content on the optical properties of experimental
2-hydroxyethyl methacrylate-added dental glass ionomer. Mater. Design, 30,
3996-4002.
Lissi, E.A., Encinas, M.V. (1991). Photochemistry and Photophysics. Rabek, J.F.
(Ed.), CRC Press, Boca Raton, FL, vol. 4, Chap. 4.
Lovell, L.G., Elliott, B.J., Brown, J.R., Bowman, C.N. (2001). The effect of
wavelength on the polymerization of multi(meth)acrylates with
disulfide/benzilketal combinations. Polymer, 42, 421-429.
233
Lowenstein, W. (1954). The distribution of aluminium in the tetrahedra of silicate
and aluminates. American Mineralogist, 39, 92-96.
Ma, H., Davis, R., Bowman, C. (2000). A Novel Sequential Photoinduced Living
Graft Polymerization. Macromolecules, 33, 331-335.
Maeda, T., Matsuya, S., Ohta, M. (1993). Application of solid-state NMR to the study
of the setting mechanism of glass-ionomer cements. Dent. Japan, 30, 106-109.
Marcus, R.A. (1956). On the theory of oxidation-reduction reactions involving
electron transfer. J. Chem. Phys., 24, 966-978.
Marcus, R.A. (1959). On the theory of electrochemical and chemical electron transfer
processes. Can. J. Chem., 37, 155-163.
Marcus, R.A. (1960). Exchange reactions and electron transfer reactions including
isotopic exchange: Theory of oxidation-reduction reactions involving electron
transfer. Part 4-A Statistical-mechanical basis for treating contributions from
solvent, ligands, and inert salt. Disc. Faraday Soc., 29, 21-31.
Matsuya, S., Maeda, T., Ohta, M. (1996). IR and NMR analysis of hardening and
maturation of glass-ionomer cement. J. Dent. Res., 75, 1920-1927.
Matsuya, S., Stamboulis, A., Hill, R.G., Law, R.V. (2007). Structural characterization
of ionomer glasses by multinuclear solid state MAS–NMR spectroscopy. J. Non-
Cryst. Solids, 353, 237-243.
McBride, M.M., Moore, W.M. (1967). The photochemistry of riboflavin, II.
Polarographic studies on the hydroxyethyl and formylmethyl analogues of
riboflavin. Photochem. Photobiol., 6, 103-113.
McCabe, J.F. (1998). Resin modified glass ionomers. Biomaterials, 19, 521-528.
234
McCabe, J.F., Walls, A.W.G. (2008). Applied Dental Materials. 9th ed., Blackwell,
London.
McComb, D. (1982). Retention of castings with glass ionomer cements. J. Prosthet.
Dent., 48, 285-288.
McLean, J.W. (1990). Cermet cements. J. Am. Dent. Assoc., 120, 43-47.
McLean, J.W., Nicholson, J.W., Wilson, A.D. (1994). Proposed Nomenclature for
Glass-Ionomer Dental Cements and Related Materials. vol. 25, Quintessence,
London, pp. 587-589.
McLean, J.W., Gasser, O. (1985a). Powder dental material and process for the
preparation thereof. ESPE Fabrik Pharmazeutischer Preparate GmbH,
assignee. US Patent 4, 527, 979.
McLean, J.W, Gasser, O. (1985b). Glass cermet cements. Quintessence Int., 16, 333-
343.
McLean, J.W., Powis, D.R., Prosser, H.J., Wilson, A.D. (1985). The use of glass
ionomer cement in bonding composite resin to dentine. Br. Dent. J., 158, 410-414.
McKinney, J.E., Antonucci, M., Rupp, N.W. (1987). Wear and microhardness of
ionomer cements. J. Dent. Res., 66, 1134-1139.
Miller, J. R., Calcaterra, L.T., Closs, G.L. (1984). Intermolecular long-distance
electron transfer in radical anions. The effects of free energy and solvent on the
reactions rates. J. Am. Chem. Soc., 106, 3047-3049.
Millett, D.T., McCabe, J.F. (1996). Orthodontic bonding with glass ionomer cement-
a review. Eur. J. Orthod., 18, 385-399.
235
Mitra, S.B. (1988). Photocurable ionomer cement systems. European Patent
Application 3,23,120.
Mitra, S.B. (1991). Adhesion to dentine and physical properties of a lightcured
glass-ionomer Liner / Base. J. Dent. Res., 70, 72-74.
Mitra, S.B., and Lee, C.-Y., Bui, H.T., Tantbirojn, D., Rusin, R.P. (2009). Long-term
adhesion and mechanism of bonding of a paste-liquid resin-modified glass-
ionomer. Dent. Mater., 25, 459-466.
Moore, D.E. (1996). Photophysical photochemical aspects of drug stability, In:
Tonnesen, H.H., (Ed.), The Photostability of Drugs and Drug Formulations.
Taylor & Francis, London, Chap. 2.
Moore, W.M., Ireton, R.C. (1977). The photochemistry of riboflavin, V. The
photodegradation of isoalloxazines in alcoholic solvents. Photochem. Photobiol.,
25, 347-356.
Moore, B.K., Swartz, M.L., Phillips, R.W. (1985). Abrasion resistance of metal-
reinforced glass ionomer materials. J. Dent. Res., 64, 37l.
Moore, W.M., Spence, J.T., Raymond, F.A., Colson, S.D. (1963). Photochemistry of
riboflavin, I. The hydrogen transfer process in the anaerobic photobleaching of
flavins. J. Am. Chem. Soc., 85, 3367-3372.
Moshaverinia, A., Roohpour, N., Darr, J.A., Rehman, I.U. (2009a). Synthesis of a
proline modified acrylic acid copolymer in supercritical CO2 for glass-ionomer
dental cement applications. Acta Biomater., 5, 1656-1662.
236
Moshaverinia, A., Roohpour, N., Darr, J.A., Rehman, I.U. (2009b). Synthesis and
characterization of a novel N-vinylcaprolactam-contaning acrylic acid terpolymer
for application in glass-ionomer dental cements. Acta Biomater., 5, 2101-2108.
Moshaverinia, A., Roohpour, N., Billington, R.W., Darr, J.A., Rehman, I.U. (2008).
Synthesis of N-vinylpyrrolidone modified acrylic acid copolymer in supercritical
fluids and its application in glass-ionomer dental cement. J. Mater. Sci. Mater.
Med., 19, 2705-2711.
Moszner, N., Fischer, U.K., Ganster, B., Liska, R., Rheinberger, V. (2008). Benzoyl
germanium derivatives as novel visible light photoinitiators for dental materials.
Dent. Mater., 24, 901-907.
Mount, G.J. (1990). Esthetics with glass ionomer cements and the sandwich
technique. Quintessence Int., 21, 93-101.
Mount, G.J. (1991). Making the most of glass ionomer cements. J. Dent. Update, 18,
276-279.
Mount, G.F. (1994). An Atlas of Glass-Ionomer Cements: A Clinician’s Guide. 2nd
ed., Martin Dunitz, London.
Mount, G.F. (2002). An Atlas of Glass-Ionomer Cements: A Clinician’s Guide. 3rd
ed., Martin Dunitz, London.
Muller, F. (1981). Spectroscopy and photochemistry of flavin and flavoproteins.
Photochem. Photobiol., 34, 753–759.
Muller, F. (1983). The flavin redox-system and its biological function. Top. Curr.
Chem., 108, 71-107.
237
Murray, A.J., Nanos, J.A., Fontenot, R.E. (1986). Compressive strength of glass
ionomer with and without silver alloy. J. Dent. Res., 65, 193.
Myers, M.L., Staffanou, R.S. (1983). Marginal leakage of contemporary cementing
agents. J. Prosthet. Dent., 50, 513-515.
Nagaraja, U.P., Kishore, G. (2005). Glass ionomer cement–the different
generations. Trends Biomater. Artif. Organs, 18, 158-165.
Naman, S.A., Tegner, L. (1986). Decay kinetics of the triplet excited state of
lumiflavin. Photochem. Photobiol., 43, 331-333.
Neumann, M.G., Schmitt, C.C., Maciel, H., Goi, B.E. (2006). The photoinitiated
copolymerization of styrenesulfonate with methacrylate monomers in hydrotropic
medium. J. Photochem. Photobiol. A: Chem.,184, 335-339.
Ngo, H. (2010). Glass-ionomer cements as restorative and preventive materials. Dent.
Clin. North Am., 54, 551-563.
Nicholson, J.W. (1991). Clinical Materials, Glass Ionomer Cements. vol 7 (4).
Elsevier Applied Science, New York.
Nicholson, J.W. (1998). Chemistry of glass-ionomer cements: a review. Biomaterials,
19, 485-494.
Nicholson, J. W. (2002). The Chemistry of Medical and Dental Materials. Royal
Society of Chemistry, Cambridge, Chap. 5.
Nicholson, J. W. (2007). Polyacid-modified composite resins (“compomers”) and
their use in clinical dentistry. Dent. Mater., 23, 615-622.
Nicholson, J.W., Beata, C. (2009). Review paper: Role of aluminum in glass-
ionomer dental cements and its biological effects. J. Biomater. Appl., 24, 293-308.
238
Nichloson, J.W., Brookman, P.J., Lacy, O.M., Wilson A.D. (1988). Fourier transform
infrared spectroscopic study of the role of tartaric acid in glass-ionomer dental
cements. J. Dent. Res., 67, 1451-1454.
Noort, R.V. (2002). Introduction to Dental Materials. 2nd ed., Mosby, London.
Numes, T.G., Garcia, F.C.P., Qsorio, R., Carvalho, R., Tolendano, M. (2006).
Polymerization efficacy of simplified adhesive systems studied by NMR and MRI
techniques. Dent. Mater., 22, 963-972.
O′Brien, W.J. (2002). Dental Materials and Their Selection. 3rd ed., Quintessence
Publishing Co, Inc. Kimberly Drive.
Oen, J.O., Gjerdet, N.R., Wisth, P.J. (1990). Glass Ionomer Cements Used as
Bonding Materials for Metal Orthodontic Brackets: An In Vitro Study. University
of Bergen, Bergen, Norway.
Ogliari, F.A., Caroline, E.C., Petzhold, C.L., Demarco, F.F., Piva, E. (2007). Onium
salt improves the polymerization kinetics in an experimental dental adhesive
resin. J. Dent., 35, 583-587.
Oliveira, M.G.D., Xavier, C.B., Demarco, F.F., Pinheiro, A.L.B., Costa, A.T., Pozza,
D.H. (2007). Comparative chemical study of MTA and Portland cements. Braz.
Dent. J., 18, 3-7.
Orellana, B., Rufs, A.M., Encinas, M.V. (1999). The photoinitition mechanism of
vinyl polymerization by riboflavin/triethanolamine in aqueous medium.
Macromolecules, 32, 6570-6573.
Osman, E., Moore, B.K., Phillips, R.W. (1986). Fracture toughness of several
categories of restorative materials. J. Dent. Res., 65, 220.
239
Oster, G., Yang, N.L. (1968). Photopolymerization of vinyl monomers. Chem. Rev.,
68, 125-151.
Oster, G., Bellin, J.S, Holmstrom, B. (1962). Photochemistry of riboflavin.
Experientia, 18, 249-253.
Oster, G., Ester, G., Prati, G. (1957). Dye-sensitized photopolymerization of
acrylamide. J. Am. Chem. Soc., 79, 595-598.
Paczkowski, J., Kucybala, Z., Scigalski, F., Wrzyszcynski, A. (1999). Dyeing
photoinitiators. Electron transfer processes in photoinitiating systems. Trends
Photochem. Photobiol., 5, 79-91.
Pagoria, D., Geurtsen, W. (2005). The effect of N-acetyl-L-cysteine and ascorbic acid
on visible-light irradiated camphorquinone/N, N-dimethyl-p-toluidine-induced
oxidative stress in two immortalized cell lines. Biomaterials, 26, 6136-6142.
Papagiannoulis, L., Tzoutzas, J., Eliades, G. (1997). Effect of topical fluoride agents
on the morphologic characteristics and composition of resin composite restorative
materials. J. Prosthet. Dent., 27, 405-413.
Parker, C.A. (1953). A new sensitive chemical actinometer, I. Some trials with
potassium ferrioxalate. Proc. Roy. Soc., (Lond.), A220, 104-116.
Park, J-Gu., Ye, Q., Topp, E.M., Mirsa, A., Spencer, P. (2009). Water sorption and
dynamic mechanical properties of dentin adhesives with a urethane-based
multifunctional methacrylate monomer. Dent. Mater., 25,1569-1575.
Pearson, G.J. (1991). Physical properties of glass ionomer-cements influencing
clinical performance. Clin. Mater., 7, 325-331.
240
Peiffer, R. (1997). Photopolymerization Fundamentals and Applications. American
Chemical Society, Washington D.C., vol. 673.
Penzer, G.R. (1970). The chemistry of flavins and flavoproteins: Aerobic
photochemistry. Biochem. J., 116, 733-743.
Penzer, G.R., Radda, G.K. (1967). The chemistry and biological functions of
isoalloxazines (Flavins). Q. Rev., 21, 43-65.
Penzer, G.R., Radda, G.K. (1971). Photochemistry of flavins. Methods Enzymol.,
18B, 479-506.
Phinney, D.J., Halstead, J.H. (2008). Dental Assisting: A Comprehensive Approach.
Thomson Delmar Learning, USA, Chap. 26.
Pires, R., Nunes, T.G., Abrahams, I., Hawkes, G.E., Morais, G. M., Fernandez, C.
(2004). Stray-field imaging and multinuclear magnetic resonance spectroscopy
studies on the setting of a commercial glass-ionomer cement. J. Mater. Sci.
Mater. Med., 15, 201-208.
Pluim, L.J., Arends, J., Havinga, P., Jongebloed, W.L., Stoknoos, I. (1984).
Quantitative cement solubility experiments in vivo. J. Oral Rehabil., 11, 171-179.
Power, J.M., Sakaguchi, R.L. (2006). Craigs Restorative Dental Materials. 12th ed.,
Mosby, Missouri, MO.
Previtali, C.M., Bertolotti, S.G., Neumann, M.G., Pastre, I.A., Rufs, A.M., Encinas,
M.V. (1994). Laser flash photolysis study of the photoinitiator system safranine
T-aliphatic amines for vinyl polymerization. Macromolecules, 27, 7454-7458.
241
Porcal, G., Bertolotti, S.G., Previtali, C.M., Encinas, M.V. (2003). Electron transfer
quenching of singlet and triplet excited states of flavins and lumichrome by
aromatic and aliphatic electron donors. Phys. Chem. Chem. Phys., 5, 4123-4128.
Prosser, H.J., Powis, D.R., Wilson, A.D. (1986). Glass-ionomer cements of improved
flexural strength. J. Dent. Res., 65, 146-148.
Prosser, H.J., Powis, D.R., Brant, P.J., Wilson, A.D. (1984). Characterisation of
glass-ionomer cements. 7. The physical properties of current materials. J. Dent.,
12, 231- 240.
Reichardt, C. (1988). Solvents and Solvent Effect in Organic Chemistry. 2nd ed.,
VCH Publishers, New York.
Reiser, A. (1989). Photoreactive Polymers: The Science and Technology of Resists.
Wiley-Interscience, New York.
Rivlin, R.S. (2007). Riboflavin (vitamin B2). In: Zempleni, J., Rucker, R.B.,
McCormick, D.B., Suttie, J.W., (Ed.), Handbook of Vitamins. 4th ed., Taylor &
Francis, CRC Press, Boca Raton, FL, Chap. 7.
Roeland J.G., De Maeyer, E.A.P., Verbeeck, M.H.R. (1998). Effect of acetic acid on
the fluoride release profiles of restoratives glass ionomer cements. Dent. Mater.,
14, 261-268.
Roberson, T.M., Heymann, H.O., Swift, E.J. (2006). Sturdevant's Art and Science of
Operative Dentistry. 5th ed., Mosby, Missouri, MO.
Rosenstiel, S.F., Land, M.F., Bruce, J., Crispin, B.J. (1998). Dental luting agents: A
review of the current literature. J. Prosthet. Dent., 80, 280-301.
242
Rosentritt, M., Shortall, A.C., Palin, W.M. (2010). Dynamic monitoring of curing
photoactive resins: A methods comparison. Dent. Mater., 26, 565-570.
Rueggeberg, F.A., Ergle, J.W., Lockwood, P.E. (1997). Effect of photoinitiator level
on properties of a light-cured and post-cure heated model resin system. Dent.
Mater.,13, 360-1364.
Sato, Y., Chakis, H., Suzuki, Y. (1984). Biphasic photolysis of riboflavin. III. Effect
of ionic strength on the photolysis. Chem. Pharm. Bull., (Jpn), 32, 1232-1235.
Sato, Y., Yokoo, M., Takahashi, S., Takahashi, T. (1982). Biphasic photolysis of
riboflavin with a low-intensity light source. Chem. Pharm. Bull., 30, 1803-1810.
Scherer, W., Cooper, H., Kaim, J., Hittleman, E., Staffa, J. (1990). A sensitivity study
in vivo: Glass ionomer versus zinc phosphate bases beneath amalgam
restorations. Oper. Dent., 15, 193-196.
Schmalz, G., Arenholt, B.D. (2009). Biocompatibility of Dental Material. Springer
Verlag, Berlin, Chap. 6.
Schmidt, W. (1982). Light-induced redoxcycles of flavins in various alcohol/acetic
acid mixtures. Photochem. Photobiol., 36, 699-703.
Schmitt, W., Purrmann, R., Jochmm, P., Gasser, O. (1982). Mixing component of
dental glass ionomer cement. US patent 4, 360, 605.
Schmitt, W., Purrmann, R., Jochmm, P., Gasser, O. (1983). Calcium depleted
aluminium fluorosilicate glass powder for use in dental and bone cements. US
patent 4, 376, 835.
Schneider, L.F.J., Cavalcante, L.M., Consani, S., Ferracane, J.L. (2009). Effect of
co-initiator ratio on the polymer properties of experimental resin composites
243
formulated with camphorquinone and phenyl-propanedione. Dent. Mater., 25,
369-375.
Schreider, S., Steiner, U., Kramer, H.E.A. (1975). Determination of pK values of the
lumiflavin triplet state by flash photolysis. Photochem. Photobiol., 21, 81-84.
Schuman Jorns, M., Schollnhammer, G., Hemmerich, P. (1975). Intramolecular
addition of the riboflavin side chain, Anion-catalysed neutral photochemistry.
Eur. J. Biochem., 57, 35-48.
Scigalski, F., Paczkowski, J. (2005). Photoinitiating free-radical polymerization
electron-transfer pairs applying amino acids and sulfur-containing amino acids as
electron donors. J. Appl. Polym. Sci., 97, 358-365.
Scoville, R. K., Foreman, F., Burgess, J.O. (1990). In vitro fluoride uptake by enamel
adjacent to a glass ionomer luting cement. ASDC J. Dent. Child., 57, 352-355.
Shin, D-Hoon., Rawls, H.R. (2009). Degree of conversion and color stability of the
light curing resin with new photoinitiator systems. Dent. Mater., 25, 1030-1038.
Sidhu, S.K. (2010). Clinical evaluations of resin-modified glass-ionomer restorations.
Dent. Mater., 26, 7-12.
Silva, E., Edwards, A.M. (Eds.) (2006). Flavin Photochemistry and Photobiology.
The Royal Society of Chemistry, Cambridge.
Silva, E., Quina, F.H. (2006). Photoinduced processes in the eye lens: Do flavins
really play a role, In: Silva, E., Edwards, A.M. (Ed.), Flavin Photochemistry and
Photobiology. The Royal Society of Chemistry, Cambridge, Chap.7.
244
Silva, E., Edwards, A.M. (1996). Generation of radical species by irradiation of
tryptophan and tyrosine solutions sensitized by riboflavin. Biological
implications. Cienc. Cult., (Sao Paulo), 48, 47-50.
Silva, E., Ugarte, R., Andrade, A., Edwards, A.M. (1994). Riboflavin-sensitized
photoprocesses of tryptophan. J. Photochem. Photobiol., B: Biol., 23, 43-48.
Silverman, E., Cohen, M., Demke, R. S., Silverman, M. (1995). A new light-cured
glass ionomer cement that bonds brackets to teeth without etching in the presence
of saliva. Am. J. Orthod. Dentofacial Orthop., 108, 231-236.
Simmons, J.J. (1983). The miracle mixture: glass-ionomer and alloy powder. Tex.
Dent. J., 100, 6-12.
Simonsen, R.J. (1996). Glass ionomer as fissure sealant-a Critical Review. J. Public
Health Dent., 56, 146-149.
Sinko, P.J. (2006). Martin’s Physical Pharmacy and Pharmaceutical Sciences. 5th
ed., Lippincott Williams & Wilkins, Philadelphia, PA, Chap. 15.
Sikorska, E., Worrall, D.R., Bourdelande, J.L., Sikorski, M. (2003). Photophysics of
lumichrome and its analogs. Polish J. Chem., 77, 65-73.
Sikorska, E., Khmelinskii, I.V., Worrall, D.R., Koput, J., Sikorski, M. (2004b).
Spectroscopy and photophysics of iso- and alloxazines: experimental and
theoretical study. J. Fluorescence, 14, 57-64.
Sikorska, E., Sikorski, M., Steer, R.P., Wilkinson, F., Worrall, D.R. (1998).
Efficiency of singlet oxygen generation by alloxazines and isoalloxazines. J.
Chem. Soc., Faraday Trans., 94, 2347-2353.
245
Sikorska, E., Khmelinskii, I.V., Prukała, W., Williams, S.L., Patel, M., Worrall, D.R.,
Bourdelande, J.L., Koput, J., Sikorski, M. (2004a). Spectroscopy and
photophysics of lumiflavins and lumichromes. J. Phys. Chem. A, 108, 1501-1508.
Sikorska, E., Khmelinskii, I.V., Kumasa, A., Koput, J., Ferreira, L.F.V., Herance,
J.R., Bourdelande, J.L., Williams, S.L., Worrall, D.R., Insinska-Rak, M., Sikorski,
M. (2005). Spectroscopy and photophysics of flavin related compounds:
riboflavin and iso-(6,7)-riboflavin. Chem. Phys., 314, 239-247.
Sikorski, M., Sikorska, E., Koziolowa, A., Moreno, R.G., Bourdelande, J.L., Steer,
R.P., Wilkinson, F. (2001). Photophysical properties of lumichrome in water. J.
Photochem. Photobiol., B: Biol., 60, 114-119.
Slifkin, M.A. (1971). Charge Transfer Interactions of Biomolecules. Academic Press,
London, pp. 132-172.
Smith, B.G.N., Wright, P.S., Brown, D. (1996). The Clinical Handling of Dental
Material. 2nd ed., Jordon Hill, Oxford, Part 3.
Smith, D.C. (1968). A New Dental Cement. Br. Dent. J., 124, 381-384.
Smith, D.C. (1998). Development of glass ionomer cements. Biomaterials, 19, 467-
478.
Smith, D.C. (1999). Polyacrylic acid-based cement: adhesion to enamel and dentin.
Oper. Dent., 5, 177-183.
Smith, E.C., Metzler, D.E. (1963). The photochemical degradation of riboflavin. J.
Am. Chem. Soc., 85, 3285-3288.
Song, P.S. (1971). Chemistry of flavin in their excited states. In: H. Kamin, (Ed.),
Flavins and Flavoproteins. University Park Press, Baltimore, pp. 37-61.
246
Song, P.S., Metzler, D.E. (1967). Photochemical degradation of flavins. IV. Studies
of the anaerobic photolysis of riboflavin. Photochem. Photobiol., 6, 691-709.
Song, P.S., Smith, E.C., Metzler, D.E. (1965). Photochemical degradation of flavins.
IV. The mechanism of alkaline hydrolysis of 6,7-dimethyl-9-
formylmethylisoalloxazine. J. Am. Chem. Soc., 87, 4181-4184.
Soratur, S.H. (2002). Essentials of Dental Materials. 1st ed., Jaypee Brothers, New
Delhi.
Sperling, L.H. (2006). Introduction to Physical Polymer Science. John Wiley &
Sons, New York.
Stamboulis, A., Law, R.V., Hill, R.G. (2004). Characterization of commercial
ionomer glasses using magnetic angle nuclear magnetic resonance (MAS–NMR).
Biomaterials, 25, 3907-3913.
Stamboulis, A., Hill, R.G., Law, R.V. (2005). Structural characterization of fluorine
containing glasses by 19F 27Al 29Si and 31P by MAS-NMR spectroscopy. J. Non-
Cryst. Solids, 351, 3289-3295.
Stansbury, J.W. (2000). Curing dental resins and composites by photopolymerization.
J. Esthet. Dent., 12, 300-308.
Stebbins, J.F., Kroeker, S., Lee, S.K., Kiczenski, T.J. (2000). Ion quantification of
five-and six-coordinated aluminum ions in aluminosilicate and fluoride-
containing glasses by high-field, high-resolution Al-27 NMR. J. Non-Cryst.
Solids, 275, 1-6.
Subbarao, V.K. (2007). Dental Materials. 5th ed., Paras Medical Publisher,
Hyderabad, India.
247
Sun, M., Moore, T.A., Song, P.S. (1972). Molecular luminescence studies of
flavins.1. The excited states of flavins. J. Am. Chem. Soc., 94, 1730-1740.
Taira, M., Urabe, H., Hirose, T., Wakasa, K., Yamaki, M. (1988). Analysis of photo-
initiators in visible light dental composite resins. J. Dent. Res., 67, 24-28.
Tanumiharja, M., Burrow, M.F., Cimmino, A., Tyas, M.J. (2001). The evaluation of
four conditioners for glass ionomer cements using field-emission electron
microscopy. J. Dent., 29, 131-138.
Tay, W.M., Lynch, E. (1990). Glass ionomer cements-clinical usage and experience.
2. Dent. Update, 17, 51-56.
Tay, F.R., Pashley, E.L., Huang, C., Hashimoto, M., Sano, H., Smales, R.J., Pashley,
D.H. (2001). The glass-ionomer phase in resin-based restorative materials. J.
Dent. Res., 80, 1808-1812.
Taylor, M.B., Radda, G.K. (1971). Flavins as photosensitizers. Methods Enzymol.,
18B, 496-506.
Tonnesen, H.H. (1996). Photostability of Drugs and Drug Formulations. Taylor &
Francis, London.
Tyas, M.J. (1989). Developments in light-cure lining materials. Aust. Dent. J., 34,
578.
Tollin, G. (1995). Use of flavin photochemistry to probe intraprotein and interprotein
electron transfer mechanisms. J. Bioenerg. Biomembr., 27, 303-309.
Tollin, G., Hurley, J.K., Hazzard, J.T., Meyer, T.E. (1993). Use of laser flash
photolysis time–resolved spectrophotometry to investigate interprotein and
intraprotein electron transfer mechanisms. Biophys. Chem., 48, 259-279.
248
Tomlinson, S.K., Ghita, O.R., Hooper, R.M., Evans, K.E. (2007). Investigation of the
dual setting mechanism of a novel dental cement using IR spectroscopy. Vib.
Spectrosc., 45, 10-17.
Toru, K.Y.N., Zhenga, C., Ohyab, S., Kannna, O.K.S. (2002). A novel photocurable
insulator material for autonomic nerve activity recording. Biomaterials, 23, 3169-
3174.
Traber, R., Vogelman, E., Schreiner, S., Werner, P., Kramer, H.E.A. (1981).
Reactivity of excited states of flavin and 5-deazaflavin in electron transfer
reactions. Photochem. Photobiol., 33, 41-48.
Treadwell, G.E., Cairns, W.L., Metzler, D.E. (1968). Photochemical degradation of
flavins, V. Chromatographic studies of the products of photolysis of riboflavin. J.
Chromatogr., 35, 376-388.
Tsai, L., Charney, E. (1969). The triplet states of a-dicarbonyls. J. Phys. Chem., 73,
2462-2463.
Turro, N.J., Ramamurthy, V., Scaiano, J.S. (2010). Modern Molecular
Photochemistry of Organic Molecules. University Science Books, Sausalito, CA,
Chap. 8, 9.
Valdebenito, M.V., Encinas, M.V. (2003). Photopolymerization of 2-hydroxyethyl
methacrylate. Effect of the medium properties on the polymerization rate. J.
Polym. Sci., Part A, 41, 2368-2373.
Van Noort, R. (2002). Introduction to Dental Materials. 2nd ed., Mosby, New York.
Visser, A.J.W.G., Muller, F. (1979). Absorption and fluorescence studies on neutral
and cationic isoalloxazines. Helv. Chim. Acta, 62, 593-608.
249
Wahl, Ph., Auchet, J.C., Visser, A.J.W.G., Mullar, F. (1974). Time resolved
fluorescence of flavin adenine dinucleotide. FEBS Lett., 44, 67-70.
Walls, A.W.G. (1986). Glass polyalkenoate (glass-ionomer) cements: a review. J.
Dent., 14, 231-246.
Walls, A.W.C., Adamson, J., McCabe, J.F., Murray, J.J. (1987). The properties of
a glass polyalkenoate (ionomer) cement incor-porating sintered metallic
particles. Dent. Mater., 3, 113-116.
Wan, A.C.A., Yap, A.U.J., Hastings, G.W. (1999). Acid-base complex reaction in
resin-modified and conventional glass ionomer cements. J. Biomed. Mater. Res.,
48, 700-704.
Wang, K., Nie, J. (2009). 6-Benzoyl-1,3-benzodioxolane as a photoinitiator for free
radical polymerization J. Photochem, Photobiol, A: Chem., 204, 7-12.
Wang, Y., Spencer, P., Yao, X., Ye, Q. (2006). Effect of coinitiators and water on the
photoreactivity and photopolymerization of HEMA/camphoquninone-based
mixtures. J. Biomed. Mater. Res. A, 78, 721-728.
Wasson, E.A., Nicholson, J.W. (1990). Study of the relationship between setting
chemistry and properties of modified glass-poly (alkenoate) cements. Br. Polym.
J., 23, 179-183.
Watts, D.C. (2005). Reaction kinetics and mechanics in photopolymerized networks.
Dent. Mater., 21, 27-35.
Watts, D.C., Cash, A.J. (1991). Determination of polymerization shrinkage kinetics in
visible light-cured materials: methods and development. Dent. Mater., 7, 281-287.
250
Watts, D.C., Amer, O., Combe, E.C. (1984). Characteristics of visible-light-activated
composite systems. Br. Dent. J., 156, 209-215.
Watts, D.C., Marouf, A.S., Al-Hindi, A.M. (2003). Photopolymerization shrinkage-
stress kinetics in resin-composites: methods and development. Dent. Mater., 19,
1-11.
Weber, G. (1950). Fluorescence of riboflavin and flavin adenine dinucleotide.
Biochem. J., 47, 114-121.
Williams, J.A., Billington, R.W., Pearson, G.J. (1992). The comparative strengths
of commercial glass-ionomer cements with and without metal additions. Br.
Dent. J., 172, 279-282.
Williams, J.A., Billington, R.W., Pearson, G.J. (2002). The glass ionomer cement
the sources of soluble fluoride. Biomaterials, 23, 2191-2200.
Wilson, A.D. (1978). The chemistry of dental cements. Chem. Soc. Rev., 7, 265-296.
Wilson, A.D. (1989). Developments in glass-ionomer cements. Inter. J. Prosthodont.,
2, 438-446.
Wilson, A.D. (1990). Resin-modified glass ionomer cements. Int. J. Prosthodont., 3,
425-429.
Wilson, A.D. (1996a). Secondary reaction of glass ionomer cements. J. Mater. Sci.,
15, 275-276.
Wilson, A.D. (1996b). A hard decade’s work: Steps in the invention of the glass-
ionomer cement. J. Dent. Res., 75, 1723-1727.
251
Wilson, A.D., Hill, R.G., Warren, C.P., Lewis, B.G. (1989). The influence of
polyacid molecular weight on some properties of glass ionomer cements. J.
Dent. Res., 68, 89-94.
Wilson, A.D., McLean, J.W. (1988). Glass Ionomer-Cement. Quintessence
Publishing Co., Chicago.
Wilson, A.D., Nicholson, J.W. (1993). Acid-Base Cements: Their Biomedical and
Industrial Applications. Cambridge University Press, Cambridge.
Wilson, A.D., Kent, B.E. (1971). The glass-ionomer cement: a new translucent dental
filling material. J. Appl. Chem. Biotechnol., 21, 313-320.
Wilson, A.D., Kent, B.E. (1972). A new translucent cement for dentistry- the glass
ionomer cement. Br. Dent. J., 132, 133-135.
Wochet, I., Schmidt-Naake, G., Beuermann, S., Buback, M., Garcia, N. (2008).
Propagation kinetics of free-radical polymerization in ionic liquid. J. Polym. Sci.
Part A Polym. Chem., 46, 1460-1469.
Wu, W., Xie, D., Puckett, A., Mays, J. (2003). Synthesis of amino acid-containing
polyacids and their application in self-cured glass-ionomer cement. Eur. Polym.
J., 39, 959-968.
Xie, D., Brantley, W.A., Culbertson, B.M., Wang, G. (2000). Mechanical properties
and microstructures of glass ionomer cements. Dent. Mater., 16, 129-138.
Xie, D., Chung, I.D., Wu, W., Mays, J. (2004b). Synthesis and evaluation of HEMA-
free glass-ionomer cements for dental applications. Dent. Mater., 2, 470-478.
252
Xie, D., Chung, I.D., Wu, W., Lemons, J., Puckett, A., Mays, J. (2004a). An amino
acid-modified and non-HEMA containing glass-ionomer cement. Biomaterials,
25, 1825-1830.
Xie, D., Culbertson, B.M., Johntson, W.M. (1998). Improved flexural strength of
N-vinylpyrrolidone modified acrylic acid copolymers for glass-ionomers. J.
Macromol. Sci. Pure Appl. Chem., 35, 1615-1629.
Xie, D., Park, J.G., Faddah, M., Zhao, J., Khanijoun, H.K. (2006a). Novel amino
acid-constructed polyalkenoates for dental glass-ionomer restoratives. J.
Biomater. Appl., 21, 147-165.
Xie, D., Park, J.G., Faddah, M., Zhao, J. (2006b). Preparation, formulation and
evaluation of novel photo-cured glass ionomers based on co-polymers of
methacrylated amino acids. J. Biomater. Sci. Polym. Ed., 17, 303-322.
Xu, H., Wu, G., Nie, J. (2008). Synthesis and photopolymerization characteristics of
amine coinitiators. J. Photochem. Photobiol. A: Chem., 193, 254-259.
Yamazaki, T., Brantley, B.W., Culbertson, B.M., Seghi, R., Schricker, S. (2005). The
measure of wear in N-vinyl pyrrolidinone (NVP) glass-ionomer cements. Polym.
Adv. Technol., 16, 113-116.
Yaobin, R., Huiming, P., Longsi, L., Jianming, X., Yongqiang, Y. (2006). Synthesis
of Polyurethane Acrylate and Application to Ultraviolet-Curable Pressure-
Sensitive Adhesive. Polym. Plast. Technol. Eng., 45, 495-502.
Ye, Q., Park, J., Topp, E., Spencer, P. (2009). Effect of photoinitiators on the in vitro
performance of a dentin adhesive exposed to simulated oral environment. Dent.
mater., 25, 452-458.
253
Yip, H.K., To, W.M. (2005). An FTIR study of the effect of artificial saliva on the
physical characteristics of GICs used for art. Dent. Mater., 21, 695-703.
Young, A.M. (2002). FTIR investigation of polymerization and polyacid
neutralization kinetics in resin-modified glass ionomer dental cements.
Biomaterials, 23, 3289-3295.
Young, H.M., Shen, C., Maryniuk, G.A. (1985). Retention of cast posts relative to
cement selection. Quintessence Int., 16, 357-359.
Young, A.M., Rafeeka, S.A., Howlett, J.A. (2004). FTIR investigation of monomer
polymerization and polyacid neutralization kinetics and mechanisms in various
aesthetic dental restorative materials. Biomaterials, 25, 823-833.
Young, A.M., Sherpa, A., Pearson, G.J., Schottlander, B. (2009). Spectroscopic
characterization of new fluoride releasing aesthetic dental restoratives.
Biomaterials, 25, 823-833.
Young, A.M., Sherpa, A., Pearson, G.J, Schottlander, B., Waters, D.N. (2000). Use of
Raman spectroscopy in the characterization of the acid-base reaction in glass
ionomer cement. Biomaterials, 21, 1971-1979.
Zainuddin, N., Karpukhina, N., Hill, R.C. (2008). A long term study on the setting
reaction of glass ionomer cements by 27Al MAS–NMR spectroscopy. Dent.
Mater., 25, 290-295.
254
AUTHOR’S PUBLICATIONS
PAPERS PUBLISHED
INTERNATIONAL
1. Iqbal Ahmad, Kefi Iqbal, Sofia Ahmed and M.A. Sheraz, “Applications of Laser
Flash Photolysis, Spectroscopy and Electron Microscopy in
Photopolymerization and Development of Glass Ionomer Dental Cements”,
International Journal of Clinical Dentistry. 4, 1-17 (2011).
2. Muhammad Ali Sheraz, Sofia Ahmed, Iqbal Ahmad, Faiyaz H.M. Vaid and Kefi
Iqbal, “Formulation and Stability of Ascorbic Acid in Topical Preparations”,
Systematic Reviews in Pharmacy, 2, 93-97 (2011).
3. Iqbal Ahmad, Sofia Ahmed, M.A. Sheraz, Kefi Iqbal and Fayiaz H.M. Vaid,
“Pharmacological Aspects of Borates”, International Journal of Medical and
Biological Frontier. 16, 977-1004 (2010).
4. Sofia Ahmed, M. A. Sheraz, M. Aminuddin, Iqbal Ahmad, Karamat Mahmood
and Kefi Iqbal, “Analysis of Amino Acids By Paper Chromatography”,
International Journal of Chemical and Analytical Science. 1, 174-176 (2010).
5. Sofia Ahmed, Muhammad Ali Sheraz, Kefi Iqbal and Iqbal Ahmad, “Surgical
Trends in the Treatment of Parkinson’s Disease and their Outcome”, Journal
of Medical Sciences 3, 142-152 (2010).
255
NATIONAL
6. Sajid Hanif, M. Noman Sheikh, S. Fareed Mohsin, Kefi Iqbal, and S. Azhar
Ahmed, “The Expression of Erythropoietin and Erythropoietin Receptor in
Oral Squamous Cell Carcinoma”, Pakistan Journal of Pathology. 21, 48-54
(2010).
7. Kefi Iqbal, Sana Adeba Islam, Iqbal Ahmad, Maria Asmat and M. Aminuddin,
“Variation in Powder / Liquid Ratio of a Restorative and Luting Glass
Ionomer Cement in Dental Clinics”, Journal of the College of Physicians and
Surgeons Pakistan. 19, 464-465 (2009).
8. Kefi Iqbal, Iqbal Ahmad and M. Aminuddin, “Spectroscopic Techniques in the
Development of Glass ionomer Cements”, Journal of Pakistan Dental
Association. 18, 1-5 (2009).
9. S. Fareed Mohsin, Saad A. Khan, Nasreen Amanat, Kefi Iqbal, Alan Cruchley
and S. Azhar Ahmed, “The Levels of Cytokines- The effect of Betel
Quid/Areca Nut on Oral Epithelium”, Pakistan Journal of Pathology. 20, 85-90
(2009).
10. Kefi Iqbal, Iqbal Ahmad, M. A. Sheraz, Sofia Ahmed, M. Aminuddin and Tania
Mirza, “Use of Different Light-Curing Units in Setting of Dental Restorative
Materials”, Journal of Baqai Medical University. 12, 51-54 (2009).
11. Tania Mirza, Kiran Qadeer, Sadia Hafeez, Kefi Iqbal and Iqbal Ahmad, “Folic
Acid and Deficiency Diseases”, Journal of Baqai Medical University. 12, 47-50
(2009).
256
12. Syed Fareed Mohsin, Shahnaz Fayyaz, Shazia Nazar and Kefi Iqbal, “Prevalence
of Periodontal Disease in Gadap Region Karachi”, Journal of Baqai Medical
University 12, 19-24 (2009).
13. Kefi Iqbal, Afreen Mushtaque, Maria Asmat, Ifthakar Ahmed, Fareed Mohsin and
Adel Siddiqui, “Role of Abrasive in Dentistry”, Journal of Baqai Medical
University. 11, 17-22 (2008).
14. Kefi Iqbal, Iqbal Ahmad and M. Aminuddin, “Development of Glass ionomer
Cements as Dental Restorative Materials”, Journal of Baqai Medical
University. 10, 9-12 (2007).
15. Iftikhar Ahmed, M. Sarwar, Hafiz Sheikh and Kefi Iqbal, “Acne in Adolescent”,
Journal of Baqai Medical University. 10, 25-30 (2007).
16. Kefi Iqbal, Maria Asmat, Sana Jawed, Majid Zia, Fareed Mohsin, Sajid Hanif,
Nuaman Sheikh and Iftikhar Ahmed, “Uses and Effects of Mercury in Medicine
and Dentistry”, Journal of Ayub Medical College (in press).
17. Kefi Iqbal, Maria Asmat, Sana Jawed, Majid Zia, Afreen Mushtaque, Fareed
Mohsin, Nuaman Sheikh, Sajid Hanif, Adel Siddiqui, Iftikhar Ahmed, Yawer
Abdi and Feroze Ali, Study of Dental Amalgam: Influence of Alloy/Mercury
mixing ratio, Uses and Waste Management”, Journal of Ayub Medical College
(in press).
18. Kefi Iqbal, Maria Asmat, Sana Jawed, Afreen Mushtaque, Fareed Mohsin, Sajid
Hanif, Nuaman Sheikh, “Role of Different Ingredients of Tooth Pastes and
Mouthwashes in Oral Health”, Journal of Pakistan Dental Association (in
press).
257
19. Tania Mirza, Kefi Iqbal and Iqbal Ahmad, “Clinical Analysis, Metabolism and
Bioavalibility of Thiamine”, Journal of Baqai Medical University (in press).
20. Tania Mirza, Sadia Hafeez Kazi, Zufi Shad, Kefi Iqbal and Iqbal Ahmad,
“Biochemical Importance, Deficiency and Clinical Assay of Cynocobalamin”,
Journal of Baqai Medical University (in press).
PAPERS SUBMITTED
21. Muhammad Irfan, Sofia Ahmed, Muhammad Ali Sheraz, Muhammad
Aminuddin, Iqbal Ahmad, Karamat Mahmood and Kefi Iqbal, “Heavy Metals
Accumulation in Fruits and Vegetables Grown on Sewage Sludge and that of
River Water”, submitted to Pakistan Journal of Botany.
22. Iqbal Ahmad, Kefi Iqbal, Sofia Ahmed, Muhammad Ali Sheraz, Muhammad
Aminuddin and Ihtesham ur Rehman, “Photoinitiated Polymerization of 2-
Hydroxyethyl Methacrylate by Riboflavin/ Triethanolamine in Aqueous
Solution: A Kinetic Study”, submitted to Journal of Dentistry.
23. Iqbal Ahmad, Kefi Iqbal, Muhammad Ali Sheraz, Sofia Ahmed, Mohammad
Aminuddin, Tania Mirza, Syed Abid Ali and Ihtesham ur Rehman, “Solvent
Effect on Photoinitiator Reactivity in the Polymerization of 2-Hydroxyethyl
Methacrylate”, submitted to Polymer Degradation and Stability.
24. Iqbal Ahmad, Tania Mirza, Sofia Ahmed, Muhammad Ali Sheraz, Kefi Iqbal and
Faiyaz H.M. Vaid, “Effect of pH on the Photolysis of Formylmethylflavin in
Aqueous Solution: A Kinetic Study”, submitted to Photochemical
Photobiological Sciences.