ISRN Computational Biology

Volume 2013, Article ID 436267, 5 pages

http://dx.doi.org/10.1155/2013/436267

## Propagation of Nonlinear Pressure Waves in Blood

Theoretical Physics Group, Faculty of Science, Mansoura University, Mansoura 35516, Egypt

Received 2 June 2013; Accepted 11 July 2013

Academic Editors: B. Vasiev and Z. Yu

Copyright © 2013 A. Elgarayhi 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.

#### Abstract

The propagation of weakly nonlinear pressure waves in a fluid-filled elastic tube has been investigated. The reductive perturbation method has been employed to derive the Korteweg-de Vries equation for small but finite amplitude. The effect of the final inner radius of the tube on the basic properties of the soliton wave was discussed. Moreover, the conditions of stability and the soliton existence via the potential and the corresponding phase portrait were computed. The applicability of the present investigation to flow problems in arteries is discussed.

#### 1. Introduction

The intermittent ejection of blood from the left ventricle produces pressure waves that flow in the arterial tree. Experimental data found that the flow velocity in blood vessels largely depends on the elastic properties of the vessel wall and they propagate towards the periphery with a characteristic diagram [1]. In arterial mechanics, the propagation of pressure waves in fluid-filled distensible tubes has been theoretically studied by several researchers [2–4]. Experimental observation for the simultaneous changes in amplitude of the pressure waves at five sites from the ascending aorta to the saphenous artery in dogs showed that the pulsatile character of the blood is soliton waves [5]. Yomosa [6] investigated the nonlinear propagation of solitary waves in large blood vessels. He found that the pulse waves of pressure and flow propagating through the arteries can be described as solitary waves excited by cardiac ejections of blood, and the features of the pulse wave such as “peaking” and “steepening” are interpreted in the viewpoint of soliton. Later, R. M. Shoucri and M. M. Shoucri studied the application of the method of characteristics of shock waves in models of blood flow in the Aorta [7]. Recently, Gaik and Demiray [8] treated the arteries as an incompressible prestressed thin walled elastic tube with a stenosis and the blood as a Newtonian fluid with variable viscosity, which vanishes on the arterial wall, and it takes the maximum value at the center of the artery. They studied the propagation of weakly nonlinear waves in the long wave approximation by the use of the perturbation methods [9]. Many authors examined the stability and the soliton existence condition via the potential and the corresponding phase portrait [10–12]. Elwakil et al. [10] studied the propagation of solitary electron acoustic waves in unmagnetized collisionless plasma. They found that, there are saddle and two-center equilibrium state in the phase plane and there is two-finite separatrix going from a saddle returning to it in the phase portrait. The evolution of small but finite-amplitude propagating solitary structures was studied the by means of Korteweg-de Vries equation (KdV). Many authors have been using the KdV equation to study the properties of solitary waves [13, 14]. The major topic of this work is to study the propagation of pressure waves in weakly nonlinear waves in a fluid-filled elastic tube. This paper is organized as follows: in Section 2, we present the basic set of fluid equations governing our model. In Section 3, long wave approximation is used to drive KdV equation, and the solution for KdV equation is obtained. In Section 4, some discussions and conclusions are given.

#### 2. Basic Equations

To drive the equation of motion of the tube, let us consider a circular cylindrical long tube of radiuswith a uniform inner pressure , let the axial stretch ratioandbe the radius of the cylindrical tube after such a finite static deformation. The position vector of a generic point of the tube may be described by the following: where andare a finite time dependent radial displacement, unit base vectors in the cylindrical polar coordinates, the spatial coordinate in the intermediate configuration and the axial coordinate of a point in the undeformed configuration, respectively. The axial displacement is neglected in view of the external tethering. The unit tangent vectorto the meridional curve and the unit exterior normal vector to the deformed membrane are given by whereis defined by

The stretches in the axial and circumferential directions may be given as follows: whereis the stretch ratio in the circumferential direction after finite static deformation.

Let and be the membrane forces acting along each unit length of the meridional and circumferential curves of the tube, respectively. The equation of motion of the tube in the radial direction is given by whereis the shear modulus of the tube material,is the strain energy density function,is the initial tube thickness,is the fluid pressure, andis the mass density of the tube material. In order to complete the field equations one must know the value of the fluid pressure. Therefore, (5) is to be complemented with the equations governing the blood fluid. Blood is known to be an incompressible non-Newtonian fluid. The main factor for blood to behave like a non-Newtonian fluid is the deformability of red blood cells and the level of cell concentration (hematocrit ratio). When blood flows in arteries the red cells move to the central region of the artery and, thus, the hematocrit ratio is reduced near the arterial wall, where the shear rate is quite high, as can be seen from Poiseuille flow. In other words, experimental observations indicate that when the shear rate is high, blood behaves like a Newtonian fluid. The ratio of the viscous terms to the nonlinear term is consideringand. Therefore, the viscous effect in comparison to the nonlinear effect can be neglected. Based on these observations, we assume that blood is an incompressible inviscid fluid whose equations of axially symmetrical motion in the cylindrical polar coordinates are given by whereare the fluid velocity components in the radial and axial directions, respectively,is the mass density of the fluid, andis the fluid pressure function. These field equations must satisfy the following boundary conditions:

Hereis the fluid pressure function,is the fluid mass density, andis the final inner radius of the tube. whereis the stretch ratio in the circumferential direction after the finite static deformation, where from (5) it is obtained that

In general, the strain energy densityis a function ofand. For our purposes, we shall assume thatis analytic inandand can be expanded into power series of the following form: where the coefficients,…,are defined by

Equations (6)–(9) give sufficient relations to determine the unknowns and .

#### 3. Long Wave Approximation

The reductive perturbation method is used to study the propagation of small but finite amplitude. Let us introduce the following types of stretched coordinates [15]: whereis a small parameter measuring the smallness of nonlinearity, dissipation, and dispersion,is the phase velocity in the longwave approximation to be determined later. All physical quantities appearing in (6) and (7) are expanded as power series in about their equilibrium values as:

We impose the boundary conditions as follows:

Substituting (11) and (12) into (6) and (9) and equating coefficients of like powers of. Then, from the lowest-order equations in the following results are obtained:

And the boundary conditions can be written as follows:

From the solution of the sets (14) and (15) we obtain that where is an unknown function whose governing equation will be obtained later andis the phase velocity in the longwave approximation.

Considering now the coefficients of, we derive with the aid of (16) the following set of equations

And the boundary conditions can be written as follows

From (17-a) we have

Eliminating the second order perturbed quantitiesand the desired KdV equation is obtained as follows: where the coefficientsandare defined by Our system can support two kinds of potential structure depending on the sign of the coefficient of the nonlinear term (). A stationary solitary wave solution of the KdV equation can be obtained by transforming the space variable to whereis velocity of the wave. This has been done by imposing the boundary conditions for localized perturbations, namely, , , and for . Thus, the steady state solution of (22) can be expressed as where the soliton amplitudeand the soliton widthare given by

#### 4. Numerical Results and Discussion

The weakly nonlinear pressure waves in a fluid-filled elastic tube have been investigated. To make our result physically relevant, numerical studies have been made using parameters close to those values corresponding to actual biologically relevant parameters for experimental data in dogs [6, 16]. The effect of the final inner radius of the tubeon the basic properties of the amplitude and width of the soliton is shown in Figure 1. It is obvious that the magnitude of the soliton amplitude and width increases with. From (20), the nonlinear equation of motion can be obtained as

This equation can be regarded as an “energy integral” of an oscillating particle of unit mass, with a velocityand positionin a potential

The kinetic energy of oscillating particle is shown in Figure 2. A necessary condition for the existence of the solitary waves is thatfor. A value of predicts the formation of a shock wave. The potential and the corresponding phase portrait are shown in Figure 3. Stable solitons will exist when; otherwise stable solitons will not be present. The application of our model might be particularly interesting in the new observations for the biological experimental data.

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