A 1D arterial blood flow model incorporating ventricular pressure, aortic valve and regional coronary flow using the locally conservative Galerkin (LCG) method

• Published in: Communications in numerical methods in engineering Vol. 24; no. 5; pp. 367 - 417
• Main Authors: Mynard, J. P., Nithiarasu, P.
• Format: Journal Article
• Language: English
• Published: Chichester, UK John Wiley & Sons, Ltd 01.05.2008; Wiley
• Subjects: aortic valve; Biological and medical sciences; blood flow; Computational techniques; coronary flow; Exact sciences and technology; Fundamental and applied biological sciences. Psychology; Fundamental areas of phenomenology (including applications); Heart; Hemodynamics. Rheology; locally conservative Galerkin; Mathematical methods in physics; one dimensional; Physics; Vertebrates: cardiovascular system; Measurement; coronary flow; Pressure gradient; Modeling; Time varying system; Pumping; Aorta; Muscle; Cardiology; Human; Branching; locally conservative Galerkin; Experimental study; Artery; Wave reflection; Blood flow; Wave transmission; Flow(fluid); External pressure; Galerkin method; Circulatory system; Hemodynamics; Non linear effect; one dimensional; Aortic valve
• ISSN: 1069-8299; 1099-0887; 1099-0887
• DOI: 10.1002/cnm.1117

There is an important interaction between the pumping performance of the ventricle, arterial haemodynamics and coronary blood flow. While previous non‐linear 1D models have focused only on one of these components, the model presented in this study includes coronary and systemic arterial circulations, as well as ventricular pressure and an aortic valve that opens and closes ‘independently’ and based on local haemodynamics. The systemic circulation is modelled as a branching network of elastic tapering vessels. The terminal element applied at the extremities of the network is a single tapering vessel which is shown to adequately represent the input characteristics of the downstream vasculature. The coronary model consists of left and right coronary arteries which both branch into two ‘equivalent’ vessels that account for the lumped characteristics of subendocardial and subepicardial flows. As contracting heart muscle causes significant compression of the subendocardial vessels, a time‐varying external pressure proportional to ventricular pressure is applied to the distal part of the equivalent subendocardial vessel. The aortic valve is modelled using a variable reflection coefficient with respect to backward‐running aortic waves, and a variable transmission coefficient with respect to forward‐running ventricular waves. A realistic ventricular pressure is the input to the system; however, an afterload‐corrected ventricular pressure is calculated and results in pressure gradients between the ventricle and aorta that are similar to those observed in vivo. The 1D equations of fluid flow are solved using the locally conservative Galerkin method, which provides explicit element‐wise conservation, and can naturally incorporate vessel branching. Each component of the model is verified using a number of tests to ensure accuracy and reveal the underlying processes that give rise to complex pressure and flow waveforms. The complete model is then implemented, and simulations are performed with input parameters representing ‘at rest’ and exercise states for a normal adult. The resulting waveforms contain all of the important features seen in vivo, and standard measures of haemodynamic state are found to be normal. In addition, one or several characteristics of some common diseases are imposed on the model and are found to produce haemodynamic changes that agree with experimental observations in the published literature. Using a patient‐specific carotid bifurcation geometry, 1D velocity waveforms are also compared with waveforms obtained from a three‐dimensional model. The 1D and 3D results show good agreement. Copyright © 2008 John Wiley & Sons, Ltd.