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. 2013 Oct 16;30(2):249–279. doi: 10.1002/cnm.2602

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© 2013 The Authors. International Journal for Numerical Methods in Biomedical Engineering published by John Wiley & Sons, Ltd.

This is an open access article under the terms of the Creative Commons Attribution License, which permits use, distribution and reproduction in any medium, provided the original work is properly cited.

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(a,d) Forward and backward components of modified wave intensity with time in the midpoint of the single-vessel aortic model coupled to a matched RCR Windkessel outflow model (Figure 3(b)). They were calculated using the original model (black solid lines), with c at diastolic pressure, and changing the (a) sampling frequency (SF in kHz) or (d) error in the PWV relative to the theoretical PWV (c error in %), as indicated by the labels (red and blue dashed lines). In the original model, we have SF = 1 kHz and c error = 0%. Note the different scaling of and . Effect of (b,c) SF and (e,f) PWV error on the transit time (TT) and apparent reflection coefficient calculated using foot (circles), peak (squares) or area-average (stars) values, as illustrated in Figure 5.

Inline graphic — (a,d) Forward and backward components of modified wave intensity with time in the midpoint of the single-vessel aortic model coupled to a matched RCR Windkessel outflow model (Figure 3(b)). They were calculated using the original model (black solid lines), with c at diastolic pressure, and changing the (a) sampling frequency (SF in kHz) or (d) error in the PWV relative to the theoretical PWV (c error in %), as indicated by the labels (red and blue dashed lines). In the original model, we have SF = 1 kHz and c error = 0%. Note the different scaling of and . Effect of (b,c) SF and (e,f) PWV error on the transit time (TT) and apparent reflection coefficient calculated using foot (circles), peak (squares) or area-average (stars) values, as illustrated in Figure 5.