investigation of the physical properties of...
TRANSCRIPT
INVESTIGATION OF THE PHYSICAL PROPERTIES OF CHOLESTERYL
ESTER LIQUID CRYSTAL AND THE INTERACTION WITH CELLS
WAN IBTISAM BINTI WAN OMAR
A thesis submitted in
fulfilment of the requirement for the award of the
Degree of Master of Electrical Engineering
Faculty of Electrical and Electronic Engineering
Universiti Tun Hussein Onn Malaysia
JANUARY 2016
iii
For my dearest mother, father, husband and family for their encouragement and
blessing...
To my beloved friend and their support and caring......
-Never tired and give up to gain knowledge and life is a journey of learning-
iv
ACKNOWLEDGEMENT
Alhamdulillah, I am grateful to ALLAH S.W.T the most merciful and the most
compassionate for the guidance and knowledge bestowed upon me, for without it I
would not been able to come this far. Peace be upon him, Muhammad the messenger
of god.
I would like to express my gratitude to honourable Assoc. Prof. Dr Soon Chin
Fhong, my supervisor of Master’s project. Under her supervision, many aspects
regarding this project has been explored and with the knowledge, idea and support
received from her. I also would like to thank my co-supervisor Dr Hatijah Basri for
sharing her knowledge to me.
Many thanks and grateful to the Malaysia Ministry of Higher Education for
research funding support (FRGS Phase 1 Vot No. 1050) and also Universiti Tun
Hussein Onn Malaysia for providing post graduate incentive research grant (GIPS
Vot 1111).
Finally, I would like to dedicate my gratitude to my parents, my family, my
husband and friends who helped me directly and indirectly in the completion of this
project. This encouragement and guidance mean a lot to me. Their sharing and
experience foster my belief in overcoming every obstacle encountered in this project.
Guidance, co-operation and encouragement from all people above are
appreciated by me in sincerely. Although I cannot repay the kindness from them, I
would like to wish them to be well and happy always.
v
LIST OF ASSOCIATED PUBLICATIONS
Journals
1. Chin Fhong Soon, Wan Ibtisam Wan Omar, Rebecca F. Berends,
Nafarizal Nayan, Hatijah Basri, Kian Sek Tee, Mansour Youseffi,
Nick Blagden, Morgan Clive Thomas Denyer (2014) “Biophysical
characteristics of cells cultured on cholesteryl ester liquid crystal,”
Micron, Vol. 56, pp. 73-79. Published by Elsevier B.V.
Conference Proceeding:
1. Chin Fhong Soon, Wan Ibtisam Wan Omar, Nafarizal Nayan, Hatijah
Basri, Martha Bt. Narawi, Kian Sek Tee (2013) “A Bespoke Contact
Angle Measurement Software and Experimental Setup for
Determination of Surface Tension.” Proceeding of 4th
International
Conference on Electrical Engineering and Informatics (ICEEI),
Procedia Technology. Vol. 11, pp. 487-494. Published by Elsevier
B.V.
2.
Wan Ibtisam Wan Omar, Chin Fhong Soon (2014) “Critical Surface
Tension of Cholesteryl Ester Liqiud Crystal.” Proceeding of Joint
International Conference on Nanoscience, Engineering and
Management (BOND 21), Bayview Beach Resort, Batu Ferringhi,
Penang, Malaysia, 19 – 21 August 2013, Advance Materials Research.
Vol. 925, No. 4, pp. 43-47. Trans Tech Publications, Switzerland.
3. Wan Ibtisam Wan Omar, Chin Fhong Soon (2015) “The Time Based
Study of Cell Morphology Using Atomic Force Microscopy.”
Proceeding of 5th
International Conference on Biomedical Engineering
(IFMBE), Vietnam, 16-18 June 2014, Vol. 46, pp. 227-230. ©
Springer International Publishing Switzerland.
vi
LIST OF AWARDS
1. Silver Medal in Research & Innovation Festival 2012
(R & I Fest UTHM)
Chin Fhong Soon, Hatijah Basri, Kian Sek Tee, Wan Ibtisam
Wan Omar, Morgan Denyer. “Simple Apparatus and a Contact
Angle Measurement Software for Automatic Computation of
Surface Tension.”
2. Gold Medal in Persidangan dan EXPO Ciptaan Institusi
Pengajian Tinggi Antarabangsa 2013 (PECIPTA)
Chin Fhong Soon, Wan Ibtisam Wan Omar, Hatijah Basri,
Morgen Denyer. “An Integrated System For Measurement and
Mapping of Single Cell Traction Force.”
3. Silver Medal in Research & Innovation Festival 2013
(R & I Fest UTHM)
Thong Kok Tung, Wan Ibtisam Wan Omar, Rosliza Mohamad
Zin, Yap Huing Yin. “Scaffoldless Technique to Culture 3D
Keratinospheroids.”
vii
ABSTRACT
Cholesteryl ester liquid crystals (CELC) were demonstrated with application in
biosensing and microtissue regeneration. The affinity of the cells to this liquid crystal
is unclear and required further investigation. This study focused on characterising the
physical properties of CELC and interaction of human keratinocytes with CELC. The
physical properties of CELC were characterised by a custom built contact angle
measurement system and bubble pressure measurement apparatus. Other methods
such as pendant drop were applied to determine the critical surface tension of the
CELC. Then, the characterization of the CELC was continued by using Differential
Scanning Calorimeter (DSC), X-ray Diffraction (XRD), Polarising Microscopy
(POM) and Fourier Transform Infrared Spectroscopy (FTIR). Nonetheless, the
morphology of cells interaction with CELC after it reached confluency was studied
using Field Emission Scanning Electron Microscopy (FESEM) and non-contact
mode of Atomic Force Microscopy (AFM). The results showed that the critical
surface tension of the liquid crystal using contact angle was 37.5 mN/m and the
surface tension measured using pendant drop method was found to be 23.6 mN/m.
Both results indicate that the surface of the liquid crystal was moderately
hydrophobic. From the DSC, CELC was found stable at room and incubator
temperature. From XRD results, the compound of CELC interacts in cell culture
media self-assembles into lyotropic layer. POM and FTIR analysis showed CELC
after immersion in media displayed lyotropic smectic phases. The AFM and FESEM
images indicated good adhesion of cells on the CELC. This research thus showed
that the hydrophilic layers of lyotropic phase of cholesteryl ester liquid crystal were
demonstrated with biophysical properties that support the adhesion of cells.
viii
ABSTRAK
Kristal cecair kolesterlat ester (CELC) telah menunjukkan aplikasi dalam biosensor
dan pertumbuhan semula tisu mikro. Pertalian sel-sel terhadap kristal cecair ini
adalah tidak jelas dan memerlukan kajian lanjut. Kajian ini memberi tumpuan kepada
pencirian sifat-sifat fizikal CELC dan interaksi CELC dengan keratinosit manusia.
Sifat fizikal CELC dicirikan dengan menggunakan sistem pengukuran dan kaedah
pengukuran tekanan gelembung sudut yang telah direka . Kaedah-kaedah lain seperti
‘pendant drop’ telah digunakan untuk menentukan ketegangan permukaan kritikal
CELC itu. Pencirian CELC diteruskan dengan menggunakan mesin Kalorimeter
imbasan perbezaan (DSC), difraksi sinar-X (XRD), mikroskop optis berkutub (POM)
dan perubahan fourier infra-merah (FTIR). Morfologi sel selepas interaksi dengan
CELC dikaji menggunakan mikroskop elektron pengimbas pancaran medan
(FESEM) dan mod tanpa sentuh mikroskop daya atomik (AFM). Keputusan
menunjukkan ketegangan permukaan kritikal kristal cecair menggunakan sudut
sentuh adalah 37.5 mN/m dan ketegangan permukaan dengan menggunakan kaedah
‘pendant drop’ ialah 23.6 mN/m. Kedua-dua keputusan menunjukkan bahawa
permukaan kristal cecair adalah sederhana hidrofobik. Daripada keputusan DSC,
CELC didapati stabil pada suhu bilik dan inkubator. Keputusan XRD menunjukkan,
apabila CELC berinteraksi dalam sel media, ia bertukar sendiri ke lapisan lyotropic.
Analisis POM dan FTIR menunjukkan CELC selepas rendaman dalam media,
memaparkan fasa smectic ‘lyotropic’. Gambar-gambar dari AFM dan FESEM
menunjukkan sel melekat dengan baik pada CELC tersebut. Kajian ini sekali gus
telah membuktikan bahawa lapisan hidrofilik fasa lyotropic cecair kolesterlat ester
kristal mempunyai ciri-ciri biofizikal yang menyokong lekatan sel.
ix
CONTENTS
TITLE i
DECLARATION ii
DEDICATION iii
ACKNOWLEDGEMENT iv
LIST OF ASSOCIATED PUBLICATION v
LIST OF AWARD vi
ABSTRACT vii
ABSTRAK viii
TABLE OF CONTENTS ix
LIST OF TABLES xiv
LIST OF FIGURES xv
LIST OF SYMBOLS xx
LIST OF ABBREVIATIONS xxii
CHAPTER 1 PROJECT OVERVIEW
1.1 Project background 1
1.2 Problem statement 2
1.3 Objective 3
1.4 Scope of project 3
1.5 Thesis organisation 4
1.6 Thesis contribution 4
x
CHAPTER 2 LITERATURE REVIEW
2.1 Introduction to liquid crystal 6
2.2 Types of liquid crystal 7
2.2.1 Thermotropic liquid crystal 7
2.2.1.1 Nematic phases 8
2.2.1.2 Cholesteric phases 8
2.2.1.3 Smectic phases 10
2.2.2 Lyotroic liquid crystal 10
2.3 Application of liquid crystal in biosensing 12
2.4 Human keratinocytes (HaCaTs) 14
2.5 Cellular adhesion 15
2.6 Surface tension measuring technique 16
2.6.1 Contact angle measurement 17
2.6.2 Bubble pressure 19
2.6.3 Pendant drop 20
2.6.4 Surface tension of liquid crystal 22
2.7 Spectrophotometer 23
2.8 Differential scanning calorimeter (DSC) 23
2.9 X-ray diffractometer (XRD) 24
2.10 Fourier transform infrared spectroscopy
(FTIR) 26
2.11 Microscopy 27
2.11.1 Phase contrast microscope 28
2.11.2 Atomic force microscopy (AFM) 29
2.11.3 Field emission scanning electron
microscope 31
CHAPTER 3 METHODOLOGY
3.1 Introduction 34
3.2 Development of a contact angle measurement
system 36
3.2.1 Experiment for validating contact
angle measurement system 44
xi
3.3 Characterising the physical properties of
cholesteryl ester liquid crystal (CELC) 45
3.3.1 Preparation of cholesteryl ester liquid
crystal (CELC) 45
3.3.2 Measuring surface tension of CELC 46
3.3.2.1 Contact angle method 46
3.3.2.2 Bubble pressure method 47
3.3.2.3 Pendant drop method 49
3.3.3 Thermal stability analysis 50
3.3.3.1 Preparation of CELC for
differential scanning
calorimeter (DSC)
50
3.3.3.2 Preparation of CELC for
optical emission spectroscopy
(OES)
51
3.3.4 Preparation of CELC for polarising
microscopy 52
3.3.5 Liquid crystal sample preparation for
x-ray diffraction (XRD) 53
3.3.6 Liquid crystal sample preparation and
fourier transform infrared analysis 54
3.4 Studying the cells interaction with CELC 55
3.4.1 Cell culture 55
3.4.2 Cell culture on the liquid crystal and
glass substrate 56
3.4.3 AFM of cells on the liquid crystal and
glass substrate 57
3.4.4 FESEM of cells on the liquid crystal
and glass substrate 58
CHAPTER 4 RESULT AND DISCUSSION
4.1 Introduction 60
4.2 The contact angle measurement system 60
xii
4.2.1 Calibration results of contact angle
measurement system 63
4.3 Physical properties of cholesteryl ester liquid
crystal (CELC) 66
4.3.1 Cholesteryl ester liquid crystal
(CELC) 66
4.3.2 Surface of cholesteryl ester liquid
crystal 66
4.3.2.1 Contact angle 66
4.3.2.2 Bubble pressure 68
4.3.2.3 Pendant drop 70
4.3.3 Thermal stability of cholesteryl ester
liquid crystal 72
4.3.4 Polarising optical microscopy (POM) 74
4.3.5 Crystallinity study of cholesteryl ester
liquid crystal 76
4.3.6 Chemistry elements in cholesteryl
ester liquid crystal 77
4.4 Cells interaction with cholesteryl ester liquid
crystal 79
4.4.1 Morphological effect and adhesion
characteristic of cells to celc 79
CHAPTER5 CONCLUSION AND FUTURE WORKS
5.1 Conclusion 89
5.2 Future works 90
REFERENCES 92
APPENDIX A Architecture of the Arduino UNO microcontroller board
APPENDIX B Specification of L293D motor driver
xiii
APPENDIX C Arduino coding
APPENDIX D Matlab coding
APPENDIX E The data of contact angle method
APPENDIX F The data of bubble pressure method
xiv
LIST OF TABLES
TABLE NO TITLE PAGE
2.1 Application of the liquid crystal as biosensor 13
2.2 Probe liquids and their interfacial tension 18
2.3 Surface tension values for liquid crystal 22
4.1 Interfacial tension value for CELC 71
4.2 Percentage of transmission calculated from
Beer’s law
73
4.3 Differences of AFM and FE-SEM for the
application in cells imaging
88
xv
LIST OF FIGURES
FIGURE NO TITLE PAGE
2.1 Basic structure of a liquid crystal molecule 7
2.2 A graphical illustration of cholesteric
phase
8
2.3 Types of cholesteric derivatives 9
2.4 Standard thermotropic liquid crystal
phases
10
2.5 Typical phases of lyotropic liquid crystal. 11
2.6 Layer of skin at epidermis consists of
keratinocytes
14
2.7 A schematic diagram of cellular adhesion 15
2.8 Contact angle measurement of a droplet of
liquid
17
2.9 Apparatus for surface tension
measurement using bubble pressure
19
2.10 A pendant drop system from AST
Products, INC
20
2.11 The pendant drop geometry 22
2.12 Light transmitted or reflected through a
sample
23
2.13 Schematic DSC heating curve of a semi-
crystalline polymer
24
2.14 PANalytical X’Pert Powder X-Ray
Diffraction
25
2.15 Setup for a scattering experiment utilizing
X-ray diffraction
25
xvi
2.16 Fourier transform infrared spectroscopy
(Perkin Elmer Spectrum 100)
26
2.17 Sample in contact with evanescent wave 27
2.18 Light path of a phase contrast microscope 28
2.19 A Nikon Eclipse TS100 phase contrast
microscope
29
2.20 Schematic diagram of an AFM 30
2.21 Atomic force microscopy XE-100 Park
System
30
2.22 FE-SEM schematic diagram 32
2.23 Field Emission Scanning Electron
Microscopy (JEOL JSM-7600F series)
32
3.1 The project flow chart 35
3.2 Flow chart of surface tension methods 36
3.3 Setup for contact angle measurement
technique
37
3.4 Circuit diagram of contact angle motor
controller
38
3.5 Flow chart to measure the contact angle of
a droplet of fluid
39
3.6 Open pushbutton in MATLAB GUI 39
3.7 Command for OPEN pushbutton 40
3.8 Distilled water interacts with PDMS 40
3.9 Command for SNAP pushbutton 41
3.10 Command for SAVE pushbutton 41
3.11 Image processing command including
Browse function
41
3.12 An enlarged image of the selected point of
a Acetone on PDMS surface
42
3.13 Tools in MATLAB GUI 43
3.14 Command for search critical surface
tension
43
3.15 Push button in GUI for Fox Zisman graph 44
xvii
3.16 Cholesteryl ester liquid crystal formulation 45
3.17 Mixture of cholesteryl ester liquid crystal 46
3.18 CELC in cholesteric phase at room
temperature
47
3.19 Differential pressure sensor ASP1400
(SENSIRION)
47
3.20 A schematic diagram of ASP 1400
pressure sensor with RS 232
48
3.21 Experimental setup for measuring surface
tension using bubble pressure method
49
3.22 Sample drop at the end of capillary tip 49
3.23 CELC sample in DSC pan 50
3.24 Q20 Differential scanning calorimeter 51
3.25 Experimental setup using OES 52
3.26 Ocean Optics HR4000 spectrophotometer 52
3.27 CELC substrate immersed in cell culture
media
53
3.28 Sample placed on the sample holder for
analysis
53
3.29 CELC sample were placed on top of ATR
crystal
54
3.30 Medium for cell harvesting 55
3.31 HaCaT cells were sub-cultured and were
plated in each petri dish
57
3.32 HaCaT were sub-culture without and with
liquid crystal
57
3.33 Image of silicon cantilever from the AFM
system over the HaCaT cell sample
58
3.34 Glass coverslips with gold sputter coater 58
4.1 The prototype models of a designed
contact angle measurement system
61
4.2 A DC motor controller circuit connected
to Arduino UNO
61
xviii
4.3 Enlaraged image for angles value at the
intersection point a droplet of Acetone
with solid surface.
62
4.4 Enlarge image of contact angles using
angle tool shows intersection point and
contact angle
62
4.5 Eight probe liquids droplets on PDMS and
Polyimide surface
63
4.6 Fluid surface tension of the eight probe
liquid generated in excel for PDMS and
Polyimide
64
4.7 CELC in cholesteric form 66
4.8 Image of sessile drops in contact with
CELC coated glass slides and their contact
angles
67
4.9 A Fox-Zisman plot for cholesteryl ester
liquid crystal
67
4.10 Hardware consists of ASP1400 pressure
sensor
68
4.11 CELC in 0.4 second, 0.8 second and 1
second before the bubble burst
69
4.12 Enlarged image of hemisphere 69
4.13 Samples reading of surface tension using
bubble pressure
69
4.14 Image of pendant drop digitized drop and
edge detection
71
4.15 DSC shows heat flow as a function of
temperature of cholesteryl liquid crystals.
No exothermic or endothermic activities
were observed at 37 °C
72
4.16 Intensity versus wavelength for CELC 73
4.17 Percentage of transmission versus
temperature
74
xix
4.18 Image comparison using phase contrast and
cross-polarizing optical microscopy.
75
4.19 A cross-polarizing micrograph of
cholesteric based lyotropic liquid crystals
shows the wide band streaks and focal
conic textures.
75
4.20 The surface of CELC after immersion in
cell culture media for 24 hours, 48 hours
and 72 hours
76
4.21 XRD for CELC and lyotropic layer of
CELC
77
4.22 The FTIR spectrum of cholesteryl ester
liquid crystals
78
4.23 HaCaT cells morphology on glass
substrate and for 24, 48 and 72 hours
79
4.24 AFM images for keratinocytes cultured on
a plain glass and liquid crystal substrates
80
4.25 Image of HaCaT cell plated on the glass
substrate and liquid crystal substrate after
24, 48 and 72 hours
82
4.26 Thickness of HaCaTs membrane cultured
with and without the presence of liquid
crystal as the substrate
83
4.27 Line profiles of cells cultured on plain
glass and liquid crystal substrate
84
4.28 Human keratinocyte cell morphology
cultured on glass on FE-SEM
85
4.29 Human keratinocyte cell morphology
cultured on cholesteryl ester liquid crystal
on FE-SEM
86
xx
LIST OF SYMBOLS
SYMBOL DESCRIPTION
a - Radius of curvature at apex drop
Å - Angstrom
Β - Drop shape factor
C - Carbon
cm - Centimetre
cm-1 - Wavenumber
°C - Degree celcius
d - Interplanar spacing
γ or σ - Surface tension
△ρ - Difference between densities
Φ - Coordinate
θ - angle
F - Free energy
H - Hidrogen
I - Intensity
l - litre
g - Gravity
N - Nitrogen
% - Percentage
O - Oxygen
P or p - Pressure
R - Radius
T - Transmission
Tg - Glass Transition
Tm - Melting points
λ - Wavelength
m - metre
xxi
mA - Mili Amp
ml - Mili litre
mg - Mili gram
mN/m - Mili Newton per metre
mM - Micro molar
kW - Kilo Watt
kV - Kilo Volt
µ - micro
xxii
LIST OF ABBREVIATIONS
SYMBOL DESCRIPTION
5CB - Pentylcyanobiphenyl
8CB - 4′-n-octyl-4-cyano-biphenyl
ATR - Attenuated Total Reflectance
AFM - Atomic Force Microscopy
CELC - Cholesteryl Ester Liquid Crystal
CST - Critical Surface Tension
DMEM - Dulbecco’s Modified Eagles’s Medium
DMSO - Dimethyl Sulfoxide
DNA - Deoxyribonucleic Acid
DSC - Differential Scanning Calorimeter
DSCG - Disudium Cromoglycate
ECM - Extracellular Matrix
EG - Ethylene Glycol
FESEM - Field Emission Scanning Electron Microscope
Fmoc - Fluorenylmethyloxycarbonyl
FTIR - Fourier Transform Infrared Spectroscopy
GND - Ground
GUI - Graphic User Interface
HaCaTs - Human Keratinocytes
HBSS - Hanks Balance Salt Solution
IPA - Isopropyl alcohol
IR - Infrared
LC - Liquid Crystal
LCD - Liquid Crystal Display
LCPA - Liquid Crystal Pixel Array
LED - Light Emitting Diode
LLC - Lyotropic Liquid Crystal
MBBA - 4-methoxybenzylidene-4’-n-butylaniline
xxiii
MMA - Methylmethacrylate
MTT - 3-(4,5-Dimethylthiazol-2-yl)-2,5-Diphenyltetrazolium
Bromide
OES - Optical Emission Spectroscopy
PEGA - Thermolysinpolyethylene Glycol Acrylamide
POM - Polarizing Optical Microscopy
PSPD - Position Sensitive Photo Diode
PWM - Pulse Width Modulation
SD - Standard deviation
TV - Television
UV - Ultraviolet
UTHM - Universiti Tun Hussein Onn Malaysia
V - Volt
Vis - Visible
XRD - X-ray Diffraction
CHAPTER 1
INTRODUCTION
1.1 Project background
Liquid crystal (LC) is a new class of biomaterial that gained attention for usage in
biomedical engineering. They provide means for label free observation of biological
phenomenon such as non-toxic thermotropic liquid crystal overlaid with matrigel that
had been used in recognizing restructuring of mammalian cells [1, 2]. Recently, a
research found that [3], cholesteryl ester liquid crystals (CELC) containing
cholesteryl moieties may have suitable biological affinity and also enable cell
adhesion and proliferation without the need for pre-treatment with extracellular
matrix molecules.
Due to the compact molecular arrangement, liquid crystal was shown to have
high resolution on sensing ability in detecting localized cell exerted force and could
be used for cell traction force sensor [4]. This is an important property that may
reveal the potential of liquid crystal in a biomaterial to function on inert surface.
Cell-compatible materials are very important in many biomedical applications [5-7].
Moreover, the cholesterol derivative in the liquid crystal was a well known
mesogenic nature with their potential to self order into liquid crystalline substances.
However, the use of liquid crystal in biological study has not been fully
explained. In 1857, Mettenheimer used a polarising light microscope and observed
double refractility and black formed cross image composed of cholesterol from
blood. Researchers proved that, occurrence of anisotropic myelin-like bodies in fatty
streaks of the atheromatous lesions of the aorta of man [8]. The anisotropic basic
structure has been interpreted as that of liquid crystal. In our living system, liquid
crystalline order of molecule occurs in degenerating tissues of liver, spleen, lung and
thyroid in the form of small spheres which appear under a conventional light
2
microscope as highly retractile and with double contours at their edges having the
inner ring brighter than the outer ring [8].
This type of liquid crystal contains cholesteryl moieties which have affinity
for cell membranes and have the abilities to change their properties. Cholesteryl
moieties homeostasis is an important element in cellular membrane traffic and cell
survival [9]. Therefore, this type of biomaterial is attractive as substrates because it
could provide universally fundamental molecule to mammalian cells. Cholesteryl
ester are considered to be easily biodegradable thus making the system suitable for
the preparation of tissue engineering that sustain cell proliferation and migration
[10]. The advantage of using liquid crystals as the biomaterial is it being non toxic
and sensitive to biological interactions [11].
In addition, in order to study the biocompatibility of a biomaterial, surface
energy property and thermal stability of a biomaterial are important factors in
attracting the adhesion of cells and may affects cell surface interface [12]. Hence,
finding surface tension of CELC was an important factor in this study. Moreover,
biomaterials are majorly reliant on the surface energy [13] and stable over certain
temperature. However, from the perspective of biophysical compability, little
publication has been studied on the physical properties of liquid crystal. Through this
study, synthesis and characterisation of surface properties CELC to interact with
human keratinocytes (HaCaT) cells were reported. Furthermore, surface properties of
CELC materials that promoted cell affinity were presented in this thesis.
1.2 Problem statement
In liquid crystal based biosensor development, an exposure to cell culture media is
unavoidable and this may alter the surface properties of the liquid crystals over
time. After immersion in cell culture media, the hydrophilic head and hydrophilic
tails of the liquid crystal molecules would reoriented to interface with the water at
the surface of the bulk liquid crystal as reported in [4]. However, the wettability of
the surface or the surface tension of these liquid crystals in attracting the adhesion
of cells have not been clearly identified and understood. Furthermore, the chemical
properties of the CELC used in cell culture remain unknown. Although new
applications of liquid crystals have been revealed [4], little is known about the
3
expression of surface proteins and effects onto morphological changes due to the
interactions with the liquid crystals. Driven by the positive reports of CELC in
supporting cell adhesion, it is necessary to further investigate the physical
properties of CELC and characteristics of cells after interaction with the CELC.
Thus, this study reveals the application of CELC that could be extended as a new
class of bio-physical relevant cells adhesion substrate which does not require pre-
conditioning with ligands.
1.3 Objectives
The main purpose of this research work was to investigate the surface properties of
CELC. To achieve the goal of this research, the following objectives had been
achieved. The objectives for this project were:
a) to develop contact angle and bubble pressured measurement systems that
enabled analysis of the surface tension of the CELC surface.
b) to investigate the physical properties of the CELC that enabled human
keratinocytes cell attachment.
c) to determine the characteristic of the human keratinocytes interaction with the
CELC.
1.4 Scopes of project
This project was divided into six scopes which involve:
a) Motorised contact angle measurement system was developed using Arduino
UNO microcontroller, L293D motor driver and MATLAB GUI.
b) Bubble pressure method used ASP1400 pressure sensor to find the surface
tension of the CELC.
c) Investigating the surface properties of the liquid crystal using a Differential
Scanning Calorimeter (DSC), Optical Emission Spectroscopy (OES),
Polarising Optical Microscopy (POM), X-ray Diffraction (XRD), and Fourier
Transform Infrared Spectroscopy (FTIR).
4
d) Use human Keratinocytes (HaCaTs) cell lines for cell interaction study.
e) Studying the cell attachment to the liquid crystal using Atomic Force
Microscopy (AFM) and Field Emission Scanning Electron Microscope
(FESEM).
1.5 Thesis organisation
This thesis is divided into five chapters. Chapter 1 provides an overview of this
project and the objectives, scopes and problem statement of the research. Chapter 2
reveals on the CELC background and its application in biosensing and generative
medicine. Chapter 3 outlines the experiment procedure of this project including the
background information on the software used for the contact angle measurement and
bubble pressure method system, preparing sample for physical properties and cells
interaction on CELC analysis. Chapter 4 presents the results and discussion of the
project. Chapter 5 was devoted for the conclusions and recommendations for future
work.
1.6 Thesis contribution
In this thesis, the experimental finding of physical properties of CELC and cell
interactions with CELC revealed a new understanding in biomaterial for biosensing
application. The contributions of this study are as listed below:
a) Fox Zisman graph automated generated using Matlab GUI
Using measured angle value, Matlab GUI can automatically generate Fox Zisman
graph thus provides the critical surface tension (CST) value of materials.
b) Surface tension of CELC
The value of surface tension of CELC were identified and clearly explain the
understanding of wettability of the surface of these liquid crystals in attracting the
adhesion of cells.
5
c) New class of biological relevant material
The physical expression of cell adhered on CELC showed biocompatibility of CELC
exploring new potentials of liquid crystals in bioengineering and biosensing.
CHAPTER 2
LITERATURE REVIEW
2.1 Introduction to liquid crystal
Liquid crystal is a state of matter in addition to the solid crystalline and liquid
phases. Liquid crystal exhibits intermediate phases in which the molecules flow like
liquids yet possess some physical properties characteristic of crystal [14]. In other
word, it is known as mesophases. The classification of the mesophases is based on
the positional and orientation order of the molecules. The molecules of the liquid
crystals are position in a lattice and orientated in a specific directions. One can
classify liquid crystal in accordance with the physical parameters controlling the
existence of the liquid crystalline phases.
The first liquid crystal was discovered in 1888 by an Austrian botanical
physiologist Fredrich Reinitzer (1865-1927) that accidentally observed that
cholesteryl benzoate changed into a cloudy liquid at 145.5 ºC and melted again into a
clear liquid at 178.5 ºC. This material has two melting points and it is quite different
from the three states of matter (solid, liquid and gas) recognised at that time. After
identifying this phenomenon, Reinitzer asked help from a physicist, Otto Lehmann
for further investigation. Lehmann examined the intermediate cloudy fluid and
reported seeing crystallites and named the new substance as ‘liquid crystal’ (LC).
Liquid crystal molecules are often aromatic and it is attached to two substituent
groups. Liquid crystals that contain benzene rings are referred to as benzene
derivatives [15].
Figure 2.1 shows the basic structure of a liquid crystal molecule of 4-
methoxybenzylidene-4’-n-butylaniline (MBBA) which can be an example of liquid
crystal molecule that contain two benzene rings as the basic structure [15].
7
Figure 2.1: Basic structure of a liquid crystal molecule [16].
2.2 Types of liquid crystal
Considering the geometrical structure of the molecules, the liquid crystal can be
grouped into several types. There are two types of liquid crystal; the thermotropic
and lytropic liquid crystals. These materials exhibit liquid crystalline properties as a
function of different physical parameters and environments. Different types of liquid
crystals have different physical properties and application. There were two processes
to enable the transition of the mesophases; one could be altered by thermal processes
and the other by the influence of solvent [17]. For example, thermotropic liquid
crystal change phases with temperature and are often composed of a single type of
molecule whereas lyotropic liquid crystals are obtained when appropriate
concentration of a material is dissolved in a solvent such as water.
2.2.1 Thermotropic liquid crystal
This type of liquid crystal changes its orientation and positional as a function of
temperature. From the form of anisotropic phase, the crystal changes into isotropic
phases gradually as the temperature increase. In isotropic phase, the physical
properties are the same in all directions, while the physical properties for anisotropic
phase are different between one direction and another. By definition, anisotropic
means the physical properties of the phases are different and depending on the
direction and orientation of the component molecules. Each molecule in thermotropic
liquid crystal is oriented in a long range order. Thermotropic liquid crystal can be
divided into three mesophases; nematic, cholesteric and smectic phases.
N CH CH3O C4H9
Substituent Substituent Aromatic group
8
2.2.1.1 Nematic phases
The simplest and least-ordered phase of liquid crystals is the nematic phase (N)
where rod-like molecules directed on average in a particular direction which is
known as the director, n [17]. The molecules possess a high degree of long-range
order with their long axes approximately parallel, but without the distinct layers of
the smectic crystal [15]. The molecules in the nematic phase are arranged parallel to
each other and slide past each other.
2.2.1.2 Cholesteric phases
Cholesterol derivatives are the most common chemical compounds that exhibit the
cholesteric and it is also known as chiral nematic phases, this is because of the first
thermotropic liquid crystalline materials exhibiting this phase were cholesterol
derivative.
Figure 2.2: A graphical illustration of cholesteric phase [18].
Chiral means the molecule cannot be transformed into their mirror image by
rotations or translations [18]. Chiral cholesteric phase has a helical structure in which
the director is twisted along the z-axis normal to the x-axis as shown in Figure 2.2.
The cholesteric phase is similar to nematic phase but chiral molecule cause a twist in
9
the nematic structure which is normal to the long axis. The strong twists in the
molecule cause cholesteric have different optical properties from nematic phase.
Figure 2.2 shows the structure of cholesteric phase where p is the pitch of helix.
Colourful textures are observed due to the selective colour reflection from the
mesogens that are lying in planes of helical structures with different pitch length. The
planar and homeotropic orientations of the cholesteric liquid crystal mesogens
portray different textures. The colour of the textures often appears dark with very
low light reflectivity in the crossed polariser when the mesogens oriented close to the
homeotropic alignment.
Figure 2.3: Types of cholesteric derivatives (a) Cholesteryl pelargonate,
(b) Cholesteryl chloride, and (c) Cholesteryl oleyl carbonate at 10× magnification.
(Scale bar: 25 µm)
Some common cholesteric liquid crystals are cholesteryl chloride, cholesteryl
pelargonate and cholesteryl oleyl carbonate. These cholesteric liquid crystals
reversibly change colour as the temperature changes. Figure 2.3 shows the
birefringence properties of the cholesteric liquid crystal.
(a) (b)
(c)
10
2.2.1.3 Smectic phase
The second common liquid crystal phase is the smectic phase, where the molecules
form single layer of thickness approximate one molecular length as shown in Figure
2.4 [17]. As the temperature increase, the liquid crystal from crystal phase change to
smectic C, smectic A, nematic, and isotropic phase. The smectic C phase (SmC)
where the director, n, at some angle with respect to the layer normal, z. The smectic
A phase (SmA) has the directors n orientates in the same direction with respect to the
layer normal, z.
Figure 2.4: Standard thermotropic liquid crystal phases arranged from left to right in
order of increasing temperature [17].
Smectic and nematic liquid crystal phases are subjected to changes in
temperature which they can change their form and their light transmission properties
splitting a beam of light into two polarised components (ordinary and extraordinary)
to produce the phenomenon of double refraction [15]. Due to the ability of the liquid
crystal in responding to magnetic field they are found useful in liquid crystal display
(LCD) which is one of the applications of thermotropic liquid crystal [15].
2.2.2 Lyotropic liquid crystal
Lyotropic liquid crystals (LLC) are forms from dissolution surfactants in a solvent
such as water [19]. An example of the LLC systems is a fluid formed by water and
amphiphilic molecules whose constituent molecules are formed from polar head
Temperature increase
Crystal Smectic C Smectic A Nematic Isotropic
n
z n n
11
group which attracts water and a nonpolar chain that avoids water [18]. The
hydrophilic group interacts strongly with water and the hydrophobic group is water
insoluble such as soaps and detergents [17]. The phase changes of lyotropic liquid
crystal are determined by the concentration of the solute material in a solvent.
Figure 2.5: Typical phases of lyotropic liquid crystal. The figure shows the
aggregation of amphiphiles into micelles and then into lyotropic liquid phases as a
function of amphiphile concentration and of temperature producing micellar cubic
phase (l1), hexagonal phase (H1), bi-continuous cubic phases (V1) and lamellar
phases (Lα) [20].
Lyotropic liquid crystal has an axial ratio of less than 15 and made up of
molecules larger than the thermotropic liquid crystal [21]. This type of liquid crystal
are mostly found in soap, food and living things such as cell membranes [14]. Figure
2.5 shows the relationship between the liquid crystalline phases of surfactants
(Surface Active Agents) and its composition concentration is expressed in a phase
diagram as a function of temperature. At 30-40wt% of amphiphile concentration, the
micellar cubic phase (l1) will be formed. Lyotropic liquid crystal turns into a cubic
lattice when the concentraton of amphiphiles get to 60% while remaining in the
isotropic phase. As the amphiphile concentration increase, cylindrical shaped that is
normal hexagonal phase (H1) was formed from the micelles in the cubic lattice. A
complex bicontinuous (V1) was formed at a very narrow range of concentrations.
12
Following by high concentration of amphiphiles, the lamellar phase (Lα) in which
the amphiphile molecules are arranged in bilayers and each bilayer is separated by
water molecules.
2.3 Application of liquid crystal in biosensing
In recent years, liquid crystals were discovered with their potential in biosensing.
Liquid crystals were applied as biosensors because they provide label free
observation of biological phenomenon. Among the applications of liquid crystal in
biosensing include the detection of distortion in bulk of lyotropic liquid crystals due
to the presence of immune complexes [22]. A study also found that a liquid crystal
can be used to discriminate fluorescence signals on a biosensor array using liquid
crystal pixel array (LCPA) [23]. Moreover, nematic liquid crystal were found to
detect and amplifies the presence of immune complexes [24] and used as protein and
deoxyribonucleic acid (DNA) separators [25].
The LCD based detection of protease for example trypsin, elastase and
thermolysin that cleaved off the Fluorenylmethyloxycarbonyl (Fmoc) peptide
backing by a thermolysinpolyethylene glycol acrylamide (PEGA) hydrogel support
and specific detection or protease function [26]. Previous study also found that
lyotropic liquid crystal was used as biosensor for the compatibility of lyotropic liquid
crystal with virus. Most of the technique exploited the optical properties of the liquid
crystal in sensing changes in biological interactions [27]. Furthermore, bacterial
detection also one of the application use liquid crystal as biosensor. Research found
that, use of liquid crystal provided infectious disease diagnostics in clinical specimen
[28].
Application of liquid crystal by using 4-cyano-4’-pentylbiphenyl (5CB) in
biosensor also had been developed for urea detection in human body [29] and
glucose biosensor [30]. In addition, by using nematic liquid crystal, 5CB, a novel
highly-sensitive liquid crystal (LC) biosensing approach based on target-triggering
DNA dendrimers (branched molecules) was developed for the detection of p53
mutation gene segment at the LC aqueous interface [31]. Recently, cholesteryl ester
liquid crystal (CELC) was discovered for its new application in detecting single cell
traction forces [4]. Table 2.1 shows the application of liquid crystals as biosensors.
13
CELC was found to support cell adhesion and response locally to cell exerted
forces because of its compact molecular arrangements. As a biosensor, liquid crystals
are very often used in the presence of cell culture media or interact with a fluidic
environment. In this environment, amphillic molecules of liquid crystals could
Types of
Liquid Crystal
Compound Application References
Lyotropic liquid
crystal
Disodium
cromoglycate
(DSCG), water
Detecting distortion in bulk of
lyotropic liquid crystals due to
the presence of immune
complexes.
[22]
Liquid crystal pixel
array (LCPA)
LCPA device from
Ferroelectric liquid
crystal (FLQ devices
(part c LV- 1300P)
and the FLC driver
(part LV-1300P)
Discriminate fluorescence
signals on a biosensor array.
[23]
Nematic liquid
crystal
Disudium
cromoglycate
(DSCG)
Detect and amplifies the
presence of immune complexes.
[24]
Nematic liquid
crystal
5CB Monitor the presence of a
targeted biological species for
rapid screening of solution
conditions leading to
crystallization of proteins at
interfaces.
[26]
Lyotropic liquid
crystal
Tetradecyldimethyl-
amineoxide C14AO,
Decanol, water.
The compatibility of LLC with
virus.
[32]
Nematic liquid
crystal
5CB Virus detection. [27]
Nematic liquid
crystal
5CB Screening the urea level in the
human body.
[29]
Nematic liquid
crystal
5CB Screening glucose in the human
body.
[30]
Nematic liquid
crystal
5CB Signal-enhanced LC biosensing
method based on target-
triggering DNA dendrimers for
the label-free and sensitive
detection of p53 mutation gene
segment.
[31]
Cholesteric ester
liquid crystal
Cholesteryl
pelargonate
C36H62O2,
Cholesteryl chloride
C27H45Cl,
Cholesteryl oleyl
carbonate C46H80O3.
Detecting single cell traction
forces.
[4]
Table 2.1: Application of the liquid crystal as biosensor.
14
reoriented due to the interaction with the water molecules. Therefore, it is important
to investigate the surface tension of the CELC.
2.4 Human keratinocytes (HaCaTs)
Human keratinocytes (HaCaTs) cells were used in this project because of long term
aim such as for pharmacology study.
Figure 2.6: Layer of skin at epidermis consists of keratinocytes.
Figure 2.6 shows the layer of skin consist of keratinocytes. This cell is one of
the major cell types from the epidermis layer of a skin which is at outermost layer of
skin. At the epidermis layer, stratum corneum is the outermost layer of the skin
serves as waterproof barriers of the epidermis protects from dirt. Selected
keratinocytes is at stratum garnulosum. Stratum spinosum is the layer where
keratinocytes become larger, flatter and contain less water as they travel to the
surface of the skin. These cells ultimately flatten and lose their nuclei, thereby
forming the stratum corneum and eventually replacing select cells that migrate to the
skin surface and die [33].
Epidermis
15
2.5 Cellular adhesion
Multicellular organisms such as keratinocytes require adhesion for cells to adhere to
each other and the extracellular matrix. The binding of a cell to an inanimate surface,
cell-cell or the extracellular matrix are called cellular adhesions [34]. Adhesion
occurs from the action of proteins such as integrins which interact with ligands
including extracellular matrix. This process participates in cell adhesions in a large
number of physiologically important processes such as wound healing [35]. Figure
2.7 shows schematic diagram of cell adhesion in order to understand the biological
role of adhesion junctions.
Figure 2.7: A schematic diagram of cellular adhesion.
Cell adhesion is mediated by cell junctions such as desmosomes, adherens,
tight and gap junctions. Desmosomes (bond) is the intermediate filaments anchor at
the extracellular junctions, whilst hemidesmosome (half) have a different function
which is to connect the intermediate filaments of a cell to the extracellular matrix
that is a substances secreted by cells lying outside the cell membrane [36]. They can
be found in skin such as muscle cells. Adherens junctions are microfilaments anchor
the plaque that occurs under the membrane of each cell. It is a complex proteins
16
found at the sites of cell-cell adhesion [37]. Transmembrane proteins, calcium
dependent, mediate cell to cell attachment at the adherens junctions.
Tight junctions or zonula occludens are formed from membrane proteins such
as occluding, claudins and e-cadherin that strongly couple the adjacent cell
membranes [37]. Gap junctions are formed from membrane spanning proteins called
connexins [38]. Each gap junction formed from six connexins molecules. It allows
direct communication between cells such as open and closed, formed from the
channel that passes through the membrane of both cells. They are found in heart
muscle, smooth muscle electrical and chemical integration as a single functional unit
and also in embryonic development. Focal adhesions are the link at the outside of the
extracellular matrix through transmembrane proteins (integrins) with the cell
cytoskeleton (actin microfilaments). They mechanically bind the cell membrane to
the extracellular matrix via specific transmembrane receptors.
2.6 Surface tension measuring technique
The study of surface tension has wide application in applied surface science.
Adhesion and morphological of cells mostly depend on the wettability or surface
energy of a biomaterial [39].
Surface tension is related to the surface energy of a surface. Surface tension,
γ, is the force, F, per unit length, L, (equation (2.1)) that must be applied parallel to
the surface so as to counterbalance the net inward pull and has the units of dyne/cm
or mN/m.
𝛾 =𝐹
𝐿 (2.1)
Greater surface tension reflects higher intermolecular force of attraction, thus
increase in hydrogen bonds induced increase in surface tension. Many techniques
used in finding surface tension of biomaterials have been produced. In this work,
surface tension of CELC was studied by using different techniques such as contact
angle, pendant drop and maximum bubble pressure methods.
17
2.6.1 Contact angle measurement
Contact angle measurement is often used to evaluate the surface and liquid
cleanliness and the effects of surface treatments developed as a part of fundamental
research in surface science as well as for industrial applications [40]. A contact angle
is the macroscopic representation of microscopic phenomena such as surface
roughness, surface energies of the materials involved and surface coatings play a role
in the wettability of a material. By definition, a contact angle is the interior angle
formed by the substrate being used and the tangent to the drop interface at the
apparent intersection of all three interfaces which is called contact line. A static
contact angle on a flat surface is defined by Young’s equation, which is related to
interfacial surface tension between solid, vapour and liquid.
Figure 2.8: Contact angle measurement for a droplet of liquid.
The Young’s equation is essentially a force which balanced in the horizontal
direction. The contact angle may also be directly determined by the ratio of
interfacial surface tension of the unknown interfacial surface tensions using equation
(2.2).
𝑐𝑜𝑠 𝜃 = γsv− γsl
γlv (2.2)
where, γsv, γsl and γlv are the interfacial force of surface and vapour, interfacial
force of liquid and surface, interfacial force of liquid and vapour, respectively. γlv
and cos θ can be determined from the experiment. θ is the contact angle formed by
18
the substrate being used and the tangent to the drop interface at the apparent
intersection of the three phase boundary (solid, liquid and vapour). This intersection
is call contact line. Fox-Zisman method was applied to determine the critical surface
energy (γc). According to Zisman, the value of γc of a solid is equal the value of γl of
a liquid being in contact with this solid and for which the contact angle is zero [41].
Based on the theory, γc value consists of the contact angle measurements for the
studied solid and liquids of a homologous series of compounds.
In Figure 2.8, it shows the contact angle measurement where a liquid was
place on top of a surface of a solid. It is assumed that the liquid does not react with
the solid and that the solid surface is smooth. In contact angle measurement,
selecting the suitable probe liquids to interface with a surface is an important part.
One must ensure that the liquid does not react or swell with the surfaces. Hence, it
can be considered a viable probe liquid for a dynamic contact angle. Different probe
liquids formed different contact angles.
Using the value of the cos θ and the known interfacial tension of each probe
liquid, Fox-Zisman graph can be plotted corresponding to the cosine values of the
contact angle at the y-axis and surface tension of different probe liquids at the x-axis.
The intersection point at which the best fit linear regression line of the data set
intercept with cos θ = 1 indicates the critical surface tension [42]. Selecting several
suitable probe liquids to interface with a surface is an important decision for contact
angle measurement. Fox-Zisman theory suggested the use of at least four probe
liquids in order to obtained enough data points for plotting the Fox-zisman graph
[43]. A liquid can be considered a viable probe liquid for a dynamic contact angle
measurement if it does not swell or react with the solid surface.
Table 2.2: Probe liquids and their interfacial tension.
Liquid Interfacial tension (mN/m) References Isopropyl alcohol (IPA) 21.7 [44]
Acetone 23.0 [44]
Methyl-methacrylate (MMA) 30.6 [45]
Mineral Oil 35 [46]
Dimethyl sulfoxide (DMSO) 42.90 [47]
Ethylene glycol (EG) 47.3 [47]
Glycerol 64 [44]
Distilled water 72.8 [44]
19
For selecting the probe liquid, using a syringe, a drop of known volume of
liquid is dropped to a test surface and observe what happened to the droplet. If it is
absorbed into the solid or completely spreads out across the surface, the probe liquid
is not suitable to be used. This is to make sure that no additional forces and thus
affects the contact angle calculation. Polar liquid is selected as probe liquid for this
test. Some standard test liquid that can be used as probe liquids and their interfacial
tensions are shown in Table 2.2. They are selected in such a way that linear
regression line on the cos θ versus surface tension graph can be obtained over a
wider range of surface tension.
2.6.2 Bubble pressure
Another technique for determining surface tension is bubble pressure method. A
simple experiment apparatus from [48] was propose in finding surface tension using
bubble method based on the Laplace Young equation [49]. While, in [50], bubble
pressure method was used to measure the surface tension of smectic liquid crystal.
Figure 2.9 shows the apparatus for measuring surface tension using bubble pressure
method.
Figure 2.9: Apparatus for surface tension measurement using bubble pressure [50].
20
From Figure 2.9, two capillaries with same diameter were used in order to
reduce the errors in pressure measurement with differing surface tension using
different materials drawn on both openings. R1 and R2 were referred to the radius of
two inflate materials respectively. After that, the materials were deflected to a bubble
by injecting the syringe. Images were recorded by a video camera perpendicular to
the capillary axes. A sensitive pressure gauge was used to determine the pressure
differences. However, this method also can be done using single capillary.
Surface tension can be measured using the straight forward Young Laplace as
in equation (2.3) [48]:
𝑝 =4𝜎
𝑅 (2.3)
where 𝑝 is inner excess pressure, R is the radius of a spherical bubble and σ is the
surface tension [51]. This method provides a direct simple access to σ and also
suitable for study of small surface tension differences.
2.6.3 Pendant drop
The apparatus for finding surface or interfacial tension by pendant drop image
analysis through video imaging digitisation and numerical curve-fitting, VCA
Optima, developed from AST Products, INC is as shown in Figure 2.10.
Figure 2.10: A pendant drop system from AST Products, INC.
21
This system applies Laplace’s equation of capillarity in order to find the value
of surface tension. This pendant drop apparatus consist of illuminating system for
improving image quality, viewing system to visualise the drop image and data
acquisition system to find the interfacial tension from the pendant drop profile. From
the image taken, extraction of the drop contour to determine the radius of curvature
at the apex is necessary for the calculation of interfacial tension. Next, shape
comparison between the theoretical and experimental drop to get interfacial tension
value. The shape of the drop hanging on the needle is determined from the balance of
force which include the surface tension of that liquid. The values of surface tension
of unknown samples are automatically generated.
Based from Laplace’s equation, the equation of Bashforth and Adam [52]
relates the drop profile to the interfacial tension through a nonlinear differential
equation which is given in equation (2.4) and (2.5).
1𝑅1
𝑎
+ sin 𝛷
𝑥
𝑎
= −𝛽𝑧
𝑎+ 2 (2.4)
where β, the shape factor of the drop is given by
𝛽 =𝑎2𝑔△𝜌
𝛾 (2.5)
where △ρ is the difference between the densities of the two liquids in contact. For
example, the density difference between air and liquid. While, g is the gravitational
constant, γ is the surface or interfacial tension, 𝑎 is the radius of curvature at the apex
of the drop, x, z and Φ are the defines coordinates and R1 is the radius of curvature at
the point with coordinates (x,z), as shown in Figure 2.11.
22
Figure 2.11: The pendant drop geometry [52].
2.6.4 Surface tension of liquid crystal
The research by [50] used bubble pressure method to measure the surface tension of
smectic liquid crystal (8CB) at room temperature, 25 °C. The surface tension
determined was 27.8 mN/m. While, from [53], surface tension measured for 5CB
liquid crystal using pendant drop method at temperature dependence is 16.22 mN/m.
Table 2.3 summarises the surface tensions value of 5CB and 8CB liquid crystals
using these two methods.
Table 2.3: Surface tension values for liquid crystal.
Technique Types of
liquid crystal
Temperature,
°C
Surface
tension, mN/m
References
Bubble
pressure 8CB 25 27.8 [50]
Pendant drop 5CB -15 to 10 16.22 [53]
23
2.7 Spectrophotometer
Spectrum was measured using a spectrometer. From the spectrophotometer, a graph
of intensity as a function of wavelength was shown. Optical Emission Spectroscopy
(OES) is one of the spectrometer that shows the intensity of light.
Figure 2.12: Light transmitted or reflected through a sample.
Figure 2.12 shows the block diagram of a spectrophotometer where incident
light beam can be absorbed, transmitted and reflected. Many compounds absorb
ultraviolet (UV) or visible (Vis) light. Based on Beer’s Law, the transmittance of any
sample at wave number is given by the ratio of the radiant power emerging from the
rear face of the sample at the wave number, I to the power of the radiation at the
front face of the sample Io [54].
Using Beer’s Law, the percentage of light transmitted can be measured using
equation (2.6):
%𝑇 =𝐼
𝐼𝑜× 100 (2.6)
Absorbance provides value of intensity of a light. Thus, if all the light passes through
a sample without any absorption, then the absorbance is zero and gives 100% of
transmittance.
Sam
ple
Incident light
beam
Transmission
Reflection
Absorption
24
2.8 Differential scanning calorimetry (DSC)
A Differential Scanning Calorimetry (DSC) measures the difference in heat flow rate
between a sample and inert reference as a function of time and temperature. DSC
provides information about the physical and chemical changes that involve
endothermic (absorption of heat) or exothermic (release of heat) activities from a
sample [55].
Figure 2.13: Schematic DSC heating curve of a semi-crystalline polymer.
The results of glass transition (Tg), melting and boiling points (Tm), and
evaporation temperature can be found from endothermic heat flows into the sample.
While results of exothermic heat flow out of the sample provides, crystallization time
and temperature, percent crystallinity, rate and degree of cure, and oxidation or
thermal stability. Figure 2.13 shows typical DSC heating curve of a semi-crystalline
polymer with glass transition, exothermic recrystallization, melting endothermic and
exothermic decomposition.
2.9 X-ray diffractometer (XRD)
The laboratory used in this project is equipped with a PANalytical X’Pert Powder X-
Ray Diffraction (XRD) machine (Figure 2.14). This machine operates with a power
of 3kW at 40 kV and 40 mA, with a cooper X-ray tube, which has a characteristic
92
REFERENCES
[1] Y.-Y. Luk, S. F. Campbell, N. L. Abbott, and C. J. Murphy, "Non-toxic
thermotropic liquid crystals for use with mammalian cells," Liquid crystals,
vol. 5, pp. 611-621, 2004.
[2] S. J. Woltman, G. D. Jay, and G. P. Crawford, "Liquid-crystal materials find
a new order in biomedical applications," Nature materials, vol. 12, pp. 929-
938, 2007.
[3] C. F. Soon, M. Youseffi, N. Blagden, and M. Denyera, "Influence of Time
Dependent Factors To The Phases and Poisson’s Ratio of Cholesteryl Ester
liquid crystals," Journal of Science and Technology, vol. 1, 2011.
[4] C. F. Soon, M. Youseffi, R. F. Berends, N. Blagden, and M. C. T. Denyer,
"Development of a novel liquid crystal based cell traction force transducer
system," Biosensors and Bioelectronics, vol. 1, pp. 14-20, 2013.
[5] J. H. Lee, H. W. Jung, I.-K. Kang, and H. B. Lee, "Cell behaviour on polymer
surfaces with different functional groups," Biomaterials, vol. 9, pp. 705-711,
1994.
[6] K. Y. Lee and D. J. Mooney, "Alginate: properties and biomedical
applications," Progress in polymer science, vol. 1, pp. 106-126, 2012.
[7] R. Landers, A. Pfister, U. Hübner, H. John, R. Schmelzeisen, and R.
Mülhaupt, "Fabrication of soft tissue engineering scaffolds by means of rapid
prototyping techniques," Journal of materials science, vol. 15, pp. 3107-
3116, 2002.
[8] Y. Hata, J. Hower, and W. Insull Jr, "Cholesteryl Ester-Rich Inclusions from
Human Aortic Fatty Streak and Fibrous Plaque Lesions of Atherosclerosis: I.
Crystalline Properties, Size and Internal Structure," The American journal of
pathology, vol. 3, pp. 423, 1974.
[9] R. Y. Hampton, "Cholesterol homeostasis: ESCAPe from the ER," Current
Biology, vol. 8, pp. R298-R301, 2000.
93
[10] J. J. Hwang, S. N. Iyer, L.-S. Li, R. Claussen, D. A. Harrington, and S. I.
Stupp, "Self-assembling biomaterials: Liquid crystal phases of cholesteryl
oligo(l-lactic acid) and their interactions with cells," Proceedings of the
National Academy of Sciences, vol. 15, pp. 9662-9667, 2002.
[11] C. F. Soon, M. Youseffi, R. F. Berends, N. Blagden, M. C. T. Denyer, B. L.
Samira, and A. J. Farideh, "Characterization and Biocompatibility Study of
Nematic and Cholesteryl Liquid Crystals," Proceedings of the World
Congress on Engineering, vol. 2, pp. 1-4, 2009.
[12] B. O. Palsson and S. N. Bhatia, Tissue Engineering Upper Saddle River, NJ,
US: Pearson Prentice Hall, 2004.
[13] B. D. Ratner, A. S. Hoffman, F. J. Schoen, and J. E. Lemons, Biomaterials
science: an introduction to materials in medicine, New York: Academic
press, 2004.
[14] I.-C. Khoo, Liquid crystals: Wiley-Interscience, 2007.
[15] S. N. I. Julia J. Hwang, Li-Sheng Li, Randal Claussen, Daniel A. Harrington,
Samuel I. Stupp, "Self-assembling biomaterials: Liquid crystal phases of
cholesteryl oligo(L-lactic acid) and their interactions with cells," 2002.
[16] H. Stegemeyer, Liquid Crystal, New York: Springer, 1994.
[17] P. Collings, "Liquid Crystal—Nature’s Delicate Phase of Matter (Hilger,"
England, 1990.
[18] S. Singh and D. A. Dunmur, Liquid crystals: fundamentals: World Scientific
Publishing Company, 2002.
[19] G. P. Crawford, Liquid Crystals: Frontiers in Biomedical Applications:
World Scientific, 2007.
[20] J. M. Brake, M. K. Daschner, Y.-Y. Luk, and N. L. Abbott, "Biomolecular
interactions at phospholipid-decorated surfaces of liquid crystals," Science,
vol. 5653, pp. 2094-2097, 2003.
[21] E. Priestley and P. J. Wojtowicz, Introduction to liquid crystals: Plenum
Publishing Corporation, 1975.
[22] S. V. Shiyanovskii, O. D. Lavrentovich, T. Schneider, T. Ishikawa,
Smalyukh, II, C. J. Woolverton, G. D. Niehaus, and K. J. Doane, "Lyotropic
chromonic liquid crystals for biological sensing applications," Molecular
Crystals and Liquid Crystals, vol. 1, pp. 259/[587]-270/[598], 2005.
94
[23] J. S. Lundgren, A. N. Watkins, D. Racz, and F. S. Ligler, "A liquid crystal
pixel array for signal discrimination in array biosensors," Biosensors and
Bioelectronics, vol. 7, pp. 417-421, 2000.
[24] S. Helfinstine, O. Lavrentovich, and C. Woolverton, "Lyotropic liquid crystal
as a real‐time detector of microbial immune complexes," Letters in applied
microbiology, vol. 1, pp. 27-32, 2006.
[25] T. Araki and H. Tanaka, "Surface-sensitive particle selection by driving
particles in a nematic solvent," Journal of Physics: Condensed Matter, vol.
15, pp. L193, 2006.
[26] L. S. Birchall, R. V. Ulijn, and S. J. Webb, "A combined SPS–LCD sensor
for screening protease specificity," Chemical Communications, vol. 25, pp.
2861-2863, 2008.
[27] L. A. Tercero Espinoza, K. R. Schumann, Y.-Y. Luk, B. A. Israel, and N. L.
Abbott, "Orientational behavior of thermotropic liquid crystals on surfaces
presenting electrostatically bound vesicular stomatitis virus," Langmuir, vol.
6, pp. 2375-2385, 2004.
[28] G. S. Martin, D. M. Mannino, S. Eaton, and M. Moss, "The epidemiology of
sepsis in the United States from 1979 through 2000," New England Journal
of Medicine, vol. 16, pp. 1546-1554, 2003.
[29] M. Khan, Y. Kim, J. H. Lee, I.-K. Kang, and S.-Y. Park, "Real-time liquid
crystal-based biosensor for urea detection," Analytical Methods, vol. 15, pp.
5753-5759, 2014.
[30] M. Khan and S.-Y. Park, "Liquid crystal-based proton sensitive glucose
biosensor," Analytical chemistry, vol. 3, pp. 1493-1501, 2014.
[31] H. Tan, X. Li, S. Liao, R. Yu, and Z. Wu, "Highly-sensitive liquid crystal
biosensor based on DNA dendrimers-mediated optical reorientation,"
Biosensors and Bioelectronics, pp. 84-89, 2014.
[32] L.-L. Cheng, Y.-Y. Luk, C. J. Murphy, B. A. Israel, and N. L. Abbott,
"Compatibility of lyotropic liquid crystals with viruses and mammalian cells
that support the replication of viruses," Biomaterials, vol. 34, pp. 7173-7182,
2005.
[33] C. T. Hess, Skin and Wound Care: Lippincott Williams & Wilkins, 2008.
[34] M. A. Daeschel and J. McGuire, "Interrelationships between protein surface
adsorption and bacterial adhesion," Biotechnology and Genetic Engineering
Reviews, vol. 1, pp. 413-438, 1998.
95
[35] D. R. Colman, Cell Adhesion: Elsevier Science, 1997.
[36] M. D. Kottke, E. Delva, and A. P. Kowalczyk, "The desmosome: cell science
lessons from human diseases," Journal of cell science, vol. 5, pp. 797-806,
2006.
[37] M. G. Farquhar and G. E. Palade, "Junctional complexes in various
epithelia," The Journal of cell biology, vol. 2, pp. 375-412, 1963.
[38] W. A. Wells, "Defining gap junctions," The Journal of cell biology, vol. 3,
pp. 379-380, 2005.
[39] F. Puoci, Advanced Polymers in Medicine, Springer, 2014.
[40] G. Lamour, A. Hamraoui, A. Buvailo, Y. Xing, S. Keuleyan, V. Prakash, A.
Eftekhari-Bafrooei, and E. Borguet, "Contact angle measurements using a
simplified experimental setup," Journal of Chemical Education, vol. 12, pp.
1403-1407, 2010.
[41] M. Żenkiewicz, "Methods for the calculation of surface free energy of
solids," Journal of Achievements in Materials and Manufacturing
Engineering, vol. 1, pp. 137-145, 2007.
[42] K. G. Kabza, J. E. Gestwicki, and J. L. McGrath, "Contact angle goniometry
as a tool for surface tension measurements of solids, using zisman plot
method. A physical chemistry experiment," Journal of Chemical Education,
vol. 1, pp. 63, 2000.
[43] H. W. Fox and W. A. Zisman, Colloid and Science, pp. 514, 1950.
[44] R. Weast, Handbook of tables for applied engineering science vol. The
Chemical Rubber Co., Cleveland, Ohio: CRC Press, 1970.
[45] D. Y. Kwok, A. Leung, C. N. C. Lam, A. Li, R. Wu, and A. W. Neumann,
"Low-rate dynamic contact angles on poly (methyl methacrylate) and the
determination of solid surface tensions," Journal of colloid and interface
science, vol. 1, pp. 44-51, 1998.
[46] E. G. Shafrin and W. A. Zisman, "Critical surface tension for spreading on a
liquid substrate," The Journal of Physical Chemistry, vol. 5, pp. 1309-1316,
1967.
[47] D. Y. Kwok and A. W. Neumann, "Contact angle measurement and contact
angle interpretation," Advances in Colloid and Interface Science, vol. 3, pp.
167-249, 1999.
96
[48] F. L. Román, J. Faro, and S. Velasco, "A simple experiment for measuring
the surface tension of soap solutions," American Journal of Physics, vol. 8,
pp. 920-921, 2001.
[49] A. W. Adamson and A. P. Gast, "Physical chemistry of surfaces," 1967.
[50] H. Schüring, C. Thieme, and R. Stannarius, "Surface tensions of smectic
liquid crystals," Liquid crystals, vol. 2, pp. 241-252, 2001.
[51] T. Stoebe, P. Mach, and C. Huang, "Surface tension of free-standing liquid-
crystal films," Physical Review E, vol. 5, pp. R3587-R3590, 1994.
[52] A. Morita, D. Carastan, and N. Demarquette, "Influence of drop volume on
surface tension evaluated using the pendant drop method," Colloid and
Polymer Science, vol. 9, pp. 857-864, 2002.
[53] T. Beica, R. Moldovan, I. Zgura, and S. Frunza, "Improved Method For
Determining The Temperature Dependence Of Interfacial Tension At Liquid
Crystal-Isotropic Liquid Interface." Romania: The Publishing House of the
Romanian Academy, vol. 7, 2006.
[54] P. R. Griffiths and J. A. De Haseth, Fourier transform infrared spectrometry:
John Wiley & Sons, 2007.
[55] G. Höhne, W. Hemminger, and H. J. Flammersheim, Differential scanning
calorimetry: Springer Science & Business Media, 2003.
[56] S. A. Speakman, "Basics of X-Ray Powder Diffraction," Retrieved June.
[57] D. Pavia, G. Lampman, G. Kriz, and J. Vyvyan, Introduction to spectroscopy:
Cengage Learning, 2008.
[58] P. Elmer, "FT-IR Spectroscopy Technical Note," USA.
[59] D. B. Murphy, Fundamentals of light microscopy and electronic imaging:
John Wiley & Sons, 2002.
[60] C. R. Kokare, "Pharmaceutical Microbiology-Principles and Applications,"
Nirali Prakashan. Pune, 2008.
[61] W. R. Bowen and N. Hilal, Atomic Force Microscopy in Process
Engineering: An Introduction to AFM for Improved Processes and Products
vol.: Butterworth-Heinemann, 2009.
97
[62] P. C. Braga and D. Ricci, "Atomic force microscopy: application to
investigation of Escherichia coli morphology before and after exposure to
cefodizime," Antimicrobial agents and chemotherapy, vol. 1, pp. 18-22,
1998.
[63] A. Engel and D. J. Müller, "Observing single biomolecules at work with the
atomic force microscope," Nature Structural & Molecular Biology, vol. 9, pp.
715-718, 2000.
[64] C. K. M. Fung, K. Seiffert-Sinha, K. W. C. Lai, R. Yang, D. Panyard, J.
Zhang, N. Xi, and A. A. Sinha, "Investigation of human keratinocyte cell
adhesion using atomic force microscopy," Nanomedicine: Nanotechnology,
Biology and Medicine, vol. 1, pp. 191-200, 2010.
[65] H. X. You, J. M. Lau, S. Zhang, and L. Yu, "Atomic force microscopy
imaging of living cells: a preliminary study of the disruptive effect of the
cantilever tip on cell morphology," Ultramicroscopy, vol. 1, pp. 297-305,
2000.
[66] S. Karrasch, R. Hegerl, J. H. Hoh, W. Baumeister, and A. Engel, "Atomic
force microscopy produces faithful high-resolution images of protein surfaces
in an aqueous environment," Proceedings of the National Academy of
Sciences, vol. 3, pp. 836-838, 1994.
[67] C. Müller, M. Allen, V. Elings, A. Engel, and D. J. Müller, "Tapping-mode
atomic force microscopy produces faithful high-resolution images of protein
surfaces," Biophysical journal, vol. 2, pp. 1150-1158, 1999.
[68] P. K. Hansma, J. P. Cleveland, M. Radmacher, D. A. Walters, P. E. Hillner,
M. Bezanilla, M. Fritz, D. Vie, H. G. Hansma, C. B. Prater, J. Massie, L.
Fukunaga, J. Gurley, and V. Elings, "Tapping mode atomic force microscopy
in liquids," Applied Physics Letters, vol. 13, pp. 1738-1740, 1994.
[69] S. G. W. Kaminskyj and T. E. S. Dahms, "High spatial resolution surface
imaging and analysis of fungal cells using SEM and AFM," Micron, vol. 4,
pp. 349-361, 2008.
[70] W. Xiao, Q. Wu, X.-t. Yan, and G. Liu, "Application of L293D in main
controlling circuit of nurse mobile robot [J]," International Electronic
Elements, pp. 018, 2007.
[71] T. Thomson, Design and Applications of Hydrophilic Polyurethanes: CRC
Press, 2000.
[72] A. J. Kinloch, Adhesion and Adhesives: Science and Technology: Springer,
1987.
98
[73] H. Rinck and H. Schneider, "Method of measuring the contact angle of
wetting liquid on a solid surface," Google Patents, 1992.
[74] E. G. Shafrin and W. A. Zisman, "Constitutive relations in the wetting of low
energy surfaces and the theory of the retraction method of preparing
monolayers1," The Journal of Physical Chemistry, vol. 5, pp. 519-524, 1960.
[75] C. F. Soon, M. Youseffi, P. Twigg, N. Blagden, and M. C. T. Denyer, "Finite
Element Quantification of the Compressive Forces Induced by Keratinocyte
on a Liquid Crystal Substrate," in Analysis and Design of Biological
Materials and Structures: Springer, pp. 79-99, 2012.
[76] J. M. Schakenraad, H. J. Busscher, C. R. H. Wildevuur, and J. Arends, "The
influence of substratum surface free energy on growth and spreading of
human fibroblasts in the presence and absence of serum proteins," Journal of
biomedical materials research, vol. 6, pp. 773-784, 1986.
[77] C. F. Soon, M. Youseffi, N. Blagden, R. Berends, S. B. Lobo, F. A. Javid,
and M. Denyer, "Characterization and biocompatibility study of nematic and
cholesteryl liquid crystals," in Proceedings of the World Congress on
Engineering, pp. 1872-1875, 2009.
[78] R. N. McElhaney, "The use of differential scanning calorimetry and
differential thermal analysis in studies of model and biological membranes,"
Chemistry and physics of lipids, vol. 2, pp. 229-259, 1982.
[79] S. A. Asher and P. S. Pershan, "Alignment and defect structures in oriented
phosphatidylcholine multilayers," Biophysical journal, vol. 3, pp. 393-421,
1979.
[80] W. Dobbs, L. Douce, and B. Heinrich, "1-(4-Alkyloxybenzyl)-3-methyl-1H-
imidazol-3-ium organic backbone: A versatile smectogenic moiety," Beilstein
journal of organic chemistry, vol. 1, pp. 62, 2009.
[81] C. F. Soon, M. Youseffi, P. Twigg, N. Blagden, and M. C. T. Denyer, "Finite
Element Quantification of the Compressive Forces Induced by Keratinocyte
on a Liquid Crystal Substrate," in Analysis and Design of Biological
Materials and Structures., A. Öchsner, L. F. M. Silva, and H. Altenbach,
Eds.: Springer Berlin Heidelberg, vol. 14, pp. 79-99, 2012.
[82] I. Kravchenko, Y. Boyko, N. Novikova, А. Egorova, and S. Andronati,
"Influence of cholesterol and its esters on skin penetration in vivo and in vitro
in rats and mice," Ukrainica Bioorganica Acta, vol. 1, pp. 17-21, 2011.
99
[83] V. A. Ziboh and M. A. Dreize, "Biosynthesis and hydrolysis of cholesteryl
esters by rat skin subcellular fractions. Regulation by prostaglandins,"
Biochemical Journal, vol. 2, pp. 281, 1975.
[84] P. G. Unna and L. Goldsdetz, Biochemical Journal, vol. 25, pp. 425-431,
1910.
[85] C. F. Soon, S. A. Khagani, M. Youseffi, N. B. Nayan, H. B. Saim, S.
Britland, N. Blagden, and M. C. T. Denyer, "Interfacial Study of Cell
Adhesion to Liquid Crystals Using Widefield Surface Plasmon Resonance
Microscopy," Colloids and Surfaces B: Biointerfaces, vol. 110, pp. 2013.
[86] C. F. Soon, W. I. W. Omar, R. F. Berends, N. Nayan, H. Basri, K. S. Tee, M.
Youseffi, N. Blagden, and M. C. T. Denyer, "Biophysical characteristics of
cells cultured on cholesteryl ester liquid crystals," Micron, vol. 56, pp. 73-79,
2014.
[87] J. L. McGrath, "Cell Spreading: The Power to Simplify," Current Biology,
vol. 10, pp. R357-R358, 2007.
[88] W. I. W. Omar and C. F. Soon, "The Time Based Study of Cell Morphology
Using Atomic Force Microscopy," in 5th International Conference on
Biomedical Engineering in Vietnam, pp. 227-230, 2015.
[89] D. E. Discher, P. Janmey, and Y.-l. Wang, "Tissue cells feel and respond to
the stiffness of their substrate," Science, vol. 5751, pp. 1139-1143, 2005.
[90] B. S. Mitchell, An Introduction to Materials Engineering and Science for
Chemical and Materials Engineers: John Wiley & Sons, 2004.
[91] C. F. Soon, M. Youseffi, N. Blagden, and M. C. T. Denyer, "Characterizing
the interfacial topology of cells attached to liquid crystals," in Biomedical
Engineering and Sciences (IECBES), 2012 IEEE EMBS, pp. 252-255, 2012.
[92] R. Jahn, T. Lang, and T. C. Südhof, "Membrane Fusion," Cell, vol. 4, pp.
519-533, 2003.
[93] A. Engler, L. Bacakova, C. Newman, A. Hategan, M. Griffin, and D. Discher,
"Substrate Compliance versus Ligand Density in Cell on Gel Responses,"
Biophysical journal, vol. 1, pp. 617-628, 2004.
[94] D. S. Katti, R. Vasita, and K. Shanmugam, "Improved biomaterials for tissue
engineering applications: surface modification of polymers," Current topics
in medicinal chemistry, vol. 4, pp. 341-353, 2008.
100
[95] E. A. Cavalcanti-Adam, T. Volberg, A. Micoulet, H. Kessler, B. Geiger, and
J. P. Spatz, "Cell Spreading and Focal Adhesion Dynamics Are Regulated by
Spacing of Integrin Ligands," Biophysical journal, vol. 8, pp. 2964-2974,
2007.
[96] V. D. C. Shields, "High resolution ultrastructural investigation of insect
sensory organs using field emission scanning electron microscopy,"
Microscopy: Science, Technology, Applications and Education, pp. 321-328,
2010.