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

2008 ◽  
Vol 24 (5) ◽  
pp. 367-417 ◽  
Author(s):  
J. P. Mynard ◽  
P. Nithiarasu
Keyword(s):  
Blood Flow ◽  
Aortic Valve ◽  
Coronary Flow ◽  
Flow Model ◽  
Arterial Blood Flow ◽  
Ventricular Pressure ◽  
Arterial Blood ◽  
Locally Conservative ◽  
Blood Flow Model

scholarly journals Development of a Blood Flow Model Including Hypergravity and Validation Against an Analytical Model

2010 ◽  
Author(s):  
M. H. A. van Geel ◽  
C. G. Giannopapa ◽  
B. J. van der Linden ◽  
J. M. B. Kroot
Keyword(s):  
Blood Flow ◽  
Wave Propagation ◽  
Flow Model ◽  
Analytical Data ◽  
Arterial Blood Flow ◽  
Solid Boundary ◽  
Aerospace Medicine ◽  
Arterial Blood ◽  
Fluid Behavior ◽  
Blood Flow Model

Fluid structure interaction (FSI) appears in many areas of engineering, e.g. biomechanics, aerospace, medicine and other areas and is often motivated by the need to understand arterial blood flow. FSI plays a crucial role and cannot be neglected when the deformation of a solid boundary affects the fluid behavior and vice versa. This interaction plays an important role in the wave propagation in liquid filled flexible vessels. Additionally, the effect of hyper gravity under certain circumstances should be taken into account, since such exposure can cause alterations in the wave propagation underexposed. Typical examples in which hyper gravity occurs are rollercoaster rides and aircraft or spacecraft flights. This paper presents the development of an arterial blood flow model including hyper gravity. This model has been developed using the finite element method along with the ALE method. This method is used to couple the fluid and structure. In this paper straight and tapered aortic analogues are included. The obtained computational data for the pressure is compared with analytical data available.

Development of a Blood Flow Model and Validation Against Experiments and Analytical Models

2010 ◽  
Author(s):  
M. H. A. van Geel ◽  
C. G. Giannopapa ◽  
B. J. van der Linden
Keyword(s):  
Blood Flow ◽  
Flow Model ◽  
Element Model ◽  
Arterial Blood Flow ◽  
Analytical Models ◽  
Experimental Investigations ◽  
Cardiovascular Research ◽  
Data Set ◽  
Arterial Blood ◽  
Blood Flow Model

In cardiovascular research, FSI is expressed by the interaction of the blood with the vessel or the heart. FSI plays a crucial role when the deformation of the boundary, in this case the vessel wall, cannot be neglected. Arterial blood flow and wave propagation in liquid filled vessels has been investigated by many researchers. Their work comprises computational, theoretical and experimental investigations and will be outlined below. This paper presents the development and validation of an arterial blood flow model. The model has been developed using finite elements and the fluid and the solid are coupled using the ALE method. This method allows moving boundaries without the need for the mesh movement to follow the material. In this paper both straight and tapered aortic analogues are included in the investigation. The pressure, pressure gradient, fluid flow and wall distension obtained from the finite element model is compared with an unique experimental data set and analytical theory. There is a good agreement between the computational, analytical and experimental results.

Preliminary observations on blood flow in the coronary arteries of two school sharks (Galeorhinus australis)

1993 ◽  
Vol 71 (6) ◽  
pp. 1238-1241 ◽  
Author(s):  
Peter S. Davie ◽  
Craig E. Franklin
Keyword(s):  
Blood Flow ◽  
Arterial Pressure ◽  
Coronary Blood Flow ◽  
Coronary Flow ◽  
Cardiac Cycle ◽  
Arterial Blood Flow ◽  
Ventricular Systole ◽  
Arterial Blood ◽  
Ventricular Mass ◽  
Aortic Blood Velocity

Coronary arterial blood flow and pressure, intraventricular blood pressure, and ventral aortic blood velocity were measured in two anaesthetized school sharks (Galeorhinus australis) in order to examine the phasic relationships between these flows and pressures. Maximum instantaneous flow recorded in the ventral coronary artery was 0.37 mL∙min−1∙kg−1 body mass (estimated 0.63 mL∙min−1∙g−1 ventricular mass). The average mean coronary blood flow was estimated as 0.28 mL∙min−1∙g−1 ventricular mass during periods of high coronary blood flow. On average, 86% of coronary flow occurred during diastole. Coronary arterial flow began during the last quarter of ventricular systole. Coronary blood flow peaked when intraventricular pressure fell to just below zero immediately after ventricular systole. Coronary blood flow fell slightly as diastole continued and reflected the small fall in coronary arterial pressure. Coronary flow reversed briefly during isovolumic ventricular contraction. Increases in the proportion of the cardiac cycle occupied by ventricular diastole, which occur during hypoxic bradycardia, have the potential to more than double coronary blood flow provided coronary arterial pressure is maintained.

scholarly journals Modelling Blood Pressure in Stenosed Coronary Arteries

2017 ◽  
Vol 61 (3) ◽  
pp. 242
Author(s):  
Viktor Szabó ◽  
Csaba Jenei ◽  
Gábor Halász
Keyword(s):  
Blood Pressure ◽  
Blood Flow ◽  
Coronary Arteries ◽  
Flow Model ◽  
Measurement Data ◽  
Arterial Blood Flow ◽  
Patient Specific ◽  
Arterial Blood ◽  
1D Model ◽  
Good Agreement

In this paper a 1D model is presented for the simulation of blood flow in stenosed coronary arteries. The model was developed by implementing a special boundary counditions in a previously published arterial blood flow model. The stenosis as well as the arterioles were modelled as linear resistances. Using patient-specific parameters, blood flow can be calculated for different inlet flow rates. The model was used to simulate blood pressure waveforms of 5 patients diagnosed with coronary stenosis. Simulation results show good agreement with measurement data.

Modeling Elastic Walls in Lattice Boltzmann Simulations of Arterial Blood Flow

2013 ◽  
Vol 23 (2) ◽  
Author(s):  
Xenia Descovich ◽  
Giuseppe Pontrelli ◽  
Sauro Succi ◽  
Simone Melchionna ◽  
Manfred Bammer
Keyword(s):  
Blood Flow ◽  
Lattice Boltzmann ◽  
Arterial Blood Flow ◽  
Arterial Blood ◽  
Lattice Boltzmann Simulations ◽  
Elastic Walls

Contribution of extravascular compression to reduction of maximal coronary blood flow

1992 ◽  
Vol 262 (1) ◽  
pp. H68-H77
Author(s):  
F. L. Abel ◽  
R. R. Zhao ◽  
R. F. Bond
Keyword(s):  
Blood Flow ◽  
Coronary Blood Flow ◽  
Coronary Flow ◽  
Perfusion Pressure ◽  
Left Ventricular Pressure ◽  
Coronary Perfusion Pressure ◽  
Left Ventricular ◽  
Ventricular Pressure ◽  
Coronary Perfusion ◽  
Storage Site

Effects of ventricular compression on maximally dilated left circumflex coronary blood flow were investigated in seven mongrel dogs under pentobarbital anesthesia. The left circumflex artery was perfused with the animals' own blood at a constant pressure (63 mmHg) while left ventricular pressure was experimentally altered. Adenosine was infused to produce maximal vasodilation, verified by the hyperemic response to coronary occlusion. Alterations of peak left ventricular pressure from 50 to 250 mmHg resulted in a linear decrease in total circumflex flow of 1.10 ml.min-1 x 100 g heart wt-1 for each 10 mmHg of peak ventricular to coronary perfusion pressure gradient; a 2.6% decrease from control levels. Similar slopes were obtained for systolic and diastolic flows as for total mean flow, implying equal compressive forces in systole as in diastole. Increases in left ventricular end-diastolic pressure accounted for 29% of the flow changes associated with an increase in peak ventricular pressure. Doubling circumferential wall tension had a minimal effect on total circumflex flow. When the slopes were extrapolated to zero, assuming linearity, a peak left ventricular pressure of 385 mmHg greater than coronary perfusion pressure would be required to reduce coronary flow to zero. The experiments were repeated in five additional animals but at different perfusion pressures from 40 to 160 mmHg. Higher perfusion pressures gave similar results but with even less effect of ventricular pressure on coronary flow or coronary conductance. These results argue for an active storage site for systolic arterial flow in the dilated coronary system.

scholarly journals Sustained Inflation Reduces Pulmonary Blood Flow during Resuscitation with an Intact Cord

Children ◽  
2021 ◽  
Vol 8 (5) ◽  
pp. 353
Author(s):  
Jayasree Nair ◽  
Lauren Davidson ◽  
Sylvia Gugino ◽  
Carmon Koenigsknecht ◽  
Justin Helman ◽  
...  
Keyword(s):  
Blood Flow ◽  
Perinatal Asphyxia ◽  
Arterial Blood Flow ◽  
Positive Pressure ◽  
Optimal Timing ◽  
Delayed Cord Clamping ◽  
Arterial Blood ◽  
Cord Clamping ◽  
Sustained Inflation ◽  
Near Term

The optimal timing of cord clamping in asphyxia is not known. Our aims were to determine the effect of ventilation (sustained inflation–SI vs. positive pressure ventilation–V) with early (ECC) or delayed cord clamping (DCC) in asphyxiated near-term lambs. We hypothesized that SI with DCC improves gas exchange and hemodynamics in near-term lambs with asphyxial bradycardia. A total of 28 lambs were asphyxiated to a mean blood pressure of 22 mmHg. Lambs were randomized based on the timing of cord clamping (ECC—immediate, DCC—60 s) and mode of initial ventilation into five groups: ECC + V, ECC + SI, DCC, DCC + V and DCC + SI. The magnitude of placental transfusion was assessed using biotinylated RBC. Though an asphyxial bradycardia model, 2–3 lambs in each group were arrested. There was no difference in primary outcomes, the time to reach baseline carotid blood flow (CBF), HR ≥ 100 bpm or MBP ≥ 40 mmHg. SI reduced pulmonary (PBF) and umbilical venous (UV) blood flow without affecting CBF or umbilical arterial blood flow. A significant reduction in PBF with SI persisted for a few minutes after birth. In our model of perinatal asphyxia, an initial SI breath increased airway pressure, and reduced PBF and UV return with an intact cord. Further clinical studies evaluating the timing of cord clamping and ventilation strategy in asphyxiated infants are warranted.

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