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Bovine Serum Albumin adhesion force measurements using an ...
Transcript of Bovine Serum Albumin adhesion force measurements using an ...
Bovine Serum Albumin adhesion force measurements using an Atomic
Force Microscopy
Chun-Chih Lai B. Sc. (Chemical Engineering),
National Chung Hsing University, Taiwan
Faculty of Built Environment and Engineering
Queensland University of Technology
2 George Street, QLD 4000, Brisbane, Australia
A thesis submitted as a requirement for the degree of:
Master of Engineering
At the Queensland University of Technology
2006
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Abstract
In this thesis, a direct method of Atomic Force Microscopy (AFM) technique has been
developed to measure the adhesion forces between BSA and two different surfaces:
mica (a hydrophilic surface); and polystyrene (a hydrophobic surface); in PBS
solution. We have shown possible to measure interactions between proteins and
substrate surface directly without any modification to the substrate and the AFM tip;
this means protein molecules can keep the natural elastic property within the force
measurements. The average measured value of adhesion forces between BSA and
mica is 0.036 ± 0.002 nN, and between BSA and polystyrene is 0.066 ± 0.003 nN. The
polystyrene surface is more adhesive to BSA than the mica surface. This is consistent
with previous research, which assessed that hydrophobic surfaces enhance protein
adhesion but hydrophilic surfaces do not.
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Contents
Abstract ............................................................................ i
List of figures............................................................................ iv
List of tables ...........................................................................vi
Abbreviations ..........................................................................vii
Statement of Original Authorship .......................................... ix
Acknowledgments ..................................................................... x
1. Introduction........................................................................... 1
2. Literature Review ................................................................. 4
2.1. Introduction.....................................................................................................4 2.2. Atomic Force Microscopy (AFM) ..................................................................4
2.2.1. Surface techniques and advantages of using AFM ..............................4 2.2.2. Principles of AFM................................................................................6 2.2.3. Sample requirements............................................................................6
2.3. Adhesion Force Measurements of Proteins with Atomic Force Microscopy .7 2.3.1. Globular protein adsorption on solid surfaces .....................................7 2.3.2. Adhesion forces models of proteins...................................................13 2.3.3. AFM methods for protein-surface adhesion force measurements .....16
2.4. The future potential of atomic force microscopy..........................................22 2.5. Conclusion ....................................................................................................23
3. Experimental Technique .................................................... 25
3.1. AFM ..............................................................................................................25 3.1.1 AFM tip...............................................................................................25 3.1.2. Piezoelectric scanner..........................................................................27 3.1.3. Detection mechanism.........................................................................27 3.1.4. Modes of AFM...................................................................................29
3.2. Force measurement procedure facility..........................................................32
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3.2.1. Spring constant calibration ................................................................33 3.2.2. The force measurement......................................................................36 3.2.3. Force curves .......................................................................................38
4. Experimental Method......................................................... 42
4.1. Atomic force microscopy..............................................................................42 4.2. BSA adsorption onto the surfaces .................................................................43
5. Results and Discussion ....................................................... 44
5.1. Experimental results......................................................................................44 5.1.1. Bare mica surface in PBS ..................................................................45 5.1.2. BSA adsorbed on mica surface in PBS ..............................................46 5.1.3. Bare polystyrene in PBS ....................................................................48 5.1.4. BSA adsorbed on polystyrene surface in PBS ...................................49
5.2. Discussions ...................................................................................................50
6. Conclusion ...............................................................................
................................................................................ 59
7. References................................................................................
................................................................................ 61
Appendix A – The AFM force curves of BSA-mica in PBS . 66
Appendix B – The AFM force curves of BSA-polystyrene in
PBS......................................................................... 71
Appendix C – The bare mica force curves in PBS and the
bare polystyrene force curves in PBS.................. 78
Appendix D – Data, SEM images and details of the
calibration procedure for the two cantilevers..... 80
iv
List of figures
Figure 1: Ordering of polypeptide chains into an �–helix (left) and a parallel �–sheet (right) (Norde, 2003). ..................................................9
Figure 2: Schematic representation of the Gouy-Stern model of an electrical double layer, indicating the distribution of the counterions ( ) and co-ions ( ), compensating the negative surface charge and the resulting
potential decay (Norde, 2003)..............................................................11 Figure 3: Schematic representation of a covalently attached BSA molecule
on an AFM tip surface (Wang et al., 2004)..........................................17 Figure 4: Theoretical force-distance curve. ................................................18 Figure 5: Schematic of force-distance curves (Green et al., 2002).............19 Figure 6: Schematic representation of the tip of an AFM (Morris et al., 1999).
..............................................................................................................26 Figure 7: Schematic representation of the atomic force microscopy (Morris
et al., 1999). .........................................................................................28 Figure 8: Force-distance curve in AFM......................................................29 Figure 9: The NT-MDT SMENA liquid head .............................................33 Figure 10: The resonance curve..................................................................34 Figure 11: Resonance curve fitted by Gaussian equation for an AFM
cantilever..............................................................................................35 Figure 12: The photo show how to adjust the laser beam focus on the AFM
cantilever in the liquid. ........................................................................37 Figure 13: The diagram shows the where the force spectroscopy mode is in
the SPM window menu........................................................................37 Figure 14: The indication of how the signal-displacement curves are
converted to cantilever deflection-displacement curves ......................38 Figure 15: Force-distance curves ................................................................39 Figure K1: Force-distance curve. First stage of the approach to the surface
..............................................................................................................40 Figure K2: Force-distance curve: the repulsive region...............................40 Figure H1: Force-distance curve: pulling the cantilever in the repulsive
region ...................................................................................................41 Figure H2: Force-distance curve: the retracting cantilever stretches the BSA
molecules .............................................................................................41 Figure 16: Photo of AFM head and sample assembly during force
measurements.......................................................................................43 Figure 17: Bare mica force curves in PBS..................................................46
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Figure 18: BSA-mica force-displacement curves in PBS...........................47 Figure 19: Bare polystyrene force curves in PBS.......................................48 Figure 20: BSA-polystyrene force curves in PBS ......................................50 Figure 21: The comparison of adhesion forces between BSA-mica and
BSA-polystyrene..................................................................................52 Figure 22: The comparison of adhesion works between BSA-mica and
BSA-polystyrene..................................................................................57 Figure A1: The adhesion force curves of BSA and mica............................66 Figure A2: The adhesion force curves of BSA and mica............................66 Figure A3: The adhesion force curves of BSA and mica............................67 Figure A4: The adhesion force curves of BSA and mica............................67 Figure A5: The adhesion force curves of BSA and mica............................68 Figure A6: The adhesion force curves of BSA and mica............................68 Figure A7: The adhesion force curves of BSA and mica............................69 Figure A8: The adhesion force curves of BSA and mica............................69 Figure A9: The adhesion force curves of BSA and mica............................70 Figure B1: The adhesion force curves of BSA and polystyrene .................71 Figure B2: The adhesion force curves of BSA and polystyrene .................71 Figure B5: The adhesion force curves of BSA and polystyrene.................73 Figure B6: The adhesion force curves of BSA and polystyrene .................73 Figure B7: The adhesion force curves of BSA and polystyrene .................74 Figure B8: The adhesion force curves of BSA and polystyrene .................74 Figure B9: The adhesion force curves of BSA and polystyrene .................75 Figure B10: The adhesion force curves of BSA and polystyrene ...............75 Figure B11: The adhesion force curves of BSA and polystyrene ...............76 Figure B12: The adhesion force curves of BSA and polystyrene ...............76 Figure B13: The adhesion force curves of BSA and polystyrene ...............77 Figure C1: no interactions were observed from the bare mica surface. .....78 Figure C2: no interactions were observed from the bare mica surface. .....78 Figure C3: no interactions were observed from the bare PS surface..........79 Figure C4: no interactions were observed from the bare PS surface..........79 Figure D1: One of resonance curves of cantilever A is fitted by Gaussian
equation................................................................................................80 Figure D2: The SEM image of cantilever A. ..............................................82 Figure D3: The SEM image of cantilever B. ..............................................83 Figure D4: One of resonance curves of cantilever A is fitted by Gaussian
equation................................................................................................84
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List of tables
Table 1: The information of Cantilever A and Cantilever B (See Appendix D for
experimental details)………………………………………………....44
Table 2: The table shows the maximum of adhesion force values of BSA-mica
and BSA-polystyrene (Errors of the average force values are the
standard deviations)……………………………………………….…51
Table 3: The student t test of adhesion forces of BSA-mica (Group A) and
BSA-polystyrene (Group B) (the student t test was calculated by
KaleidaGraph, Synergy software)…………………………………....52
Table 4: The adhesion forces between BSA and hydrophilic surfaces………..54
Table 5: The adhesion forces between BSA and hydrophobic surfaces………54
Table 6: The table shows the overall work for pulling BSA off the mica surface
and the overall work for pulling BSA off the polystyrene…………...55
Table D1: The resonance frequency values and the Q factor values were obtained
and calculated from the 10 resonance frequency curves of cantilever A
...….......................................................................................................81
Table D2: The resonance frequency values and the Q factor values were obtained
and calculated from the 10 resonance frequency curves of cantilever B
….…………………………………………………………………….85
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Abbreviations
Φ I the electrostatic potential
ρ∞ the bulk concentration of electrolytes
Φe exterior electrostatic potential
ρi the charge distribution
-Lg -lactoglobulin ( -Lg)
�fi (fc) the hydrodynamic function of the cantilever
εi the dielectric permittivity of the protein interior
AFM atomic force microscopy
Al32 Hamaker constant
b the width of the AFM cantilever
BSA bovine serum albumin
d the displacement AFM cantilever
DLVO Derjaguin-Landau-Verweey-Overbeek
dtip the deflection of the AFM tip
E the electronic charge
ESCA electron spectroscopy for chemical analysis
F force
f the bandwidth of the resonance frequency curve
f1 the lower cutoff frequency
f2 the upper cutoff frequecny
fc the resonance frequency
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I the value of current signal
k Boltzmann constant
kz the spring constant of the AFM cantilever
L the length of the AFM cantilever
PBS phosphate-buffered saline
Qf the quality factor of the resonance frequency fc
R the radius of the sphere
SAMs self-assembled monolayers
SEM scanning electron microscopy
SFA surface force apparatus
T the temperature
XPS X-Ray photoelectron spectroscopy
Wmica adhesion work between BSA and mica Wpolystyrene adhesion work between BSA and polystyrene
Zi the ion valency
Z the nearest distance between the sphere and the plane
� the density of the fluid
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Statement of Original Authorship
The work contained in this thesis has not been previously submitted to meet
requirements for an award at this or any other higher education institution. To the best
of my knowledge and belief, the thesis contains no material previously published or
written by another person except where due reference is made.
Chun-Chih Lai
x
Acknowledgments
I thankfully acknowledge my supervisor Professor John M. Bell for the guidance,
support, encouragement within my entire Master’s study.
I also would like to appreciate Professor Nunzio Motta, Dr. Thor Bostrom and Dr.
Edeline Wentrup-Byrne for their great helps and instructions regarding the AFM
technique. Thanks also to Dr. Cameron Wilson for his advice regarding protein
properties.
I would like to thank Mr. Loc Duong for his support with SEM. Thanks to Miss
Christina Theodoropoulos for her help with SEM, protein solution preparation.
Finally, I would like to appreciate my parents and my wife for their constant support
and encouragement.
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1. Introduction
Many fundamental studies in recent few years have dealt with the adsorption
behaviour of proteins onto different surfaces using various experimental methods and
instruments. Adhesion properties between protein and surfaces in solutions have been
a significant area of research in biology and biotechnology providing researchers with
the key information to attached cells and living tissues onto surface. This is of critical
importance in medical applications like bone implants, prosthesis, dentures, etc.
Protein adsorption plays a vital role in determining the nature of the tissue-implant
interface, since the adsorbed proteins can significantly affect biomaterial surface
properties such as blood coagulation and cell adhesion. Bovine Serum Albumin (BSA)
is a globular protein and the most abundant protein in plasma. Although the structure
and the adsorption of BSA have been investigated with various instruments such as
X-Ray photoelectron spectroscopy (XPS) (Fitzpatrick, Luckham, Eriksen, &
Hammond, 1992), the adhesion interactions between BSA and the different surface
(mica-hydrophilic and polystyrene-hydrophobic) measured directly by AFM in PBS
are still not well understood.
Developed in 1986 Atomic force microscopy (AFM) has become quickly a versatile
and unique technique to probe interactions between proteins and surfaces in a real
physiological environment (Morris et al., 1999). Since then, more and more
researchers are using AFM to explore further the protein adsorption in solution at the
nanometer (10-9m) scale. The forces involved in the adhesion between protein and the
surface are the order of 10-9 N (or 1 nN) and AFM probes are perfectly suited to
measure forces in this range and in real time.
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In this work, a direct method of identifying the interaction between protein and
surface properties by AFM has been established. We used AFM to measure the
adhesion forces between BSA and two different surfaces (mica and polystyrene)
without any modification of AFM tip or the substrate surface; this means protein
molecules can keep the natural elastic property during the force measurements. The
force-distance curves allow us to compare the interactions between BSA and different
surface properties from the quantified adhesion forces. In future, this AFM technique
can be exploited to study protein adhesion to new synthetic biomaterials promoting a
nanotechnology approach to tissue engineering research.
The remainder of this thesis consists of five chapters. Those five chapters are: � Chapter 2: Literature review – The main findings in the area of protein
adhesion are reviewed, with reference to the most important publication in the field. The main work that has guided our research is the fundamental book of Israelachvili, “Intermolecular and surface forces” (Israelachvili, 1992).
� Chapter 3: Experimental technique – Atomic Force Microscopy is explained
here, starting from the basic concepts, and developing the practical realization of a Force-distance experiment, including the spring constant calibration of the cantilever.
� Chapter 4: Experimental methodology – The experimental realization, sample
preparation, and measurement technique have been performed and described in this chapter.
� Chapter 5: Results and discussion – The results of the Force-distance
measurements are presented and discussed, explaining in details the physical interaction between AFM tip, BSA protein and surface.
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� Chapter 6: Conclusion - The AFM technique has applied successfully to identify the protein adhesions with the hydrophobic and hydrophilic surfaces.
� References
� Appendix A – All adhesion force curves of BSA and mica in PBS
� Appendix B – All adhesion force curves of BSA and polystyrene in PBS
� Appendix C – Two examples of adhesion force curves of bare mica in PBS and
two examples of adhesion force curves of bare polystyrene in
PBS.
� Appendix D – Data, SEM images and details of the calibration procedure for the
two cantilevers used in this study.
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2. Literature Review
2.1. Introduction
Scientists and engineers are now utilizing atomic force microscopy (AFM) to develop
new techniques to understand the adsorption mechanisms of proteins and the adhesion
interactions between proteins and surfaces. The goal of this chapter is to discuss
atomic force microscopy-based techniques for evaluating protein adhesion on
biomaterial surfaces.
This discussion includes:
� Advantages and principles of using atomic force microscopy;
� Basic theories of protein adsorption on solid surfaces;
� Atomic force microscopy technique to measure protein adhesion forces;
� Previous research and the issues uncovered in this research;
� Future potential of atomic force microscopy.
2.2. Atomic Force Microscopy (AFM)
2.2.1. Surface techniques and advantages of using AFM
Surface analytical techniques and methods in biomaterial surfaces provide
information about the surface characteristics related to biological responses (Dee,
2002). For example, contact angle analysis can measure the angle of contact (θ)
between a liquid and a surface, and give information on the interaction about a
particular liquid with a surface. If the liquid is water, a smaller contact angle is a
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hydrophilic surface, on which water spreads to a greater extent; a larger contact
angle indicates a hydrophobic surface, on which water beads (Dee, 2002). Scanning
electron microscopy (SEM) can give images of surface topography. X-Ray
photoelectron spectroscopy (XPS, also called electron spectroscopy for chemical
analysis, ESCA) is based on the process of photoemission and measures the
distribution of electrons for each energetic level in atoms, molecules and solids. By
using x-rays to eject electrons from inner-shell orbital, this technique is widely used
for accurate chemical analysis of the surfaces. The surface force apparatus (SFA) is
another surface analytical instrument that can measure the surface forces between two
mica sheets. One of the surfaces is held fixed and the other is mounted on a spring to
measure the force between the surfaces. However, the main drawbacks of SFA are
lack of spatial resolution, the restriction to mica surfaces, and the jump-to-contact
instability in the force measurement due to large interacting surface areas (Patil et al.,
2005).
More recently, the introduction of atomic force microscopy (Binning & Quate, 1986)
has transformed surface science. This versatile microscopy, that scans the surface with
a tiny tip attached to a cantilever, has crucial advantages that other surface techniques
do not have, namely, to image the surface and to interact with it on a nanometer scale.
This allows researchers to measure the interactions between the surface and molecules
by modifying the surface or the tip of AFM and to analyse electrochemical
phenomenon. In addition, AFM can be used in vacuum, air and liquid environments.
Particularly, biologists can make use of AFM to observe samples with the fluid cell
under physiological conditions (Zhang, Bremmell, Kumar & Smart, 2004).
Furthermore, the observation and analysis of the interactions between proteins and
samples can be achieved and more detailed dynamic information can be obtained
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using AFM. That is why AFM has been become a uniquely valuable device for
biomaterial researchers. Consequently, this literature review will focus on the
principles, functions and sample requirements of AFM, protein adsorption in the
aqueous environment, the theories of adhesion behaviours, adhesion forces
measurements between proteins and several substrates with AFM, and the future
potential of using AFM in the biomaterial research area.
2.2.2. Principles of AFM
Atomic force microscopy is a technique designed to investigate both conductors and
insulators on an atomic scale. Using the variation of forces between the surface and
the AFM tip can, in principle, measure any type of force, not only the interatomic
forces arising from atomic potentials (attractive and repulsive), but electromagnetic
forces arising from charged surfaces or particles as well (Binning & Quate, 1986).
2.2.3. Sample requirements
Contemporary AFMs allow any sample size to be used (Jandt, 2001), but the
restrictions of the scanners limit the typical imaging area from 1 1 nm2 to 250
250 m2. The z-direction range of AFM scanners is usually limited to around 8 m,
hence, rougher or bent samples cannot be imaged. Samples should be smooth and
clean.
For high-resolution imaging of molecules, flat substrates are needed. For example, if
the diameter of a protein is about a few nanometers (Scheuring, 2001), but the
substrate also has a roughness of a few nanometers, we may not be able to resolve the
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protein in AFM height image, because it is hidden by the surface topography. There
are a number of experiments involving imaging single molecules on different flat
substrates, for instance, silicon (Ortega-Vinuesa, Tengvall & Lundstrom, 1998), glass
(Fritz et al., 1995), HOPG (Ta, Sykes & McDermott, 1998) and mica (Quist, Bjorck,
Reimann, Oscarsson & Sundqvist, 1995), that show good sub nanometer resolution.
2.3. Adhesion Force Measurements of Proteins with Atomic Force Microscopy
AFM has been used by many investigators to carry out adhesion force measurements
of proteins and material surfaces. The AFM cantilever can be functionalized at the end
with particles of specific characteristic to measure surface forces between the
“particle” and the surface. Duker et al. (1991) introduced this method by attaching a
silica colloidal sphere (3.5 m) on the end of AFM tip, and they also performed the
force measurements between silica surfaces with the “colloid” probe as a function of
surface separation, salt concentration, and pH (Duker, Senden & Pashley, 1992). This
technique can be used in the measurement of other forces between different colloid
particles and surfaces. This section discusses the theories of globular protein
adsorption, the methods of achieving protein adhesion force measurements, previous
studies and current issues.
2.3.1. Globular protein adsorption on solid surfaces
The adsorption behaviour of proteins plays a crucial role in determining the nature of
the tissue-implant interface, since the adsorbed proteins can significantly have an
effect on biomaterial surface properties. Furthermore, the focus of protein adsorption
research has often been on the rearrangement of protein molecules. The reason is not
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only its relevance to the biological functioning of the molecules, but also the essential
importance in the mechanism of the adsorption process. Additionally, although
globular proteins, for example bovine serum albumin (BSA), represent only a
minority of the available protein mass, they form the greatest proportion of protein
species. Many applications and implications are relevant to the adsorption of the
globular proteins, for instance, biomedical engineering, biosensors and immunological
test systems (Norde, 2003). As a result, the following focuses on the adsorption of
globular proteins.
2.3.1.1. The stability of globular proteins in aqueous solution
The adsorption process depends on intramolecular forces within the protein molecules
that might lead to an alteration of protein conformation (Valle-Delgado et al., 2004).
Several factors determine the protein conformation: conformational entropy of the
protein; hydrophobic interactions; Lifshitz-van der Waals interactions; and hydrogen
bonding. The conformational entropy of the protein and hydrophobic interactions are
the major factors, because their opposing effects, the comparable magnitude in the
Gibbs energy, are much larger than other factors (Norde, 2003). These factors are
mentioned briefly below (Hlady & Buijs, 1996; Norde, 2003).
Conformational entropy
Most globular proteins contain a large amount of �-helices and �-sheets (Fig. 1).
These structures are stabilized by hydrogen bonds between the peptide units in the
polypeptide backbone. These intramolecular hydrogen bonds decrease the rotational
mobility of the bonds in the polypeptide chain and, therefore, the conformational
entropy. Thus, the stable structure is possible only if interactions within the protein
9
molecule and interactions between the protein molecules and its environment are
sufficiently favourable to compensate for the low conformational entropy (Norde,
2003).
Figure 1: Ordering of polypeptide chains into an �–helix (left) and a parallel �–sheet (right) (Norde, 2003).
Hydrophobic interactions
Protein molecules contain both polar and nonpolar sections. Dehydration of nonpolar
components under aqueous conditions causes a rise of the entropy of the water
molecules released and, as a result, in the lowering of the Gibbs free energy. This
hydrophobic dehydration results in polar parts of the polypeptide to link in water. The
significance of hydrophobic dehydration for protein folding was first introduced in a
10
previous study (Kauzmann, 1959), and it is now regarded as the primary driving force
for the folding process.
Lifshitz-van der Waals interactions
Lifshitz-van der Waals interactions come from interactions between fixed and/or
induced dipoles, and are very sensitive to the distance of separation L between the
dipoles. Upon folding the polypeptide chain into a compact structure, the entire effect
of dipolar interactions for promoting protein stability is not unambiguous, although it
is generally assumed that due to the relatively high packing density, dipolar
interactions tend to enhance a compact structure (Nir, 1977).
Hydrogen bonds
Most of the hydrogen bonds in globular proteins are between the amide and carbonyl
groups of the polypeptide backbone (Fig. 1). In �-helices and �-sheets such intrachain
hydrogen bonds reinforce each other since they are aligned more or less parallel to
one another. Although the net effect on the stabilization of the protein structure is still
unclear, the hydrogen bonds may be a part of the stabilizing protein structure if the
polypeptide chain and side chain that are able to form hydrogen bonds are forced into
the nonpolar interior of a compact protein (Norde, 2003).
2.3.1.2. Globular protein adsorption from aqueous solution onto solid surfaces
Although globular protein adsorption on a solid surface is an important research field
not only for a number of biological systems but also in the development of diverse
biomedical applications, some aspects of protein adsorption are still not well
understood, such as the extent and the rate of protein conformational change (Hlady &
Buijs, 1996). In this section we discuss some of the forces which come into play in the
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globular protein adhesion process on solid surfaces.
Electrostatic protein-surface interaction
In an aqueous environment the protein molecule and the surface are electrically
charged, and there is an effect of electrostatic protein-surface interactions on the
behaviour of protein adsorption. When the surface and the protein move toward each
other, their electrical double layers overlap (Fig. 2) and give rise to electrostatic
interactions, as illustrated in Figure 2.
Figure 2: Schematic representation of the Gouy-Stern model of an electrical double layer, indicating the distribution of the counterions ( ) and co-ions ( ), compensating the negative
surface charge and the resulting potential decay (Norde, 2003).
There are a few papers that emphasize the effect of the heterogeneous charge
distribution in the protein molecule (Roth & Lenhoff, 1993, 1995; Yoon & Lenhoff,
1992). Itoh et al. (1995) showed that the adsorption behaviour of -lactoglobulin (
-Lg) on a stainless steel surface at pH 6.85 at 75 was altered by chemical
modification of the carboxyl and amino groups in -Lg molecules. When -Lg
was charged negatively by the chemical modification of the carboxyl groups, the
amount of negatively charged -Lg adsorbed was larger than that of native -Lg.
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On the other hand, when -Lg was charged positviely by the chemical modification
of the amino groups, -Lg was not adsorbed on the same surface. The discoveries
suggest that electrostatic interactions do affect the adsorption of -Lg onto a surface
with a negative charge.
Hydration alterations
As mentioned above, protein molecules contain both polar and nonpolar moieties. In
an aqueous environment the globular proteins tend to be buried in the inner part of the
molecule in which they are shielded from contact with water. Early works (Gorbunov,
Lukyanov, Pasechnik & Vakhrushev, 1986; Regnier, 1987) have demonstrated that the
hydrophobicity of the protein influences its adsorption. On the other hand, protein
adsorption behaviour may be not only influenced by the hydrophobicity of the protein
surface, but the overall hydrophobicity of the protein may also be relevant.
Effects of ionic concentration on protein adsorption behaviour
The effect of ionic solution concentration and pH value has also been examined (Chen
et al., 1998; Frank & Belfort, 2000; Vengasandra, Sethumadhavan, Yan & Wang,
2003). Vengasandra et al. (2003) utilized AFM to measure the alteration of protein
binding rate by electrolyte. They discovered that when an electrolyte is present in the
medium, both long-range interactions (protein-surface) and short-range interactions
(protein-protein) require a longer time for bonding formation (Vengasandra et al.,
2003).
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2.3.2. Adhesion forces models of proteins
2.3.2.1. Derjaguin-Landau-Verweey-Overbeek model
Derjaguin-Landau-Verweey-Overbeek forces
The Derjaguin-Landau-Verweey-Overbeek (DLVO) theory has been used to define
the stability of dispersions for decades. In the DLVO theory, the net balance of
attractive and repulsive potential energies at any point in the separation between
simple model particles (or surfaces) is calculated, based upon knowledge of
parameters including the particle surface potential, the dielectric constant and ionic
strength of the medium, and the effective “Lifhsitz-Hamaker constant” of the particle
in that medium (Rowe, 2001). The Lifhsitz-Hamaker constant defines the strength of
the van der Waals forces, and the particle attraction.
At the solid-liquid interface, electrostatic double-layer forces are always present
between charged surfaces in electrolyte solutions. As mentioned above, the protein
molecule and the surface are electrically charged in an aqueous environment, and
there is an effect of electrostatic protein-surface interactions on the behaviour of
protein adsorption. Also, DLVO theory assumes that the stability of colloidal
suspensions in aqueous electrolyte solutions is controlled by long-range forces
between the particles (or surfaces), particularly in the balance between attractive van
der Waals and repulsive electrostatic forces (Leckband & Sivasankar, 1999). The van
der Waals and the electrostatic forces have been shown to control protein aggregation,
crystallization, and adsorption (Marra & Israelachvili, 1984). The expression for the
van der Waals interaction energy between a sphere and an infinite plane is:
14
���
���
��
�
�
++
++−=∆
ZRZ
ZRR
ZRA
F planesphere 2ln
)2(6132
/
(1)
where R is the radius of the sphere, Z is the nearest distance between the sphere and
the plane, and Al32 is the Hamaker constant, essentially a material property (Roth &
Lenhoff, 1993). The electrostatic potential ΦΦΦΦ i within the protein is described by the
Poisson equation:
i
ii
ερ−=Φ∇ 2 (2)
where ρρρρi represents the charge distribution and εεεεi the dielectric permittivity of the
protein interior, with its dielectric constant generally taken to be in the range from
2 to 4 (Roth & Lenhoff, 1993). For an exterior electrostatic potential ΦΦΦΦ e is described
by the linearized Poisson-Boltzmann equation:
ee k Φ=Φ∇ 22
(3)
where κκκκ2 is kT
Zieeε
ρ ∞222, e is the electronic charge, Zi the ion valency, k the
Boltzmann constant, T the temperature, and ρρρρ∞∞∞∞ the bulk concentration of electrolytes
before dissociation.
Non-DLVO forces
Some studies confirmed that the DLVO theory describes the long-range interactions
between proteins, as mentioned above. On the other hand, direct force measurements
also quantified the non-DLVO forces (e.g. hydrodynamic and solvation forces) to the
15
entire force fields that mediate protein interactions (Helm, Knoll & Israelachvili, 1991;
Leckband, Schmitt, Israelachvili & Knoll, 1994).
The hydrodynamic force occurs in the drainage of the thin film of fluid between the
small particles, and the 2-10 nm dimensions of most proteins are substantially smaller
than colloidal particles (diameters 10 nm). Thus, hydrodynamic force must also be
considered relevant to the magnitudes of the double-layer and van der Waals forces
between them. It should be noted that it is not the same as the friction experienced by
the protein as it translates through the medium (Leckband & Sivasankar, 1999).
Solvation forces or hydration forces occur when molecules must overcome the
obstacle caused by the water layer adsorbed on the surface of the macromolecule. The
energy for displacing this water regulates the self-assembly of protein aggregates and
other biomolecules. The raised intermolecular repulsion because of solvation layers is
a well-accepted phenomenon. Further, the exclusion of water from protein interfaces
stabilizes the interaction. This solvent-mediated attraction is associated with the
disruption of hydrogen bonds between water molecules by the non-polar solute
(Israelachvili & Weenerstrom, 1996; Leikin, Parsegian, Rau & Rand, 1993).
To sum up, although the DLVO theory can be used in biological colloids, protein
interactions are complicated because short-range forces have a significant impact on
the rates and strengths of protein associations when involve, for example, solvation
and hydrodynamic forces. Therefore, in order to describe the solution behavior of
proteins, DLVO theory and other forces’ fields (e.g. non-DLVO forces) must be
considered (Leckband & Sivasankar, 1999).
16
2.3.3. AFM methods for protein-surface adhesion force measurements
Adhesion force measurements between protein and material surfaces can be generally
divided into two parts which are the preparation of AFM tips and the adhesion force
measurement itself. To prepare the AFM tips the researchers immobilized the proteins
onto the AFM cantilever tips (Chen et al., 1998; Sethuraman, Han, Kane & Belfort,
2004; Wang, Palmer, Schwartz & Razatos, 2004). Then, adhesion force measurements
are conducted by using the protein-functionalized AFM tip to approach and retract
from the surface. Adhesion force values can be obtained from AFM force-distance
curves.
2.3.3.1. Modifications of the AFM tip
There are methods of controlling the surface topography and chemistry using
self-assembled monolayers (SAMs) as substrates. SAMs not only imitate the chemical
properties of a surface, but also have the ability to immobilize adsorbed molecules,
which is advantageous for AFM imaging of single molecules. Therefore, a few
approaches using SAMs have enabled the measurement of the interactions between
proteins and substrates (Sethuraman et al., 2004; Wang et al., 2004).
Wang et al. (2004) evaluated protein adhesion to biomaterials with the AFM. First of
all, the AFM cantilevers (Si3N4) were coated with gold. Secondly, SAMs were
attached on the gold-coated surface of the AFM tips. Finally, bovine serum albumin
(BSA) was immobilized on the SAM covering the AFM tip surface (Fig. 3).
17
Figure 3: Schematic representation of a covalently attached BSA molecule on an AFM tip surface (Wang et al., 2004).
Chen et al. (1998) used another way to coat protein onto AFM tip. Silicon-nitride
AFM cantilevers were cleaned and oxidized with oxygen plasma before being
immersed into a toluene solution of 3-aminopropyldimethylethoxysilane for two
hours. Then, the cantilevers were rinsed in methanol followed by potassium
phosphate buffer before being immersed into aqueous solutions of glutaraldehyde for
half an hour and then moved into BSA solutions for an hour.
2.3.3.2. Adhesion force measurements
AFM is often used to obtain both topography and chemical and mechanical properties
of a surface. In addition, AFM has the capability to perform force measurements. The
tip on the cantilever of the AFM is a force sensor with a sensitivity of pN (Ruger &
Hansma, 1990). Consequently, AFM can be utilized to perform the measurement of
force-distance curves, providing quantitative information on forces between the tip
and the sample as a function of tip-sample distance.
The total tip-sample force is the sum of two components: a long-range attractive force
and a short-range repulsive force. As the atoms of the tip and sample are brought
18
together they initially weakly attract each other. This attractive force increases until
the interacting atoms are so close that their electron clouds begin to repel one another
electrostatically. This electrostatic repulsion continues to weaken the attractive force
as the separation distance decreases. The attractive force goes to zero (i.e., approaches
the limit of zero) when the distance comes within the length of a chemical bond (a
few angstroms). Once the total van der Waals forces (repulsive forces) are positive,
the atoms are in “contact”.
Figure 4: Theoretical force-distance curve.
A practical example of an acquisition of a force-distance curve is shown in Figure 5.
During the approach, when the sample-tip distance is large the cantilever is
undeflected (I). At a certain point the tip jumps into contact with the sample, because
the surface exerts an attractive force on the tip (II). As the tip is moved closer to the
surface, a repulsive force starts to overcome the attraction (contact region) and the
force-distance curve has a linear behaviour (II-III). When the tip is removed from the
sample surface, the repulsive force on the tip decreases (III-IV). The adhesive force
between the tip and the sample keeps the tip still in contact with the sample and
breaks off when the maximum adhesion force is overcome (IV
19
Figure 5: Schematic of force-distance curves (Green et al., 2002).
Cantilever calibration
Hooke’s law (Eq. 4) can be applied to calculate the force (F) of interaction between
the tip and the sample. Although the spring constant is defined by the manufacturer,
the actual spring constant may show variations from this value by an order of
magnitude (Green et al., 2002). Therefore, it is necessary to calibrate the spring
constant of each cantilever. Several methods of calibrating the spring constant have
developed by measuring the resonant frequency of the cantilever with a little mass
attached to the tip (Cleveland, Manne, Bocek & Hansma, 1993), measuring its free
oscillation (Sader, Larson, Mulvaney & Lee R, 1995) or measuring the thermal noise
(Hutter & Bechhoefer, 1993). The details of the procedure that has been used in this
research (free oscillation) will be explained in the chapter regarding experimental
techniques.
20
Previous research
Since AFM has been invented in 1986, several AFM techniques have been developed
and applied to measure the interactions between proteins and surface, but those
techniques still have drawbacks need to be considered. Three previous researches
described below can represent general AFM techniques about the adhesion force
measurement between proteins and the substrate surface. The advantages and the
disadvantages of these techniques have also been addressed.
Adhesion forces between individual ligand-receptor pairs
Adhesive force measurements of ligand-receptor interactions have been performed
(Florin, Moy & Gaub, 1994) by using a avidin (receptor)-functionalized tip to probe a
biotinylated (ligand) agarose bead. Under the condition of positioning the AFM tip on
the top of the agarose bead by an eplilight microscope, the area between the AFM tip
and the bead allowed only a limited number of molecular pairs to interact, and the
unbinding forces of individual molecular pairs have been obtained.
The advantage of this method would gain an unbinding force of a molecular pairs due
to the limited interaction area between the AFM tip and the substrate surface, but the
disadvantage would be because the AFM tip (silicon nitride) is sharp and much harder
than the protein molecules, the AFM tip may destroy and penetrate the protein
molecules until the tip is hit the surface during the force measurement. Hence, the
interaction which has been measured could be only the interaction between the AFM
tip and the agarose bead.
21
Interactions between proteins and different substrates by atomic force
microscopy
Sagvolden et al. (1998) showed a method capable of measuring the adhesion forces of
proteins to solid surfaces. Proteins are first attached to glass micro spheres that are
subsequently adsorbed to various substrates. After a relaxation time, the proteins
attached micro spheres are dislodged using the AFM cantilever and the force values
are obtained by the AFM cantilever deflection. The experimental results have shown
proteins adsorb better on a hydrophobic polystyrene substrate than hydrophilic glass
surfaces. Additionally, those researchers found when proteins were cross-linked with
glutaraldehyde on the surface, the adhesion forces of cross-linked proteins were lower
than the adhesion forces of natural proteins, which suggested using glutaraldehyde to
immobilize proteins on the surface may change the nature of the interaction between
proteins and surface. The main disadvantages of this technique are described below:
1. Because the mass of a micro sphere is larger than protein molecules, it would cause
damage on the flexibility of the protein molecules attached on the micro spheres when
the micro spheres have arrived on the substrate. Hence, due to the damaged flexibility
of the protein molecules, the measured adhesion interactions would be not the
“nature” interactions between proteins and the substrate.
2. Because the protein molecules may not attach to the micro sphere surface evenly,
the adhesion interactions which have been obtained may not the interactions between
proteins and the substrate surface.
22
Interactions between proteins adsorbed on different substrates using atomic
force microscopy with a colloid probe
Valle-Delgado et al. (2004) used a colloid AFM probe technique which was attached a
micro sphere with a diameter of 5 µm to the end of a AFM cantilever to measure the
interaction forces between bovine serum albumin (BSA) layers adsorbed on different
substrates (silica and polystyrene) at a function of pH and slat concentration. The
experimental results were fit to theoretical predictions in DLVO theory satisfactorily
and obtained an opportunity to calculate the hydration forces between proteins.
The colloid probe technique is to use a micro sphere attached to the end of the AFM
cantilever instead of the sharp AFM tip, and it has advantages that the sharp tip may
not have. For example, the proteins functionalized colloid probe can measure the
interactions between the proteins and the surface without penetrating the protein
molecules during the action of approaching to the surface. However, after attaching
the micro sphere to the end of AFM cantilever, the original spring constant of the
AFM cantilever can be changed, which may obtain inaccurate force measurements.
Hence, the spring constant of the colloid probe needs to be calibrated after the micro
sphere has been glued to the end of AFM cantilever.
2.4. The future potential of atomic force microscopy
Since the invention of AFM in 1986, researchers have been trying to utilize AFM to
understand surface interactions in a wide variety of situations. Carbon nanotubes that
have diameters as small as 5 nm can improve the lateral resolution, and they can be
employed in fine organic or biological samples because they have a low force
constant that makes them strong but limiting the maximum force (Green et al., 2002).
23
Some authors have used the AFM tip functionalized with nanotubes to obtain the
high-resolution surface images (Woolley, Cheung, Hafner & Lieber, 2000). Cho and
Sigmund. (2002) suggested that using a multiwalled carbon nanotube (MWNT) as a
nanosized probe can overcome the limitation of an AFM tip for studying nanoparticles,
due to the small diameter, low surface roughness and minimization of subsidiary
effects.
2.5. Conclusion
For years the adsorption of globular proteins plays a significant role and has been
investigated in many research areas, for example, biomedical engineering. Globular
protein adsorption onto a solid surface is influenced mainly by conformation entropy
and hydrophobic interactions, and electrostatic and hydrophobic interactions play the
major roles in determining the behaviour of globular protein adsorption on solid
surfaces. Because Bovine serum albumin (BSA) is globular proteins and has been
often studied for the adsorption of proteins, BSA was chosen to be used in this thesis.
Since 1986 atomic force microscopy has been utilized to develop techniques that can
give researchers an opportunity to explore and understand the adhesion interactions of
the protein molecules with different surfaces at the atomic level. Although the AFM
techniques have several advantages that other surface instruments can not achieve (e.g.
the spatial images, various ranges of substrates and real time measurements in liquid
condition), they still have few disadvantages, for example, the protein attached AFM
tip may not measure the “real” interaction between proteins and proteins, because the
“hard and sharp” AFM tip can penetrate the “soft” protein molecules during the force
measurement. Hence, in order to eliminate these disadvantages, we have established
24
an AFM technique which not only can keep the nature flexibility of proteins during
the force measurement, but also can measure directly and simply the “real” adhesion
interactions between proteins and the substrate surface. The following chapter will
describe and explain how this novel AFM technique works.
25
3. Experimental Technique
This chapter introduces the principles of atomic force microscopy (AFM) and the
methods of carrying out force measurements.
3.1. AFM
Atomic force microscopy is a technique designed to investigate both conductors and
insulators on an atomic scale by exploiting the forces between the surface and the
AFM tip. By keeping constant the force while the tip sweeps over the surface, it is
possible to obtain microscopic images of the surface with nearly atomic resolution.
Generally the force considered in AFM is the repulsive or attractive force generated
by the interaction of the two atomic potentials of the tip and of the surface. However
it is possible in principle to use any type of force, not only the interatomic forces, but
electromagnetic forces as well (Binning & Quate, 1986). In force spectroscopy mode
the AFM can measure the values of these forces as a function of the tip-sample
distance. The following section discusses the main features of AFM and explains how
it can achieve such high and fine resolution.
3.1.1 AFM tip
The most important part of AFM is the tip, because AFM images samples by sensing,
rather than by looking as other microscopes do (in the extended sense also SEM and
TEM “look” at the sample, since electrons behave like waves as photons do), and
the tip is the sensing tool (Morris, Gunning & Kirby, 1999). An AFM tip is shown
below in the electron micrograph (Fig. 6).
26
Figure 6: Schematic representation of the tip of an AFM (Morris et al., 1999).
The AFM tip is a micro-fabricated, particularly sharp point made of a hard material
(usually Si, SiO2 or SiC) installed on the end of a cantilever, a little bar of Si or
similar material, that must have good elastic properties in the used range. The
cantilever allows the tip to move up and down in z-direction, and it has a force
constant suited to respond to the force between the tip and the sample. The resolution
of an AFM depends strongly on the shape of the tip (Wiesendanger, 1995). The
smaller and sharper the tip is, the smaller is the surface area sampled by the tip (Jandt,
2001). The deflection of the cantilever as a spring can be converted to force,
according to Hooke’s law:
F = - kzd (4)
Where kz is the force constant of the cantilever and d is its displacement. The minus
sign indicates that the force is opposite to the displacement of the tip.
27
3.1.2. Piezoelectric scanner
The second crucial component of the AFM is the piezoelectric scanner. Generally,
AFM uses one of two fundamental scanning mechanisms, namely, scanning the
sample or scanning the tip. These two scanning mechanisms both rely on a
piezoelectric scanner. The scanner is usually a tube made of zirconate titanate
ceramics (PZT) that converts electric signals produced by the control electronics into
the mechanical scanning action along x-y and z directions. The distance in the
z-direction between the probe and the sample is usually kept constant by a feedback
mechanism in the AFM controller (constant force mode). A detailed mathematical
study (Taylor, 1993) of the dynamics of tube scanners (with respect to a piezoelectric
tripod) has addressed both their advantages and disadvantages. One of the few
disadvantages is the motion of the end of the tube which drives the tip or sample in
the x-y directions, tracing out an arc rather than a straight line, causing an effect
known as “eyeballing” when it is scanning on a large area.
3.1.3. Detection mechanism
The final feature of AFM is the detection mechanism. When scanning across the
sample, the deflection of the tip should be monitored. There are several different ways
of detecting the motion of the tip. The most common method, the optical lever system,
is illustrated below (Figure 7):
28
Figure 7: Schematic representation of the atomic force microscopy (Morris et al., 1999).
A laser beam is concentrated on the end of the tip, and reflected from the back of the
tip to a photodiode detector that is divided into four segments. While the tip is
travelling on the surface, the angle of laser reflection from the tip is changing as well,
and the laser reflection that is falling onto the photodiode detector is producing
changes in intensity in each of its quadrants. This chain of action affects the
mechanical amplifier that is sensitive enough to detect the tip movement at atomic
scale during scanning. The difference in laser intensity between the top two segments
and the bottom two segments generate the electrical signal that quantifies the z
deflection (up and down) of the tip, while the difference in the laser intensity between
the right and left segments can be used to quantify the lateral deflection of the tip.
29
3.1.4. Modes of AFM
Generally, AFM has three operating modes for imaging: the contact mode,
semi-contact mode and non-contact mode. In all three modes the cantilever is
scanning across the sample surface, and the topography of a sample is exhibited by
interpreting the signal of the cantilever deflection. By approaching the surface (Fig. 8),
the tip feels an attractive force (non-contact region) due to the long-range part of the
atomic potential up to an equilibrium point where the attractive force (negative)
reaches its maximum (minimum in the force-distance curve). Over this point the
repulsive component of the atomic potential (due to the repulsion of the atomic clouds
connected to the Fermi principle) starts to be larger than the attractive part. This is the
contact region. The region around the minimum is used in the intermittent contact
mode (tapping mode).
Figure 8: Force-distance curve in AFM
30
Contact mode
Using the tip in contact mode may be appropriate when the samples are sufficiently
hard (e.g. titanium) because the tip is in close contact with the sample. For softer
samples this mode may destroy the surface: for example, when studying the weakly
adsorbed biomolecules on surfaces. An advantage of the scanning of contact mode is
that it can be executed in air, vacuum and fluid environments.
Care must be taken to keep the tip always in close contact: this is obtained by using an
appropriate feedback to maintain the deflection signal at the set point value. The set
point value should not be too far from the zero deflection level (i.e. the tip should not
be pressed too much on the surface) because this might result in the destruction of the
tip and of the surface. On the other hand, a too small difference between the value of
set point and the zero deflection level could cause instabilities in the tracking system
(Morris et al., 1999).
The contact mode can also be a basis for the operation of other contact techniques,
because the contact mode uses the tip deflection, which can be converted according to
Hooke’s law (Equation 1) into a net force (Hartmann, 1998). The net force is
composed of a long-range attractive interaction between the probe and the sample and
a short-range repulsive interaction between the probe and the sample (Hartmann,
1998). With an appropriate detection system (four quadrant photodetector) lateral
forces can be measured. Since the tip is in stable contact with the surface, the
scanning motion results in some torsion of the tip in the lateral x-y plane that also
reflects the frictional properties of a surface (Jandt, 2001).
31
Non-contact mode
The non-contact mode of AFM is used to study the long-range attractive forces and
the tip never actually touches the sample surface during the scan. However, the forces
applied to the tip are extremely low, resulting in low deformation and shear. As a
result, this is the most suitable method for soft samples (e.g. polymers) since the risk
of possible destruction of the sample surface is greatly reduced. Choosing a flexible
tip with a low resonant frequency is important since van der Waals forces would have
little deflective effect on a stiff cantilever (Morris et al., 1999). The non-contact mode
can be used to test various tip-sample interactions such as magnetic and electrostatic
interactions. For this purpose, a special coating of the tip is necessary. For example,
magnetic force imaging can provide information about the surface magnetization of
the sample, hence, the tip has to be coated with a thin magnetic film.
Semi-contact mode
The semi-contact mode is also known as the “tapping mode”. In the semi-contact
mode the tip is oscillating (frequencies in air 50-500 kHz, in fluids approximately 10
kHz) with amplitude of several tens of nm. This oscillation is driven by the cantilever
piezodriver, so that the tip approaches the surface several thousands of times per
second, slightly touching or “tapping” the surface (Jandt, 2001). The contact time
between the tip and the sample is greatly reduced by using the semi-contact mode,
and the friction force is minimized while the tip is travelling over the surface. This
should prevent the tip from attracting or sweeping the molecules on the surface
(Putman, Van der Werf, De Grooth, Van Hulst & Greve, 1994). For this reason
biological samples are mostly scanned by the semi-contact mode. In the semi-contact
mode, phase imaging can be achieved, because the various material properties lead to
a phase shift of the tip oscillation, relative to the signal sent to the cantilever
32
piezodriver. Therefore, using phase imaging we can also acquire some characteristic
properties of the sample, for example, surface adhesion and viscoelasticity.
Force spectroscopy mode
Additionally, AFM not only has the function for the surface imaging, but also has the
function for studying different kinds of surface forces. The function for AFM to
measure the surface forces is called force spectroscopy mode. The AFM force
spectroscopy mode is based on the changes of the cantilever deflection as the AFM tip
approaches to the surface or retracts from it, and the AFM cantilever deflection can be
converted according to Hooke’s law (Equation 1) into a force value(Hartmann, 1998).
Heniz, et al. (1999) has explained the AFM force spectroscopy mode can be used to
study the adhesion interactions between proteins and the substrate surface. Hence, in
this work the AFM force spectroscopy mode has been utilized to establish the
technique of estimating the interactions between proteins and different surface
properties from the force-distance curves.
3.2. Force measurement procedure facility
The atomic force microscopy is a NT-MDT SMENA model equipped with a
50µ scanner. The SMENA is a stand-alone STM/AFM head that allows performing
measurements virtually on any surface. It is equipped also of an optional liquid head
which permits the dipping of the AFM cantilever in a liquid solution. This head has
been used extensively in this work.
33
Figure 9: The NT-MDT SMENA liquid head
Sample preparation
The sample is prepared in an appropriate size (1 cm2) and glued to a substrate which
is mounted on a metallic sample holder. The sample holder is then immersed into a
liquid cell (a small Petri dish filled with the appropriate solution) leaning on a
magnetic stage, which has the role of keeping the sample holder still.
AFM can detect forces in the range of 10-9 Newton (nano-Newton). There are three
main steps to obtain a reliable force measurement. The first is the calibration of the
AFM cantilever spring constant, the second is the force measurement, and the final
step is the conversion from photodiode current to force.
3.2.1. Spring constant calibration
An AFM cantilever can be considered as a spring Hooke’s law (Eq. 4) can therefore
be applied to calculate the forces applied to the AFM tip. Since the shape of all the
AFM cantilevers in this study is a rectangular, the method developed by Sader et al.
(1999) is particularly suitable. The equation used is:
34
kz = 0.1906 � b2 L Qf fc2 �
fi (�f) (5)
Where � is the density of the fluid, b and L are, respectively, width and length of the
AFM cantilever, Qf is the quality factor of the resonance frequency fc, and �fi (fc) is
the hydrodynamic function of the cantilever. The Qf is defined as the resonance
frequency (center frequency) fc divided by the bandwidth �f:
Qf = fc / (f2-f1) = fc /�f (6)
f2 is the upper and f1 the lower cutoff frequency. On a graph (Fig. 10) of response
versus frequency, the bandwidth is defined as the 3 dB change in level (voltage,
current, or power) on either side of the centre frequency. The bandwidth is not the
same as the "full width at half maximum" or FWHM. It is necessary to measure the
resonance frequency of the thermal oscillations, without applying any exciting
voltage. This is performed by leaving the cantilever far enough from the surface and
setting the amplification of the lock-in detector to 106. A typical frequency curve is
shown in Figure 10 below:
Figure 10: The resonance curve
35
Error calculations
In order to evaluate the accuracy of our measurements, we have to compute the error
in the cantilever calibration. The Q factor (fc/∆fc) and the standard deviation of the
resonance frequency (fc) of an AFM cantilever can be obtained by fitting a Gaussian
equation to the resonance frequency curve. An example is shown below (Fig. 11):
Figure 11: Resonance curve fitted by Gaussian equation for an AFM cantilever
The total relative error on the spring constant can be obtained by error propagation.
The errors for Q factor and resonance frequency are obtained from the Gaussian fit.
The length and width of the AFM cantilever can be measured on the SEM image
based on the scale bar, and the error (0.79 ) is obtained from some SEM calibrations.
Therefore, the errors of the measured length (∆∆∆∆L) and width (∆∆∆∆b) of an AFM
cantilever can be calculated from the equations
0
0.5
1
1.5
2
5 10 15 20 25 Frequency (kHz)
y = Ao+A1*exp(-(x-fc)2/σσσσ2)
Error Value 0.0043 0.1144 Ao 0.019 1.331 A1 0.013 13.231 fc 0.019 1.119 σσσσ
0.984 Chisq
0.981 R
• Amplitude
−−−− Gaussian fitted
13.231
36
∆∆∆∆L = 0.0079 L (7a)
∆∆∆∆b = 0.0079 b (7b)
The relative error of the AFM cantilever spring constant (∆∆∆∆kz), by assuming no error
on the fluid density � is:
∆∆∆∆kz / kz = 2 (∆∆∆∆b / b) + ∆∆∆∆L / L + ∆∆∆∆ Qf / Qf + 2 (∆∆∆∆ fc / fc) (8)
3.2.1.1. Experimental works
The AFM cantilever A was chosen to do the bare mica adhesion force measurements
and the BSA-mica adhesion force measurements. The AFM cantilever B was chosen
to do the bare polystyrene adhesion force measurements and the BSA-polystyrene
adhesion force measurements. We have obtained 10 resonance frequency curves of
cantilever A and 10 resonance frequency curves of cantilever B, respectively. Also, we
fitted the Gaussian equation to those resonance frequency curves of cantilever A and
cantilever B. Appendix D contains all data, SEM images and details of the calibration
procedure for the two cantilevers.
3.2.2. The force measurement
Before the force measurement, the AFM has to be set in the contact mode. The laser
beam which is reflected from the back of the cantilever to the photodiode should be
previously adjusted in order to reach the four quadrant sensor. After the immersion in
the liquid (usually in a Petri dish) the laser beam needs to be readjusted. This can be
achieved by placing the Petri dish on a stand so that the laser can be seen across the
glass on a white paper placed on the table (Fig. 12).
37
Figure 12: The photo show how to adjust the laser beam focus on the AFM cantilever in the liquid.
The force measurements are conducted by the AFM force spectroscopy mode. After
the AFM cantilever is landed in the contact mode, the force spectroscopy mode can be
opened by pressing the “operation” button in the SPM window menu (Fig. 13).
Figure 13: The diagram shows the where the force spectroscopy mode is in the SPM window menu.
The laser is seen across the glass on the white paper.
38
3.2.3. Force curves
During the force measurement the force spectroscopy mode allows the AFM
cantilever to approach the surface and then retracts from it at a fixed speed. In this
way the interaction between the tip and the surface is detected. The raw signal is
current (nA) versus displacement (nm). Fig. 14 indicates how the deflection
signal-displacement curves can be transferred to the cantilever
deflection-displacement curves:
Figure 14: The indication of how the signal-displacement curves are converted to cantilever deflection-displacement curves
By using the slope of the approach curve m we can write:
dtip = I / m (9)
Where dtip (nm) is the deflection of the AFM tip, I is the value of current signal
(nA). Once the spring constant kz and the cantilever deflection are obtained via
equation 9, Hooke’s law (equation 4) can be applied to calculate the force between the AFM tip and the sample.
-4
-3
-2
-1
0
1
2
3
-200 -100 0 100 200 300 400
Mica current-displacement curves 0428Tip approach (nA) Tip retract (nA)
Displacement (nm)
m = ∆∆∆∆I/∆∆∆∆x ∆∆∆∆I
∆∆∆∆X
39
Figure 15: Force-distance curves
The current-displacement curves have been converted to the force curves (Fig 15).
The following will describe how the force curves describe the AFM tip behaviours of
picking up BSA molecules.
-20
-15
-10
-5
0
5
10
15
20
-100 0 100 200 300 400
Mica force 0428
Tip approach (nN) Tip retract (nN)
Displacement (nm)
40
AFM tip approaching
When the AFM tip starts to approach the surface, at a distance of about 150 nm, the
cantilever should begin to bend downward before the actual surface is attained at
about 5-20 nm. This is caused by an attraction between the surface and the tip.
-0.1
-0.05
0
0.05
0.1
0.15
0.2
-20 0 20 40 60 80 100 120
Tip approach (nN)
Distance (nm)
Figure K1: Force-distance curve. First stage of the approach to the surface
However, in water the electrostatic forces (like Van der Waals) are greatly reduced and
it is quite difficult to see the bending. The final stage of the approach is a repulsive
behaviour, with the force increasing as the tip is pushed towards the surface; this is
typical of a rigid substrate, showing that the tip reaches the actual mica surface.
-0.1
-0.05
0
0.05
0.1
0.15
0.2
-20 0 20 40 60 80 100 120
Tip approach (nN)
Distance (nm)
Figure K2: Force-distance curve: the repulsive region
41
AFM tip retracting
When the AFM tip is raised, the force distance curve reflects initially the elastic
behaviour of the cantilever leaving the mica surface.
-0.15
-0.1
-0.05
0
0.05
0.1
0.15
0.2
-20 0 20 40 60 80 100 120
Tip retract (nN)
Distance (nm) Figure H1: Force-distance curve: pulling the cantilever in the repulsive region
Then the BSA molecules attach to the tip start again to pull downward, being
stretched by the cantilever (Fig H2).
-0.15
-0.1
-0.05
0
0.05
0.1
0.15
0.2
-20 0 20 40 60 80 100 120
Tip retract (nN)
Distance (nm)
Figure H2: Force-distance curve: the retracting cantilever stretches the BSA molecules
In conclusions, we have been able to calibrate the instrument and to measure the
forces acting between the tip and the mica surface in liquids. We will show the
complete set of results in next chapter.
42
4. Experimental Method
In this work we have developed a technique to directly identify the interactions
between protein molecules and the substrate surface by using AFM in liquid. In
literature hydrophobic interactions play a significant role in the protein adhesion
which means the adhesion forces between proteins and a hydrophobic surface are
larger than the adhesion forces between proteins and a hydrophilic surface. Therefore,
we chose Bovine serum albumin (BSA) as the proteins and mica and Polystyrene as
substrates. Because mica is hydrophilic (Leonenko, Z. V., Carnini, A., Cramb D.
T., 2000), and polystyrene is hydrophobic, the adhesion force values between BSA
and two different surfaces would be obvious comparable.
4.1. Atomic force microscopy
Our AFM (NT-MDT Solver P47, Moscow, Russia) was equipped with a CSG-11
350µm length AFM cantilever (Silicon). All AFM force measurements were
conducted in phosphate-buffered saline (PBS) buffer solution at 22 using the AFM
SMENA liquid head. All accessories were cleaned by rinsing in ethanol and deionised
water before using the liquid head. The spring constants of two AFM cantilevers were
calibrated by using the method of Sader et al. (1999) as discussed in the previous
chapter. The sample was fixed to a magnetic sample holder by adhesive tape, and the
ensemble was carefully placed into a glass dish with sufficient amount of PBS buffer
solution to completely cover the sample surface (Fig. 16). All experiments were
carried out in the Analytical Electron Microscopy Facility (AEMF) where a constant
temperature of 22° is maintained.
43
Figure 16: Photo of AFM head and sample assembly during force measurements.
4.2. BSA adsorption onto the surfaces
Bovine serum albumin (BSA, A2153-10G, Sigma-Aldrich, Australia) is a kind of
globular proteins and a single polypeptide chain consisting of about 583 amino acid
residues and no carbohydrates. We used the same species of BSA for our experiments
in this work.
A cleaved mica (muscovite) surface was dipped into the solution of 10 gL-1 BSA
(A2153-10G, Sigma-Aldrich, Australia) with 10 ml 1M phosphate-buffered saline
(PBS) buffer solution (pH 7.4) for 3 hours. The solution of 10 gL-1 BSA (A2153-10G,
Sigma-Aldrich, Australia) with 10 ml 1M phosphate-buffered saline (PBS) buffer
solution (pH 7.4) was in a polystyrene 55mm petri dish (S5514UV10, Techno-Plas
PTY LTD, Australia) for 3 hours and covered the whole area of the polystyrene dish
bottom. The mica surface and the polystyrene surface were rinsed with appropriate
amount of deionised water to clear loosely bound BSA before the AFM experiment.
SMENA head
Glass dish
44
5. Results and Discussion
5.1. Experimental results
Four sets of AFM adhesion force measurements have been performed:
1. bare mica (expand PBS in full) (PBS)
2. BSA adsorbed mica surface in PBS
3. bare polystyrene in PBS
4. BSA adsorbed polystyrene surface in PBS
A CSG-11 AFM cantilever (Cantilever A) was chosen for the experiment on mica,
while a different cantilever (Cantilever B) was chosen to carry out the force
measurements on polystyrene. While belonging to the same batch, and having the
same dimensions, the two cantilevers have slightly different properties. The measured
values of length, width, Q factor, resonance frequency and spring constant value for
the two cantilevers are shown in Table 1.
CSG-11 Length
(µm)
Width
(µm) Q factor
Resonant
Frequency
(kHz)
The spring
constant (N/m)
Cantilever A
(mica) 343±3 40.0±0.3 12.0±2.5 13.25±0.03 0.026±0.006
Cantilever B
(polystyrene) 347±3 35.3±0.2 13.2±2.9 12.90±0.08 0.025±0.006
Table 1: The information of Cantilever A and Cantilever B (See Appendix D for experimental details)
45
The results of the force-distance measurements are obtained as a current (the
deflection of the AFM cantilever), which is converted into a force using the method
described in Chapter 3. These have been displayed as force vs displacement curves..
The X-axis (displacement) represents that the displacement between the tip and the
substrate surface, and the Y-axis represents that the force values measured when the
tip was approaching or retracting from the substrate surface. The red curve describes
the force actions of when the AFM tip was approaching to the substrate surface, and
the blue curve describes the force actions of when the AFM tip was retracting from
the substrate surface. In this work we are interested in the protein adhesions to
different surfaces, so we focus on the results on the pull-off force curve of each force
measurement.
5.1.1. Bare mica surface in PBS
Figure 17 contains one of the many Force curves (more than 100) we have acquired
on bare mica surface in PBS solution. All measurements appear very similar, like the
one reported in Fig 17. Upon approach, no force is detected until a short-range
repulsive force is observed starting at about 10 nm; upon retract no hysteresis is
observed and the retracting line is perfectly superposed to the approach line. No
attractive interactions were observed.
46
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm)
Figure 17: Bare mica force curves in PBS
5.1.2. BSA adsorbed on mica surface in PBS
A total of 120 force-displacement curves were measured at four different places on the
same mica surface in PBS. Owing to the small fraction of the surface covered, only 9
adhesion force measurements between the BSA molecules and the mica surface were
recorded (See Appendix A). One of those ten adhesion force measurements is shown
in Fig. 18 as an example. The approach curve (red) shows that when AFM tip was
approaching the surface a repulsive force raised up smoothly compared to the
approach curve in Figure 17, which suggests the AFM tip hits an elastic layer of BSA
molecules before hitting the mica surface (Lin, S., Chen, J. L., Huang, L. S., & Lin H.
W., 2005). The retraction curve shows an adhesion of about 0.03 nN, followed by
47
several jumps of about 0.01nN each. We have observed that when the AFM tip starts
retracting from the mica surface, the repulsive force decreases dramatically. Then, a
short-range attractive force is generated by the BSA molecules attached to the tip and
this causes jumps of about 0.01 nN, possibly corresponding to the unfolding of the
proteins (Florin, Moy & Gaub, 1994; Heinz, W. F., Hoh, J. H. 1999). Due to the
elastic properties of the BSA molecules we think that the AFM tip stretches one or
more BSA molecules, and they detach one at a time until the tip or the BSA detaches
completely. At this point the tip returns to its original position entirely. The average
adhesion force value of the interactions between the BSA molecules and the mica
surface measured by our experiment is 0.036 nN, and the standard error is 0.002nN.
-0.1
-0.05
0
0.05
0.1
0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure 18: BSA-mica force-displacement curves in PBS
48
5.1.3. Bare polystyrene in PBS
The force curves (Fig. 19) show the interactions between the AFM tip and the bare
polystyrene surface in PBS solution. In the approach part (red), a short-range
repulsive force was detected at a distance of ~ 25 nm, and the repulsive force had
began to decrease dramatically since the AFM tip started retracting from the
polystyrene surface. No interactions were observed.
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
TIp approach (nN)Tip retract (nN)
Displacement (nm) Figure 19: Bare polystyrene force curves in PBS
49
5.1.4. BSA adsorbed on polystyrene surface in PBS
A total of 100 force measurements were measured at four different places on the same
polystyrene surface in PBS, and only 13 adhesion events were recorded (See
Appendix B). An example of the force curves between the BSA molecules and the
polystyrene surface is below (Fig. 20). Once the AFM tip is close to the surface a
repulsive force raises up smoothly compared to the approach curve in Figure 19,
which suggests to his the elastic BSA molecules (Lin, S., Chen, J. L., Huang, L. S., &
Lin H. W., 2005). Then, during the retraction the repulsive force decreased
dramatically, similarly to what occurs to the bare polystyrene surface, but suddenly
jumps are detected. We have fitted the elastic properties of the BSA molecules by
fitting the small curves appearing like jumps which are possibly the unbinding forces
of BSA molecules (Florin, Moy & Gaub, 1994; Heinz, W. F., Hoh, J. H. 1999).
We believe that the AFM tip is unfolding the BSA molecules until the AFM tip had
picked the BSA molecules completely and returned to its original position. The mean
adhesion force value of the interactions between the BSA molecules and the
polystyrene surface is 0.066 nN, and the standard error is 0.003 nN.
50
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80 100
Tip approach (nN)Tip retract (nN)
Displacement (nm)
Figure 20: BSA-polystyrene force curves in PBS
5.2. Discussions
Table 2 has listed the maximum of measured adhesion force of BSA-mica (Group A)
and BSA-polystyrene (Group B). Two groups were analyzed statistically by an
unpaired Student t test. The statistical analysis of the results shows clearly that the
adhesion force between BSA and polystyrene is twice the adhesion force between
BSA and mica, and the mean difference of the mean adhesion forces between the
BSA-mica and the BSA-polystyrene is about 0.03 nN (Table 3). The t Probability is
smaller than 0.0001 which means the mean difference between Group A and Group B
at 99.9999 % level is highly significant, and this shows our quantitative experimental
results are statistically significant. Figure 21 shows the comparison of adhesion forces
between BSA-mica and BSA-polystyrene and a clear separation between the group of
BSA-polystyrene data and the group of BSA-mica data. Because during the adhesion
51
force measurements we used the same source of the AFM cantilevers and BSA, the
difference of the measured adhesion forces between BSA-mica and BSA-polystyrene
could be due to the interactions between BSA and different surfaces, not the
interactions between the AFM tip and BSA. Furthermore, hydrophobic interaction is a
strong attractive force between non-polar species interacting in an aqueous solution
(Tilton, R. D., Robertson, C. R., & Gast, A. P., 1991; Castner, D. G. & Ratner, B. D.,
2002), and in the literature review it has been discussed that the hydrophobic
interaction is the main driving force of the protein molecules adsorption onto the
surface and the stabilization of a compact protein structure due to the decreasing of
free energy (Norde, W., 1986).
Item
Maximum of adhesion force values between BSA and mica (nN) in each force measurement (Group A)
Maximum of adhesion force values between BSA and polystyrene (nN) in each force measurement (Group B)
1 0.028 0.057
2 0.029 0.083 3 0.030 0.068 4 0.032 0.082 5 0.037 0.058 6 0.042 0.065 7 0.046 0.086 8 0.043 0.063 9 0.036 0.061
10 0.053 11 0.056 12 0.060 13 0.060
Table 2: The table shows the maximum of adhesion force values of BSA-mica and
BSA-polystyrene.
52
Group A (BSA-mica) Group B (BSA-polystyrene) Count 9 13 Mean 0.036 0.066
Variance 0.00004 0.0001 Standard Deviation 0.007 0.01
Mean Difference -0.03 Degrees of Freedom 19
t Value -7.85 t Probability 0.0001
Table 3: The student t test of adhesion forces of BSA-mica (Group A) and
BSA-polystyrene (Group B) (the student t test was calculated by KaleidaGraph,
Synergy Sofeware).
0.02
0.03
0.04
0.05
0.06
0.07
0.08
0.09
0 2 4 6 8 10 12 14
BSA-mica adhesion forceMean BSA-mica adhesion forceMean - standard deviation (BSA-mica) Mean + standard deviation (BSA-mica)BSA-PS adhesion forceMean BSA-PS adhesion forceMean - standard deviation (BSA-PS)Mean + standard deviation (BSA-PS)
Counts
Figure 21: The comparison of adhesion forces between BSA-mica and BSA-polystyrene.
53
Ying et al. (2002) modified silicon surfaces as hydrophilic and hydrophobic surfaces.
They found the surface concentration of adsorbed BSA on the hydrophobic surface
was twice the surface concentration of adsorbed BSA on the hydrophilic surface. In
other words, the adhesion force between the BSA molecules and the hydrophobic
surface should be larger than the adhesion force between the BSA molecules and the
hydrophilic surface. In table 4 and table 5 Chen et al. (1998) used BSA-functionalized
AFM tip to measure the adhesion forces with –NH2 SAM surface (a hydrophilic
surface) and -CH3 SAM surface (a hydrophobic surface). They also found that the
adhesion force between BSA and -CH3 SAM surface are four times larger than the
adhesion force between BSA and –NH2 SAM surface due to the hydrophobic
interaction between BSA and –CH3 SAM surface. The AFM cantilevers they used
were stiffer than the AFM cantilevers we used due to the different spring constants,
the magnitudes of their average adhesion forces are larger than the magnitudes of our
average adhesion forces.
Sagvolden et al. (1998) developed a method capable of measuring the adhesion forces
of proteins to solid surfaces. Proteins were first attached to glass microspheres. After a
certain time, the BSA-coated microspheres were spread on glass surface and
polystyrene surface in buffer solution. The BSA-coated glass microspheres were
dislodged using the AFM cantilever, and the force values were obtained by the AFM
cantilever deflections. The results had larger adhesion forces between BSA-coated
microsphere and polystyrene surface than the adhesion forces between BSA-coated
microsphere and glass surface as well because of the hydrophobic interactions (Table
4 and Table 5). However, the technique they developed still has disadvantages. For
example, the AFM cantilever could need to overcome the total mass of the
BSA-coated glass microspheres, the friction forces between the microspheres and the
54
surface and the interactions between BSA and the surface to dislodge the BSA-coated
glass microspheres, so the measured adhesion forces may not be the direct
interactions between BSA and the surface. When BSA molecules are at a hydrophobic
polystyrene surface in aqueous solution, due to the hydrophobic interactions
BSA-coated microspheres may become sticky to adhere to each other and spread not
evenly on the surface. Thus, the AFM cantilever may not dislodge only one
microsphere at once within each force measurement, and the measured adhesion
forces could be greatly larger (Table 5).
On AFM
tip On substrate
Average forces (nN)
AFM cantilever spring constants
(N/m) Reference
None BSA adsorbed mica surface 0.036 ± 0.002 0.026 Lai (2006)
BSA -NH2 terminated SAM 4.6 0.32 Chen et al.
(1998)
None BSA adsorbed glass
microspheres-glass surface 0.07 0.3
Sagvolden
(1998)
Table 4: The adhesion forces between BSA and hydrophilic surfaces.
On AFM
tip On substrate
Average forces (nN)
AFM cantilever spring constants
(N/m) Reference
None BSA adsorbed polystyrene
surface 0.066 ± 0.003 0.025 Lai (2006)
BSA -CH3 terminated SAM 19 ± 9 0.32 Chen et al.
(1998)
None
BSA adsorbed glass
microspheres-polystyrene
surface
99 0.3 Sagvolden
(1998)
Table 5: The adhesion forces between BSA and hydrophobic surfaces.
55
From the table 2 the adhesion forces between BSA and mica surface or polystyrene
can be obtained. However, the values of adhesion forces only can identify the protein
affinity to the surface, but they can not characterize the measured adhesion
interactions which are protein-surface interactions or the combinations of the
protein-surface interactions and the unfolding of protein molecules. Thus, in order to
clarify the adhesion interactions in the force curves we have integrated the adhesion
works from each detected adhesion force curves.
Item The overall work of pulling off BSA from
mica surface (aJ)
The overall adhesion work of pulling off BSA from
polystyrene surface (aJ)
1 0.25 ± 0.02 1.08 ± 0.24
2 0.29 ± 0.04 2.19 ± 0.35
3 0.60 ± 0.01 2.43 ± 0.32
4 0.30 ± 0.01 1.80 ± 0.05
5 0.20 ± 0.05 1.51 ± 0.04
6 0.34 ± 0.04 0.84 ± 0.04
7 0.31 ± 0.06 4.06 ± 0.08
8 0.48 ± 0.02 0.68 ± 0.02
9 0.34 ± 0.02 2.67 ± 0.07
10 1.23 ± 0.05
11 1.20 ± 0.02
12 1.09 ± 0.01
13 0.71 ± 0.02
Mean 0.35 1.65
Standard deviation 0.12 0.97
Table 6: The table shows the overall work for pulling BSA off the mica surface and the overall work for pulling BSA off the polystyrene.
56
In table 6 the overall (Wmica and Wpolystyrene) work required to pull BSA molecules off
the surface has been integrated from each force curves and obtained the mean values
by KaleidaGraph, Synergy Sofeware. Also, for calculating the relative errors of each
adhesion work value we calculated the difference between the integral for the original
data and the integral for the data which was actually the moving average of the
original data over 5 points. The relative errors of each BSA-mica adhesion work are
in the range of 3 % ~ 25 % of each original BSA-mica adhesion work data, and the
relative errors of each BSA-polystyrene adhesion work are in the range of 1 % ~ 22 %
of each original BSA-polystyrene adhesion work data.
In figure 22 the mean and standard deviation of Wmica are 0.35 ± 0.12 aJ, and the third
Wmica and the eighth Wmica are larger than the mean Wmica. This is because the third
Wmica and the eighth Wmica may not only include the energy of pulling BSA off the
mica surface, but also including the energy of detaching BSA from the AFM tip. The
mean and standard deviation of Wpolystyrene are 1.65 ± 0.97 aJ. Because the AFM tip
could be unfolding the BSA molecules, the seventh Wpolystyrene in figure 22 is twice
the mean Wpolystyrene and probably includes the conformational energy of BSA
molecules. The ninth Wpolystyrene is also larger than the mean Wpolystyrene, which could
be also due to the combination energy of BSA-polystyrene interactions and
BSA-AFM tip. Figure 22 shows the mean Wpolystyrene is obviously larger than the
mean Wmica, which also demonstrates that on polystyrene surface the AFM tip needs
larger energy to pull off BSA molecules due to the hydrophobic interactions. This
result is also consistent with the results of the adhesion forces of BSA-mica and
BSA-polystyrene.
57
Figure 22: The comparison of adhesion works between BSA-mica and BSA-polystyrene.
Generally, our AFM technique provides us to compare the protein adhesions with two
different surfaces in a simple and direct way. The results have also proved that by
using our AFM technique we are able to investigate protein adhesion force
measurements without damaging the natural elastic property of protein molecules, and
it is an advantage over other AFM techniques described in the section of previous
research. Nevertheless, our AFM technique still has the disadvantages which need to
improve. For example, because the AFM cantilevers we chose have the low spring
constants, during the protein adhesion force measurements the softer AFM cantilever
may be too sensitive in aqueous solution and detect the needless interactions. Also, if
0
1
2
3
4
0 2 4 6 8 10 12 14
BSA-mica adhesion work
Relative error Mean BSA-mica adhesion work Mean-standard deviation (BSA-mica) Mean+standard deviation (BSA-mica)
BSA-PS adhesion work Relative error Mean BSA-PS adhesion work Mean-standard deviation (BSA-PS) Mean+standard deviation (BSA-PS)
Counts
58
we can blunt our sharp AFM tip, it may be able to measure the protein-surface
interactions more easily because of the stronger protein attachment onto a blunt AFM
tip than onto a sharp AFM tip within the adhesion force measurements.
59
6. Conclusion
Protein adsorption plays a significant role in determining the nature of the
tissue-implant interface, because the adsorbed proteins can importantly affect
biomaterial surface properties. For decades many researchers have dedicated to
discover the protein adsorption action with different surface, but no surface analysis
techniques such as SFA can observe the real-time protein interactions with the
different desired substrate surfaces in liquid environment at nano scale until the AFM
was invented in 1986. The AFM not only can provide the atomic resolution surface
image, but also offer the ability that can measure the interaction forces between
particles. Hence, we have used the AFM outstanding advantage to develop the AFM
technique that can measure the interactions between proteins and the surface.
The AFM technique we have established allows obtaining the direct measurements of
the interactions between protein and surfaces and consists of three main parts. At first,
in order to obtain more precise results of the AFM force measurements we have used
the method of Sader et al. (1999) to calibrate the AFM cantilever spring constant.
Secondly, in the force spectroscopy mode of NT-MDT SMENA head the AFM allows
us to obtain the relationships between the protein molecules and the surface properties
by using the AFM tip to pick up proteins from the surface. Thirdly, we convert the
AFM cantilever deflection signal (amplitude) curves to the force (nN) curves by using
the equation 9.
In this work, we selected the same proteins (BSA) adsorbed onto mica (hydrophilic)
and polystyrene (hydrophobic). The results show that BSA molecules prefer to adsorb
onto polystyrene surface than mica surface, and they are also consistent to the
60
previous observations (Castner, D. G. & Ratner, B. D., 2002) that hydrophobic
surfaces promote protein adhesion but hydrophilic surfaces do not. Consequently, the
AFM technique we have developed allow to measure and compare directly the
adhesions between proteins and different surfaces without any modification to the
substrate or to the AFM tip; this means we can keep the nature elastic property of
protein molecules during force measurements.
61
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Appendix A – The AFM force curves of BSA-mica in PBS
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure A1: The adhesion force curves of BSA and mica
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure A2: The adhesion force curves of BSA and mica
67
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure A3: The adhesion force curves of BSA and mica
-0.1
-0.05
0
0.05
0.1
0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure A4: The adhesion force curves of BSA and mica
68
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure A5: The adhesion force curves of BSA and mica
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure A6: The adhesion force curves of BSA and mica
69
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure A7: The adhesion force curves of BSA and mica
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure A8: The adhesion force curves of BSA and mica
70
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure A9: The adhesion force curves of BSA and mica
71
Appendix B– The AFM force curves of BSA-polystyrene in PBS
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure B1: The adhesion force curves of BSA and polystyrene
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80 100
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure B2: The adhesion force curves of BSA and polystyrene
72
-0.1
-0.05
0
0.05
0.1
0 40 80 120 160
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure B3: The adhesion force curves of BSA and polystyrene
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80 100
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure B4: The adhesion force curves of BSA and polystyrene
73
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure B5: The adhesion force curves of BSA and polystyrene
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80 100
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure B6: The adhesion force curves of BSA and polystyrene
74
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80 100 120 140
Tip approach (nN)Tip retract (nN)
Displacement (nm)
Figure B7: The adhesion force curves of BSA and polystyrene
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80 100 120
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure B8: The adhesion force curves of BSA and polystyrene
75
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80 100 120 140
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure B9: The adhesion force curves of BSA and polystyrene
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure B10: The adhesion force curves of BSA and polystyrene
76
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure B11: The adhesion force curves of BSA and polystyrene
-0.1
-0.05
0
0.05
0.1
-10 0 10 20 30 40 50 60
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure B12: The adhesion force curves of BSA and polystyrene
77
-0.1
-0.05
0
0.05
0.1
-20 -10 0 10 20 30 40 50 60
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure B13: The adhesion force curves of BSA and polystyrene
78
Appendix C – The bare mica force curves in PBS and the bare polystyrene force curves in PBS
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure C1: no interactions were observed from the bare mica surface.
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure C2: no interactions were observed from the bare mica surface.
79
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
TIp approach (nN)Tip retract (nN)
Displacement (nm) Figure C3: no interactions were observed from the bare PS surface.
-0.1
-0.05
0
0.05
0.1
-20 0 20 40 60 80
Tip approach (nN)Tip retract (nN)
Displacement (nm) Figure C4: no interactions were observed from the bare PS surface.
80
Appendix D – Data, SEM images and details of the calibration procedure for the two cantilevers.
Cantilever A
10 resonance curves of cantilever A were obtained and showed in Appendix A. Figure
D1 is one of the resonance curves of the cantilever A and has been fitted by the
Gaussian equation. After fitting the Gaussian equation to those 10 resonance
frequency curves, the average value of the resonance frequency (fc) is 13.246 which
obtained from the 10 values of the resonance frequency, and the error (standard
deviation) can be also calculated (Table D1 shows those values).
Figure D1: One of resonance curves of cantilever A is fitted by Gaussian equation
0
0.5
1
1.5
2
10 15 20 Frequency (kHz)
y = A0+A1*exp(-(x-f0)2/σσσσ2
Error Value 0.0079 0.3281 A0 0.036 0.842 A1 0.025 13.261 f0 0.037 0.723 σσσσ
3.342 Chisq 0.859 R
• Amplitude
−−−− Gaussian fitted
13.261
81
The table D1 shows the values of the resonance frequency and the Q factor from the
10 resonance frequency curves of cantilever A. The Q factor values can be calculated
by the equation 6 from those 10 resonance frequency curves. The average value of Q
factor (Qf) is 12.048 and the error (standard deviation) is 2.531.
Resonance Frequency
(kHz) Q Factor
1 13.259 9.545
2 13.234 15.868
3 13.215 15.864
4 13.257 9.945
5 13.246 14.017
6 13.235 10.639
7 13.307 10.324
8 13.261 10.660
9 13.209 9.289
10 13.240 11.917
Average 13.246±0.027 12.048±2.531
Table D1: The resonance frequency values and the Q factor values were obtained and calculated from the 10 resonance frequency curves of cantilever A.
In order to measure the length and width of the cantilever A the SEM image of
cantilever A was taken (Fig. D2). The measured length (L) and width (b) of the
cantilever A are 342.8µm and 40.0µm, respectively. The errors (∆∆∆∆L and ∆∆∆∆b) can be
calculated by equation 7a and equation 7b.
82
Figure D2: The SEM image of cantilever A.
Since
b = 40.0µm
L = 342.8µm
Qf = 12.048
fc = 13.246 kHz
We have applied those four values to Sader’s method (Equation 5) and obtained the
spring constant of the cantilever A (kz = 0.0257 N/m). The error of the spring constant
of the cantilever A (∆∆∆∆kz) is 0.0061 can be calculated by the equation 8. Where
∆∆∆∆b = 0.3µm
∆∆∆∆L = 2.8µm
∆∆∆∆Qf = 2.531
∆∆∆∆fc = 0.027 kHz
AFM
cantilever A
83
Cantilever B
In order to measure the length and width of the cantilever B the SEM image of
cantilever A was taken (Fig. D3). The measured length (L) and width (b) of the
cantilever A are 347.1µm and 35.3µm, respectively. The errors (∆∆∆∆L and ∆∆∆∆b) can be
calculated by equation 7a and equation 7b.
Figure D3: The SEM image of cantilever B.
10 resonance curves of cantilever B were also obtained and showed in Appendix A.
Figure D4 is one of the resonance curves of the cantilever B and has been fitted by the
Gaussian equation. After fitting the Gaussian equation to those 10 resonance
frequency curves, the average value of the resonance frequency (fc) is 12.896 which
obtained from the 10 values of the resonance frequency, and the error (standard
deviation) can be also calculated (Table D2 shows those values).
AFM
cantilever B
84
Figure D4: One of resonance curves of cantilever A is fitted by Gaussian equation
The table D2 shows the values of the resonance frequency and the Q factor from the
10 resonance frequency curves of cantilever A. The Q factor values can be calculated
by the equation 6 from those 10 resonance frequency curves. The average value of Q
factor (Qf) is 13.22 and the error (standard deviation) is 2.873.
0.2
0.4
0.6
0.8
1
1.2
1.4
1.6
6 8 10 12 14 16 18 20
Frequency (kHz)
y = A0+A1*exp(-(x-f0)2/σσσσ2222
Error Value 0.0077 0.3879 A0 0.039 0.694 A1 0.028 12.878 f0 0.041 0.619 σσσσ
3.294 Chisq 0.796 R
• Amplitude
−−−− Gaussian fitted
12.878
85
Resonance Frequency
(kHz) Q Factor
1 12.885 9.739
2 13.046 14.227
3 12.841 13.912
4 12.757 12.757
5 12.892 10.916
6 12.878 12.371
7 12.901 14.287
8 12.929 8.251
9 12.853 18.520
10 12.971 14.380
Average 12.896±0.077 13.22±2.873
Table D2: The resonance frequency values and the Q factor values were obtained and calculated from the 10 resonance frequency curves of cantilever B.
Since
b = 35.3µm
L = 347.1µm
Qf = 13.22
fc = 12.896 kHz
We have applied those four values to Sader’s method (Equation 5) and obtained the
spring constant of the cantilever A (kz = 0.0257 N/m).
86
The error of the spring constant of the cantilever A (∆∆∆∆kz) is 0.0062 can be calculated
by the equation 8. Where
∆∆∆∆b = 0.2µm
∆∆∆∆L = 2.7µm
∆∆∆∆Qf = 2.873
∆∆∆∆fc = 0.077 kHz