Mathematical Problems in EngineeringVolume 2012 (2012), Article ID 479087, 18 pagesdoi:10.1155/2012/479087

Research Article

Williamson Fluid Model for the Peristaltic Flow of Chyme in Small Intestine

Sohail Nadeem,¹ Sadaf Ashiq,¹ and Mohamed Ali²

¹Department of Mathematics, Quaid-i-Azam University, Islamabad 45320, Pakistan²Department of Mechanical Engineering, King Saud University, Riyadh 11451, Saudi Arabia

Received 21 September 2011; Revised 24 December 2011; Accepted 2 January 2012

Academic Editor: Angelo Luongo

Copyright © 2012 Sohail Nadeem 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.

Mathematical model for the peristaltic flow of chyme in small intestine along with inserted endoscope is considered. Here, chyme is treated as Williamson fluid, and the flow is considered between the annular region formed by two concentric tubes (i.e., outer tube as small intestine and inner tube as endoscope). Flow is induced by two sinusoidal peristaltic waves of different wave lengths, traveling down the intestinal wall with the same speed. The governing equations of Williamson fluid in cylindrical coordinates have been modeled. The resulting nonlinear momentum equations are simplified using long wavelength and low Reynolds number approximations. The resulting problem is solved using regular perturbation method in terms of a variant of Weissenberg number . The numerical solution of the problem is also computed by using shooting method, and comparison of results of both solutions for velocity field is presented. The expressions for axial velocity, frictional force, pressure rise, stream function, and axial pressure gradient are obtained, and the effects of various emerging parameters on the flow characteristics are illustrated graphically. Furthermore, the streamlines pattern is plotted, and it is observed that trapping occurs, and the size of the trapped bolus varies with varying embedded flow parameters.

1. Introduction

The object of this study is to investigate the flow induced by peristaltic action of chyme (treated as Williamson fluid) in small intestine with an inserted endoscope. Williamson fluid is characterized as a non-Newtonian fluid with shear thinning property (i.e., viscosity decreases with increasing rate of shear stress). Since many physiological fluids behave like a non-Newtonian fluid [1], so chyme in small intestine is assumed to behave like Williamson fluid. Peristaltic motion is one of the most characteristics fluid transport mechanism in many biological systems. It pumps the fluids against pressure rise. It involves involuntary movements of the longitudinal and circular muscles, primarily in the digestive tract but occasionally in other hollow tubes of the body, that occur in progressive wavelike contractions. The waves can be short, local reflexes or long, continuous contractions that travel the whole length of the organ, depending upon their location and what initiates their action.

In human gastrointestinal tract, the peristaltic phenomenon plays a vital role throughout the digestion and absorption of food. The small intestine is the largest part of the gastrointestinal tract and is composed of the duodenum which is about one foot long, the jejunum (5–8 feet long), and the ileum (16–20 feet long). The rhythmic muscular action of the stomach wall (peristalsis) moves the chyme (partially digested mass of food) into the duodenum, the first section of the small intestine, where it stimulates the release of secretin, a hormone that increases the flow of pancreatic juice as well as bile and intestinal juices. Nutrients are absorbed throughout the small intestine. There are blood vessels and vessels contained a fluid called lymph inside the villi. Fat-soluble vitamins and fatty acids are absorbed into the lymph system. Glucose, amino acids, water-soluble vitamins, and minerals are absorbed into the blood vessels. The blood and lymph then carry the completely digested food throughout the body [2].

The endoscope effect on peristaltic motion occurs in many medical applications. Direct visualization of interior of the hollow gastrointestinal organs is one of the most powerful diagnostic and therapeutic modalities in modern medicine. A flexible tube called an endoscope is used to view different parts of the digestive tract. The tube contains several channels along its length. The different channels are used to transmit light to the area being examined, to view the area through a camera lens (with a camera at the tip of the tube), to pump fluids or air in or out, and to pass biopsy or surgical instruments through [3]. When passed through the mouth, an endoscope can be used to examine the esophagus, the stomach, and first part of the small intestine. When passed through the anus, an endoscope can be used to examine the rectum and the entire large intestine.

After the pioneering work of Latham [4], a number of analytical, numerical and experimental studies [5–13] of peristaltic flows of different fluids have been reported under different conditions with reference to physiological and mechanical situations. Several mathematical and experimental models have been developed to understand the chyme movement aspects of peristaltic motion. But less attention has been given to its relevance with endoscope effect. Lew et al. [14] discussed the physiological significance of carrying, mixing, and compression, accompanied by peristalsis. Srivastava [15] devoted his study to observe the effects of an inserted endoscope on chyme movement in small intestine. The important studies of recent years include the investigations of Saxena and Srivastava [16, 17], L.M. Srivastava and V.P. Srivastava [18], Srivastava et al. [19], Cotton and Williams [20], and Abd El-Naby and El-Misery [21].

The aim of present investigation is to investigate the peristaltic motion of chyme, by treating it as Williamson fluid, in the small intestine with an inserted endoscope. For mathematical modeling, we consider the flow in the annular space between two concentric tubes (i.e., outer tube as small intestine and inner tube as endoscope). Moreover, the flow is induced by two sinusoidal peristaltic waves of different wave lengths, traveling along the length of the intestinal wall. The solution of the problem is calculated by two techniques: (i) analytical technique (i.e., regular perturbation method in terms of a variant of Weissenberg number ), (ii) numerical technique (i.e., shooting method). The expressions for axial velocity, frictional force, pressure rise, axial pressure gradient and stream function are obtained and the effects of various emerging parameters on the flow characteristics are illustrated graphically. Streamlines are plotted, and trapping is also discussed. Trapping is an important fluid dynamics phenomenon inherent in peristalsis. At high flow rates and occlusions, there is a region of closed stream lines in the wave frame, and thus, some fluid is found trapped within a wave of propagation. The trapped fluid mass (called bolus) is found to move with the mean speed equal to that of the wave [9].

2. Mathematical Development

We consider the flow of an incompressible, non-Newtonian fluid, bounded between small intestine (outer boundary) and inserted cylindrical endoscope (inner boundary). A physical sketch of the problem is shown in the Figure 1(a). We assume that the peristaltic wave is formed in nonperiodic rush mode composing of two sinusoidal waves of different wave lengths, traveling down the intestinal wall with the same speed . We consider the cylindrical coordinate system in the fixed frame, where - axis lies along the centerline of the tube, and is transverse to it. Also a symmetry condition is used at the centre.

(a)

(b)

Figure 1: (a) Physical sketch of the problem. (b) Comparison of numerical and perturbation solutions of axial velocity for , , and .

The geometry of the outer wall surface is described as where is the radius of the outer tube (small intestine), and are the amplitude and the wave length of first wave, and are the amplitude and the wave length of the second wave, is the propagation velocity, is the time, and is the axial coordinate.

The governing equations in the fixed frame for an incompressible Williamson fluid model [6] are given as follows: where is the pressure, and , are the respective velocity components in the radial and axial directions in the fixed frame, respectively. Further, the constitutive equation of extra shear stress tensor for Williamson fluid [22] is expressed as where is the infinite shear rate viscosity, is the zero shear rate viscosity, is characteristic time and the generalized shear rate is expressed in terms of second invariant strain tensor as, in which , and denotes the velocity vector.

We consider the case and for constitutive equation (2.3). Hence, the extra stress tensor can be written as such that

In the fixed coordinates , the flow is unsteady. It becomes steady in a wave frame moving with the same speed as the wave moves in the -direction. The transformations between the two frames are in which and are the velocities in the wave frame. The corresponding boundary conditions in the wave frame are where is the radius of the inner tube (endoscope). In order to reduce the number of variables, we introduce the following nondimensional variables: Here , , and represent the Reynolds number, Weissenberg number, and wave number, respectively. Moreover, and are nondimensional amplitudes of the waves, is the annulus aspect ratio, and represents the wave length ratio between two waves. By using (2.7) and (2.9), we get and components of the extra stress tensor take the following form:

Under the assumption of long wavelength and low Reynolds number approximations, the above equations are further reduced to Equation (2.12) shows that . Now putting expression of in (2.13) we get The corresponding nondimensional boundary conditions thus obtained are

3. Solution of the Problem

3.1. Perturbation Solution

Since (2.15) is a nonlinear equation and the exact solution may not be possible, therefore, in order to find the solution, we employ the regular perturbation method in terms of a variant of Weissenberg number . For perturbation solution, we expand and as To first order, the expressions for axial velocity and axial pressure gradient satisfying boundary conditions (2.16) directly yield where the involved quantities are defined in Appendix.

The expressions of pressure rise and the frictional forces and at the outer and inner boundaries, respectively, in their nondimensional forms, are given as where is defined through (3.3), and flow rate in dimensionless form is defined as where is flow rate in the fixed frame of reference, and is square of displacement of the walls over the length of an annulus, defined as Also in order to establish stream lines, we obtain stream function by using the following relation: which yields where the involved quantities are defined in Appendix.

3.2. Numerical Solution

Equation (2.15) is solved numerically by using shooting method [23]. The numerical result for axial velocity is compared with the perturbation result, and both results reveal a very good agreement with each other, as demonstrated in Table 1 and Figure 1(b).

Table 1: Numerical and perturbation solutions for axial velocity .

Numerical Sol.
Perturbation Sol.
Error

0.10
−1.0000
−1.0000
0.0000

0.15
−1.0284
−1.0286
0.0002

0.20
−1.0470
−1.0473
0.0003

0.25
−1.0599
−1.0601
0.0002

0.30
−1.0687
−1.0689
0.0002

0.35
−1.0745
−1.0748
0.0003

0.40
−1.078
−1.0781
0.0001

0.45
−1.0794
−1.0795
0.0001

0.50
−1.0790
−1.0790
0.0000

0.55
−1.0770
−1.0770
0.0000

0.60
−1.0734
−1.0734
0.0000

0.65
−1.0685
−1.0684
0.0001

0.70
−1.0622
−1.0622
0.0000

0.75
−1.0546
−1.0547
0.0001

0.80
−1.0461
−1.0460
0.0001

0.85
−1.0362
−1.0361
0.0001

0.90
−1.0251
−1.0252
0.0001

0.95
−1.0128
−1.0131
0.0003

1.0
−1.0000
−1.0000
0.0000

4. Graphical Results and Discussion

In this section, the graphical representations of the obtained solutions are demonstrated along with their respective explanation. The expressions for pressure rise and frictional forces are not found analytically; therefore, MATHEMATICA software is used to perform the integration in order to analyze their graphical behavior. It is also pertinent to mention that the values of all embedded flow parameters are considered to be less than 1.

Figures 2(a) to 2(d) are graphs of pressure rise versus flow rate to show the effects of different parameters on pumping rate. For peristaltic pumping, we divide the whole region into three parts. The region corresponding to and is known as the peristaltic pumping region. At is the free pumping region. And the region at and is called augmented pumping. Figure 2(a) shows that the pumping rate decreases by increasing the values of Weissenberg number , and this behavior remains the same in all three pumping regions. Figure 2(b) indicates the effect of the wavelength ratio on . Here, pressure rise decreases with an increase in peristaltic pumping region, and after a critical value of , it increases in the free and augmented pumping regions. Figure 2(c) explains the effect of the amplitude ratio on . Here, pressure rise decreases with an increase in value of in the free and peristaltic pumping region, and after a critical value of , it increases in the augmented pumping region. Figure 2(d) shows that pressure rise decreases when annulus aspect ratio increases.

(a)

(b)

(c)

(d)

Figure 2: Variation of pressure rise per wavelength for different values of (a)   with ,  ,  ,   and ,  (b)   with ,  ,  ,  , and ,  (c)   with ,  ,  ,  , and , and (d)   with ,  ,  ,  , and .

Similarly the effects of , , , and on frictional forces are plotted in Figures 3-4. Figures 3(a) to 3(d) represent the variation of the frictional force at the outer wall and Figures 4(a) to 4(d) indicate the variation of the frictional force at the inner wall with flow rate . It can be noted that the phenomena presented in these figures possess opposite character to the pressure rise for any given set of parameters. Also the graphs of both and show similar behavior when compared to their respective parameters. It is significant to mention that inner friction force attains higher magnitude than outer friction force with increasing values of any given set of parameters.

(a)

(b)

(c)

(d)

Figure 3: Variation of frictional force at the inner wall for different values of (a) with , , , , and , (b)    with , , , , and , (c) with , , and , and (d)    with , , , and .

(a)

(b)

(c)

(d)

Figure 4: Variation of frictional force at the outer wall for different values of (a)    with , , , , and , (b)   with  , , , , and , (c)   with ,, , , and , and (d)     with , , , and .

In order to discuss the effects of variation of various parameters on the axial pressure gradient , MATHEMATICA has been used for the numerical evaluation of the analytical results, and the results are graphically presented in Figures 5(a) to (5(e). In these figures, the pressure gradient distribution for various values of , , , , and is depicted. It is observed that pressure gradient increases with increasing the values of previously mentioned parameters.

(a)

(b)

(c)

(d)

(e)

Figure 5: Pressure gradient verses for different values of (a)    with , , , , and , (b)    with , , , , and , (c)   . with , , , , and , (d)    with , , , and , and (e)   with  , , , and .

The influence of various parameters on streamlines pattern is depicted in Figures 6, 7, 8, 9, 10. It is noted that trapping is observed in all these cases. Figures 6, 7, 8, 9 show that the size of trapped bolus increases for higher values of Weissenberg number , wave length ratio , and amplitude . Figure 9 exhibits the effects of radius ratio on streamlines pattern. It can be seen that the size and number of the trapped bolus increase with an increase in . However, the size and number of trapped bolus decrease with increasing values of flow rate as shown in Figure 10.

(a)

(b)

Figure 6: Streamlines pattern for (a) (b)    with , , , and .

(a)

(b)

Figure 7: Streamlines pattern for (a) (b) with , , , and .

(a)

(b)

Figure 8: Streamlines pattern for (a) (b) with , , , and .

(a)

(b)

Figure 9: Streamlines pattern for (a) (b) with , , , and .

(a)

(b)

Figure 10: Streamlines pattern for (a) (b) with , , , and .

5. Conclusion

The peristaltic flow of chyme (treated as Williamson fluid) in small intestine with an inserted endoscope is investigated. The flow is considered between annular space of small intestine and inserted endoscope and is induced by two sinusoidal peristaltic waves of different wave lengths, traveling along the length of the intestinal wall. Long wavelength and low Reynolds number approximations are used to simplify the resulting equations. The solution of the problem is calculated using analytical technique (i.e., regular perturbation method) and numerical technique (i.e., shooting method). Also results of axial velocity for both solutions are compared and found a very good agreement between them.

The performed analysis can be concluded as follows:(1)the peristaltic pumping rate decreases with increasing the values of , , , and . This shows that the effects of these parameters on the pressure rise are qualitatively similar;(2)frictional forces show an opposite behavior to that of pressure rise in peristaltic transport;(3)the inner friction force attains higher magnitude than outer friction force with increasing values of any given set of parameters.(4)Pressure gradient increases with increasing the values of all embedded parameters that is, , , , , and ;(5)an increase in radius ratio results in the increase of the size and number of trapped bolus. Also the size of trapped bolus increases for higher values of amplitude rate , Weissenberg number , and wave length ratio ;(6)moreover, it is observed that the size and number of trapping bolus decrease with increasing values of flow rate .

Appendix

The values of quantities appearing in the expressions (3.2), (3.3), and (3.4) are given as

Acknowledgments

The first and second author is thankful to higher education of Pakistan for the financial support and the third author extends his appreciation to the deanship of Scientific Research at king Saud University for funding this work through the research group Project no. RGP-VPP-080.

References

L. M. Srivastava and V. P. Srivastava, “Peristaltic transport of a non-Newtonian fluid: applications to the vas deferens and small intestine,” Annals of Biomedical Engineering, vol. 13, no. 2, pp. 137–153, 1985.

S. Keshav, The Gastrointestinal System at a Glance, Wiley-Blackwell, Malden, Mass, USA, 2003.

H. G. Beger, A. Schwarz, and U. Bergmann, “Progress in gastrointestinal tract surgery: the impact of gastrointestinal endoscopy,” Surgical Endoscopy and Other Interventional Techniques, vol. 17, no. 2, pp. 342–350, 2003.

T. W. Latham, Fluid Motion in a Peristaltic Pump, M.S. thesis, Massachusetts Institute of Technology, Cambridge, Mass, USA, 1966.

S. Srinivas and R. Gayathri, “Peristaltic transport of a Newtonian fluid in a vertical asymmetric channel with heat transfer and porous medium,” Applied Mathematics and Computation, vol. 215, no. 1, pp. 185–196, 2009.

S. Srinivas, R. Gayathri, and M. Kothandapani, “The influence of slip conditions, wall properties and heat transfer on MHD peristaltic transport,” Computer Physics Communications, vol. 180, no. 11, pp. 2115–2122, 2009.

M. Kothandapani and S. Srinivas, “Peristaltic transport of a Jeffrey fluid under the effect of magnetic field in an asymmetric channel,” International Journal of Non-Linear Mechanics, vol. 43, no. 9, pp. 915–924, 2008.

S. Srinivas and M. Kothandapani, “Peristaltic transport in an asymmetric channel with heat transfer. A note,” International Communications in Heat and Mass Transfer, vol. 35, no. 4, pp. 514–522, 2008.

A. H. Sharpio, M. Y. Jaffrin, B. R. P. Rao, and S. I. Weinberg, “Peristaltic pumping with long wavelength and low Reynolds number,” Journal of Fluid Mechanics, vol. 37, no. 4, pp. 799–825, 1969.

S. Nadeem and N. S. Akbar, “Numerical solutions of peristaltic flow of Williamson fluid with radially varying MHD in an endoscope,” International Journal for Numerical Methods in Fluids, vol. 66, no. 2, pp. 212–220, 2011.

S. Nadeem, N. S. Akbar, and M. Y. Malik, “Numerical solutions of peristaltic flow of a Newtonian fluid under the effects of magnetic field and heat transfer in a porous concentric tubes,” Zeitschrift fur Naturforschung A, vol. 65, no. 5, pp. 369–389, 2010.

S. Nadeem and N. S. Akbar, “Effects of heat transfer on the peristaltic transport of MHD Newtonian fluid with variable viscosity: application of a domain decomposition method,” Communications in Nonlinear Science and Numerical Simulation, vol. 14, pp. 3844–3855, 2009.

S. Nadeem, T. Hayat, N. S. Akbar, and M. Y. Malik, “On the influence of heat transfer in peristalsis with variable viscosity,” International Journal of Heat and Mass Transfer, vol. 52, no. 21-22, pp. 4722–4730, 2009.

H. S. Lew, Y. C. Fung, and C. B. Lowenstein, “Peristaltic carrying and mixing of chyme in the small intestine,” Journal of Biomechanics, vol. 4, no. 4, pp. 297–315, 1971.

V. P. Srivastava, “Effects of an inserted endoscope on chyme movement in small intestine—a theoretical model,” Applications and Applied Mathematics, vol. 2, no. 2, pp. 79–91, 2007.

M. Saxena and V. P. Srivastava, “Particulate suspension flow induced by sinusoidal peristaltic waves,” Japanese Journal of Applied Physics, vol. 36, no. 1 A, pp. 385–390, 1997.

V. P. Srivastava and M. Saxena, “A two-fluid model of non-Newtonian blood flow induced by peristaltic waves,” Rheologica Acta, vol. 34, no. 4, pp. 406–414, 1995.

L. M. Srivastava and V. P. Srivastava, “Peristaltic transport of blood: casson model. II,” Journal of Biomechanics, vol. 17, no. 11, pp. 821–829, 1984.

L. M. Srivastava, V. P. Srivastava, and S. N. Sinha, “Peristaltic transport of a physiological fluid: part I. Flow in non-uniform geometry,” Biorheology, vol. 20, no. 2, pp. 153–166, 1983.

P. B. Cotton and C. B. Williams, Practical Gastrointestinal Endoscopy, Oxford University Press, London, UK, 3rd edition, 1990.

A. E. H. Abd El Naby and A. E. M. El Misiery, “Effects of an endoscope and generalized Newtonian fluid on peristaltic motion,” Applied Mathematics and Computation, vol. 128, no. 1, pp. 19–35, 2002.

I. Dapra and G. Scarpi, “Perturbation solution for pulsatile flow of a non-Newtonian Williamson fluid in a rock fracture,” International Journal of Rock Mechanics and Mining Sciences, vol. 44, no. 2, pp. 271–278, 2007.

R. L. Burden and J. D. Faires, Numerical Analysis, PWS Publishing Company, Boston, Mass, USA, 5th edition, 1985.