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Abstract and Applied Analysis
Volume 2013 (2013), Article ID 858597, 13 pages
The Effect of Boundary Slip on the Transient Pulsatile Flow of a Modified Second-Grade Fluid
1Department of Mathematics and Statistics, Curtin University, Perth, WA 6845, Australia
2Department of Mathematics, Mahidol University, Faculty of Science, Bangkok 10400, Thailand
Received 20 May 2013; Accepted 9 August 2013
Academic Editor: Rasajit Bera
Copyright © 2013 N. Khajohnsaksumeth et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.
We investigate the effect of boundary slip on the transient pulsatile fluid flow through a vessel with body acceleration. The Fahraeus-Lindqvist effect, expressing the fluid behavior near the wall by the Newtonian fluid while in the core by a non-Newtonian fluid, is also taken into account. To describe the non-Newtonian behavior, we use the modified second-grade fluid model in which the viscosity and the normal stresses are represented in terms of the shear rate. The complete set of equations are then established and formulated in a dimensionless form. For a special case of the material parameter, we derive an analytical solution for the problem, while for the general case, we solve the problem numerically. Our subsequent analytical and numerical results show that the slip parameter has a very significant influence on the velocity profile and also on the convergence rate of the numerical solutions.
In this paper, we study a fluid-structure interaction problem, namely, the effect of boundary slip on the flow of a non-Newtonian fluid through microchannels. This problem has many applications, and in this paper we particularly focus on blood flow in the cardiovascular system.
For the study of blood flow in arteries, two major types of constitutive models have been used. The first type of models is based on the microcontinuum or the structured continuum theories [1–6] in which the balance laws are used to determine the characteristics of blood motion. In the other type of models, blood is considered as a suspension, and its flow is modeled by the non-Newtonian fluid mechanics. Due to the red blood cells (RBC) migration as shown experimentally, blood has been modeled as a two-stage fluid by many researchers [7–9]. The first stage is a peripheral layer which is modeled as a Newtonian viscous fluid, while the other one is a centre core which is modeled as a non-Newtonian fluid. The effect of body acceleration and pulsatile conditions were taken into account under the same problem by Majhi et al. [7, 10]. Later, Massoudi and Phuoc  used the (generalized) second-grade fluid constitutive model to describe the shear thinning and normal stress effect, and the behavior of blood flow near the wall is modeled by the Newtonian fluid model, while the behavior of the blood flow at the core is described by the second-grade fluid model.
In all of the above mentioned models, the so-called no-slip boundary condition is used; namely, the velocity of flow relative to the solid is zero on the fluid-solid interface . Although the no-slip condition is supported by many experimental results, the existence of slip of a fluid on the solid surface was also observed by many other researches [13–20]. The Navier slip condition has been used by various researchers to describe boundary slip and is a more general boundary condition, in which the fluid velocity component tangential to the solid surface, relative to the solid surface, is proportional to the shear stress on the fluid-solid interface and the slip length. The surface characteristics constant, slip length, describes the “slipperiness” of the surface. Recently, we and many other researchers have investigated various flow problems of Newtonian fluids with the traditional no-slip and the Navier slip boundary conditions [12, 20–30], and it is found that the boundary slip and the slip parameter have significant influence on the flow of Newtonian fluids through microchannels and tubes.
Motivated by the above mentioned work, we extend previous work on slip flows of Newtonian fluids [21, 22] to the case involving both Newtonian and non-Newtonian fluid flow in the flow region. The new feature and contribution of this work include establishment of the underlying boundary value problem for the problem, the derivation of an exact solution for a special case, and demonstration of the influence of the slip parameter on the flow profile and flow behavior. The rest of the paper is organized as follows. In Section 2, we present the underlying boundary value problem for the problem in dimensionless form. Then in Section 3, we derive an exact solution for a special case. In Section 4, we investigate numerically the effect of the slip parameter for the general case. Finally, a conclusion is given in Section 5.
2. Mathematical Formulation
The flow of a fluid with no thermochemical and electromagnetic effects can be described by the conservation equations of mass and linear momentum; namely, where is the density of the fluid, is the partial derivative with respect to time, is the velocity vector, is the body force vector, and is the stress tensor.
The stress tensor is related to the velocity gradient by the constitutive equations. For a modified (generalized) second-grade fluid [11, 31, 32], the constitutive equations can be expressed by where is a material parameter, is the second invariant of , is the fluid pressure, is the coefficient of viscosity, are material moduli (the normal stress coefficients), and are the kinematical tensors given by in which is and the superscript refers to matrix transposition.
For the axially symmetrical blood flow through a circular tube of radius , we can assume that , where is the axial direction and is the radial direction. Under the periodic body acceleration and a unsteady pulsatile pressure gradient [7, 10], the momentum equation in the -direction in the cylindrical polar coordinate is
The shear stress for a generalized second-grade fluid can be expressed by
The approximate periodic form of the pressure gradient generated by the heart can be described by where , and are the constant component of the pressure gradient, the amplitude of the pressure fluctuation (establishing the systolic and diastolic pressures), the circular frequency, and the frequency of pulse rate, respectively.
The body acceleration can be approximated by where is the amplitude, is the frequency, and is the lead angle of with respect to the action of the heart.
In order to completely define the problem, boundary and initial conditions are required. In this work, the Navier slip condition is applied. That is, on the solid-fluid interface , the axial fluid velocity, relative to the solid surface, is proportional to the shear stress on the interface. As the fluid layer near the wall is modeled as a Newtonian fluid in our model, the shear stress on the boundary is related to the shear strain rate by . Thus, the Navier slip condition can be written as where is the slip parameter. Moreover, we assume that the slip parameter does not change along the axial direction.
On , the symmetry condition is introduced:
On the interface between two different fluids, for continuous and smooth behavior of the velocity and shear stresses, we require
The initial conditions are set to which is essential for the numerical scheme adopted to estimate the time at which the pulsatile steady state is achieved.
To simplify the equations, we introduce the following nondimensional variables and parameters:
The boundary conditions and initial conditions, in dimensionless form, can be expressed by
3. Analytical Solution
For , the model reduces to the linear model with different viscosity in the peripheral layer and the centre core. In this case, (14) have the same form:
By the superposition principle, if , and are the solution of , respectively, for ,, and , then the complete solution of (20) is .
For , we get which has the general solution: .
For , we have
Let ; then,
Let ; we have
The general solution of (27) is where and are integration constants and and denote the zero-order Bessel functions of the first kind and the second kind, respectively.
Similarly, for , we have and the general solution is where .
Solving the above system of equations yields
To show the flow behavior and the effect of the slip parameter, we investigate the velocity profiles in the arteries with different values of the slip parameter under various different conditions. In the first example of investigation, the radius of the artery is taken as cm, and the other parameters are set to dyne/cm3, , ,,,,, and . Figure 1 shows the 3-dimensional velocity profile as a function of time and location and the 2-dimensional velocity profile as a function of time at three different radial locations for two different slip parameters (no-slip) and . The results show that boundary slip has a very dramatical effect on the fluid flow in the artery. It affects not only the magnitude of the flow velocity significantly, but also the flow pattern and velocity profile on the cross-section of the artery. For the no-slip flow , the pulsatile flow nature gradually disappears toward the arterial wall, while with boundary slip, the flow near the arterial wall also displays a pulsatile nature.
We then investigate whether the above observed flow phenomena associated with boundary slip are affected or not by the radius of the artery, and for this purpose, we consider the fluid flow through an artery with a larger radius cm. The constant pressure gradient is set to dyne/cm3 in order to achieve a mean velocity magnitude approximately equal to that in the smaller artery, while all other parameters are set to the same values as those used for the smaller radius. Figure 2 shows the velocity profile in the artery for two different slip parameter values including (no-slip) and . The 3-dimensional graph shows the variation of the flow velocity with time and radial position, while the 2-dimensional graphs demonstrate the variation of the flow velocity with time at three different radial locations including (centre), (inner-outer layers interface), and (arterial wall). From Figures 1 and 2, it is clear that the boundary slip related flow phenomena and behavior observed for the smaller artery also appear in the artery with a larger radius, and further, a more significant pulsatile nature of fluid flow is observed for the larger artery.
To further investigate the effect of the slip parameter on the velocity profile near the artery wall, we show in Figure 3 the velocity of fluid on the artery wall for four different values of the slip parameter including , 2, 4, 6, and 8. The results clearly demonstrate that the slip parameter has a very significant effect on the near-wall velocity and that the magnitude of the average wall velocity is proportional to the slip parameter.
4. Numerical Investigation
A numerical scheme, based on the finite different method, is established to solve the underlying boundary value problem for the general case , consisting of (14) and boundary condition (15)–(19). To validate the numerical technique, we apply the numerical scheme to generate a series of numerical solutions for the case and then compare the numerical results with the exact solution derived in Section 3.
Figure 4 presents the velocity profile in the small and large arteries for two different slip parameters (no-slip) and obtained by the numerical technique. The numerical errors between the exact solution and the numerical solution, , are presented in Figure 5 in which is the exact solution and is the numerical solution. The results clearly indicate that the numerical solution converges to the exact solution. This shows that a larger slip length has a lower convergence rate.
We then investigate the flow phenomena for the general case , and here we consider in the investigation. Figure 6 gives the 3D graph showing the convergence of the transient velocity field to a steady state pulsatile velocity field and also demonstrating the substantial influence of boundary slip on the steady state velocity profile in both magnitude and flow pattern. Figure 7 shows the variations of velocities with time at three arterial locations for different slip parameters and artery radii and also clearly demonstrates the significant effect of boundary slip on the flow through the artery. Figure 8 shows the variation of fluid velocity along the artery wall under different slip parameters and artery radii. The results show that as the slip parameter increases, the time required for achieving convergence results increases, and the magnitude of the average steady state velocity also increases.
In this paper, a mathematical model for the transient pulsatile flow of fluids through vessels, taking into account boundary slip and the Fahraeus-Lindqvist effect, is established. For a special case of the underlying boundary value problem, an exact solution for the velocity field has been derived in explicit form, which provides one with an exact analytical method for investigating the flow phenomena under the special case and also a mean for validating the subsequently developed numerical scheme for generating numerical results for the general case. Our analytical and numerical studies show that for the flow of fluids with the Fahraeus-Lindqvist effect, boundary slip has a very significant influence on the magnitude of the mean flow velocity and on the flow pattern and velocity profile on the cross-section. With boundary slip, the boundary layer near the wall also displays significant pulsatile flow nature. The results also show that as the boundary slip length increases, the convergence rate of numerical results to the exact solutions decreases and the time required to achieve the steady state pulsatile flow increases.
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