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i
ELECTROKINETIC TRANSPORT WITH TEMPERATURE AND SOLUTAL GRADIENT
Thesis submitted in partial fulfillment of the requirements for the award of the degree
of
Master of Technology in
Mechanical Engineering
(Thermal Sciences and Engineering)
by
Arka Prabha Roy Roll no. 07ME3203
Under the guidance of
Prof. Suman Chakraborty
DEPARTMENT OF MECHANICAL ENGINEERING INDIAN INSTITUTE OF TECHNOLOGY, KHARAGPUR
MAY 2012
ii
CERTIFICATE
This is to certify that the thesis entitled Electrokinetic Transport with Temperature
and Solutal Gradient, submitted by Arka Prabha Roy (Roll No. 07ME3203) in partial
fulfillment of the requirements for the degree of Master of Technology in Thermal Sciences
and Engineering in the Department of Mechanical Engineering, is a bona fide research work
carried out by him under my supervision and guidance during the year 2011-2012.
Prof. Suman Chakraborty
Department of Mechanical Engineering
Indian Institute of Technology, Kharagpur
iii
DECLARATION
I hereby declare that:
a. The work contained in this thesis is original and has been done by me under the
guidance of my supervisor.
b. The work has not been submitted to any other institute for any degree or diploma.
c. Whenever I have used materials (data, theoretical analysis figures, text) from other
sources, I have given due credit to them by citing them in the text of the thesis and
giving their details in the references.
Arka Prabha Roy Department of Mechanical Engineering
Indian Institute of Technology, Kharagpur
iv
ACKNOWLEDGEMENT
I would sincerely thank my project supervisor- Professor Suman Chakraborty for
giving me opportunity to work in this fascinating topic and for his continuous motivation.
I would also like to thank my senior Mr. Jeevanjyoti Chakraborty for guiding me in
the analytical work pertaining to computer simulations.
I pay my sincere regards to my father Mr. Nirmal Kumar Roy and my mother Mrs.
Sujata Roy, who have encouraged me and helped me to remain motivated throughout my life.
I would also like to take this opportunity to thank Pratiti and my brother, Anish for their
unfailing faith in me and for their support throughout the duration of the work.
v
ABSTRACT
Electrokinetic transport has been utilized extensively in the micro-/nano-fluidics
community and the fundamental understanding behind such transport has also been
investigated for long in the colloidal science literature. Yet, most traditional studies have
focused rather simplistically on phenomena that are intrinsically coupled in reality through
expeditious assumptions leading to modeling paradigms that are, at best, piecemeal
representations of such real problems. As such, looming questions in electrokinetic transport
coupled intricately with ancillary flow effects still do remain unanswered; these have
potentially far-reaching consequences in micro-/nano-fluidics. The present thesis addresses
two such coupled phenomena with the critical role of osmotic pressure in establishing the
concerted interplay (between the fluid dynamics and the temperature and/or the
concentration) acting as the common refrain in both.
In the first example problem, a non isothermal electro-osmotic fluid flow has been
considered for a micro-confinement filled with a binary electrolyte. We have incorporated
the effect of the induced thermo electric field due to the temperature gradient with the
traditional electrokinetic flow in a microchannel to study the changes in the ionic species
distribution and the velocity profile. In the process we have shown that the deposition of the
ionic species on the charged surface is altered in an uneven way. We have found that the
velocity profile for a non-uniform temperature distribution significantly varies from the
isothermal condition. The discrepancy also depends heavily on the characteristics of the ions
and the zeta potential of the wall surfaces.
In the second example problem, a novel transport mechanism which we term
“induced diffusioosmosis” is brought about through imposition of a zeta potential gradient as
a clear departure from the established norm of actuating diffusioosmotic flow through
imposed concentration gradients. Since under conditions of electric double layer (EDL)
overlap, the channel centre-line concentration is a function of the zeta potential, it is the
gradient of the zeta potential which induces a gradient in concentration implicitly. It is this
latter induced concentration gradient which results in the diffusioosmotic flow. The induced
diffusioosmotic flow is computed as a function of the gradients of zeta potential at the walls
vi
of the channel, the concentration of the electrolyte solution and reservoir concentration. It is
revealed that for thick EDLs, the fluid velocity increases with increasing magnitudes of the
zeta potential and increasing reservoir concentration. As a concrete proof of concept we also
show that the diffusioosmotic flow vanishes when the gradient in the zeta potential is set to
zero.
vii
LIST OF SYMBOLS
Zeta Potential
Debye Length
Induced Potential in medium
u
u
v
E
T1(x)
T2(x)
0T
e
Applied Potential
Velocity vector
Horizontal velocity component
Vertical velocity component
Electric field acting in the system
Temperature at the top wall surface
Temperature at the bottom wall surface
Reference temperature at the inlet
Charge density
i
E
Electrochemical potential of i-th species
Electronic charge
z
Valency of positive / negative species
n
n
J
D
Number density of positive / negative species
Total number density of both ions
Current of the positive/ negative species
Einstein diffusion coefficient for positive/ negative species
viii
Q
Bk
T
r
0
P
F
0P
Pc
k
H
L
w
U
To
0
Ionic heat of transport of positive/negative species
Boltzmann constant
Temperature
Dielectric permittivity of water
Relative dielectric permittivity
Permittivity of vacuum
Pressure
Effective body force
Osmotic pressure
Density of fluid
Specific heat of fluid
Thermal conductivity of fluid
Viscosity of fluid
Viscous dissipation
Electrical conductivity of the fluid
Microchannel height
x– extent of the microchannel
Microchannel width
Entry velocity
Ambient temperature
Applied voltage at entry
ix
Re
x
y
n
T
u
v
P
n
n0
1A
2A
3A
4A
B
1C
2C
3C
4C
Reynolds number
Dimensionless x co-ordinate
Dimensionless y co-ordinate
Dimensionless positive/ negative ion density number
Dimensionless induced potential
Dimensionless potential
Dimensionless temperature
Dimensionless horizontal velocity component
Dimensionless vertical velocity component
Dimensionless pressure
Normal unit vector
Ion concentration at both entry and exit of microchannel
0/ Bez k T
0/ BQ k T
0 0/ Bez k T
/UH D
20 /ezn H
1/ Re
20 0 /Bn k T U
20 /zen U
20 0 /zen U
x
1D
2D
3D
a
b
C
0p
h
L
2H
LR
C
x
Pe
m
F
R
Vref
/ Pk C UH
0/ PU C HT
20/ PC UHT
Temperature gradient at the top wall surface
Temperature gradient at the bottom wall surface
Ratio of the ionic heat of transports
Centreline potential
Centreline pressure
Nanochannel half height
Length of the nanochannel
Reservoir height
Reservoir length
Dimensionless centreline potential
Dimensionless axial electric field
x-derivative
Chacarteristic diffusion coefficient
Peclet number
Ionic mobility of positive/ negative ion
Faraday constant
Universal gas constant
Reference velocity
xi
A
S
ind
/ refzFC h V
/refV h D
/zF RT
2 /zFCh
Surface Area
Dimensionless induced potential at left reservoir boundary
Slope of zeta potential on the top wall surface
xii
LIST OF FIGURES
Fig. 1.1 Formation of EDL close to the charged surface and the variation of the potential field within the same.
Fig. 3.1 Schematic representation of the Temperature Gradient problem
Fig. 4.1 Schematic Diagram of the slit nanochannel
Fig. 5.1.1(a) Ion Number Distribution along the cross section at x = 0.7 for = 10,
0T T = 0.12, = -50mV and 0 = 25mV
Fig. 5.1.1(b) Induced Potential Distribution along the cross section at x = 0.7 for = 10,
0T T = 0.12, = -50mV and 0 = 25mV
Fig. 5.1.2 Horizontal Velocity profile ( u ) at x = 0.7 for = 10, 0T T = 0.12, = -
50mV and 0 = 25mV
Fig 5.1.3 Variation of Ion Number Density Differences 0( )wn n on the wall with
0T T
Fig 5.1.4 Profiles of axial velocity ( u ) for = 1, 10 and 25 for constant 0T T = 0.12
Fig. 5.1.5 Variation of axial velocity ( u ) with 0T T for = 10 and 0 = 25m
Fig. 5.1.6 Variation of axial velocity ( u ) with 0T T for = 10 and 0 = 50mV
Fig. 5.2.1(a) Concentration of the positive (c+ ) and negative (c-− ) ions along the x- axis for diffusioosmotic problem
Fig. 5.2.1(b) Induced electric potential along the x-axis for diffusioosmotic problem
Fig. 5.2.2 Variation of the horizontal velocity component along the axial direction of the nanochannel with different gradients ( 0 , 0.6 and 1.2 ) of wall surface zeta potential with fixed ion concentrations ( / 1c C ) at the reservoirs
Fig. 5.2.3 Variation of the horizontal velocity component along the axial direction of the nanochannel with different reservoir concentrations ( / 1c C , / 1.5c C and
xiii
/ 1c C ) for constant zeta potential gradient ( 1.2 )
Fig. 5.2.4 Variation of the horizontal velocity component along the axial direction of the
nanochannel with different for the channel height to debye length
( / 1.6h , / 3.2h and / 4.8h ) for constant zeta potential gradient
( 1.2 )
xiv
CONTENTS
TITLE PAGE i
CERTIFICATE ii
DECLARATION iii
ACKNOWLEDGEMENT iv
ABSTRACT v
LIST OF SYMBOLS vii
LIST OF FIGURES xii
CONTENTS xiv
CHAPTER 1: INTRODUCTION 1
1.1 Electrical Double Layer 2
1.2 Overview of Electrokinetic Effects 3
1.3 Thermal Effects on Electroosmosis 4
1.4 Diffusioosmotic Flow 6
1.5 Objective and Outline 7
CHAPTER 2: THEORETICAL MODEL FOR THE COUPLED TRANSPORT OF IONIC
SPECIES, MOMENTUM AND HEAT 9
2.1 Concentration Distribution 9
2.2 Velocity Profile 11
2.3 Temperature Distribution 11
CHAPTER 3: INFLUENCE OF TEMPERATURE GRADIENT ON ELECTROSMOTIC
FLOW IN MICROCHANNEL 13
3.1 Mathematical Description 14
3.2 Non Dimensional Formulation 16
3.3 Boundary Conditions 17
3.4 Numerical Analysis 18
xv
CHAPTER 4: DIFFUSIOOSMOTIC FLOW INDUCED BY ZETA POTENTIAL
GRADIENT 19
4.1 Preliminaries 19
4.1.1 Semi Analytical Method 20
4.2 Fully-Coupled Model Formulation 23
4.3 Non Dimensional Formulation 25
4.4 Boundary Conditions 26
4.5 Code Validation 27
CHAPTER 5: RESULTS AND DISCUSSIONS 28
5.1 PART A: Influence of the Temperature Gradient on Electro-osmotic Flow in
Microchannel 28
5.1.1 Variation in Ion Number Density 31
5.1.2 Effect on Velocity Profile 32
5.2 PART B: Diffusioosmotic Flow Induced by Zeta Potential Gradient 35
CHAPTER 6: CONCLUSIONS AND FUTURE WORK 40
6.1 PART A: Influence of the Temperature Gradient on Electro-osmotic Flow in
Microchannel 41
6.2 PART B: Diffusioosmotic Flow Induced by Zeta Potential Gradient 42
REFERENCES 44
1
CHAPTER 1
INTRODUCTION In recent years, many researchers have focused their research on developing
micro-/nano devices to study small biological species, such as DNA, proteins, and other
molecules for bio-chemical analysis (Berg & Wessling, 2007; De Leebeeck & Sinton,
2006; Eijkel & Berg, 2005; Mukhopadhyay, 2006; Austin, 2006). In such devices one of
the primary challenges is to propel and control the fluid movement along with fluid
mixing and separation. This challenge stems from the fact that the routinely utilized
pressure-gradient- or gravity- driven mechanism in macroscopic flows cannot be trivially
scaled down to the micro-/nanoscopic regimes. The reason is simple: as dimensions scale
down, hydraulic resistances to volumetric actuation mechanisms (like pressure-gradient
or gravity) scale as the third power of the characteristic micro- or nano- dimension; thus,
necessitating impractically high values of pressure-gradient and a total uselessness of
gravity for all practical purposes. This is apparently a paradox. For, while lower
dimensions offer the practical benefits of handling lower volumes of fluid (with the
attendant benefits of lower times in fluidic assays and lower quantities of sample
required), these very same small dimensions make the traditional actuation mechanisms
largely impractical. Interestingly, the answer to this paradox lies in the scaling argument
itself: since volumetric actuation mechanisms face cubic orders of hydraulic resistance, it
is the surface actuation mechanisms which face only quadratic orders of hydraulic
resistance that might be usefully exploited with the scaling down of the characteristic
dimensions of the fluidic devices. Two very important surface effects which
fundamentally lay behind many different flavours of these surface actuation mechanisms
are surface tension and electrokinetics. Again, of all the flow manipulation techniques
which exploit surface effects, electrokinetic effects are, arguably, the most popular ones
because these offer numerous controls over the fluid flow as a consequence of the
intricate coupling between the fluid dynamics and the physico-chemical characteristics
both of the surface and of the fluid. Before launching into any discussion of electrokinetic
2
effects and of harnessing its advantages for fluid flow actuation at the micro-/nano-scale,
it is important to realize that the understanding of all electrokinetic phenomena is
contingent on an understanding of the electrical double layer. As such, we first describe
the genesis of all electrokinetic phenomena: the electrical double layer (EDL, in short) in
the following.
1.1 ELECTRICAL DOUBLE LAYER Electrolyte solutions invariably have dissolved ions (e.g., from dissolved salts or
dissociated water groups) present in them. The ions which are charged oppositely to the
charged surface are called counter-ions, and the ions which have the same charge polarity
as the surface are called co-ions. The charged surface, naturally, attracts the counter-ions
and repels the co-ions. If there were no thermal motion of the ions, the charged surface
would be perfectly shielded by a layer of counter-ions stacked against the surface.
However, ions have non-zero absolute temperature and the concomitant random thermal
motion of the ions precludes such a physical picture. What happens, then, is that a balance
is established between the electrostatic forces and the thermal interactions so that, at
equilibrium, a certain charge distribution prevails adjacent to the surface (of course, with
the predominant presence of the counter-ions in the vicinity of the surface). This charge
distribution with the predominant distribution of counter-ions together with the surface
charge is called the electrical double layer (EDL).
A schematic depicting the charge and the potential distribution associated with the
EDL is shown in Fig. 1.1. A layer of immobile counter-ions is present just next to the
charged surface. This layer is known as the compact layer or the Stern layer or the
Helmholtz layer. The thickness of this layer is about a few Angstroms and, hence, the
potential distribution within it may be assumed to be linear. From this Stern layer to the
electrically neutral bulk liquid, the ions are mobile. This layer of mobile ions beyond the
Stern layer is called the Gouy–Chapman layer or the diffuse layer of the EDL (Hunter,
1981). Besides this, there is a plane called the shear plane or surface which is considered
to be the plane at which the mobile portion of the EDL can flow past the charged surface.
The potential at the shear plane is called the zeta potential (ζ). The zeta potential is an
extremely significant parameter that may eventually dictate the necessary coupling
between electrostatics and hydrodynamics. One may characterize the span of the EDL as
3
the distance from the shear plane over which the EDL potential reduces to (1/e) times of
ζ, which is also known as the Debye length (λ).
Figure 1.1: Formation of EDL close to the charged surface and the variation of the
potential field within the same.
1.2 OVERVIEW OF ELECTROKINETIC EFFECTS
The four primary electrokinetic effects are as follows:
1. Electroosmosis: It refers to the relative movement of liquid over a stationary
charged surface, with an external electric field acting as the actuator.
2. Streaming Potential: It refers to the electric potential that is induced when a
liquid, containing ions, is driven by a pressure gradient to flow along a stationary
charged surface.
3. Electrophoresis: It refers to the movement of a charged surface (for example, that
of a charged particle) relative to a stationary liquid due to the application of an
external electric field.
4. Sedimentation Potential: It refers to the potential that is induced when a charged
particle moves relative to a stationary liquid.
It is clear from the preceding discussion that the primary electrokinetic
phenomena may be divided between those which are driven by an externally applied field
(electroosmosis and electrophoresis) and those which are driven by a flow (streaming
potential and sedimentation potential). Close in spirit with these primary electrokinetic
phenomena, as far as the fundamental dependence on the EDL goes, are:
4
Diffusioosmosis, Diffusioophoresis, Thermoosmosis, Thermophoresis and so on. While
attention to these important effects in the micro- and nano-fluidics community have only
recently started to be given (Daiguji, 2010; Fayolle, Bickel, & Würger, 2008; Keh & Ma,
2007a; Qian, Das, & Luo, 2007; Würger, 2007), the fundamentals of these have been
studied for long in the context of classical colloid science. Yet, inspite of the presence of
the extensive literature on the fundamental aspects of these various phenomena, certain
important issues pertaining to these very fundamentals still remain unresolved. For
instance, what is the effect of thermal effects on electroosmotic flow which have
traditionally been modelled under the simplifying assumption of isothermal flow
conditions? How far does the imposition of temperature gradients affect electroosmotic
flow through intricate couplings of the latter with thermoosmotic flow which may not be
negligible under these conditions? Is it not possible to establish diffusioosmotic flows in
situations where such concentration gradients are not externally imposed (as done
traditionally) but are, in turn, established as a consequence of other effects? Another
extremely important point on which the electrokinetic effects in micro- and particularly
so, in nano-fluidics depart from the classical developments of the colloidal science
literature is the breakdown of the thin-Debye-layer limit routinely invoked in the latter.
The use of the thin-Debye-layer limit relegates the hydrodynamics within the EDL to a
thin boundary layer region near the substrate, with the hydrodynamics in the outside
region influenced by the electrokinetic effects only through effective boundary conditions
stemming from the solutions of the inner boundary layer region. While the use of such
limits have successfully captured many colloidal phenomena (because, first, while
colloidal particles themselves may be small macroscopically they are still orders of
magnitude larger than typical Debye-layer thickness; second, the physical domains of
interest confining such colloidal phenomena are indeed macroscopic. It is these latter
conditions especially that are necessarily violated in micro- and nano-fludic domains. As
such, the resolution of these questions and issues has far reaching consequences in the
micro- and nano-fluidics domain; the current thesis is a humble attempt towards that
broad aim. However, before attempting to investigate these apparently sophisticated
issues it is necessary to first present the backdrops against which such profound questions
arise. In what follows, we focus, for the sake of the discussions in the ensuing chapters of
this thesis, on only a couple of these aspects.
5
1.3 THERMAL EFFECTS ON ELECTROOSMOSIS The theory behind electroosmosis is well-established, and is successfully used to
model and predict practical applications. It is important to realize that this theory is,
nevertheless, based on many simplifying assumptions – the biggest among which is the
assumption of isothermal flow conditions. While such an assumption does indeed
expedite the mathematical development necessary for achieving a decent understanding
of the physical picture, it does remain far from complete. Also, these ideal isothermal
conditions are extremely hard to realize in practice. Pertinently, however, there might
indeed be advantages to actually impose external thermal gradients to bring about fine-
tuned control over analyte distributions that often accompany electroosmotic flow. In
these latter cases, isothermal idealizations of electroosmotic flow are fundamentally
wrong, and are essentially incapable of capturing the entire physical picture. There have
been some efforts to address these issues in recent times: foremost, among which has
been the through the incorporation of Joule heating effects which invariably accompany
electro-osmotic flow because of the passage of an electric current under the application of
an electric field (Xuan, 2008; Xuan, Xu, Sinton, & Li, 2004). Considerable research has
also been done to study the heat transfer characteristics on various forms of electrokinetic
flow. However, most of these models are again not devoid of simplifications and
assumptions. The most striking simplifying assumption is that the electrokinetic flow
velocity, which is inherently dependent on the ionic distribution, is independent of the
temperature, when this ionic distribution itself is actually dependent on the temperature.
Moreover, the temperature gradients generated as a result of Joule heating may also
induce local gradients in conductivity, permittivity, density and viscosity. These are
together categorized under electrothermal effects which may lead to net forces acting on
the liquid. For example, conductivity gradients produce free volumetric charges and
Coulombic forces, while gradients in the permittivity lead to dielectric forces
(Chakraborty, 2008). Closely associated with the fluid forces originating due to
electrothermal effects is the phenomenon of thermoosmosis. It refers to the actuation of
fluid motion due to gradients in osmotic pressure which are induced due to gradients in
temperature. Thermoosmosis will take place irrespective of the mechanism in which the
thermal gradients are generated. Thus, in the absence of any other actuator like pressure-
gradient or electrical field, the sole application of a temperature gradient may also lead to
the actuation of fluid motion through the phenomenon of thermoosmosis.
6
Another phenomenon which is a direct consequence of the presence of thermal
gradients in a solution containing ions is the generation of a thermoelectric field (Würger,
2008). Indeed, when a temperature gradient is imposed on a solution containing free ions,
these migrate (Soret Effect)(Fayolle et al., 2008) so that in the stationary state, a
concentration gradient is built up. The variable degree and direction of migration of the
ions ultimately lead to the generation of an electric field. Although described, here, in a
step-by-step way, this stationary state is achieved through a transient equilibrating
mechanism where all the three effects of temperature gradient, Soret effect migration and
the inducement of an electric field develop synchronously. The electric field thus
developed is fundamentally a consequence of the imposed temperature gradient and is,
hence, referred to as the thermoelectric field.
1.4 DIFFUSIOOSMOTIC FLOW
Instead of externally applying an electric field, an electrolyte solution in a micro-
/nano-channel can also be driven by means of diffusioosmosis through the application of
gradients of solute concentration. Like the well-known electroosmosis phenomenon,
diffusioosmosis originates from electrostatic interaction between the electrolyte and the
charged solid surface that is in contact with the electrolyte solution. The concept of
diffusioosmosis is mainly based on difference in ion concentrations along the channel
axial direction. Due to the presence of the concentration gradient, electrolyte ions diffuse
in the nanochannel, accompanied by a net diffusive flux of charge when the mobilities of
the anion and cation are not equal. As a result, an electric field is induced that
compensates for the net diffusive flux of charge across the nanochannel. The induced
electric field, through its action on the counter-ions accumulated in the EDL, creates a
body force that, in turn, induces fluid motion. In contrast to the electroosmotic flow
driven by an externally applied electric field, the fluid motion due to the electroosmotic
effect in diffusioosmosis phenomenon is driven by the induced electric field in the
absence of an externally applied electric field. Therefore, it is obvious to note that both
electroosmosis and diffusioosmosis fall into the same category of surface-driven
phenomena that take advantage of the increase of surface to volume ratio (Ajdari &
Bocquet, 2006).
Previously researchers have studied diffusioosmotic flows near plane surfaces and
capillary tubes with uniform zeta potential along the wall surfaces (Keh & Ma, 2007a). In
7
addition, most analysis of diffusioosmotic flows has been subjected to several restrictions,
such as a thin EDL (Lowell, 1984; Prieve, 1952), low zeta potential consideration along
the wall (Keh & Wu, 2001a), and neglected effects of the ionic concentration
distributions and the induced local electric field .
1.5 OBJECTIVE AND OUTLINE Traditionally electrokinetic transport in microfluidics is studied under isothermal
conditions and with no concentration gradient in the flow direction. The corresponding
implications in electroosmotic flow and flows mediated by streaming potential are well
studied and documented in the literature (Andrade, 1980; Chakraborty & Das, 2008; Das
& Chakraborty, 2009; Yariv, Schnitzer, & Frankel, 2011). There also exists some related
literature on heat transfer effects on electrokinetic transport. However, in those works, the
electrochemical transport is decoupled from the energy equation and averaged
temperature in the Poisson-Boltzmann formalism is employed to represent the
consequences of ionic species transport. This approximation, although practical for
several problems, suffers from some fundamental shortcomings. The primary
shortcoming stems from the fact that gradients in temperature introduce additional
gradients in the number density of the ionic species leading to an EDL potential profile
that may significantly deviate from a Poisson-Boltzmann picture hypothesized in terms of
an equivalent temperature. In addition, the gradients in the system are likely to introduce
osmotic pressure gradients which can influence the flow characteristics. Thus, the
scenario can be more appropriately assessed by a coupled consideration of Poisson-
Nernst-Planck-Navier-Stokes-Energy equations (PNPNST) which is a consideration yet
to be invoked in the literature.
Interestingly, electrokinetic transport may also be assessed with concentration
gradients along the intended flow direction. Such concentration gradients imposed
externally may be trivial. However, in several circumstances the concentration gradients
may be implicitly induced in the system as a combined consequence of surface charge
patterning and EDL overlap. Surface charge patterning or axial variation in zeta potential
over the surfaces is a more realistic condition than uniform wall potential and essentially
mimic the surface defects or inhomogeneity of the platform (Ghosal, 2004). Another
important point is that surface charge modulation induces longitudinal gradient in the
axial velocity, due to which a transverse velocity component is introduced. Now,
8
satisfying the flow continuity some re-circulating velocity components are generated
which forms local vortices that can enhance mixing of adjacent streams and cross stream
migration. Motivated by the observation of mixing in narrow confinements, various
researchers have considered axial variation of the interfacial potential in a controlled way
to achieve their desired functionalities (Chang & Yang, 2008; Chen & Cho, 2007, 2008;
Meisel & Ehrhard, 2006; Zhang, He, & Liu, 2006).
Importantly, subjected to the combined effect of axial gradients of zeta potential
and EDL overlap, axial gradients in the concentration of the ionic species may be
spontaneously induced in a fluidic channel. This, in turn, may give rise to a
diffusioosmotic transport, as a combined consequence of osmotic pressure gradients and
species diffusion. Although a plethora of literature has been reported on diffusioosmosis
in micro- and nano-fluidic confinements, this issue has by far been overlooked.
Aim of the present thesis, accordingly, is to assess the implications of temperature
and concentration gradients on electrokinetic transport in narrow confinements. In an
effort to delve deeper into the underlying consequences, two separate yet related
problems are investigated. The first problem analyzes electroosmosis in a narrow
confinement with imposed temperature gradients on the system. The second problem
addresses diffusioosmosis in narrow confinements as a combined consequence of axially
patterned zeta potential and EDL overlap phenomenon. The organization of the remaining
part of the thesis is as follows. In Chapter 2, a theoretical model is described to address
coupled transport of ionic species, momentum and heat. In Chapter 3, the same model is
utilized to assess the implications of heat transfer on electroosmotic transport in narrow
confinements. In Chapter 4, mathematical modelling on diffusioosmosis in presence of
implicitly induced concentration gradient due to non uniform zeta potential at the wall
surfaces is presented. In Chapter 5, some key results are presented and discussed. In
Chapter 6, conclusions are drawn from the present work and further scopes of work are
identified.
9
CHAPTER 2
THEORETICAL MODEL FOR THE COUPLED
TRANSPORT OF IONIC SPECIES, MOMENTUM AND HEAT
In this chapter we state the governing equations for fluid motion, concentration
distribution and temperature distribution. The basic equation system for the fluid motion
consists of the Continuity equation and the Navier-Stokes equation. Similarly, the
concentration distribution inside any fluidic confinement is governed by the Nernst-
Planck equation and the Poisson equation. In order to study the thermal profile we have
taken the Energy equation as well. These equations forms a coupled system that
determines the basic variables related to an electrolytic fluid motion inside a micro-
/nanochannel.
2.1 IONIC SPECIES TRANSPORT
The transport of ions in an electrolyte, in a general continuum model, is given by
the species conservation equation:
·ii
n Jt
. . . (2.1)
where in is the local concentration of the i-th ionic species, and iJ
is the flux, assuming
that there is no source term due to generation or consumption of ions by any bulk reaction
within the electrolyte. In a moderately dilute solution, the flux can be expressed in terms
of the gradient of the electrochemical potential i as
i i i i iuJ m n n . . . (2.2)
where im is the mobility and u is the mean fluid velocity. It is important to understand
that while the first term on the RHS subsumes within it ion transport due to both diffusion
and electro-migration it is not a truly generally representation of concentration multi-
10
component transport because it does not include any inter-species interactions other than
those between a particular diffusing species and the solvent. In the dilute solution limit,
however, the electrochemical potential i may be conveniently decomposed as,
lni B i ik T n z e . . . (2.3)
where is the electric potential, iz is the ionic valence and e is the electronic charge. The
Nernst-Einstein relation i B iD k Tm expresses the diffusivity, iD , in terms of the mobility.
In this limit, the traditional expression of the flux popularly used to address
electrochemical transport problems is recovered:
ii i i i i
B
z eJ D n n n uk T
. . . (2.4)
Considering, henceforth, the electrolyte to be a binary one with symmetric valencies of
the cations (+) and anions (-), the flux expression becomes
B
z eJ D n n n uk T
. . . (2.5)
Now this expression is valid only when there is no thermal inhomogeneity in the system.
But if there is a thermal gradient present, then because of the enhanced solute-solvent
interaction the particle velocity modifies and becomes a function of the temperature
gradient (Fayolle et al., 2008; Rasuli & Golestanian, 2008; Würger, 2007, 2008).
Previously it has been studied for charged colloids that, how the particle velocity is
affected due to the manifestation of salinity gradient caused by the Soret effect of the
mobile ions in the system (Würger, 2008). In order to incorporate the alteration of the
concentration distribution due to the temperature variation, the current of each mobile ion
is taken as directly proportional to the local thermal gradient. So, to consider the effect of
the diffusion and advection in a non isothermal condition the flux per unit area of an ionic
species is taken as a function of the potential gradient as well as the temperature gradient
and local fluid velocity. Thus, the current of the charged species can be written
respectively as,
2B B
Q z eJ D n n T n n uk T k T
. . . (2.6)
11
where, first term in the R.H.S refers to the normal diffusion with Einstein Coefficient D ,
second term comprises the thermal diffusion with the Ionic Heat of Transport *Q , third
term denotes the drift caused by total potential gradient and the last term is due to the
advection by the fluid flow.
Assuming steady state, the modified Nernst-Planck equation for the charged
species is given by
0J
. . . (2.7)
According to the theory of electrostatics, due to the variation of the charged
species number density the potential distribution is governed by the Poisson Equation
(near the wall surface), written as
.( ) e . . . (2.8)
where, ( )e ez n n is the charge density assuming z z z , consists of the
relative dielectric permittivity ( r ) and permittivity of vacuum ( 0 ) such that o r .
2.2 VELOCITY PROFILE
The fluid velocity and pressure are governed by the continuity and momentum
equation for incompressible fluids,
0u
. . . (2.9) 2u u P u F
. . . (2.10)
where, P is the hydrostatic pressure of the fluid and F
is the body force density that
consists contributions from the osmotic pressure ( 0 BP nk T ) and the potential gradient.
Thus F
can be represented as:
B eF k n T T n
. . . (2.11)
where n is the total number density of the mobile ions and is denoted by n n n .
2.3 TEMPERATURE DISTRIBUTION As the developed thermo-electric field induces the thermo-osmotic flow in the
entire two dimensional space, the electric current passing through results in Joule Heating
(Ruckenstein, 1981). So, the general Energy equation in steady condition takes the form:
2
Pu T k T Ec . . . (2.12)
12
where, Pc and k are the specific heat and thermal conductivity of the fluid, and are
the fluid density and viscosity, respectively, all are assumed to be constant. The last term
is due to the joule heating. is the viscous dissipation term and expressed as, 2 22
2 2u v u vy x x y
. . . (2.13)
It is important to note that the presented system of equations is intricately coupled
and non-linear in nature. There does exist previous instances in the literature where such
coupled Poisson-Nernst-Planck (PNP) equations together with the Navier-Stokes (N-S)
equations have been fully considered; however, none of them have considered the
thermoelectric effect as done here. Additionally, the explicit consideration of the osmotic
pressure contribution to the body force term in the momentum equation imparts a hitherto
unaddressed coupling among the N-S, the PNP equations and the energy equation. While
such an intricate set of equations precludes any analytical tractability, it does free up the
analysis, albeit numerical, from any restrictive regimes ensuing from the simplifying
assumptions that have to be otherwise invoked. For the sake of nomenclature, we call this
the coupled Poisson-Nernst-Planck-Navier-Stokes-Energy (PNPNST) system. The
numerical resolution of this PNPNST system is achieved through the commercial Finite
Element package COMSOL Multiphysics.
13
CHAPTER 3
INFLUENCE OF TEMPERATURE GRADIENT ON ELECTROOSMOTIC FLOW IN MICROCHANNEL
In the present chapter we want to study the effect that the application of an
imposed temperature gradient has on the flow physics (inside a micro-channel) of a fluid
which is basically an aqueous solution of ions, together with the consideration of the
surface charging effects leading to the establishment of an Electric Double Layer (EDL),
which is driven by a combined pressure and potential gradient. The application of a
temperature gradient leads to fluid flow as described earlier following electrothermal
effects and the phenomenon of thermoosmosis. Concomitantly, the surface charging
effects due to the interaction of the confining surface with the aqueous solution of ions
lead to the establishment of an EDL through the equilibration of Coulombic and entropic
interactions. But, contrary to simple isothermal condition such EDL distribution may not
be simply described through the Boltzmann distribution. Indeed, in our case, gradients of
temperature (and, hence, of thermo-physical quantities) exist. But for simplicity, the
gradients of thermo-physical quantities are neglected. Simultaneously, the imposition of a
temperature gradient tends to establish a thermoelectric field. The establishment of the
EDL, or more generally, a concentration gradient depends on this developed
thermoelectric field. Conversely, the thermoelectric field itself is dependent on the
concentration field. Thus, in this situation, we have a rich and coupled interplay between
the imposed temperature gradient, the induced gradients of ionic distribution, and the
induced thermoelectric field. The temperature gradient and concentration gradient
changes the osmotic pressure in the fluid flow. The developed thermoelectric field
determines the effective body force in the fluid flow. So, we can see that the coupled
parameters have a direct impact on determining the fluid flow.
14
3.1 MATHEMATICAL DESCRIPTION As a physical system we consider a parallel plate microchannel of height H, length
L and width w, with w>>H, L. In this problem, E
is the total electric field developed
due to the combined influence of the external electric field, the thermoelectric field and
the EDL distribution (so that, E
). The two parallel plate surfaces possess
unequal temperature profile with different temperature gradients. The temperature profile
at the bottom surface and top surfaces are taken as T1(x) and T2(x) respectively. It is
assumed that the left end of the domain is at constant temperature, such
that 1 2 0(0) (0)T T T . In Fig. 3.1, the schematic diagram is shown; origin is taken at the
bottom surface of the left boundary.
Figure 3.1: Schematic representation of the present problem
As explained earlier the distribution of these ions in the stationary state will be a
consequence of the coupled equilibrating influences of the EDL, induced thermoelectric
field and applied electric field. This is like a two way coupling process where the
temperature driven migration of the ions originates a thermoelectric field which
eventually again re-distributes the ion distribution in the non-uniformly charged fluidic
system. In this case, the Poisson equation (for induced potential) and Laplace equation
(for applied electric field) should be solved simultaneously with the species continuity
and the energy equation to get the ionic species distribution and the overall potential
distribution. The Navier-Stokes momentum equations and continuity equation are solved
with the above mentioned equations in a coupled way to determine the velocity field.
15
Here, the theoretical concept from the previous chapter is used to analyze the
intricate electro osmotic flow. Due to the axially applied electric field is modifications are
done in the terms consisting of the potential gradients. Now the current of the charged
specie can be expressed as,
2B B
Q z eJ D n n T n n uk T k T
. . . (3.1)
where, the third term denotes the drift caused by total electric field.
Assuming steady state, the modified Nernst Planck equation for the charged
species is given by
0J
. . . (3.2)
According to the theory of electrostatics, due to the variation of the charged
species number density the potential distribution is governed by the Poisson Equation
(near the wall surface), written as
.( )o r e . . . (3.3)
The fluid velocity and pressure are governed by the continuity and momentum
equation for incompressible fluids,
0u
. . . (3.4) 2u u P u F
. . . (3.5)
where, F
is the body force density that consists effects of the osmotic pressure
( 0 BP nk T ) and the total potential gradient. Thus F
can be represented as
( )B eF k n T T n
. . . (3.6)
As the developed thermo-electric field induces the thermo-osmotic flow in the
entire two dimensional domain, the electric current passing through results in Joule
Heating. So, the general Energy equation in steady condition takes the form
2
Pu T k T Ec
. . . (3.7)
where, is the viscous dissipation term and the last term is due to the joule heating.
As one new variable is introduced to the coupled system, so to close the system one
more equation is needed. The potential developed, due to the externally applied electric
field, inside the channel satisfies the Laplace Equation, given by 2 0 . . . (3.8)
16
3.2 NON DIMENSIONAL FORMULATION The governing equations are rewritten in dimensionless form using the
characteristic parameters of the system: the channel height H , the inlet ionic number
density 0n , the wall zeta potential , the applied voltage 0 , the ambient temperature 0T
and the entry velocityU . The hydrostatic pressure is non-dimensionalised by 2U . Thus
the new dimensionless variables become:
xxH
, yyH
, 0
nnn
,
, 0
, 0
TTT
, uuU
, vvU
, 2
PPU
Thus the coupled non linear equation system takes the following form.
Nernst Planck Equation:
1 2 3 42. 0Tn A A A A u nT T T
. . . (3.9)
1 2 3 42. 0Tn A A A A u nT T T
. . . (3.10)
where, 10B
ezAk T
, 20B
QAk T
, 03
0B
ezAk T
, 4UHAD
Poisson Equation:
2 B n n . . . (3.11)
where,2
0ezn HB
Laplace Equation: 2 0 . . . (3.12)
Continuity Equation:
. 0u
. . . (3.13)
Navier-Stokes Equation:
21 2 3 4u u P C u C n T T n C C
. . . (3.14)
where, 11
ReC
UH
, 0 0
2 2Bn k TC
U , 0
3 2
zenCU
, 0 0
4 2
zenCU
17
Energy Equation: 2
21 2 3u T D T D D E
. . . (3.15)
where, 1P
kDC UH
, 20P
UDC HT
,
2
30P
DC UHT
3.3 BOUNDARY CONDITIONS We consider the left boundary of the domain as an equi-potential and an
isothermal surface with the 0 and 0T as the respective values. As boundary conditions on
the entry side we take both the ion number densities as constant and equal to 0n . There is
no induced potential on the left and right side of the channel. We have previously used
the inlet horizontal velocity as the reference velocity. Thus, at 0x we have, 1 , 1n , 1u , 0v , 1T , 0 . . . (3.16)
On the outlet boundary the pressure and the potential is taken as zero. We used the
convection boundary condition for the temperature and concentration field. Thus at
Lx LH
we get,
0 , n 0J
, 0P , 0Tx
, 0 . . . (3.17)
where, n is the unit vector along the normal to the surface. At all channel wall surfaces no
slip and no penetration boundary condition is applied for the flow field. It is considered
that both the positive and negative ions on reaching the solid wall surface do not give up
their electric charge or in any way do not react with the surface so that the ion flux normal
to the surface (relative to the surface) must be zero (Cox, 1997). Both the walls are
assumed to be at fixed zeta potential. There is no potential gradient along the normal to
the wall surface for the applied electric field. Moreover, the temperature gradient on the
top surface is considered to be less compare to the bottom wall surface. So, on the top
surface ( 1y ) we have,
0y
, n 0J n u
, 0u , 1 1T T ax , 1 . . . (3.18)
and on the bottom surface ( 0y ) the boundary conditions look like,
18
0y
, n 0J n u
, 0u , 2 1T T bx , 1 . . . (3.19)
where, a b .
3.4 NUMERICAL ANALYSIS
The numerical simulation is done by the commercial finite-element-method
software COMSOL Multiphysics 3.5 and the post-processing is performed by writing
scripts in Matlab 2007. The most significant changes of the variable parameters occur
near both the wall surfaces. So to study the variation of the flow field with respect to the
characteristics variable it is necessary to have a fine discretization mesh near the channel
wall. The size ratio of the triangular mesh used near the wall boundary and subdomain
space is almost five times smaller.
At first the numerical simulation is done using some practical values for the
variable parameters considering the non isothermal condition. Then the variation of the
ion number density and velocity profile is studied for various temperature gradient and
combinations of ionic heat of transports.
19
CHAPTER 4
DIFFUSIOOSMOTIC FLOW INDUCED BY ZETA
POTENTIAL GRADIENT
The basic premise for bringing about diffusioosmosis is the existence of an axial
concentration gradient. While traditional implementations of diffusioosmosis have been
solely realized through externally imposed concentration gradients it is important to
understand that there is no fundamental requirement on how such a gradient is
established; thus, diffusioosmotic flow might very well be actuated through an induced
gradient. Here in this chapter, we have described such a method for inducing the axial
concentration gradient which, in turn, induces a diffusioosmotic flow. Generally, the zeta
potential at the channel walls is taken as constant as the surface charge at the solid walls
is uniform. But, if we consider a gradient in zeta potential along the channel walls in the
axial direction, then due to the non uniform electrostatic interaction, a concentration
gradient is created in the axial direction for both the co-ions and counter ions.
Importantly, this is of significance only when the EDL penetrates sufficiently into the
bulk, that is, under conditions in which EDL overlap exist whence the channel centre-line
concentration is different from the bulk reservoir values. Notably, under these conditions,
the channel centre-line potential gets manifested as function of the surface charging
condition (expressed through the zeta potential). Due to the presence of the concentration
gradient, electrolyte ions diffuse in the nanochannel, accompanied by a net diffusive flux
of charge when the mobilities of the anions and cations are not equal. As a result, an
electric field is induced that compensates for the net diffusive flux of charge across the
nanochannel. The induced electric field, through its action on the counter-ions
accumulated in the EDL, creates a body force that, in turn, induces fluid motion. 4.1 PRELIMINARIES
Diffusioosmosis has been extensively studied through simplified mathematical
models by Keh and co-workers (Hsu & Keh, 2009; Keh & Hsu, 2007, 2009; Keh & Ma,
20
2004, 2005, 2007b, 2008; Keh & Wei, 2002a, 2002b; Keh & Wu, 2001b; Ma & Keh,
2005, 2006, 2007; Wei & Keh, 2003a, 2003b; Wu & Keh, 2003). In these models, the
ionic concentration of each species is described by the Boltzmann distribution and the
electrical potential is then described by the commonly used Poisson–Boltzmann model.
Consequently, the electrostatics and hydrodynamics are decoupled. However, the
Boltzmann distribution is strictly valid under the following assumptions: (i) the system is
in equilibrium (i.e., no convection and diffusion); (ii) the channel wall has a
homogeneous surface charge; and (iii) the charged surface is in contact with an infinitely
large liquid medium where the potential is zero and the ionic concentration is the same as
that of the bulk solution (Li, 2004). Inspite of these assumptions, these simplified models
are useful in obtaining physical insights into the problems. As such, in what follows, we
first develop a similar simplified model based, particularly on the work of Keh and Ma
(2006), discuss a possible algorithm to resolve the one-way coupled equations and then
move on to a model based on the fully-coupled set of equations, following Qian et al.
(2007).
4.1.1 Semi Analytical Method We consider diffusioosmostic flow induced by the interplay of zeta potential
gradient and EDL overlap in a channel of height 2h and length L connecting two
reservoirs having electrolyte with concentration n . Here, a simplified semi-analytical
model for the determination of the axial velocity is described. The major assumption
behind this model is that Poisson-Boltzmann equation is valid and 1D flow is considered.
This scheme considers an iterative way of solving the momentum equations to predict the
velocity distribution. In the first step the pressure distribution is calculated from the y
momentum equation in a 1D approach and then using the pressure we find the axial
velocity profile from the x momentum equation. In the following discussion, number
density ( n and n ) is considered instead of the molar concentration to specify the
concentration of the ionic specie. Here the centreline potential is taken as C and
centreline potential as 0p . Here the non dimensional parameters are taken in a slightly
different manner as, , ,B
ez x yx yk T L H
Now writing the y momentum equation, neglecting the transverse velocity, we get
21
0dze n ny dp
y
. . . (4.1)
From the literature we get the local number density as a function of the reservoir ionic
concentration ( n ) and the absolute temperature (T ) (Baldessari & Santiago, 2008). So
the above equation becomes
0Bdn k T e edy
py
. . . (4.2)
Solving the equation by integrating and using the centreline condition
as, 0y , 0 , Cp p , we get the final expression of pressure as,
0 2 cosh cosh CBp p n k T . . . (4.3)
Now let us look at the x momentum equation with an electrical body force based on the
axial electric field ( E )
2
2
u p ez n n Ey x
. . . (4.4)
Differentiating the pressure term, obtained from the previous expression, with respect to x
and substituting it, we get
2
2 2 sinh sinh 2 sinhCC
du dn ez n ez Ey dx dx
. . . (4.5)
Integrating the above equation, using the symmetric boundary condition ( 0 at 0u yy
)
at channel centreline and no slip boundary condition ( 0 at u y H ) at the wall, we
obtain
0
2 sinh sinh sinhy y C
CH
ddu n ez E dydydx dx
. . . (4.6)
Now we have expressed the axial velocity as an integral function of some non
dimensionalised parameter, as following,
2
1 0
2 sinh sinh sinhy y CB
Cref
dk Tn H du dydyV L dx dx
. . . (4.7)
where, denotes the non dimensional axial electric field, such that, B
ezELk T
.
We have obtained the functional value of from the local zero current condition, i.e, it is
considered that the current density of the positive and negative ions are same at every
22
point inside the domain. This is a necessary simplification which was very much needed
to solve . So considering J J and writing the axial component only, we get
x x x xB B
B B
ez ezD n D n D n D n n n uk T k T
ez ezD n E D n Ek T k T
. . . (4.8)
Substituting the values for u , and n n in the above equation the expression for E is
found.
2 sinh 11 1
ref BV k TuE
D eze e
. . . (4.9)
where D DD D
.
Finally the expression for is obtained by using the above expression,
2 sinh1 1
uPe
e e
. . . (4.10)
where
2
refV LPe
D D
This scheme has some major simplifications, but it can be used to determine the
nature of an approximate velocity profile. At first, a guess value of zero is taken for
and using that value, the distribution of u is determined from equation (4.5). Then from
equation (4.10), the induced axial electric field is predicted and it is modified from the
initial guess, which is further used to determine the u profile. In this iterative manner the
procedure is done until the difference of consecutive iteration values exceeds a certain
minimum tolerance value. This is a good approach to study the velocity profile in an
analytical way considering 1D approach and Poisson Boltzmann approximation.
However, as already mentioned, the Boltzmann distribution is not valid in our case. The
flow field affects the mass transport due to convection. On the other hand, the mass
transport, in turn, affects the flow field through the induced electric field. The model
requires one to simultaneously solve the coupled equations including the Navier-Stokes
equations, the Nernst–Planck equation, and the Poisson equation. This intricately coupled
model is described in detail in the subsequent section.
23
4.2 FULLY-COUPLED MODEL FORMULATION Let us consider a charged slit nanochannel with length L and height 2h connecting
two identical reservoirs on either side. The schematic is depicted in Fig. 4.1(Qian et al.,
2007). The length and height of the reservoir are respectively LR and 2H. Utilizing the
symmetry of the geometry, a two dimensional Cartesian co-ordinate system (x, y) with
origin located at the centre of the nanochannel is represented. The x and y coordinates are,
respectively, parallel and perpendicular to the axis of the nanochannel. The symmetrical
model geometry is represented by the region bounded by the outer boundary and the line
of symmetry, AB. The dashed line segments, BC, CD, GH, and HA, represent the regions
in the reservoirs. The length LR and height 2H of the reservoir are sufficiently large to
ensure that the electrochemical properties at the locations of BC, CD, GH, and HA are not
influenced by the nanochannel.
Figure 4.1: Schematic Diagram of the slit nanochannel
We consider that the walls of the two reservoirs (line segments DE and FG) are
electrically neutral surfaces and the channel wall surfaces have a horizontally varying zeta
potential. The left and right reservoirs are filled with two identical electrolyte solutions
with same bulk concentration, C, so that there is no imposed concentration gradient along
the x-direction. We also assume that there is no externally applied pressure gradient and
horizontal electric field across the two reservoirs. In the following sections, we present
dimensional mathematical models and the non dimensional formulation for the fluid
motion and ionic concentration distribution through the nanochannel.
A
Virat Kohli is always involved in wonderful chases.
B
H G
F E
D C
h
L
H
LR LR
x y
24
We assume a binary, symmetric electrolyte solution enclosed in the nanometer
channel between the two reservoirs. Due to the low Reynolds number of the fluid flow,
we neglect the inertial forces in the Navier-Stokes equation. So, the motion of the
incompressible solution due to the pressure gradient and electrical body force created as
the effect of the induced concentration gradient is described by the modified Stokes
equation,
u 0 . . . (4.11) 2u ( ) 0p F z c z c . . . (4.12)
In the above, ˆ ˆu i ju v is the fluid velocity, where i and j are respectively the unit
vectors in the x- and y-directions; u and v are respectively the velocity components in the
x- and y-directions; p is the pressure; is the electric potential in the electrolyte
solution; c and c are, respectively, the molar concentrations of the positive and negative
ions in the electrolyte solution; z and z are respectively the valences of the positive and
negative ions satisfying the relation z z z ; F is the Faraday Constant; and is the
dynamic viscosity. The last term of the left hand side describes the electrostatic force
through the net charge density and induced electric field. The concentration distribution of the solution inside the nanochannel can be found
out by solving the bi-ion mass transport model that includes the Nernst–Planck equation
for the concentration of each ionic species and the Poisson equation for the electric
potential in the electrolyte solution. The flux density of each aqueous species is given by
(Qian et al., 2007),
N uc D c z m Fc . . . (4.13)
In the above, c denotes the respective ion molar concentration; D is the respective ion
Diffusion coefficient; z is the respective ion valence; and m is the respective ion
mobility. The three terms in the right hand side of the equation denotes the convective,
diffusive and migratory fluxes respectively. The mobility m is expressed in terms of the
diffusivity D , the universal gas constant R , and the absolute temperatureT using the
Nernst–Einstein relation as following,
DmRT
. . . (4.14)
25
Thus the ionic concentration distribution, at the steady state, can be solved using
the Nernst Planck equation,
N 0 . . . (4.15)
In the above equation there are three unknowns; the +ve and –ve ion concentrations
c and c respectively and the potential . We can find the potential using the Poisson
equation: 2 ( )Fz c c . . . (4.16)
where, is the permittivity of the electrolyte solution.
4.3 NON DIMENSIONAL FORMULATION
The governing equations are rewritten in dimensionless form using the
characteristic parameters of the system: the nanochannel height h , the ion concentration at
the reservoirsC and the wall zeta potential .The velocity components are non-
dimensionalised by a reference velocity refV and the pressure by refVh
. So the new
dimensionless variables become:
xxh
, yyh
, ccC
, ccC
,
, ref
uuV
, ref
vvV
, ref
ppVh
Thus the coupled non linear equation system takes the following form:
Continuity Equation:
.u 0 . . . (4.17)
Navier Stokes equation:
2u 0p c c . . . (4.18)
Nernst Planck equation:
. u 0c c . . . (4.19)
. u 0c c . . . (4.20)
Poisson equation:
2 c c . . . (4.21)
26
In the above equations, some non dimensional coefficients appeared which depend on the
characteristic physical values. These are as following:
A=ref
zFC hV
, refV hD
, refV hD
, zFRT ,
2zFCh
4.4 BOUNDARY CONDITIONS
A no-slip boundary condition (i.e., 0u v ) is used at the wall surfaces of the
nanochannel and the reservoirs (line segments DE, EF and FG in Fig. 2). At the planes
BC and AH of the reservoirs, normal pressure equals to zero is specified, since there is no
externally applied pressure gradient across the two reservoirs. Slip boundary conditions
are used on the segments CD and GH, since they are far away from the entrances of the
nanochannel. Finally, a symmetric boundary condition is used along the line of
symmetry, AB.
In the plane BC and AH, the concentrations of the positive and negative ions are
the same as the bulk concentration C of the electrolyte solution present in the two
reservoirs. At the walls of the reservoirs and the wall of the nanochannel (line segments
DE, EF and FG in Fig.1), the net ion fluxes normal to the rigid walls are zero as the wall
surfaces are impervious to ions. Zero normal flux is used for the segments CD and GH, as
these surfaces are in the bulk electrolyte reservoirs. Along the segment AB, symmetric
boundary condition is used. Thus the boundary conditions for the Nernst–Planck
equations are as following:
1c c in the plane BC and AH . . . (4.22)
ˆ ˆn N n u 0c c . . . (4.23)
in the plane AB, CD, DE, EF, FG and GH
ˆ ˆn N n u 0c c . . . (4.24)
in the plane AB, CD, DE, EF, FG and GH; where, n is the outward unit normal vector.
Now, the boundary condition for the Poisson equation along the plane HA is
specified by ind , which is determined from the zero current condition (Qian et al.,
2007),
+ ˆN N nS
Fz dS
. . . (4.25)
27
Here, S is the surface area of the plane HA and the current density is denoted by,
+N Ni Fz . The condition of non-zero ionic current is valid for any cross section of
the reservoir and the nanochannel. So, in our non-dimensional scheme, the boundary
condition for the plane HA can be written as,
ind . . . (4.26)
A symmetric boundary condition is used along the plane AB. As the walls of the
reservoirs (planes DE and FG) do not carry a fixed charge and since the surfaces CD and
GH are far away from the nanochannel, no charge boundary condition is used for these
four surfaces, i.e.,
n 0 . . . (4.27)
Along the plane BC, the potential is taken as zero, i.e.,
0 . . . (4.28)
A linearly varying zeta potential is used as the boundary condition on the wall
surface EF. Thus, the potential in the plane EF looks like,
1 *( 15) / 30x . . . (4.29)
where is an arbitrary constant.
4.5 CODE VALIDATION
We solved the strongly coupled system with the commercial finite element
package COMSOL Multiphysics 3.5. The computational domain bounded by
ABCDEFGH in Fig. 4.1 was discretized into quadrilateral non-uniform elements. We
compared the solutions obtained for different mesh sizes to ensure that the numerical
solutions are convergent, independent of the size of the finite elements, and satisfy the
various conservation laws. At first we simulated the ionic mass transport in nanofluidic
channels without considering the convection (i.e., u=0), solving the set of Nernst–Planck
equations and the Poisson equation and our numerical results agree well with those
obtained from previous literature (Daiguji, 2010). Then, the numerical scheme is
validated with the results for previous study on diffusioosmotic flows in slit nanochannel
by Qian et al., 2007. As compared to their work, our model shows that a non-zero
velocity can be achieved without the externally imposed concentration gradient, just by a
linear variation in surface zeta potential value.
28
CHAPTER 5
RESULTS AND DISCUSSION
In this chapter, some key results are mentioned from the numerical simulations of
the two example problems described in the previous chapters. In Part A, the variation in
the ion number density and the effect on axial velocity profile due to the applied
temperature gradient on the wall surfaces is discussed. In Part B, the induced
diffusioosmotic flow inside a nanochannel due to the gradient in wall surface zeta
potential is explained.
5.1 PART A: Influence of the Temperature Gradient on Electro-osmotic Flow in Microchannel
The geometrical domain for the numerical calculation is taken as a rectangular
channel, with height ( H ) equals to 1 micron and length ( L ) ten times the height. Other
parameters with constant values are taken as the following: = -0.05 V, 0 = 25 mV, U =
0.01 mm/sec, 0n = 1×1021 per cubic meter and 0T = 300 Kelvin. The variables are non-
dimensionalised using these characteristics value and the constant physical parameter
values of , , k , PC and . Generally the ionic heat of transport of positive ions is
greater than the negative ions. Here we have defined a new non dimensional parameter
such that*
*
, considering ionic heat of transport for negative ions ( *Q ) as 8.8×10-21
Joules per ion. The temperature gradients on the wall surfaces are so chosen that the
temperature difference along the entrance and exit for the bottom wall surface is 60
degree Kelvin and for the top wall surface is 10 degree Kelvin. The focus of our analysis
is at the cross section which is at 7x . Thus the temperature difference ( T ) between
the two wall surfaces at that cross section is 35 degree Kelvin which implies 0/T T =
0.12.
29
Fig. 5.1.1(a) shows the distribution of both the opposite ions along that cross
section. In our model both the wall surfaces are considered as negatively charged, so the
positive ion density is maximum at the channel walls. This is due to the fact that
positively charged ions possess a strong affinity towards negative surface. Here the
electric double layer is thick enough to merge for the two walls. Thus in the centerline of
the channel the bulk concentration condition is not achieved. The number densities for the
opposite ions at the centre of a cross section, differs by a certain amount which implies a
non zero induced potential. It is important to note that due to the temperature gradient
created vertically along the cross section, the ion distributions are asymmetric with
respect to the centerline; the minimum ion density for the positive ions appears below the
centerline and maximum ion density for the negative ions occurs above the centerline.
The difference in temperature distribution also affects the ion number densities on the
wall surfaces. The positive ion concentration is less on the hot surface in comparison to
cold surface, although the difference of ion densities at the walls for negative ions is less
than the difference for the positive ions, which shows that the temperature field has a
larger effect on determining the positive ions’ distribution than negative ions’
distribution.
(a)
Figure 5.1.1: (a) Ion Number Distribution along the cross section at x = 0.7 for = 10,
0T T = 0.12, = -50mV and 0 = 25mV
30
(b)
Figure 5.1.1: (b) Induced Potential Distribution along the cross section at x = 0.7
for = 10, 0T T = 0.12, = -50mV and 0 = 25mV
The combined induced potential, due to the electric double layer and thermo-
electric effect, is plotted against the height of the micro-channel in Fig. 5.1.1(b). The
induced potential has a maximum value of unity at both the walls and the minimum value
is at the middle of the channel where the difference in number density is minimum for the
oppositely charged ions.
In Fig. 5.1.2, x-velocity profile is plotted along the cross section. The magnitude
of the horizontal velocity near the wall surfaces are greater compared to the value at the
middle of the channel. This can be explained by the effective electrical body force which
is huge near the wall as the positive ion concentration is more than the negative ion
concentration in this region. But, in the middle of the channel the difference between the
negative ion concentration and positive ion concentration decreases, so the effect of
osmotic pressure dominates over the electrical body force. As the osmotic pressure acts as
a positive pressure gradient for a fluid flow with charged species, thus in this case mainly
due to the influence of osmotic pressure the velocity profile goes backward and gradually
decreases and attains a local minimum near the centre of the channel. Similar to the
31
potential distribution, the cross sectional velocity profile also shows asymmetry with
respect to the centerline, which is studied in a greater detail in the later sections.
Figure 5.1.2: Horizontal Velocity profile (u ) at x = 0.7 for
= 10, 0T T = 0.12, = -50mV and 0 = 25mV
5.1.1 Variation in Ion Number Density
Now we have seen that the concentration distributions for opposite ions vary for
the same temperature gradient, which can be demonstrated by the effects of wall surface
potential and the different ionic heat of transports. The term ionic heat of transport has a
significant relevance on determining the ionic charge distribution inside the medium
because this term along with the temperature gradient incorporates the deviation from
isothermal condition. The non dimensional parameter signifies the comparison of the
effect of temperature gradient on positive ion over negative ion. If we consider the
isothermal condition on both the negatively charged wall surfaces then there will be no
difference in corresponding ion densities on the walls at a certain cross section; i.e., ion
density for positive ion on top surface and bottom surfaces are same. But for different
temperature on the wall surfaces, the ion number densities of corresponding ions vary.
Let the difference of ion number density on the wall surfaces for corresponding ions are
denoted by wn and it is non-dimensionalised by 0n . In Fig. 5.1.3, the non dimensional
32
wn (for both the ions) is plotted against the non dimensional temperature differences for
different . From the graph it is seen that 0wn n for negative ions is invariant with the
temperature variation and is almost zero, i.e. the negative ion number densities are same
on both the channel walls. But on the other hand, wn for positive ions increases (almost
linearly) with the increasing wall temperature differences; under normal conditions 0.12
is considered as the maximum achievable value of 0T T for the cross section at x = 0.7.
It is also observed that with the increment of , 0wn n increases with a steeper slope,
which reflects the greater association of positive ions with the temperature variation.
Figure 5.1.3: Variation of Ion Number Density Differences 0( )wn n on the wall with
0T T
5.1.2 Effect on Velocity Profile
The horizontal velocity component highly depends on the effective body force term
appearing in the momentum equation, which comprises of the osmotic pressure as well as
the effects of the potential gradients. Now as the ionic distribution of positive ions varies
33
with different and varying temperature difference ( T ), so it is easily understood that
the velocity profile has a direct connection with these two parameters.
Figure 5.1.4: Profiles of axial velocity ( u ) for = 1, 10 and 25
for constant 0T T = 0.12
In Fig. 5.1.4, the non dimensionalised velocity profile is plotted along the cross
section for 3 different values of , considering 0T T being 0.12. For = 1, the velocity
profile is almost symmetric with respect to the centerline. But for = 10 and = 25, we
can see the asymmetric nature of the velocity profile. The maximum velocity occurs at
y = 0.81 and its value is 1.37 (for = 25) and 1.28 (for = 10). On the other hand near
the bottom surface the velocity increases but it is less than the velocity reported near the
top surface. The non dimensional velocity magnitude at the middle of the channel is less
than unity. As increases, the positive ion concentration increases near the cold surface
than the warm surface. Considering the negative ion concentration as to be almost similar
near to the both walls, we can say that the effective body force due to the applied
potential is more near the colder surface. This account for an increasing trend of velocity
profile near the cold surface (top wall) compare to the hot surface (bottom wall).
34
Figure 5.1.5: Variation of axial velocity ( u ) with 0T T for = 10 and 0 = 25mV
In Fig. 5.1.5, the velocity profile is plotted against the channel height for 3
different values of temperature difference along the cross section. is taken as constant
and equals to 10. It shows that with increasing temperature difference the magnitude of
maximum velocity increases near the colder surface. This can be explained by the less
accumulation of positive ions towards the warm surface for an increased temperature
difference. But the local minimum for the velocity profile near the center line appears
below the centerline. One important factor determining the velocity profile is the applied
potential; if we double the value of 0 from 25 mV to 50 mV then the asymmetric nature
of velocity profile becomes more prominent. We have plotted the velocity profile
considering as 10 and 0 as 50 mV in Fig 5.1.6. In this case, minimum non
dimensional velocity in the middle of the channel goes below 0.5, which is less than half
of the value attained for 0 = 25 mV. The maximum velocity also increases and for
0T T = 0.12, u reaches almost 1.8. This shows that the channel surfaces with high zeta
potential and uneven temperature gradients can heavily influence the cross sectional
velocity profile inside a microchannel.
35
Fig. 5.1.6 Variation of axial velocity ( u ) with 0T T for = 10 and 0 = 50mV
5.2 PART B: Diffusioosmotic Flow Induced by Zeta Potential Gradient
In this section, we present some selected numerical results to highlight the key
trends of the induced diffusioosmotic flow in a slit nanochannel. In order to have a
concrete basis for comparison of our simulation results, we follow Qian et al. [ref] and
consider the following values for the various geometrical and physic-chemical
parameters, 5h nm, 150L nm, 20H nm, 30RL nm, 10C mM, 0.050 V, and
1.2 . The temperature ( 0T ) of the electrolyte solution in the nanochannel is taken as
300K. The diffusion coefficients of the ions K+ ( c ) and Cl- ( c ) are respectively,
91.95 10 m2/s and 92.03 10 m2/s.
36
(a)
(b)
Figure 5.2.1: (a) Concentration of the positive (c+ ) and negative (c-− ) ions along
the x- axis (b) Induced electric potential along the x-axis
Fig. 5.2.1(a) depicts the concentration of the positive and the negative ions along
the x-direction of the nanochannel when 1.2 . The concentration distributions are
plotted for the symmetry plane AB. Due to the influence of the negative surface potential,
the concentration of the positive (K+) ions is enhanced and the concentration of the
37
negative (Cl-) ions is reduced near the wall surface. Here the electric double layer is thick
enough so that a condition of EDL overlap is established throughout the channel length.
Thus in the centerline of the channel the concentration is different from the bulk value
(i.e. equal to that in the reservoir) that would, otherwise, have been established had there
been no EDL overlap. Furthermore, it is expected that the concentration of the positive
ions is greater than the concentration of the negative ions inside the nanochannel, which
is clearly seen in the figure. Another point to be noted is that at the steady state, along the
channel, the concentration of positive ion increases but the concentration of negative ion
decreases. It is fundamentally the establishment of these gradients, brought about solely
(and implicitly) through a gradient of the zeta potential, and without externally imposing
any differences in the concentrations, that lies at the heart of the novel transport
mechanism we address here. It is also seen, that a non-zero potential is manifested self-
consistently with the EDL overlap scenario. Fig. 5.2.1(b) shows the distribution of the
induced potential. The potential ind obtained from our numerical simulations, considering
the ionic current to be zero at any cross section, is non zero and have a finite positive
value. The non-dimensional potential increases along the +ve x-direction inside the
channel. The potential is almost zero at the two reservoirs since is no effect of the varying
zeta potential.
Figure 5.2.2: Variation of the horizontal velocity component along the axial direction of
the nanochannel with different gradients ( 0 , 0.6 and 1.2 ) of wall surface zeta
potential with fixed ion concentrations ( / 1c C ) at the reservoirs
38
Fig. 5.2.2 depicts the variation of centre-line velocity with three different values.
It is extremely important to note the case 0 denoting a constant value of the zeta
potential along the wall surface. Even with EDL overlap, the absence the zeta potential
gradient precludes the establishment of any gradient in the concentration along the
channel centre-line; as such, no (induced) diffusioosmosis is possible. In this scenario the
fluid velocity is expected to be zero which is indeed seen (bold line) in the figure. This
important case acts a concrete proof of concept of the hypothesized novel transport
mechanism. Of course, as the surface potential is varied linearly, an axial velocity does
get induced. We can see from Fig. 5.2.3, in the middle of the nanochannel, for 0.6
there is a non-dimensional axial velocity of 0.12, and which increases with the zeta
potential gradient, along the channel. For 1.2 , the enhancement in the centre-line
velocity is more pronounced; the centre-line velocity increases almost one and a half
times as the fluid moves from left reservoir to right reservoir.
Figure 5.2.3: Variation of the horizontal velocity component along the axial direction
of the nanochannel with different reservoir concentrations ( / 1c C , / 1.5c C
and / 1c C ) for constant zeta potential gradient ( 1.2 )
These studies are done for a fixed reservoir concentration of 10mM i.e.,
1c c . Since for thick EDLs the positive and negative ions possesses different
39
centerline concentration, so there is a concentration difference along the channel. For this
reason, there is always a potential gradient induced along the centre-line. It is also
noticeable that with increasing the reservoir concentration of both ions, for a fixed
gradient of zeta potential ( 1.2 ) the axial velocity increases in a non-linear way.
Now the effect of zeta potential gradient on concentration and velocity
distribution is highly dependent on the thickness of the debye length ( ). As the ratio of
height is to debye length increases, the concentration difference at the centreline
decreases and as a result the effective induced electric field is lowered. So, with
increasing channel height, for a fixed reservoir concentration and constant zeta potential
gradient, the magnitude of the axial velocity at the centre of the channel decreases. In the
previous results the debye length is 3.15 nm; obtained from the theoretical expression of
debye length, as 02 22
Bk Tn e z . From Fig. 5.2.4, we can observe that as the value of
/h increases from 1.6 to 3.2 and 4.8, the velocity magnitude gets decreased; if the
channel height increases further, the axial velocity might get lowered and eventually
becomes zero.
Figure 5.2.4: Variation of the horizontal velocity component along the axial direction of
the nanochannel with different for the channel height to debye length
( / 1.6h , / 3.2h and / 4.8h ) for constant zeta potential gradient ( 1.2 )
40
CHAPTER 6
CONCLUSIONS AND FUTURE WORK
In the present study, we have set up and investigated two model problems with the
intention of addressing some fundamental issues in electrokinetic transport especially as it
pertains to the micro-/nano-fluidics domain. As mentioned in the prefatory remarks of
this work, the motivation behind this is to contribute towards a deeper insight into
intrinsically coupled phenomena for which traditional modeling paradigms are, at best,
incomplete representations. In the two model problems, we study interesting flow
phenomena originated out of interactions between externally imposed gradients (such as
temperature gradients and zeta potential gradient) and concentration distribution together
coupled with electrical potential gradients in narrow confinements. Perhaps the most
important point to note is the critical role played by osmotic pressure gradients in
establishing the concerted interplay between the fluid dynamics influenced by electrical
potential gradients and the gradients of temperature and concentration. Interestingly, it is
the deceptively simple dependence of the osmotic pressure on temperature and
concentration that ultimately gives rise to the rich non-linear coupling, and, indeed, it this
gradient of the osmotic pressure which is the common refrain throughout both the
problems addressed. Another thematic commonality stems from the clear departure in the
models of both problems from the thin-Debye-layer limit routinely invoked in the
colloidal science literature (and to a great extent even in the microfluidics literature). The
use of such limits is predicated on the assumption that the characteristic thickness of the
EDL is orders of magnitude smaller than the characteristic physical dimensions of the
system. This justifies the relegation of the flow dynamics mediated by the physico-
chemical factors to be relegated to thin boundary layer regions. Such an artifice is perfect
from the point of view of analytical tractability achieved through the asymptotic matching
formalism. It also simplifies the analysis to a considerable extent by the representation of
the entire physics within those thin boundary layers as effective boundary conditions for
the rest of the so-called “outer region”. However, in the nano-fluidic domain, such
simplifying assumptions routinely do break down because the characteristic physical
41
dimensions indeed match the orders of the characteristic thickness of the EDL.
Appreciating this, we have, thus, kept our formulations more general. While such
relaxations come at the price of analytical tractability and necessitate the use of full-scale
numerical simulations as done in the current work, they do, however, allow the set-up of a
framework that is not constrained to work only within narrow, restrictive regimes of
interest. In the following sections, the summary of the trends obtained from the results of
the two problems based on the afore-mentioned broad modeling paradigms and
additionally incorporating full-fledged non-linear couplings are delineated. Even beyond
such sophisticated investigations, the scope of future works that may provide further
insights into certain interesting niche areas is identified.
6.1 PART A: Influence of the Temperature Gradient on Electro-osmotic Flow in Microchannel
In the first problem, the temperature dependency of the ionic species distribution
is studied in the case of fluid flow taking place inside a narrow confinement. The outcome
confirms that the accumulation of the ions on the channel surfaces depends heavily on the
temperature gradient of the wall surface along with the zeta potential. From the results
obtained for this study, considering the fact that the driving forces of the fluid flow
(external pressure gradient and electric field) are kept constant, it can be inferred that the
fluid velocity profile deviates significantly due to temperature variation inside the
domain. With increasing temperature gradient on the wall surfaces the deviation of the
cross-sectional velocity from the isothermal case is enhanced. It is seen that by applying
different temperature gradient on each wall surface, the velocity profile becomes
asymmetric with respect to the channel centerline as well. The maximum value of the
velocity profile is then identified near the less warm channel surface. It is also observed
that the deviation of the velocity profile from the isothermal case increases with high wall
surface zeta potential and high ratio of the characteristic ionic heat of transports for the
ionic species. The minimum value of the velocity is being attained at centerline, which is
almost halved when the wall surface zeta potential is doubled.
The work presented here is focused primarily on the effect of a linear temperature
gradient on the ionic distribution and velocity profile of an electro-osmotic flow. The
effect of patterned temperature distribution and non linear thermal gradient on wall
42
surfaces, on the flow physics of an electroosmotic fluid transport can be studied in the
future. Furthermore, the non isothermal electroosmotic flow for altering zeta potential can
also be investigated. This might give some idea on controlling and counter balancing the
effect of thermal gradients on transport characteristics by the imposed surface potential.
6.2 PART B: Diffusioosmotic Flow Induced by Zeta Potential Gradient
In the second problem, we test our proposed hypothesis of the novel transport
mechanism “induced diffusioosmosis” brought about through the interplay of zeta
potential gradient and EDL overlapping. The most notable feature is that despite the
absence of any of the traditional external fields, namely pressure gradient or electric field
or a concentration gradient a flow is established due to the induced concentration gradient
along the channel, in the thick EDL regime. In particular, the manifested flow field is
strongly dependent on the zeta potential gradient as well as the magnitude of the bulk
concentration in the reservoirs; the axial velocity shows an increasing trend with increase
in the zeta potential gradient and also with increase in the reservoir concentration. As it is
expected from the consideration of the basic assumption of EDL overlapping, the results
showed a decreasing magnitude of axial velocity with increasing channel height.
The comparison of normal diffusioosmotic flow due to the axially applied
concentration gradient with the induced diffusioosmotic flow due to the imposed gradient
in surface potential, on the flow parameters can be investigated. As a future assignment,
the study of induced diffusioosmotic flow for a non isothermal case can be done, which
might have more significance related to nanofluidics based experiments.
Another important point to note is that the current investigation of the
diffusioosmotic problem serves primarily as a proof of concept of the hypothesized novel
induced transport mechanism. The smooth linearly varying zeta potential utilized to
induce such diffusioosmotic transport is but only an idealization, and is extremely
difficult to realize in practice. What is practically realizable, however, is to have discrete
patches of different zeta potentials. It is intuitive to expect that when arranged in
increasing (or, decreasing) steps these patches may also induce such diffusioosmotic
transport. This problem may be addressed, in the future, as a more practical flavour of the
current one. Such investigations may be of immediate interest to experimentalists because
43
these can provide a generalized framework for design of experiments. Even from the
point of view of fundamental flow physics, this proposed future work may offer
sophisticated avenues to delve into richer fluid dynamical phenomena (with possibilities
of vortical structures) through an expected interplay between the different length scales-
with an important extra contribution being from the length scale of the zeta potential
patches.
44
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