局部狭窄血管中血液振荡流的速度和切应力

本文建立一种分析局部缓慢狭窄血管中血液振荡流的数学模型，给出了血液的轴向流速，径向流速和切应力的包含压力梯度项的解析表达式，并讨论了血管内由局部狭窄引起的压力梯度沿轴向变化的规律。文章以局部余弦狭窄为例进行数值计算，详细讨论上游均匀管段压力梯度的定常部分和不同次谐波对狭窄管段内流速和切应力的影响。数值结果表明，与均匀管情况相比，在狭窄段内，血液振荡流轴向流速无论平均值还是脉动幅值均明显增大，且径向流速不再为零。但径向流速仍远小于轴向流速。同时，切应力也不再仅由轴向流速梯度提供，径向流速梯度也将产生切应力，但是在计算管壁切向上的切应力时，径向流速梯度的贡献仍相当大。与均匀管管壁切应力沿流运方向保持恒定不同。狭窄管管壁切应力（平均值和脉动值）将随着狭窄高度的增大而增大，在狭窄最大高度处达到最大，因而沿流动方向产生了较大的切应力梯度。     

刚性圆管中血液周期振荡流的切应力分布

本文通过求解圆管内血液振荡流的基本方程，求得圆管内血液流的压力梯度与切应力之间的关系式。在此基础上，详细讲座了圆管中轴向流速和切变率谐波的变化规律，指出流速谐波和切变率谐波的幅值都将随着谐波次数的增大而逐渐减小。为了使所得结果便于应用。文章通过管轴向中心线流速与压力梯度之间的关系式，进一步给出一种利用管轴向中心线流速计算管内切应力分布的简便方法。该方法用于检测活体血管内血液振荡流的切应力分布，具有操作简单，精度较高的优点。最后，以人体颈动脉为例，讨论血液周期振荡流的切应力的分布特性。发现在任意时刻，除了邻近管壁处切应力急剧增大到一定数值之外，沿管截面切应力分布相当均匀且接近于零，呈现出与定常流不同的切应力分布特征。     

一种确定均匀动脉壁面切应力的非线性方法

从Ling和Atabek提出的``局部流'理论出发，提出一种利用测量血液黏度、管轴上 的血流速度、压力和管径波形计算均匀动脉管壁切应力的非线性方法. 将这种方法与柳兆荣 等提出的利用测量血液黏度、管轴上的血流速度和平均管径计算切应力的线性方法比较，结 果表明，当管壁脉动幅度较小时，两种方法计算的压力梯度、流速剖面和管壁切应力差别较 小；而当管壁脉动幅度增大时，两种方法计算的压力梯度、流速剖面和管壁切应力差别增大. 对于小幅脉动均匀动脉，用线性方法计算管壁切应力有较高的精度；而对于大变形 均匀动脉，则需要考虑非线性因素对管壁切应力的影响. 由于作为输入量的血液黏度、轴心 血流速度、压力波形和管径波形可在活体上通过无损伤或微损伤的检测方法得到， 所提出的计算切应力的方法为在体或离体研究切应力与动脉重建的关系提供了方法学基础.     

动脉压对静脉血管壁周向应力分布的影响

自体静脉是病变动脉管段常用的替代物。移植后因承受压力急剧升高引起的静脉管壁应力改变是影响移植手术的主要因素之一。为了比较移植前(静脉压作用下)和移植后(动脉压作用下)静脉管壁的周向应力分布，本文通过检测一定轴向伸长比条件下静脉管的p(压力)——V(容积)试验数据，利用3参数的应变能密度函数对实验数据进行拟合，进而求得静脉管壁的残余应力和沿血管壁的周向应力分布。对狗的股静脉和颈静脉的分析结果表明，在动脉压作用下静脉管壁周向应力将急剧增大。与处于静脉压环境相比，处于动脉压环境中的颈静脉管周向应力将增大差不多2个数量级。计算结果还显示，静脉管壁残余应力的数值虽然比动脉管壁的相应值小很多，但是与动脉管相同，血管壁残余应力依然对静脉管壁上的周向应力分布影响显著，残余应力的存在将大大削弱在静脉管内壁处的周向应力集中，使周向应力沿静脉管壁厚的变化梯度明显减小。     

弯曲狭窄管内血液流的分析

与血管狭窄有关的异常血液动力学特征在血管疾病的发生和发展过程中起着重要的作用,由于血管狭窄和弯曲的综合影响,将会出现一系列有趣的流体力学现象,本文研究具有对称狭窄的弯曲小动脉内定常血液流动,在一定的假设条件下,直接从支配血液流动的Navier-Stokes方程求出问题的摄动解,由此求得弯曲狭窄管內血液流动的轴向速度、二次流速度及压力梯度等分析表达式,并进一步求得轴向和周向血管壁切应力。本文的结果是先前有关狭窄直管和弯曲均匀管流动研究的拓广。     

脉劝流条件下血管壁的应力分布

为了分析血液-血管耦合运动所产生血液脉动压力载荷对血管壁应力分布的影响,利用线性化的血液-血管耦合运动方程的Womersley解,导得血液脉动压力载荷下的血管壁Green应变,同时利用Fung的血管壁应变能密度函数,导得相应血管壁应力分布的一般表达式.数值结果表明,在脉动流条件下,当考虑血液-血管耦合运动时,血管壁中周向应力最大,轴向应力居中,径向应力最小;血管壁的残余应力将明显减小血管内壁的应力集中;脉动压力载荷将导致血管壁周向应力在一个心动周期中随时间的脉动,而且随着Womersley数α和血管轴向约束参数K～＊的增大,血管壁周向应力的脉动将明显加剧,提示在分析动脉重建时必须计及血液-血管耦合运动对血管壁应力分布的影响.     

脉动流条件下血管壁的应力分布

为了分析血液-血管耦合运动所产生血液脉动压力载荷对血管壁应力分布的影响,利用线性化的血液-血管耦合运动方程的Womersley解,导得血液脉动压力载荷下的血管壁Green应变,同时利用Fung的血管壁应变能密度函数,导得相应血管壁应力分布的一般表达式.数值结果表明,在脉动流条件下,当考虑血液-血管耦合运动时,血管壁中周向应力最大,轴向应力居中,径向应力最小;血管壁的残余应力将明显减小血管内壁的应力集中;脉动压力载荷将导致血管壁周向应力在一个心动周期中随时间的脉动,而且随着Womersley数α和血管轴向约束参数K*的增大,血管壁周向应力的脉动将明显加剧,提示在分析动脉重建时必须计及血液-血管耦合运动对血管壁应力分布的影响.     

用管轴流速确定动脉中血液振荡流的速度剖面

本文通过求解圆管内血液振荡流的基本方程，求得圆管内血液流的速度与压力梯度之间的关系式，文章提出一种利用管轴外流速计算管内压力梯度，进而确定血液振荡流动速度分布的方法，该方法用于检测活体血管内血液振荡流的速度剖面，具有操作简单，精度较高的优点，最后，以人体颈动脉为例，讨论血液周期振荡流的速度分布特征，发现在任意时刻，除了邻近管壁速度迅速降为零之外，沿管截面速度分布相当均匀，呈现出与定常流不同的速度分布特征。     

Taylor补丁对新型动脉旁路移植流场影响的数值分析

为了研究Taylor补丁对新型(S型)动脉旁路移植术中吻合口处流场的影响,使用数值方法研究了采用Taylor补丁和未采用该补丁的两个S型旁路移植模型内流场的血流动力学差异. 对流速、壁面切应力和切应力梯度等参数进行了比较分析. 结果表明,Taylor补丁对吻合口的流场有显著影响. 采用Taylor补丁的模型其下游吻合口处的流场分布较未采用补丁的模型更均匀,二次流平均流速减小约34.48%,壁面切应力梯度减小约52.22%,从壁面切应力梯度方面分析,这将有助于改善血流动力学分布,抑制动脉粥样硬化. 但从壁面切应力值分析,其动脉底部的壁面低切应力区明显增大,平均壁面切应力值减小30.33%,这又将促使动脉粥样硬化. 因此,Taylor补丁是否对S型搭桥术具有治疗优越性,仅从血流动力学分析尚不能定论,配合数值计算结果进行动物和临床实验研究是十分必要的.      

在体轴向伸长比条件下血管壁的周向应力分布

本文通过检测在体轴向伸长比条件下血管段的压力－容积数据,利用应变能密度函数,求得血管壁周向应力沿壁厚的分布。文章的正常大鼠腹主动脉为例进行计算,结果发现,在生理压力作用下（例如ｐ＝１３．３ｋＰａ）,不考虑残余应力确实出现在血管内壁处的周向应力集中,血管内、外壁处的应力值之比可达１５左右,而存在于实际动脉管中的残余应力会使血管壁中的周向应力沿壁厚的分布明显趋于均匀,血管处的周向应力之比差不多只有２左     

An analytical solution for steady flow of a Quemada fluid in a circular tube

An analytical solution is obtained for steady flow of Quemada-type fluids in a circular tube driven by a constant pressure gradient. Expressions are derived for velocity distribution and for volumetric flow rate as a function of pressure gradient or wall shear stress.     

Mathematical modeling and parametric investigation of blood flow through a stenosis artery

In this study, a mathematical model is formulated to examine the blood flow through a cylindrical stenosed blood vessel. The stenosis disease is caused because of the abnormal narrowing of flow in the body. This narrowing causes serious health issues like heart attack and may decrease blood flow in the blood vessel. Mathematical modeling helps us analyze such issues. A mathematical model is considered in this study to explore the blood flow in a stenosis artery and is solved numerically with the finite difference method. The artery is an elastic cylindrical tube containing blood defined as a viscoelastic fluid. A complete parametric analysis has been done for the flow velocity to clarify the applicability of the defined problem. Moreover, the flow characteristics such as the impedance, the wall shear stress in the stenotic region, the shear stresses in the throat of the stenosis and at the critical stenosis height are discussed. The obtained results show that the intensity of the stenosis occurs mostly at the highest narrowing areas compared with all other areas of the vessel, which has a direct impact on the wall shear stress. It is also observed that the resistive impedance and wall shear pressure get the maximum values at the critical height of the stenosis.

     

Peristaltic flow of MHD Jeffrey fluid through finite length cylindrical tube

The present investigation studies the peristaltic flow of the Jeffrey fluid through a tube of finite length. The fluid is electrically conducting in the presence of an applied magnetic field. Analysis is carried out under the assumption of long wavelength and low Reynolds number approximations. Expressions of the pressure gradient, volume flow rate, average volume flow rate, and local wall shear stress are obtained. The effects of relaxation time, retardation time, Hartman number on pressure, local wall shear stress, and mechanical efficiency of peristaltic pump are studied. The reflux phenomenon is also investigated. The case of propagation of a non-integral number of waves along the tube walls, which are inherent characteristics of finite length vessels, is also examined.     

A fluid flow model in the lacunar-canalicular system under the pressure gradient and electrical field driven loads

The lacunar-canalicular system (LCS) is acknowledged to directly participate in bone tissue remodeling. The fluid flow in the LCS is synergic driven by the pressure gradient and electric field loads due to the electro-mechanical properties of bone. In this paper, an idealized annulus Maxwell fluid flow model in bone canaliculus is established, and the analytical solutions of the fluid velocity, the fluid shear stress, and the fluid flow rate are obtained. The results of the fluid flow under pressure gradient driven (PGD), electric field driven (EFD), and pressure-electricity synergic driven (P-ESD) patterns are compared and discussed. The effects of the diameter of canaliculi and osteocyte processes are evaluated. The results show that the P-ESD pattern can combine the regulatory advantages of single PGD and EFD patterns, and the osteocyte process surface can feel a relatively uniform shear stress distribution. As the bone canalicular inner radius increases, the produced shear stress under the PGD or P-ESD pattern increases slightly but changes little under the EFD pattern. The increase in the viscosity makes the flow slow down but does not affect the fluid shear stress (FSS) on the canalicular inner wall and osteocyte process surface. The increase in the high-valent ions does not affect the flow velocity and the flow rate, but the FSS on the canalicular inner wall and osteocyte process surface increases linearly. In this study, the results show that the shear stress sensed by the osteocyte process under the P-ESD pattern can be regulated by changing the pressure gradient and the intensity of electric field, as well as the parameters of the annulus fluid and the canaliculus size, which is helpful for the osteocyte mechanical responses. The established model provides a basis for the study of the mechanisms of electro-mechanical signals stimulating bone tissue (cells) growth.

     

A calculation method for blood flow velocity distribution in smallep elocd vessels

The calculative method presented in this paper is based on an improvement of boundary conditions for a micro-continuum fluid model with blood flow assuming that the blood cell velocity at blood vessel wall is unequal to zero. As for steady state flood flow equation (flow in vitre—a rigid circular tube) presented by Eringen, the magnitude of the blood cell gyroscopic velocity at blood vessel wall and the slope of the blood cell gyroscopic velocity distribution curve at the axis of the blood vessel are assumed. From the above mentioned assumptions the calculating method of velocity distribution curve in blood vessel is derived. The curve calculated by this method is compared with the test curve measured by Bugliarello and Hayden. The results obtained by Turk, Sylvester and Ariman as well as with this method are compared with each other, too.     

The stress analysis of vessel wall in the entrance region of a tapered vessel

ＴＨＥＳＴＲＥＳＳＡＮＡＬＹＳＩＳＯＦＶＥＳＳＥＬＷＡＬＬＩＮＴＨＥＥＮＴＲＡＮＣＥＲＥＧＩＯＮＯＦＡＴＡＰＥＲＥＤＶＥＳＳＥＬＣｅｎＲｅｎ－Ｊｉｎｇ（岑人经）ＴａｎＺｈｅ－ｄｏｎｇ（谭哲东）ＣｈｅｎＺｈｅｎｇ－ｚｏｎｇ（陈正宗）（ＳｏｕｔｈＣｈｉｎ...     

A Two-Layer Mathematical Model of Blood Flow in Porous Constricted Blood Vessels

In this paper, we discussed a mathematical model for two-layered non-Newtonian blood flow through porous constricted blood vessels. The core region of blood flow contains the suspension of erythrocytes as non-Newtonian Casson fluid and the peripheral region contains the plasma flow as Newtonian fluid. The wall of porous constricted blood vessel configured as thin transition Brinkman layer over layered by Darcy region. The boundary of fluid layer is defined as stress jump condition of Ocha-Tapiya and Beavers–Joseph. In this paper, we obtained an analytic expression for velocity, flow rate, wall shear stress. The effect of permeability, plasma layer thickness, yield stress and shape of the constriction on velocity in core & peripheral region, wall shear stress and flow rate is discussed graphically. This is found throughout the discussion that permeability and plasma layer thickness have accountable effect on various flow parameters which gives an important observation for diseased blood vessels.