assessment of the quality of resin_dentin bonded interfaces
TRANSCRIPT
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Available online at www.sciencedirect.com
journal homepage: www.int l .e lsevierheal th.com/ journals/dema
Assessmentof the quality of resindentinbonded
interfaces: An AFM nano-indentation, TBS and confocal
ultramorphology study
Salvatore Sauroa,b,, Raquel Osoriob, Timothy F. Watson a, Manuel Toledano b
a Biomaterials, Biomimetics and Biophotonics Research Group (B3), Kings College London Dental Institute, Guys Dental Hospital,
London, UKb Dental Materials, School of Dentistry, University of Granada, Colegio Mximo, Campus de Cartuja, Granada, Spain
a r t i c l e i n f o
Article history:
Received 3 June 2011
Received in revised form
4 November 2011
Accepted 16 February 2012
Keywords:
AFM/nano-indentation
Biomechanical properties
Confocal microscopy
EDTA
Resindentin interfaces
TBS
a b s t r a c t
Objective. The aim of this study was to assess by using confocal microscopy (CLSM), AFM
nano-indentation and microtensile bond strength test (TBS) thequality of theresindentin
interfaces created with selected bonding parameters.
Methods. Dentin conditioned with H3PO4or EDTA was bonded in ethanol- or water-wet condi-
tion using a HEMA-free or HEMA-containing adhesive. The resin-bonded teeth were stored
in distilled water (24 h) and sectioned as match-sticks (0.9mm2) for TBS. Further resin-
bonded teeth were sectioned and analyzed using CLSM, and AFM nano-indentation. The
AFM imaging and nano-indentation processes were undertaken using a Berkovich diamond
indenter. The modulus of elasticity (Ei) and hardness (Hi) across the interface were evalu-
ated with the specimens in a fully hydrated status. The AFM imaging was performed both
in dry and wet conditions for evaluating the shrinkage of the hybrid layer on dehydration.
Results. The HEMA-containing adhesive applied onto H3PO4-etched ethanol or water-wet
dentin created hybrid layers with the lowest biomechanicalnano-properties (p < 0.05);no sig-
nificant differences in TBS were found between the two wet-bonding techniques (p > 0.05).
However, the ethanol-wet bonding reduced the dye penetration into the adhesive layer cre-
ated with the HEMA-containingadhesive. Hybrid layers with high biomechanical properties,
low micropermeability and no shrinkagewere onlypossiblewhen usingHEMA-free adhesive
applied in ethanol wet-dentin. In particular, a significant increase in Ei and Hi was achieved
at the hybrid layer and underneath the resindentin interface of ethanol-wet EDTA-treated
dentin.
Significance. The use of HEMA-free adhesives applied onto ethanol-wet dentin may be con-
sidered as an alternative and suitable bonding strategy to achieve high quality resindentin
interfaces.
2012 Academy of Dental Materials. Published by Elsevier Ltd. All rights reserved.
Corresponding author at: Biomaterials, Biomimetics and Biophotonics Research Group (B3), Kings College London Dental Institute, Floor17 Guys Tower, London SE1 9RT, England, UK. Tel.: +44 0207 188 3874; fax: +44 0207 188 1823.
E-mail address: [email protected] (S. Sauro).0109-5641/$ see front matter 2012 Academy of Dental Materials. Published by Elsevier Ltd. All rights reserved.
doi:10.1016/j.dental.2012.02.005
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1. Introduction
The demineralization of dentin and the exposure of the colla-
gen matrix is a crucial step in adhesive dentistry to achieve a
micromechanical interlocking between resin monomers and
dentin [1,2]. The water-wet bonding technique is commonly
used in etch-and-rinse bonding procedures to suspend thedemineralized collagen fibrils and prevent shrinkage caused
by the electrostatic attraction (i.e. hydrogen bonds forma-
tion) of dentinal proteoglycans and glycosaminoglycans [3].
Unfortunately this bonding technique does not allow a com-
plete resin infiltration of the demineralized dentin, leaving
unprotected collagen fibrils below and within the hybrid layer
[46]. The imperfect resin infiltration is mainly due to the
incomplete replacement of water from the demineralized col-
lagen network, especially when vital dental pulps perfuse
dentinal fluid [7,8]. Unprotected collagen fibrils within the
hybrid layer may be degraded by the action of endogenous
matrix metalloproteinases (MMPs) derived from the deminer-
alized dentin [9,10]. Moreover, poor infiltrated hybrid layershave an evident attitude to water-sorption that contributes
to the hydrolytic degradation of the resindentin interface
[11,12]. The ethanol-wet bonding technique has been shown
to increasethe longevityof resin-bondedH3PO4-etcheddentin
[3,13]. In this technique, absolute ethanol, a polar solvent with
less hydrogen bonding capacity than water [14], may be used
to chemically dehydrate the demineralized collagen matrix,
reduce the hydrophilicity of the collagen matrix and create
wider interfibrillar spaces for a better resin infiltration [15,16].
It has been demonstrated that poor-quality hybrid layers
are characterized by an excessive presence of water are also
affected by nano/micro porosities phase separation and low
monomer polymerization[15,18]. The assessment of thehard-nessand modules of elasticityalong the resindentin interface
[18] and the hybrid layer resistance to dry shrinkage may be
suitable to achieve further knowledge on the quality of hybrid
layers created using the etch-and-rinse technique. Neverthe-
less, there is still little information available regarding the
quality of formed resindentin interfaces with etch-&-rinse
adhesives applied with water or ethanol-wet bonding tech-
niques and with HEMA-free or HEMA-containing resins [20].
The aim of this study was to evaluate the bond
strength (TBS), the ultramorphology/micropermeability and
the biomechanical nano-properties of the resindentin inter-
face created with two experimental etch-&-rinse adhesives
applied onto 37%-H3PO4 or 0.5 M-EDTA conditioned dentinwhen using the water-wet or ethanol-wet bonding techniques
(5min.). The null hypotheses to be tested are that the use
of: (1) H3PO4 vs. EDTA to condition dentin, (2) water-wet vs.
ethanol-wet bonding techniques and (3) HEMA-free vs. HEMA-
containing adhesives do not affect the quality of the created
resindentin interfaces.
2. Materials and methods
2.1. Specimenpreparation
Caries-free human molars (age:1840 yr) extracted for surgical
reasons under an informed consent, reviewed and approved
by the Institutional Ethics Committee, were stored in 0.5%
chloramine-Tat 4 Cfornomore than 1 month.The teeth were
sectioned 1 mm beneath the cemento-enamel junction using
a diamond wafering blade (Isomet 11/1180, Buehler, Coventry,
UK). The occlusal enamel was removed to expose the middle
coronal dentin and a standard smear layer was created using
500 grit SiC paper (Struers LaboPol-4. Struers, Copenhagen,
Denmark).
2.2. Experimental adhesives and bondingprocedures
Two experimental etch-and-rinse bonding systems were pre-
pared: (i) a HEMA-containing resin blend (HEMA-containing)
was formulated using UDMA-60%/BisGMA-10%/TEGDMA-30%
(Esstech Essington, PA, USA). A hydrophilic monomer (2-
hydroxyethyl methacrylate, Aldrich Chemical Co, Gillingham,
UK) [2040%] and absoluteethanol (AldrichChemical), [70%for
the primer and 10% for the bond] were subsequently added to
the neat resin blend. (ii) a HEMA-free resin blend (HEMA-free)
was formulated using UDMA-60%/BisGMA-10%/TEGDMA-30%
(Esstech Essington, PA, USA) and dissolved in absolute ethanol(Aldrich Chemical), [70% for the primer and 10% for the
bond]. The experimental resin blends were finally mixed with
0.5wt% of camphoroquinone (Aldrich Chemical) and 1.0wt%
of ethyl 4-dimethylaminobenzoate (Aldrich Chemical). Forty-
eight dentin specimens were divided into two main groups.
Five-minute sonication (Model QS3, Ultrawave Ltd, Cardiff,
UK) and 2-day shaking (Orbital Shakers PSU-20i, Cole Fisher
Scientific Ltd, Loughborough, UK) were required to yield well-
mixed resin solutions. The specimens (n = 12) of the first group
were etched using a 37% phosphoric acid gel (H3PO4; Bisco,
Itasca, IL, USA) for 15s and the specimens of the second group
(n = 12)wereconditioned for60 s usinga 0.5M water solutionof
ethylenediaminetetraacetic acid (EDTA: 99.995%, Lot. 431788-Aldrich Chemical).
The specimens of each group were copiously rinsed with
water for 1 min and immediately immersed in absolute ethyl
alcohol (EtOH), (Aldrich Chemical) for 5 min (n =6) or in deion-
ized water (H2O) for 1min (n =6), [17,18]. The dentin surface
wasalways covered by ethanol to avoid surface tension forces,
keeping it visibly moist prior to the application of the resins.
The water-wet bonding substrate was achieved by water-
rinsing the dentin surfaces and gently blowing off the excess
water to leave a wet reflective surface [17]. The primer and
the bond were applied within a period of 20s and light-cured
for 30s using a halogen light-curing unit (Translux EC Kulzer
GmBh, Bereich Dental, Werheim, Germany). The output inten-sity was monitored with a Demetron Radiometer (Model 100,
Demetron Research, Danbury, CT, USA) to maintain a mini-
mal light output intensity of 600 mW/cm2 throughout all the
experiment. A flowable resin composite (X-FlowTM, Dentsply,
Caulk, UK) was placed incrementally in two 1 mm layers and
light-cured for 40 s (Demetron Research).
2.3. AFM imaging and nano-indentation
The resin-bonded specimens were left undisturbed in water
for 3h and then cut perpendicularly to the bonding zone
using a diamond saw (Isomet 11/1180) to obtain 3 resindentin
slabs with a thickness of 2 mm. The resindentin slabs were
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Table 1 Mean and standard deviation (SD) of the biomechanical nano-elasticity (Ei) and nano-hardness (Hi).
Ei HEMA-containing H2O HEMA-containing EtOH HEMA-free H2O HEMA-free EtOH
GPa PA EDTA PA EDTA PA EDTA PA EDTA
1st HL 2.2 0.8 A1 12.0 0.9 A2 2.2 0.8 A1 12.0 0.9 A2 6.4 0.6 A1 11.7 1.2 A2
2nd 10.9 1.1 B1 14.1 2.0 A2 10.9 1.1 B1 14.1 2.0 A2 11.7 1.4 B1 14.9 1.0A2
3rd 17.4 1.1 C1 16.8 1.7 B1 17.4 1.1 C1 16.8 1.7 B1 16.9 0.6 C1 18.9 1.0 B1
4th 18.1 1.1 C1 17.7 1.1 B1 18.1 1.1 C1 17.7 1.1 B1 18.2 1.4 C1 19.9 1.1 B15th 19.1 0.9 C1 18.2 1.2 B1 19.1 0.9 C1 18.2 1.2 B1 19.2 0.9 C1 20.1 0.7 B1
6th 19.8 1.1 C1 18.7 1.0 B1 19.8 1.1 C1 18.7 1.0 B1 19.2 1.5 C1 20.3 1.2 B1
Hi HEMA-containing H2O HEMA-containing EtOH HEMA-free H2O HEMA-free EtOH
GPa PA EDTA PA EDTA PA EDTA PA EDTA
1st HL 0.1 0.01 A1 0.3 0.03 A2 0.1 0.01 A1 0.3 0.12 A2 0.3 0.01 A2 0.3 0.04 A2
2nd 0.4 0.04 B1 0.6 0.05 B2 0.4 0.08 B1 0.6 0.07 B2 0.5 0.08 A2 0.6 0.03 B2
3rd 0.7 0.09 C1 0.7 0.04 C1 0.7 0.09 C1 0.7 0.03 C1 0.7 0.09 C1 0.8 0.05 C1
4th 0.6 0.16 C1 0.7 0.05 C1 0.7 0.10 C1 0.7 0.07 C1 0.7 0.10 C1 0.8 0.04 C1
5th 0.7 0.11 C1 0.7 0.08 C1 0.7 0.12 C1 0.7 010 C1 0.8 0.12 C1 0.9 0.09 C1
6th 0.7 0.06 C1 0.8 0.07 C1 0.8 0.08 C1 0.8 0.07 C1 0.8 0.08 C1 0.9 0.06 C1
Mean and standard deviation (SD) of the biomechanical properties (Ei and Hi) along the tested resindentin interfaces. Same letter indicatesno
differences in columns (p > 0.05). Same number indicates no differences in rows (p > 0.05).
Fig. 2 Topographic AFM images obtained in dry and wetconditions from the resindentin interfaces created using the
HEMA-containing experimental adhesives applied onto H3PO4-etched water-wet dentin. [A] In this image it is possible to
observe how the hybrid layer (HL) collapsed and formed a wide gap between the dentin (d) and the adhesive (a)
characterized by the presence of uncollapsed resin tags (t). [B] The re-hydration of the specimen induced a complete
expansion of the hybrid layer (hl), leaving only a thin gap between the adhesive (a) and the hybrid layer.
Table 2 Microtensile bond strength values (MPa) to dentin when resin adhesives were applied with the ethanol- orwater-wet bonding in EDTA or H3PO4 treated dentin.
EDTA PA: H3PO4
HEMA-containing H2O-wet 41.3 (13.1) a1 (5%) [0/72/28] 38.3 (12.2)a1 (12%) [0/69/31]
HEMA-containing EtOH-wet 43.8 (11.1) a1 (0%) [0/84/16] 45.2 (10.9)a1 (2%) [0/78/22]
HEMA-free H2O-wet
HEMA-free EtOH-wet 44.9 (10.1) a1 (8%) [2/68/30] 36.1 (11.5)a1 (16%) [12/71/17]
Mean (standard deviation) microtensile bond strength (MPa) to dentin. Same superscripts letters indicate no differences (p > 0.05) in columns.
Same superscript numbers indicate no differences (p > 0.05) in rows. Percentage of premature failures is indicated in parentheses. The modes
of failure are also expressed in percentage into brackets as [adhesive/mix/cohesive].
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Fig. 3 Topographic AFM images obtained in dry and fully hydrated conditions from the resindentin interfaces created
using the two experimental etch & rinse adhesives applied onto the EDTA or H3PO4 treated dentin in ethanol or water-wet
bonding. [A] A resindentin interface created using the HEMA-containing adhesive that was applied onto H3PO4-etched
water-wet dentin is presented. The imaging process performed in dry conditions caused the shrinkage of the hybrid layer
(HL) and the formation of a wide gap (78m)between the dentin (d) and the adhesive layer (a). [B] The experimental
HEMA-containing adhesive applied onto EDTA treated dentin with the water-wet bonding technique was also characterized
by the presence of a wide gap (78m)between the dentin (d) and the composite (c) due to the shrinkage of the hybrid (hl)
and adhesive layer (a). [C] The hybrid layer of the resindentin interface created using the HEMA-containing adhesive
applied onto ethanol-saturated H3PO4-etched dentin showed only a slender gap/shrinkage (34m) of the hybrid layer (a) in
the proximity of the dentin (d); uncollapsed resin tags (t) are still present within the gap. [D] The resindentin interface
created using the HEMA-containing adhesive applied onto ethanol-wet EDTA-treated dentin showed a well extended
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sub-dived (n = 5)according to the wet-bonding technique (EtOH
or H2O). The specimens were sectioned with a diamond blade
(Accutom-50, Struers, Copenhage, Denmark) using a hard tis-
sue saw (330-CA RS-70300, Struers, Copenhage, Denmark) in
both x andy directions across the adhesive interface to obtain
match-sticks with cross-sectional areas of 0.9mm2.
Eachbeam was attached to a modified Bencor Multi-testing
apparatus (Danville Engineering Co., Danville, CA, USA) withcyanoacrylate adhesive (Zapit, Dental Ventures of America
Inc., Corona, CA, USA) and tested using a microtensile bond
strength testing machine (Instron 4411, Instron Corporation,
Canton, MA, USA) at a crosshead speed of 0.5 mm/min. Bond
strength datawere calculated in MPa. Pre-testing failures were
arbitrarily assigned with a value 0 and included in the sta-
tistical analysis. Two-way ANOVA including interactions and
Student-Newman-Keuls multiple comparisons were used for
the statistical analysis. Adhesive systems and dentin sur-
face treatment were considered as independent variables and
TBS as the dependent variable. Statistical significance level
was set in advance at =0.05.
2.5. Confocal laser scanning microscopy evaluation
(CLSM)
Further dentin specimens (n =12) for each principal group
(Hema-free or Hema-containing) were first dived in 2 sub-
groups (n =6) according to the dentin conditioning method
(EDTA or H3PO4) and subsequentlysub-dived (n = 3) according
to thewet-bonding technique (EtOH or H2O).The dentinspeci-
mens were bonded as previously described with the adhesives
doped with 0.1wt% Rhodamine B (Sigma Chemicals, St. Louis,
MO, USA). The pulp chamber of the specimens was exposed
by gently removing the pulpal tissue using a thin tissue pin-
cers. The specimens were immediately filled with 0.1wt%water solution of fluorescein (FL: Sigma Chemicals) for 3h
[17,18]. The specimens were finally rinsed in a H2O ultrasonic
bath for 2min and sectioned into 1mm mesio-distal slabs
using a slow-speed water-cooled diamond saw (Labcut, Agar
Scientific, Stansted, UK). The resindentin slabs were finally
polished using 1200-grit SiC paper for 30s followed by H2O
ultrasonic bath (1m). Each resin-dentin interface was com-
pletely investigated and five images representing the most
common features of micropermeability were randomly cap-
tured and recorder. The imaging procedures were performed
using a confocal laser scanning microscope (Leica SP2 CLSM,
Heidelberg, Germany) equipped with a 63/1.4 NA oil immer-
sion lens using488 nm argon/heliumand a 633nm krypton ion
laser illumination. CLSM fluorescence images were obtained
from 20m optical sections using a 1m z-step below the sur-
face. The z-axis scan of the interface surface were converted
into pseudo-color for better visualization, and compiled into
both single and topographic projections using Leica SP2 CLSM
image-processing software (Leica, Heidelberg, Germany). The
configuration of the system was standardized and used at the
same level for the entire investigation.
3. Results
3.1. AFM imaging and nano-indentation
Ei and Hi were both affected by dentin surface treat-
ment (EDTA/H3PO4), (p 0.05). Mean andstandard deviations of Ei andHi measured
along the resindentin interfaces are shown in Table 1.
The H3PO4-etched water-wet dentin exhibited the lowest
(p
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Fig. 4 Confocal fluorescence images of the resindentin interfaces created with the two experimental etch-&-rinse
adhesives (i.e. HEMA-free and HEMA-containing) applied onto H3PO4 or EDTA-treated dentin in water-wet or ethanol-wet
bonding conditions. The scale bar is 20m. [A] CLSM fluorescence 3D-single projection of resin-bonded dentin interfaces
created with HEMA-containing resin applied onto H3PO4etched water-wet dentin. This image shows how the water-wet
bonding induces severe micropermeability within the interface. The fluorescein dye penetrated throughout the dentinal
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type (EtOH/H2O), (F = 84.11; p 0.05). Mean bond strengths in MPa and
mode of failures obtained for each group are shown in Table 2.
The HEMA-containing adhesive produced no statistical dif-
ferences in bond strengths when applied onto H3PO4 acid
or EDTA-treated water-wet dentin. The failure mode waspredominantly cohesive or mixedin both groups. The applica-
tion of the HEMA-containing adhesive induced no statistical
differences when applied both onto H3PO4 acid etched or
EDTA-treated ethanol-wet dentin. Also in this case the failure
mode was predominantly cohesive or mixed in both groups.
No statistical difference was observed when the HEMA-
containing adhesive was applied onto H3PO4 acid etched or
EDTA-treated water-wet dentin.
The HEMA-free adhesive applied onto water-wet H3PO4acid etched or EDTA-treated dentin failed completely dur-
ing the cutting procedures. Conversely, when the HEMA-free
adhesive was applied onto ethanol-wet H3PO4 acid etched or
EDTA-treated dentin it was possible to obtain values (MPa)comparable to those attained with HEMA-containing adhe-
sive; no statistical differences were observed between H3PO4acid etched and EDTA-treated ethanol-wet dentin.
3.3. Confocal laser scanning microscopy evaluation
(CLSM)
The CLSM images of the resindentin interfaces created with
the two experimental etch-&-rinse adhesives applied onto
H3PO4 or EDTA-treated water/ethanol-wet dentin are shown
in Fig. 4.
The HEMA-containing adhesive applied onto H3PO4
etched or EDTA-treated water wet dentin was character-ized by severe micropermeability throughout the dentinal
tubules, hybrid layer and adhesive layer (Fig. 4A and B). On
the contrary, the resindentin interfaces created with HEMA-
containing adhesive applied onto H3PO4 etched ethanol-wet
dentin was characterized by long resin tags and an opti-
mal sealing ability; hybrid and adhesive layers were devoid
of any FL penetration (Fig. 4C). The resin-bonded dentin
interfaces created with HEMA-containing adhesive applied
onto EDTA-conditioned ethanol-wet dentin showed no FL dif-
fusion both into the adhesive layer and hybrid layer (Fig. 4D).
The HEMA-free adhesive applied onto H3PO4-etched
ethanol-wet dentin presented modest micropermeability (FL)
localized at the bottom of a hybrid layer (Fig. 4E and F).
Likewise, the micropermeability of the resindentin inter-face created with the HEMA-free adhesive applied onto
EDTA-conditioned ethanol-wet dentin was only detected
throughout the dentinal tubules and on the bottom of the
hybrid layer (Fig. 4G and H).
4. Discussion
The null hypotheses have to be rejected as the
biomechanical nano-properties, TBS and microperme-
ability/ultramorphology were influenced by the dentin
conditioning approach (H3PO4 or EDTA), bonding technique
(ethanol-wet or water-wet) and adhesive type (HEMA-free orHEMA-containing) selected in this study.
The results of this study have shown that the resindentin
interfaces created using the HEMA-containing adhesive
applied onto EDTA-treated ethanol-wet dentin were charac-
terized by a slender shrinkage of the hybrid layer (when
imaged in dry condition), (Fig. 3D). However, the biomechani-
cal nano-properties of the hybrid layer and the dentin region
immediately underneath the hybrid layer resulted higher than
those observed along the resindentin interfaces created in
H3PO4-etched dentin (Table 1). The demineralized zone at the
bottom of the hybrid layer is a critical part of the resin-dentin
interfaces created when using the etch-and-rinse bonding
approach [18,19]. In this particular area of the resin-dentininterface the resin probably remains partially polymerized
[22,23] and more susceptible to enzymatic and hydrolytic
degradation [24,25].
The H3PO4-etched water-wet dentin bonded using the
HEMA-containing adhesive exhibited the lowest (p
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ultramorphology analysis showed that the hybrid layer com-
pletely collapsed in dry conditions forming a gap within the
interface (Figs. 2A, 3A and B). Conversely, the resindentin
interface created with the HEMA-containing adhesive applied
onto H3PO4-etched ethanol-wet dentin showed hybrid layer
shrinkage of only a few microns in the proximity of
its underside (Fig. 3C). The Confocal micropermeabil-
ity/ultramorphology evaluation showed that the HEMA-containing resin applied onto water-wet H3PO4-etched or
EDTA-treated dentin was characterized by severe FL penetra-
tion throughout the hybrid layer and adhesive layer (Fig. 4A
and B) whereas, the ethanol-wet dentin allowed the formation
of a resindentininterface which prevented the FL penetration
throughout the hybrid and adhesive layer (Fig. 4C and D). In
terms of bond strength, this study confirmed that the appli-
cation of a HEMA-containing resin applied onto H3PO4 acid
or EDTA-treated dentin results in comparable TBS results
both when using the water-wet or the ethanol-wet bond-
ing technique (Table 2). These results are in accordance with
those reported by Sauro et al. [16,26] who showed that the
resindentin interface created in EDTA-treated dentin withHEMA-containing adhesives presented bond strength val-
ues comparable to those of H3PO4-etched dentin and higher
resistance to chemical degradation, possibly due to a higher
amount of residual apatite crystallites left within the collagen
matrix which prevented the denaturation of collagen [27].
The ethanol-wet bonding technique employed during the
bonding procedures of the HEMA-free adhesive favored the
formation of hybrid layers with higher biomechanical proper-
ties compared to those obtained with the HEMA-free adhesive
applied onto water-wet dentin (Table 1) which could not be
tested due to premature failure of the resindentin inter-
faces caused by a lack of diffusion of the hydrophobic resin
comonomers into the water-rich demineralized dentin [3,15]The AFM analysis performed along the resindentin inter-
faces createdwith HEMA-free resin appliedon theethanol-wet
dentin showed a high quality hybrid layer with no sign
of shrinkage in dry conditions (Fig. 3E). Furthermore, the
HEMA-free resin applied onto H3PO4 acid or EDTA-treated
ethanol-wet dentin showed modest micropermeability local-
ized at the bottom of the hybrid layer (Fig. 4EH).
Since there was no statistical differences between the
3rd, 4th, 5th and 6th indentation along any of the tested
resindentin interface, it is possible to affirm that both the
etching procedures used in this study may considerably influ-
ence the bio-mechanical nano-properties of the dentin within
the hybrid layer and at the bottom of the hybrid layer.The maintenance of a wet demineralized dentin sur-
face to prevent the collapse of the acid-etched dentin is
remarkably essential during the bonding procedure [28,29].
Although the water-wet-bonding is the most common tech-
nique used to prevent the collapse of the demineralized
collagen matrix, it remains a sensitive technique which may
influence substantially the formation of the hybrid layer
[3,30]. An excessive presence of water may be responsible
for the formation of a poor-quality hybrid layer character-
ized by micro-porosities and phase separation within the
resindentin interface [15,17,18,32,31]. Moreover, water may
compete with a hydrophilic resin monomers (i.e. HEMA) for
space in the demineralized zone, decreasing the monomer
density within the collagen network, and probably inter-
fering with its polymerization [32]. The reversible hybrid
layers shrinkage observed within the interface of the HEMA-
containing bonded dentin (Fig. 2A and B) and the FL
penetration within thehybrid andadhesive layers (Fig. 4A and
B) was probably due to the high water content rather than
polymerized resin. The ethanol-wet bonding technique may
indeed offer the possibility to replace water by an excess ofabsolute ethanol, achieving an enhanced coating of the col-
lagen fibrils and sealing ability (Fig. 4CH) that allow more
hydrophobic resin comonomers to diffuse into the demineral-
ized dentin [3,15]. A higherdegree of polymerization wasmost
likely achieved due to the hydrogen bond formation between
comonomers containing hydroxyl groups, such as BisGMA,
and ethanol [25].
The advantage of using HEMA-free rather than HEMA-
containing adhesives in clinical practice is that restoration
performed with more hydrophobic adhesives absorb much
less water over time, increasing bond longevity, if compared
to those performed with adhesivesbased on more hydrophilic
monomers [3335].In conclusion, this study showed an improvement of qual-
ity of the hybrid layer within the resindentin interfaces
created using both the HEMA-free and the HEMA-containing
adhesives with the ethanol-wet-bonding technique. Further
investigations regarding the ability of this experimental bond-
ing technique to improve the quality of the resindentin
interface via remineralizationof the hybrid layer are at present
ongoing.
Acknowledgments
This work was supported by grants CICYT/FEDER MAT2008-
02347, CICYT/FEDER MAT2011-24551, JA-P07-CTS2568 and
JA-P08-CTS-3944. This article presents independent research
commissioned by the National Institute for Health Research
(NIHR) under the Comprehensive Biomedical Research Cen-
tre at Guys & St. Thomas Trust. The views expressed in this
publication are those of the author(s) and not necessarily
those of the NHS, the NIHR or the Department of Health. The
authors also acknowledge support from the Centre of Excel-
lence in Medical Engineering funded by the Wellcome Trust.
The authors have no financial affiliation or involvement with
any commercial organization with direct financial interest in
the materials discussed in this manuscript. Any other poten-
tial conflict of interest is disclosed.
r e f e r ence s
[1] Marshall GW, Marshall SJ, Kinney JH, Balooch M. The dentinsubstrate: structure and properties related to bonding. JDent 1977;25:44158.
[2] Nakabayashi N, Pashley DH. Hybridization of dental hardtissues. Tokyo: Quintessence Publishing Co. Ltd.; 1998.
[3] Pashley DH, Tay FR, Carvalho RM, Rueggeberg FA, Agee KA,Carrilho M, Donnelly A, Garca-Godoy F. From dry bonding towater-wet bonding to ethanol-wet bonding. A review of the
interactions between dentin matrix and solvated resins
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