Simulation of pulsatile flow in arteries using the finite-element method

Weerappuli, D.P.V.

doi:10.31274/rtd-180813-12200

Cited by 6 publications

(20 citation statements)

References 92 publications

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“…was taken to be equal to 0.2 for all of the arterial segments. The selection of this value was rather arbitrary, but it was consistent with values calculated by Raines et al (1974) for the human leg and measured by Weerappuli (1987) for the hindlimb of the dog. Thus, the major component (80%) of the terminal resistance was assumed to occur in the distal microvasculature.…”

Section: Systemic Terminal Impedancessupporting

confidence: 63%

“…where C; and C"I are the coefficients of linear and non-linear compliance, respectively. This relationship has been used successfully by several investigators (Rooz et al, 1982;Porenta, 1982;Porentaerfl/., 1986;Weerappuli, 1987;Balar efa/., 1989;Stergiopulos, 1990).…”

Section: Lumped Parameter Modelsmentioning

confidence: 96%

“…where TH, represents the shear stress acting on the internal wall of the vessel. This form of the governing flow equations has been used extensively by several researchers (Streeter et al, 1963;Olsen and Shapiro, 1967;Anliker et al, 1971;Wemple and Mockros, 1972;Raines et al, 1974;Rumberger and Nerem, 1977;Rooz, 1980;Young et al, 1980;Porenta et al, 1986;Weerappuli, 1987;Balare/a/., 1989;Stergiopulos, 1990).…”

Section: Lumped Parameter Modelsmentioning

confidence: 99%

“…However, several investigators have used the same assumptions in similar studies to obtain a set of governing equations and obtained satisfactory results. The validity of the above assumptions is reviewed in further detail by Weerappuli (1987).…”

Section: Chapters Mathematical Formulationmentioning

confidence: 99%

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Computer simulation of coronary blood flow

Frake

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NOMENCLATURE a ratio of inner radius to wall thickness of arterial cross-section OO pulse wave velocity A arterial cross-sectional area ALV scaling factor for end-diastolic pressure of left ventricle Amax maximum arterial cross-sectional area Ao reference value for arterial cross-sectional area As effective area of stenotic arterial cross-section Aref arterial cross-sectional area at a reference pressure, b. body force term in axial direction BLV exponential factor for end-diastolic pressure of left ventricle CU unsteadiness coefficient for wall shear stress Cv viscous coefficient for wall shear stress c, first terminal compliance C2 second terminal compliance CA arterial area compliance c, linear compliance coefficient CMAX maximum arterial area compliance C"I non-linear compliance coefficient CT total terminal compliance

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Section: Systemic Terminal Impedancessupporting

confidence: 63%

Section: Lumped Parameter Modelsmentioning

confidence: 96%

Section: Lumped Parameter Modelsmentioning

confidence: 99%

Section: Chapters Mathematical Formulationmentioning

confidence: 99%

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Computer simulation of coronary blood flow

Frake

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“…The finite element method has also been used to simulate pulsatile arterial blood flow (Rooz 1980, Young et al 1980, Gray 1981, Porenta 1982, Rooz et al 1982, Rangarajan 1983, Weerappuli 1987. Some examples in which computer modeling has been used include studies of the canine femoral artery; human femoral artery; human radial, brachial, and ulnar arteries; and bovine uterine artery.…”

Section: Lumped Parameter Modelsmentioning

confidence: 99%

Assessment of bovine uterine artery hemodynamics using Doppler ultrasound and a computer model

Waite

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Computer simulation of blood flow in the human arm

Balar

Rogge

Young

1989

Journal of Biomechanics

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This paper considers a finite element method to characterize blood flow in the human arm arteries. A set of different pressure waveforms, which represent normal and diseased heart pulses, is used for the proximal boundary conditions, and a modified Windkessel model is used for the distal arterial boundary conditions. A comparison of the distal pressure and flow waveforms, for each different proximal pressure, is made to determine whether such waveforms are significantly altered from normal waveforms. The results show that the distal pressure and/or flow waveforms in certain cases are sufficiently different to be possibly used as a diagnostic indicator of an abnormal heart condition. Also considered is the effect of stenosis, change of compliance, and dilatation of the distal beds on the pressure and flow waveforms. A stenosis which has an area reduction of greater than approximately 75% is found to significantly alter both the distal pressure and flow waveforms. Changes in arterial compliance, however, do not strongly influence the waveforms. Dilatation of distal vascular beds is simulated by reducing the lumped resistance of these beds, and this reduction increases mean flow and decreases mean distal pressure, but has little effect on the basic shape of either the pressure or flow waveform.

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Simulation of pulsatile flow in arteries using the finite-element method

Cited by 6 publications

References 92 publications

Computer simulation of coronary blood flow

Computer simulation of coronary blood flow

Assessment of bovine uterine artery hemodynamics using Doppler ultrasound and a computer model

Computer simulation of blood flow in the human arm

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