By Herbert Oertel Herbert, Kathrin Spiegel, Sven Donisi
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Additional info for Modelling the Human Cardiac Fluid Mechanics, Second edition
2006)) leads to O = f (ReD , Wo ) . 8 · 106 of the healthy ventricle has been determined from the p-V diagram of Figure 26. Further ventricle flow simulations for several ventricle reconstruction have to be done to determine the function f for evaluating surgery reconstructions. Because of the alteration in the flow cycle described in the previous section, the work done in pumping is less in the ventricle with aneurysm and the postsurgery ventricle than in the healthy ventricle. The time the blood remains in Parameters F1 healthy F1 pre F1 post E: 63% 37% 24% M (1.
Model. , 2000. Computational mechanics of the heart. J. , 2004. Biofluid Mechanics of Blood Circulation. In: Prandtl’s Essentials of Fluid Mechanics. Ed. , 2005. Modelling the Human Cardiac Fluid Mechanics. , 2006. Str¨omungsmechanik . , 2003. Numerische Str¨omungsmechanik . , 1991. Pulsatile non–Newtonian Flow Characteristics in a Three-dimensional Human Carotid Bifurcation Model . J. of Biomech. , 1997. Fluid Dynamics of the Heart and its Valves. In: Case Studies in Mathematical Modeling — Ecology, Physiology, and Cell Biology.
This means, that during diastole the intake jet is no longer slowed down by the blood at rest up to the apex of the ventricle. Hence, a stagnation point flow arises. The branching is no longer asymmetrical as in the unhealthy heart before surgery, but rather a further ring vortex appears temporarily in the lower region of the ”apple-shaped” ventricle. This disturbs the exit flow process during the systole. First the focus (F1) passes through, while the counter-rotating focus (F2) remains in the ventricle and weakens as the systole continues.
Modelling the Human Cardiac Fluid Mechanics, Second edition by Herbert Oertel Herbert, Kathrin Spiegel, Sven Donisi