Mathematical model of pulsatile blood flow in a distensible aortic bifurcation subject to body acceleration

Chakravarty, S.; Mandal, Prashanta Kumar; Mandal, Arunava

doi:10.1016/s0020-7225(99)00022-1

Cited by 23 publications

(6 citation statements)

References 15 publications

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“…In order to obtain a complete FSI model of coupled system, two coupling conditions on the fluid-solid interface are required [18,19,[24][25][26][27][28][29][30][31][32][33][34] . The first condition describes the fluid-solid interface as a Dirichlet boundary for the fluid i.e.…”

Section: The Wall Modelmentioning

confidence: 99%

Flow Characteristics in Elastic Arteries Using a Fluid-Structure Interaction Model

Oscuii¹,

Tafazzoli-Shadpour²,

Ghalichi³

2007

American J. of Applied Sciences

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Abstract:In this study the interaction of blood flow with arterial wall has been investigated using FSI (Fluid-Structure Interaction) modeling. Computer simulation of pulsatile blood flow was carried out on the basis of the time dependent axisymmetric Navier-Stokes equations for an incompressible Newtonian fluid flow. An elastic incompressible material with large deformation was considered for the arterial wall and momentum and continuity equations of elastodynamics have been solved. The specified boundary conditions for the Navier-Stokes equations were the pulsatile pressure waveforms of the brachial artery at inflow and outflow to the given pulse wave form of a cardiac cycle. Fluid and solid equations were solved with the ALE-based loose coupling method for FSI problems. Resultant flow, wall displacement, wall shear stress and wall circumferential strain waves, and their phase differences were determined. Stiffening of the arterial wall resulted in a significant decrease in the mean values of flow and wall shear stress and altered waveforms. A tenfold increase in wall stiffness caused 33% drop in flow and negative values of shear stress in 21% of the pressure pulse. For elastic moduli corresponding to wall displacements less than 1% the blood flow and wall shear stress were not sensitive to wall stiffness. Stress phase angle was altered by stiffening of the arterial wall. It was concluded that FSI modeling with pressure boundary conditions provides a proper evaluation of hemodynamic parameters that may determine endothelial injury.

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Section: The Wall Modelmentioning

confidence: 99%

Flow Characteristics in Elastic Arteries Using a Fluid-Structure Interaction Model

Oscuii¹,

Tafazzoli-Shadpour²,

Ghalichi³

2007

American J. of Applied Sciences

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“…The pressure gradient term in the momentum equation characterizes the pulsatile flow nature of blood flow. Hence, it is quite common to assume the pressure gradient term in the momentum equation (8) as the sum of the constant pressure gradient A 0 (for steady flow) and pulsatile pressure gradient A 1 (for unsteady flow) multiplied by a cosine function of the product of angular frequency and time as given below [16,30].…”

Section: Geometry Of the Flow Filed And Governing Equationsmentioning

confidence: 99%

Mathematical Analysis for MHD Flow of Blood in Constricted Arteries

Sankar

Lee

Ismail

2013

Int. J. Nonlinear Sci. Numer. Simul.

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The unsteady oscillatory magneto-hydrodynamic flow of blood in small diameter arteries with mild constriction is analyzed, blood being modelled as a HerschelBulkley fluid. Finite difference method is employed for solving the associated initial boundary value problem. Explicit finite difference schemes for velocity distribution, flow rate, skin friction and longitudinal impedance to the flow are obtained. The effects of pressure gradient, yield stress, magnetic field, power law index and maximum depth of the stenosis on the aforesaid flow quantities are discussed through appropriate graphs. It is found that the velocity and flow rate decrease and the skin friction and longitudinal impedance to flow increase with the increase of the magnetic field parameter. It was recorded that the flow rate increases and the skin friction decreases with the increase of the phase angle. It was also noted the skin friction and longitudinal impedance to flow that increase almost linearly with the increase of maximum depth of the stenosis. The estimates of the increase in the longitudinal impedance to flow and skin friction are increased considerably by the presence of the magnetic field.

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“…Several researchers attempted to study the effects of stenosis size and shape on the blood flow characteristics, treating the blood as Newtonian fluid which is found to be valid only when it flows through arteries of larger diameters ( 1300 m > µ ) at high shear rates ( 1 100 s − > ) [9,10]. Since, blood exhibits significant non-Newtonian flow characteristics when it flows in small diameter arteries (artery diameter 50µm-1300µm) at low shear rates ( 1 100 s − < ), several researchers attempted to investigate the effect of non-Newtonian character blood on the physiologically important flow quantities such as skin friction and impedance to flow under normal and abnormal (stenosis, aneurysm, catheter, stenting etc) flow conditions [11,12].…”

Section: Introductionmentioning

confidence: 99%

Mathematical analysis of Carreau fluid model for blood flow in tapered constricted arteries

Sankar

Lee

Nagar

et al. 2018

AIP Conference Proceedings

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The pulsatile flow of blood through a tapered constricted narrow artery is investigated in this study, treating the blood as Carreau fluid model. The constriction in the artery is due to the formation of asymmetric stenosis in the lumen of the artery. The expressions obtained by Sankar (2016) for the various flow quantities are used to analyze the flow with different arterial geometry. The influence of various flow parameters on the velocity distribution, wall shear stress and longitudinal impedance to flow is discussed. The velocity of blood increases with the increase of the power law index and stenosis shape parameter and it decreases considerably with the increase of the maximum depth of the stenosis. The wall shear stress and longitudinal impedance to flow decrease with the increase stenosis shape parameter, amplitude of the pulsatile pressure gradient, flow rate, power law index and Weissenberg number. The estimates of the percentage of increase in the wall shear stress and longitudinal impedance to flow increase with the increase of the angle tapering and these increase significantly with the increase of the maximum depth of the stenosis. The mean velocity of blood decreases considerably with the increase of the artery radius (except in arteriole), maximum depth of the stenosis and angle of tapering and it is considerably higher in pulsatile flow of blood than in the steady flow of blood.

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Mathematical model of pulsatile blood flow in a distensible aortic bifurcation subject to body acceleration

Cited by 23 publications

References 15 publications

Flow Characteristics in Elastic Arteries Using a Fluid-Structure Interaction Model

Flow Characteristics in Elastic Arteries Using a Fluid-Structure Interaction Model

Mathematical Analysis for MHD Flow of Blood in Constricted Arteries

Mathematical analysis of Carreau fluid model for blood flow in tapered constricted arteries

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