Research Papers

Effect of Non-Newtonian Behavior on Hemodynamics of Cerebral Aneurysms

[+] Author and Article Information
Carolyn Fisher

Department of Mechanical Engineering, Lafayette College, Easton, PA 18042

Jenn Stroud Rossmann

Department of Mechanical Engineering, Lafayette College, Easton, PA 18042rossmanj@lafayette.edu

J Biomech Eng 131(9), 091004 (Aug 04, 2009) (9 pages) doi:10.1115/1.3148470 History: Received October 09, 2008; Revised April 14, 2009; Published August 04, 2009

Blood flow dynamics near and within cerebral aneurysms have long been implicated in aneurysm growth and rupture. In this study, the governing equations for pulsatile flow are solved in their finite volume formulation to simulate blood flow in a range of three-dimensional aneurysm geometries. Four constitutive models are applied to investigate the influence of non-Newtonian behavior on flow patterns and fluid mechanical forces. The blood’s non-Newtonian behavior is found to be more significant, in particular, vascular geometries, and to have pronounced effects on flow and fluid mechanical forces within the aneurysm. The choice of constitutive model has measurable influence on the numerical prediction of aneurysm rupture risk due to fluid stresses, though less influence than aneurysm morphology.

Copyright © 2009 by American Society of Mechanical Engineers
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Figure 1

Effective viscosity as a function of shear rate for the non-Newtonian models evaluated

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Figure 2

Mean velocity of blood in the basilar artery (after Ref. 28)

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Figure 3

Base geometries for simulations

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Figure 4

Spatially averaged wall shear-stress calculated near fundus of 7 mm bifurcation aneurysm for all constitutive models lags the inlet velocity waveform

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Figure 5

WSS distribution in 7 mm aneurysm geometry at diastole; WSS ranges from 0 to 0.05 N/m2

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Figure 6

Velocity vectors in 10 mm aneurysm geometry at systole: velocity ranges from 0 to 0.5 m/s; (a) shows vectors on the shaded plane at an angle near 90 deg to the daughter vessels; (b) shows vectors on the shaded plane containing the daughter vessels’ midplane

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Figure 7

Velocity vectors on aneurysm neck cross section on curved vessel at systole (Carreau B model)

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Figure 8

Instantaneous streamlines in the aneurysm on a curved vessel for the Carreau B model at systole (left) and diastole (right). Note that streamlines are colored by their distance from the symmetry plane to illustrate three-dimensionality of flow

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Figure 9

Non-Newtonian importance factor IL distributions at systole in 7 mm geometry

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Figure 10

IL distributions at diastole in 7 mm geometry

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Figure 11

Streamlines (colored by their distance from the symmetry plane) in the high AR geometry for the Casson model at systole (left) and diastole (right)

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Figure 12

IL distributions in the high AR geometry at systole

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Figure 13

IL distributions in the high AR geometry at diastole

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Figure 14

Variation in WSS over cycle versus EI

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Figure 15

Comparison of non-Newtonian to Newtonian WSS at aneurysm fundus for six aneurysm morphologies. Vertical clusters of data represent morphology cases; observed trends demonstrate that WSS at the fundus is more sensitive to morphology than to constitutive law. A similar trend is observed for the spatially averaged WSS over the entire aneurysm wall.




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