Madhusudan Senapati | Sampada Kumar Parida*
© 2021 IIETA. This article is published by IIETA and is licensed under the CC BY 4.0 license (http://creativecommons.org/licenses/by/4.0/).
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In this study, the heat and mass transfer of the blood flow, particularly in a capillary tube having a porous lumen and permeable wall in the presence of external magnetic field are considered. The velocity, temperature and concentration of blood flow become unsteady due to the time dependence of the stretching velocity, surface temperature and surface concentration. The thermal and mass buoyancy effect on blood flow, heat transfer and mass transfer are taken into account in the presence of thermal radiation. This analysis is very much useful in the treatment of cardiovascular disorders. The equations governing the flow under some assumptions are complex in nature, but capable of presenting the realistic model of blood flow using the theory of boundary layer approximation and similarity transformation. First, the system of coupled partial differential equations (PDEs) is converted into a system of coupled ordinary differential equations (ODEs). Then the solutions are obtained by Runge-Kutta method of 4thorder with shooting technique. The effects of various parameters such as Hartman number, radiation parameter, unsteadiness parameter, permeable parameter, thermal buoyancy parameter, Prandtl number, mass buoyancy parameter, velocity slip parameter, thermal slip parameter, Schmidt number on velocity, temperature, concentration, skin friction, Nusselt number and Sherwood number are depicted through graphs. Local Sherwood number enhances because of increase in Schmidt number. Moreover, some of the important results, which are discussed in the present study and have an impact on diseases like hyperthermia, stoke and moyamoya in human body.
thermal radiation, slip flow, permeability, thermal and mass buoyancy, Runge-Kutta method
The blood flow with heat and mass transfer plays a vital role in the field of biomedical engineering and biomedical science. Blood is a fluid that transports oxygen and other essential substances throughout the human body. Blood which is a very important liquid in human limbs and that execute numerous operations like removal of carbon dioxide, transport of nutrients, removal of metabolic product, oxygen transport. Circulation of blood is classified as circulation of capillary, circulation of systemic and microcirculation. The flow of blood can be quantified by various processes such as video capillary, microscopic and laser doppler anemometry. Moreover, it plays a vital role in digestion and endocrine system functions in the body. Blood absorbs and distributes heat throughout the body to maintain homeostasis. The influence of heat and mass transfer has received a lot of attention due to various applications in human thermotherapy, cardiovascular disease, conduction process in tissues, radiation between the surface and its environment. Heat transfer in individual blood vessels for three different configurations investigated by Chato [1]. Misra and Shit [2] discussed the role of velocity slip in blood flow through stenosed arteries. Barozzi and Dumas [3] presented a study of convective heat transfer in blood vessels at the wall of the vessel numerically. They found that a more increase in the rate of heat transfer in the small vessels due to comparatively low rheological behavior of blood. Convective heat transfer of fully developed two- fluid model at the time of blood flow in small tubes with constant heat flux studied by Wang [4]. He found that the less viscous cell-free wall layers the increases the flow and promotes the heat transfer and large blood vessels can produce steep temperature gradients in heated tissues during hypothermia. Nakayama and Kuwahara [5] presented a volume averaging theory (VAT) model to derive bioheat transfer equations for blood flows and its surrounding biological tissue in a saturated porous medium. A two-phase model consists of a central core of suspended erythrocytes and a cell-free layer surrounding the core for the blood flow in a narrow tube described by Sharan and Popel [6]. Some experimental investigations on the role of blood in the presence of heat source/sink in human organs carried by Ducharme and Tikuisis [7]. The experimental study of temperature variation along artery-vein pairs in rat hind limb investigated by He et al. [8].
Due to the existence of an exterior magnetic field, blood receive paramagnetic and diamagnetic response. Haemoglobin molecule is an iron content which is the cause of creating paramagnetic response. The vessels tissue which has hydrogen, carbon atoms, oxygen, nitrogen inside it, is the cause of creating diamagnetic response. Among the three-blood cell, red blood cell is a biomagnetic element and hence chances are high that flow of blood will be affected due to the existence of exterior magnetic strength. There have been reports regarding the use of a magnetic field for the purpose of nerve regeneration, grafting bone and healing of fracture. Bearing all of these things into attention, existence of an exterior magnetic field having received some sorts of considerations in the current study. The peristaltic motion of blood flow of couple stress fluid in a non-uniform channel has an influence due to the act of exterior magnetic field discussed by Mekheimer and Al-Arabi [9]. From their study, they analysed that due to the existence of exterior magnetic field, the physical quantity pressure act as a mathematical function which increases effectively. On the other hand, for couple stress fluid parameter its behaviour is completely different. The pumping aspect of the peristaltic motion of Jeffery fluid in an inclined medium with surface wall being permeable analysed by Sreenadh et al. [10]. In the past, the flow of blood over a plate which is stretching outward has introduced by many research workers. In certain methods of medical treatment like MRI scanning, magnetic drug targeting for cancer diseases, magneto therapy, peristaltic biofluid subject to the act of exterior magnetic field is so much meaningful. The bio magnetic fluid flow over a stretching sheet discussed by both Tzirtzilakis and Tanoudis [11]. Relief from soft tissue injury and chronic pelvic pain can be obtained by the use of pulsed magnetic field. The flow of blood with radiation effect being an imperative area of analysis, due to its fruitful contribution towards biomedical science and various technique used in medical treatment, especially in the procedure of thermal therapeutic. Among all the useful techniques, infrared radiation is mostly used because it has made use of heat treatment on a distinct unit of human anatomy. When some part of the body gets overwhelmed, blood started to clot around that area, in order to rescue from healing, we generally preferred heat therapy. Infrared radiation which is a part of heat therapy directly apply heat to the blood vessel particularly to the capillary of the injured portion of the physique. In order to prevent from certain disease like muscle pain, contracture, fibromyalgia, muscle spasm the medical treatment method heat therapy seems to be very useful. Further in the treatment of disease like bursitis (which occur due to inflamed fluid presence in between skin and bone or bone and tendon or skin and tendon) technique of heat therapy played an important role. The influence of radiative heat transfer for flow of blood in a stenosed tube, particularly in a stenosed arteries line examined theoretically by Prakash and Makinde [12] subject to the action of laser irradiation, and the influence of temperature over flow of blood in breast tumour was discussed by them using numerical model. When the atmospheric temperature exceeds to 20-degree centigrade, the heat transfer will occur from skin surface by means of evaporation through the process of sweat. Also, whenever the atmospheric temperature is less than 20-degree centigrade, then the body will diffuse heat by means of conduction and radiation. The flow of blood with heat transfer by means of radiation on account of a theoretical survey discussed by both Ogulu and Bestman [13]. Some research analysts modelled a device using which the coefficient of heat convection can be measured for the endothelial surface of arteries line. Researchers like Clegg and Cracinescu [14] analysed the influence of pulsatile motion of fluid inside the arteries line by applying the medical treatment of thermal therapy. As liquid like blood conducts electricity, so its motion provides magneto hydrodynamic (MHD) flow due to the presence of an exterior magnetic field. The qualitative research in the subject of physiological fluid dynamics carried out by Misra and his group [15-18].
The mass transfer plays a vital role in the diffusion process such as mass diffusion in tissues and drug synthesis in the human body. Srinivas et al. [19] studied theoretically the unsteady MHD flow of heat and mass transfer in porous blood vessel over a permeable stretching sheet with slip conditions. Akbar [20] discussed the effect of heat and mass transfer of Prandtl fluid model in a tapered stenosis artery and found that the velocity decreases due to an increase in Prandtl fluid parameters and the maximum height of the stenosis. Ellahi et al. [21] considered the effects of heat and mass transfer on peristaltic flow of viscous fluid in a non-uniform rectangular duct. Moreover, they have studied the peristaltic motion of blood for Ree-Eyring fluid pattern under the action of exterior magnetic field influence on the heat and mass transfer.
Recently, Amiri et al. [22] have presented a 3-D numerical simulation of non-Newtonian blood flow through femoral artery bifurcation with a moderate arteriosclerosis: investigating Newtonian/non-Newtonian flow and its effects on elastic vessel walls. In the present study they have considered, a fluid structure interaction simulation of the blood flow in the femoral artery with a small occlusion. They have also accounted for unstable blood flow at the inlet specifically in leg blood vessels. The important observations in respects of hemodynamic parameters such as velocity profiles, vortices shape and pressure drops are noteworthy. Their study reveals that employing Newtonian models for blood flow does not head the promising result, particularly through occluded passage and beyond, in comparison with non –Newtonian model. The result is more relevant to blood vessels modelled as an isotropic elastic wall.
Very recently Zigta [23] has considered the effect of thermal radiation and chemical reaction MHD flow of blood in stretching permeable vessel. This topic is closer to the present analysis, irrespective of solute concentration, thermal radiation and time dependent magnetic field intensity but the study does not account for the two additional free convective body forces due to mass and thermal buoyancy affecting the flow. That become the new findings of the present analysis. Zigta [23] has observed that the temperature of the blood increases at the vessel wall as the Prandtl number and Hartman number increase. Concentration of blood decreases as Schmidt number increases.
On the basis of all the discussion Misra and Sinha [24] examined the MHD blood flow in a tube and its artery is porous and the surface is permeable. Since the velocity in stretching motion and temperature of surface are function of time so that occur the unsteadiness in the flow field and temperature field, velocity slip, thermal radiation, thermal slip condition and mass slip conditions are taken into consideration. we have interested to study the unsteady behaviour of MHD fluid flow, heat and mass transfer of blood in certain thin permeable capillary vessel which has significant use in many clinical sciences, mainly in thermal therapy. In this study, we also proposed to investigate the impact of thermal buoyancy and mass buoyancy on MHD flow of blood in a permeable capillary with stretching motion in the presence of radiation. The governing equations of the flow mechanism are streamlined under the consideration of lengthy wave length. The impact of magnetic field is also taken into consideration by the use of Ohms law. The transformed coupled PDEs are work out numerically. The influence of the embedding parameters of concern problem is interpreted using the graphs.
Unsteady flow of blood with radiation through a narrow tube with permeable surface under the action of an unsteady magnetic field B(t) which applied in a transverse direction is considered. The effect of thermal buoyancy, mass buoyancy during the flow will also considered in the analysis. Let us consider the flow is along the x-axis and y-axis is perpendicular to it. It is considered that the sheet is moving with an initial velocity $U_{w}(x, t)$ along the direction of x-axis, where the sheet and ambient temperatures are assumed as $T_{w}(x, t), T_{\infty}$ respectively. However, the concentration near the sheet and far away from it are treated as $C_{w}(x, t), C_{\infty}$. The geometry of flow model is shown in Figure 1. Since the flow of blood is MHD in nature, so that magnetic Reynolds number is very small. Therefore, the induced magnetic field is dominated by the applied magnetic field which is not considered in our present analysis. Although the flow in the system is 3-D in nature, but flow in micro vessels can be considered to be 2-dimensional in many problems. Here the flow of blood is considered as passing through a narrow porous medium with permeable surface. So, the mathematical formulation that characterises the flow of blood, heat and mass transfer phenomena under different boundary conditions for this study can be represented in the following form.
Figure 1. Geometrical interpretation of the physical problem
$\frac{\partial u}{\partial x}+\frac{\partial v}{\partial y}=0$ (1)
$\frac{\partial u}{\partial t}+u \frac{\partial u}{\partial x}+v \frac{\partial u}{\partial y}=v \frac{\partial^{2} u}{\partial y^{2}}-\frac{v}{k_{1}(t)} u-\frac{\sigma B^{2}(t)}{\rho} u$
$+g \beta\left(T-T_{\infty}\right)+g \beta^{*}\left(C-C_{\infty}\right)$ (2)
$\frac{\partial T}{\partial t}+u \frac{\partial T}{\partial x}+v \frac{\partial T}{\partial y}=\frac{k}{\rho c_{p}} \frac{\partial^{2} u}{\partial y^{2}}-\frac{1}{\rho c_{p}} \frac{\partial q_{r}}{\partial y}$ (3)
$\frac{\partial C}{\partial t}+u \frac{\partial C}{\partial x}+v \frac{\partial C}{\partial y}=D \frac{\partial^{2} C}{\partial y^{2}}$ (4)
The wall being permeable, velocity, thermal and mass slip is taken into consideration and the boundary conditions are
$u=U_{w}+N \mu \frac{\partial u}{\partial y}=U_{w}+u_{s}, T=T_{w}+K \frac{\partial T}{\partial y}=T_{w}+$$T_{s}, v=V_{w}$
$C=C_{w}+C_{s}=C_{w}+K_{1} \frac{\partial C}{\partial y},$ at $y=0$ (5)
$u \rightarrow 0, C \rightarrow \infty, T \rightarrow \infty,$ at $y \rightarrow \infty$
Wall of the capillary which is expressed by
$V_{w}=-\sqrt{\frac{U_{w} v}{x}} f(0)$ (6)
From the above equation, the flow at the surface of the tube with a velocity Vw, where Vw is positive for injection and Vw is negative for suction. Unsteady permeability parameter of blood in the capillary tube, which is a function of time being defined in Eq. (2) is $k_{1}(t)=k_{2}(1-c t) . {\text { The }}$ velocity, mass, thermal slip factor in equation (5) are $N=N_{0} \sqrt{1-c t}, K_{1}=K_{1_{0}} \sqrt{1-c t}, K=$$K_{0} \sqrt{1-c t}$ respectively. The absence of slip conditions can be evaluated by substituting $N=K_{1}=K=0$.
In order to get similarity solution, we consider the surface temperature Tw(x,t), the velocity of blood Uw(x,t), the surface mass Cw(x,t), magnetic strength at t=0 within a capillary $B(t)=\frac{B_{0}}{1-c t}$ magnetic strength at t=0 within a capillary are in the following form
$T_{w}(x, t)=T_{\infty}+\frac{b x}{1-c t}, U_{w}(x, t)=\frac{a x}{1-c t}$ $C_{w}(x, t)=\mathrm{C}+\frac{d x}{1-c t}$ and $B(t)=\frac{B_{0}}{1-c t}$ (7)
Here $b, a, c, d$ and $B_{0}$ are constants, such that $b \geq 0, a>$ $0, d \geq 0$ and $c t<1$.
With the help of Rosseland approximation, the relative heat flux is represented by
$q_{r}=-\frac{\partial T^{4}}{\partial y} \frac{4 \sigma^{*}}{3 k^{*}}$ (8)
Now let us assume that the temperature difference along the blood vessel is very negligible and by the help of expansion of Taylor series and truncating the higher order terms we have
$T^{4}=T_{\infty}^{3}\left(4 T-3 T_{\infty}\right)$ (9)
Here $T_{\infty}$ stands for ambient temperature.
The following similarity transformations with suitable choice of stream function $\psi$ are used in Eqns. (1), (2), (3) and (4),
$\begin{aligned} \theta(\eta)=\frac{T-T_{\infty}}{T_{w}-T_{\infty}}, f(\eta) &=\frac{\psi}{\sqrt{v x U_{W}}}, \phi(\eta)=\frac{C-C_{\infty}}{C_{w}-C_{\infty}} \\ \eta &=\sqrt{\frac{U_{w}}{x v}} y \end{aligned}$ (10)
where, $u=\frac{\partial \psi}{\partial y}$ and $v=-\frac{\partial \psi}{\partial x}$.
We obtained a system of coupled nonlinear ordinary differential equation
$f^{\prime \prime \prime}+f^{\prime \prime}(f-A(\eta / 2))-f^{\prime}\left(M^{2}+A+1 / k_{3}\right)-$
$f^{\prime 2}+\lambda_{1} \theta+\lambda_{2} \phi=0$ (11)
$(N r+1) \theta^{\prime \prime}+\operatorname{Pr} f \theta^{\prime}-\operatorname{Pr} f^{\prime} \theta$
$-\operatorname{APr}\left(\frac{1}{2} \eta \phi^{\prime}+\phi\right)=0$ (12)
$\phi^{\prime \prime}+\operatorname{Sc} \phi^{\prime}(f-(A / 2) \eta)-\operatorname{Sc} \phi\left(f^{\prime}+A\right)=0$ (13)
where the unknown physical quantities like $A, \operatorname{Pr}, S c, M, k_{3}, N r, \lambda_{1}$ and $\lambda_{2}$ are defined in nomenclature with their values given as follows:
$\operatorname{Pr}=\frac{\mu c_{p}}{k}, S c=\frac{D}{v}, \lambda_{1}=\frac{g \beta b(1-c t)}{a^{2}}, \lambda_{2}=\frac{g \beta^{*} d(1-c t)}{a^{2}}$
$A=\frac{c}{a}, M=B_{0} \sqrt{\frac{\sigma}{\rho a}}, k_{3}=\frac{a k_{2}}{v}, N r=\frac{16 \sigma^{*} T_{\infty}^{3}}{3 k^{*} k}$
With the help of (5), we have the transformed boundary conditions for solving equations from (11) to (13) are
$f(0)=S, f^{\prime}(0)=S_{f} f^{\prime \prime}(0)+1, \theta(0)=S_{t} \theta^{\prime}(0)+$1 and $\phi(0)=S_{m} \phi^{\prime}(0)+1$
$f^{\prime}(\eta) \rightarrow 0, \theta(\eta) \rightarrow 0, \phi(\eta) \rightarrow 0$ as $\eta \rightarrow \infty$ (14)
where, $S_{t}, S_{m}$ and $S_{f}$ stands for dimensionless thermal, mass and velocity slip factor respectively. In the above mathematical expression, the primes stand for the rate of change of dimensionless function with a corresponding change of physical variable $\eta .$ Putting $A=0$ in Eqns. (11), (12) and (13) the system of equation for unsteady problem has changed to that of steady one.
$S_{t}=K_{0} \sqrt{\frac{b}{v}}, S_{m}=K_{1_{0}} \sqrt{\frac{a}{v}}, S_{f}=N_{0} \rho \sqrt{a v}$ (15)
The behaviour of physical parameter in the fluid flow like wall shear stress, heat and mass transfer rate of interest are defined by
$C_{f}=\frac{2 \tau_{w}}{\rho U_{w}^{2}}$ (16)
where the surface wall skin friction is defined as
$\tau_{w}=\mu\left(\frac{\partial u}{\partial y}\right)_{y=0}$ (17)
and the mass flux (mw) and the heat flux (qw) at the surface wall are defined as
$q_{w}=-K\left(\frac{\partial T}{\partial y}\right)_{y=0}$ and $m_{w}=-D\left(\frac{\partial c}{\partial y}\right)_{y=0}$ (18)
Now Nux is the local Nusselt number and Shx is the local Sherwood number, which are expressed as
$N u_{x}=\frac{x q_{w}}{T_{w}-T_{\infty}}=-R e_{x}^{\frac{1}{2}} \theta^{\prime}(0)$ and
$S h_{x}=\frac{x m_{w}}{D\left(C_{w}-C_{\infty}\right)}=-R e_{x}^{\frac{1}{2}} \phi^{\prime}(0)$ (19)
where, $\mathrm{Re}_{x}^{\frac{1}{2}}=K \sqrt{\frac{x U_{W}}{v}}$ local Reynolds number.
The non-linear coupled ordinary differential Eqns. (11)-(13) along with prescribed boundary conditions (14) form a two-point BVPs. First, these equations are converted into an IVPs and then solved numerically by Runge Kutta method of order 4 with shooting technique. Let us consider
$f^{\prime}=p, q=p^{\prime}, q^{\prime}=-\left(q\left(p-A \frac{\eta}{2}\right)\right)-p\left(M^{2}+A+\right.$
$\left.\frac{1}{k_{2}}\right)-p^{2}+\lambda_{1} r+\lambda_{2} s$ (20)
$\theta^{\prime}=r, r^{\prime}$$\left.=-(\operatorname{Pr}(1+N r))\left(f r-p \theta-A\left(\frac{\eta s^{\prime}}{2}+s\right)\right)\right)$ (21)
$\phi^{\prime}=s, s^{\prime}=-(S c)\left(f-(p+A) \phi-\frac{A}{2} s\right)$ (22)
with the corresponding initial conditions are
$f(0)=S, p(0)=S_{f} q(0)+1, \theta(0)=S_{t} r(0)+1$
$\quad$ and $\phi(0)=S_{m} s(0)+1$ (23)
The initial conditions (23) are not sufficient, so$q(0), r(0)$ and $s(0)$ values are required to solve the Eqns. (20),(21) and (22) . These conditions are absent in the present problem. First, the initial values of $q(0), r(0)$ and $s(0)$ are chosen and using $4^{\text {th }}$ order Runge-Kutta method computed the values of $f^{\prime}(\eta), \theta(\eta)$ and $\phi(\eta)$ at a suitably large value of $\eta$. Again, the initial approximations are improved using Newton method to get an improved solution. Finally, the computed values of will converge to the boundary conditions $f^{\prime}(\eta)=$ $0, \theta(\eta)=0$ and $\phi(\eta)=0$. as $\eta \rightarrow \infty$. The computation has been carried out with step size $\delta \eta=0.008$. We have computed the values again the smaller value of $\delta \eta$ but that does not give any moderate change in the computed results. This indicates the accuracy, stability and convergence of our numerical technique.
Eqns. (11) (12) and (13) with the prescribed boundary conditions (14) have been solved numerically by 4th order Runge-Kutta method association with Shooting technique. From the experimental point of view, we are able to know that the blood of human being has been influenced by the physical parameters like viscosity ($\mu$), specific heat at constant pressure (cp), thermal conductivity (k) which are dependent upon time. Researcher Chato [1] has presented the following set of data for blood of human being at a temperature $T=310^{\circ} \mathrm{K}, c_{p}=14.65 \mathrm{j} / \mathrm{kg}^{0} \mathrm{~K}, \mu=3200 \mathrm{~kg} / \mathrm{ms} \text { and } k=$$0.0022 \mathrm{j} / \mathrm{ms}^{0} \mathrm{~K}$. On the basis of all these above information's, we have evaluated that Pr=21 for blood of human being. The computations have been carried out for value of $\begin{aligned} S &=0.5, k_{3}=0.4, A=1, S_{f}=2.5, S_{t}=1, S_{m}=1, \operatorname{Pr}=\\ 21, t &=0.1, N r=0.2, S c=1, \lambda_{1}=1, \lambda_{2}=1 \text { for Figure } 2-19 \end{aligned}$ for . The influence of magnetic parameter in absence of thermal and mass buoyancy on velocity distribution is depicted in Figure 2. It is observed that the velocity profile retards with rise in magnetic parameter. This is because of Lorentz force which acts in the opposite direction of flow of blood. The increase in generated Lorentz force reduces the blood velocity in the capillary tube. The figure also indicates that the velocity of blood flow in the capillary tube is reduced with an increase in the height from the lower wall. Results presented in Figure 2 which establishes the validity of the results obtained by comparing with Misra and Sinha [24].
Figure 2. Effect of M2 on velocity
Figure 3. Effect of Nr on velocity
Figure 4. Effect of A on velocity
Figure 5. Effect of k3 on velocity
Figure 3 depicts the influence of radiation parameter (Nr) over non-dimensional axial velocity. The effect of radiation by thermal process increases then the velocity of blood rises in the capillaries. In some pathological process, we can reduce the pain in the affected area by applying heat due to which blood clot breaks and starts to flow in a regular manner. The change of non-dimensional axial velocity for various values of unsteadiness parameter (A) has been depicted in Figure 4. The present figure shows that velocity of blood in the capillary falls down with rise up of the unsteadiness parameter (A) but one interesting property is marked here that the velocity of blood is very low in absence of (A). Increase in permeability parameter that tends to rise in axial velocity which is illustrated in Figure 5. In addition, small change in value of permeability parameter (k3) produces faster declination in axial velocity. Figure 6 represents the velocity profile for different values of buoyancy parameter (λ1). Now the velocity of blood rises toward the axis of the capillary line, when the value of thermal buoyancy parameter (λ1) go high within the region where flow assist (λ1>0), while it’s value drop-down when the thermal buoyancy parameter (λ1) rises within the region where the flow opposes (λ1<0). In physical science, the flow opposing region is meant for increase temperature of fluid or decrease temperature of stretching tube, while flow assisting region meant for decrease temperature of fluid or increase temperature of tube. The current picture further reveals that when the temperature of the surface wall of capillary tube decreases, the boundary layer thickness of velocity rises whereas when temperature of blood decreases, then the boundary layer thickness of physical quantity velocity increases. It has been noted that for the case when the temperature of surface wall of the capillary vessel increases with increase of λ1 then the velocity of blood becomes zero at inflection point. The blood flow velocity which flows towards the radial direction for different value of mass buoyancy parameter has been depicted in Figure 7. Buoyancy is an opposing force act in upward direction exerted by a fluid that opposes the weight of a mass object in the blood so the velocity of blood goes high, when the thermal buoyancy parameters rise up. The influence of the velocity slip factor and thermal slip factor on axial velocity has been described in Figure 8 and Figure 9 respectively. Figure 8 shows that the velocity in axial direction decreases when the velocity slip factor (Sf) increases. A similar effect is also observed for the mass slip factor (St) that has shown in Figure 9. It is noticed that for higher value of (Sf) and (St) the frictional resistance within the blood and surface wall is completely removed. Figure 10 to Figure 15 depict the temperature distribution for various values of thermal buoyancy parameter (λ1), mass buoyancy parameter (λ2), Hartmann number (M), Prandtl number (Pr) and radiation parameter (Nr). The influence of thermal buoyancy parameter and mass buoyancy parameter presented in Figure 10 and Figure 11 respectively. So, the flow velocity increases with an increase in thermal buoyancy parameter because of the contribution of gravity helps blood particles in attaining higher kinetic energy. Figure 12 represents the influence of magnetic parameter (M2) over distribution of temperature. This is an interesting fact to note that the temperature of the boundary layer of the capillary vessel increases due to the existence of a magnetic field. It is an important fact to see that an opposing type of force is well known as Lorentz force has been exhibited from an electrically conducting fluid subject to the action of magnetic field, which is normal to the surface. The forces have the capability to increase the temperature of blood flow.
Figure 6. Effect of λ1 on velocity
Figure 7. Effect of λ2 on velocity
Figure 8. Effect of Sf on velocity
Figure 9. Effect of St on velocity
Figure 10. Effect of λ1 on temperature
Figure 11. Effect of λ2 on temperature
Figure 12. Effect of M2 on temperature
Figure 13. Effect of Nr on temperature
The influence of thermal radiation over the temperature distribution has been depicted in Figure 13. The increase of thermal radiation at the time of blood flow in the capillary tube gives rise to the corresponding increase in the thickness of the boundary layer which has been highlighted in the figure. The variation of the temperature in the boundary layer due to the corresponding variation in the Prandtl number (Pr) has been shown in Figure 14. The present reveals that the Prandtl number rises up when the temperature of the boundary layer falls down. It is an important fact to notice that the thickness of the thermal boundary layer declines due to the increase of Prandtl number (Pr). It further marks that the temperature distribution at the surface wall increases due to increase in Prandtl number because when Prandtl number of blood is very high, then the thermal conductivity (k) let down and due to which heat conduction capacity decreases by reducing the thickness of boundary layer, therefore the rate of heat transfer at the surface of vessel increases. Figure 15 depicts the variation of temperature profile in blood for the various values of thermal slip factor (St). The temperature at any point in the flow decreases due to increase in the thermal slip parameter.
Figure 14. Effect of Pr on temperature
Figure 15. Effect of St on temperature
Figure 16. Effect of λ1 on concentration
Figure 17. Effect of λ2 on concentration
Figure 18. Effect of Sm on concentration
Figure 19. Effect of Sc on concentration
Figure 20. Effect of $\lambda_{1}$ on skin friction with $M^{2}$ for $S=0.5, k_{3}=0.4, S_{f}=2.5, S_{t}=2.5, S_{m}=1, \operatorname{Pr}=21, t=$$0.1, N r=0.2, S c=1, A=1, \lambda_{2}=1$
The dimensionless concentration profile $\phi(\eta)$ for different values of thermal buoyancy parameter ($\lambda_{1}$), mass buoyancy parameter ($\lambda_{2}$), mass slip factor, Schmidt number (Sc) are plotted from Figures 16-19. The dimensionless concentration distribution for various values of thermal buoyancy parameter ($\lambda_{1}$) and mass buoyancy parameter ($\lambda_{2}$) has been depicted in Figure 16 and Figure 17 respectively. The influence of both the above said parameters is to reduce the concentration of solute in the capillary tube. The influence of the mass slip factor (Sm) over temperature variation has been presented in Figure 18. Finally, the influence of Schmidt number (Sc) over concentration distribution has been depicted through Figure 19. The current figure reveals that concentration profile reduces due to an increase in Schmidt number (Sc). This is important to know that skin friction, heat and mass transfer rate at the wall of the capillary tube. These results are shown in Figure 20-23. Figure 20 represents the effect of skin friction over the change of Hartmann number for different values of thermal buoyancy parameter ($\lambda_{1}$). It is found that skin friction decreases with increase of thermal buoyancy parameter and in Figure 21 it shows that these value decrease when the unsteadiness parameter (A) increases. The change of local Nusselt number for the corresponding change in unsteadiness parameter for various values of Prandtl number is presented in Figure 22. It demonstrates that local Nusselt number grows up when the Prandtl number rises. Figure 23 presents the effect of local Sherwood number with the unsteadiness parameter for various values of Schmidt number (Sc) and it reveals the fact that local Sherwood number rises with the increase in Schmidt number.
Figure 21. Effect of $A$ on Skin friction with $M^{2}$ for $S=0.5, k_{3}=0.4, S_{f}=2.5, S_{t}=2.5, S_{m}=1, \operatorname{Pr}=21$$t=0.1, N r=0.2, S c=1, \lambda_{1}=1, \lambda_{2}=1$
Figure 22. Effect of Pr on Nusselt number with $A$ for $S=0.5, k_{3}=0.4, S_{f}=2.5, S_{t}=2.5, S_{m}=1, t=0.1, M=$$0.5, N r=0.2, S c=1, \lambda_{1}=1, \lambda_{2}=1$
Figure 23. Effect of $S$ con Sherwood number with $A$ for $S=0.5, k_{3}=0.4, S_{f}=2.5, S_{t}=2.5, S_{m}=1, t=0.1$$M=0.5, N r=0.2, \operatorname{Pr}=21, \lambda_{1}=1, \lambda_{2}=1$
Unsteady blood flow with radiation through a narrow tube with permeable surface has been discussed in the presence of applied unsteady magnetic field. The influence of thermal and mass buoyancies was investigated in this model. The velocity of blood flow, temperature and mass concentration distributions along with dimensionless skin friction, Nusselt number and Sherwood number at the capillary for various values of parameters are studied and shown graphically. The model would be very much useful to medical engineering like human thermotherapy, cardiovascular diseases. We have established the accuracy of numerical results computed by Misra and Sinha [24] in our study. The important findings of the present study have outlined as given below:
By controlling the exterior magnetic field intensity, the velocity of the blood can be regulated and the velocity profile retards with rise in magnetic parameter. Moreover, when the velocity slip and thermal slip factor increases, then the velocity of blood towards the axial direction decreases.
It is the ability of thermal radiation to produce a meaningful variation in the temperature distribution of boundary layer. The thermal boundary layer thickness goes high to a great extent when an increase in thermal radiation and also the blood temperature along the boundary layer decreases if the Prandtl number of thermal slip factor increases.
The blood velocity towards the axis of tube goes high due to increase in permeability parameter. It is concluded that the amount of mass concentration inside the capillary tube falls down due to the increase of Schmidt number, thermal buoyancy parameter and mass buoyancy parameter.
The concentration distribution of blood at any position of the capillary tube decreases if the mass slip factor increases.
In future, the present paper will be helpful in determining experimental as well as theoretical analysis of more complicated blood flow model.
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Ts |
thermal slip |
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H |
heat transfer coefficient |
|
v |
velocity of blood in tube along the direction of normal |
|
us |
velocity- slip at the permeable wall |
|
u |
blood velocity along the axis of the tube |
|
B(t) |
unsteady magnetic field |
|
k2 |
permeability |
|
K |
thermal slip factor |
|
qr |
radiative heat flux |
|
N |
velocity slip factor |
|
M |
Hartman number |
|
A |
unsteadiness parameter |
|
Pr |
Prandtl number |
|
v |
kinematic coefficient of viscosity |
|
Sf |
velocity slip factor |
|
Nux |
local Nusselt number |
|
Sm |
mass slip factor |
|
$\eta$ |
distance |
|
Uw |
stretching velocity |
|
$\sigma$ |
electrical conductivity |
|
k* |
mean absorption coefficient |
|
Tw |
surface temperature |
|
cp |
specific heat at constant pressure |
|
Nr |
radiation parameter |
|
D |
mass diffusivity |
|
k3 |
permeability parameter |
|
k1(t) |
unsteady permeability parameter |
|
T |
temperature of blood at any point in the tube |
|
K1 |
mass-slip factor |
|
k |
thermal conductivity |
|
St |
thermal-slip factor |
|
vw |
injection or suction velocity |
|
$\sigma^{*}$ |
Stefan-Boltzmann constant |
|
Cf |
skin-friction coefficient |
|
Sh |
Sherwood number |
|
r |
radius of the artery line |
|
S |
injection or suction parameter |
|
$\rho$ |
density |
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