Applications of FSI for Cardiovascular Haemodynamics - Computational Hemodynamics: Theory, Modelling and Applications - page 283

Fig. 8.48 Stress/strain distributions and flow characteristics from a 3D FSI model ( 10 % axial
stretch, 7�8 inner circumferential shrinkage ), Pin = 100 mmHg. ( a ) Plot of maximum principal
stress ( Stress-P1 ) distribution on B-cut surface; ( b ) Plot of maximum principal strain ( Strain-P1 )
distribution on B-cut surface; ( c ) Stress-P1 on L-cut surface; ( d ) Flow velocity reaching its maxi-
mum in the stenotic region; ( e ) Pressure plot on L-cut surface; ( f ) Flow maximum shear stress plot
on L-cut surface showing a maximum at the stenosis throat. (Image from Yang et al. 2010)

8.5.6 Mechanical Stresses in 2D Carotid Plaque

In this next group of examples, we review recent work in the literature that focusses
on the mechanical stresses in simplified and patient specific 2D geometries models.
Li et al. (2006) used a fluid-structure-interaction model to simulate the blood flow
through a vessel with an atheromatous plaque. This work evaluated the effect of
luminal stenosis and fibrous cap thickness on plaque vulnerability. An idealised 2D
model with a lipid core was used.
The modelling approach conforms to the previous examples presented where the
flow was assumed laminar, Newtonian, viscous, and incompressible and applied
within an Arbitrary Lagrangian-Eluerian formulation using the COMSOL software
package (see Appendix for list of software). The inflow boundary condition in this
case was a fully developed laminar velocity profile on the left boundary, but the
amplitude of the flow varied with time. The outflow, on the right boundary was a
pressure condition with P = 0. The lipid core of the plaque was assumed incompress-
ible and nonlinear using a 2-term Ogden strain energy formulation to represent the