Fluid-Structure Interaction Simulation of Blood Flow Inside a Diseased Left Ventricle With Obstructive Hypertrophic Cardiomyopathy in Early Systole

2009 ◽  
Author(s):  
Ahmad Moghaddaszade-Kermani ◽  
Peter Oshkai ◽  
Afzal Suleman
Keyword(s):  
Blood Flow ◽  
Hypertrophic Cardiomyopathy ◽  
Left Ventricle ◽  
Fluid Structure Interaction ◽  
Left Ventricular Pressure ◽  
Left Ventricular ◽  
Ventricular Pressure ◽  
Fluid Structure ◽  
Structure Interaction ◽  
Systolic Phase

Mitral-Septal contact has been proven to be the cause of obstruction in the left ventricle with hypertrophic cardiomyopathy (HC). This paper presents a study on the fluid mechanics of obstruction using two-way loosely coupled fluid-structure interaction (FSI) methodology. A parametric model for the geometry of the diseased left ventricular cavity, myocardium and mitral valve has been developed, using the dimensions extracted from magnetic resonance images. The three-element Windkessel model [1] was modified for HC and solved to introduce pressure boundary condition to the aortic aperture in the systolic phase. The FSI algorithm starts at the beginning of systolic phase by applying the left ventricular pressure to the internal surface of the myocardium to contract the muscle. The displacements of the myocardium and mitral leaflets were calculated using the nonlinear finite element hyperelastic model [2] and subsequently transferred to the fluid domain. The fluid mesh was moved accordingly and the Navier-Stokes equations were solved in the laminar regime with the new mesh using the finite volume method. In the next time step, the left ventricular pressure was increased to contract the muscle further and the same procedure was repeated for the fluid solution. The results show that blood flow jet applies a drag force to the mitral leaflets which in turn causes the leaflet to deform toward the septum thus creating a narrow passage and possible obstruction.

Investigation of the Blood Flow and Mitral-Septal Opposition in the Left Ventricle With the Obstructive Hyperthrophic Cardiomyopathy During Systole Using Fluid-Structure Interaction Technique

2010 ◽  
Author(s):  
Ahmad Moghaddaszade Kermani ◽  
Afzal Suleman
Keyword(s):  
Blood Flow ◽  
Mitral Valve ◽  
Left Ventricle ◽  
Fluid Structure Interaction ◽  
Left Ventricular ◽  
Anterior Leaflet ◽  
Fluid Structure ◽  
Structure Interaction ◽  
Narrow Passage ◽  
Aortic Orifice

In this article, fluid-structure interaction methodology was used to analyze the blood flow and Mitral-Septal opposition in the Left ventricle with the Obstructive Hyperthrophic Cardiomyopathy (OHCM). The geometry of the computational model includes the diseased left ventricle with thickened septum and Mitral valve. A semi-ellipsoidal geometry was developed with the dimensions, extracted from MR images of the diseased left ventricle. Also, the geometry of the Mitral valve was created using anatomical data provided in literature [1]. The three element Windkessel model and atrial pressure [2, 3] were used to introduce mass flow and pressure boundary conditions to the aortic orifice and left atrium respectively. Effect of the fibers was taken into account by varying the Young’s modulus of the mitral valve tissue with circumferential and radial coordinates. The fluid-structure interaction algorithm started at the beginning of the systole (when the mitral valve is fully open with zero stress) by applying the left ventricular pressure on the left ventricular wall and aortic mass flow outlet on the aortic orifice. The Navier-Stokes equations were solved with SIMPLE algorithm and finite volume method to calculate the blood flow inside the diseased left ventricle. The calculated pressure was applied to the surface of the mitral valve and the structural model of the tissue was solved using non-linear finite element. The deformation of the mitral valve was transferred to the blood by moving the fluid mesh. In the next time step, the same procedure was repeated with the new mesh. This algorithm was followed up to the end of the systole. The thickened septum creates a narrow passage for the blood flowing out of the left ventricle, thus a jet of blood flow is developed in this narrow passage which applies high shear stress on the anterior leaflet of the mitral valve. The drag force deforms the anterior leaflet toward the septum, obstructing the blood flow rushing toward the aortic orifice.

Fluid-Structure Interaction Modeling and Validation of Idealized Left Ventricular Blood Flow

2020 ◽  
Author(s):  
Megan Laughlin ◽  
Sam Stephens ◽  
Hanna Jensen ◽  
Morten Jensen ◽  
Paul Millett
Keyword(s):  
Blood Flow ◽  
Fluid Structure Interaction ◽  
Flow Analysis ◽  
Left Ventricular ◽  
Maximum Pressure ◽  
Flow Loop ◽  
Fluid Structure ◽  
Pressure Drops ◽  
Structure Interaction ◽  
Custom Made

Abstract Fluid Structure Interaction (FSI) models are an essential tool in understanding the complex coupling of blood flow in the heart. The objective of this study is to establish a method of comparing data obtained from FSI models and benchtop measurements from phantoms to identify sources of flow changes for use in intraventricular flow analysis. Two geometries are considered: 1) a vascular model consisting of a straight channel with an ellipsoidal swell and 2) an idealized left ventricle (LV) model representative “acorn” shape. Two phantoms are created for each of the two geometries: 3D printed rigid phantoms from a resin and custom-made tissue-mimicking phantoms from a medical gel. Benchtop measurements are made using the phantoms within a custom flow loop setup with pulsatile flow. Computational Fluid Dynamics (CFD) simulations are conducted with a Smoothed Particle Hydrodynamics (SPH) model. The two flow channel geometries utilized in the experiments are replicated for the simulations. The cavity walls are defined by ghost particles that are rigidly fixed. Maximum pressure drops were 57 mmHg and 196 mmHg for the rigid swell and rigid LV, respectively, whereas maximum pressure drops were 155 mmHg for the gel swell and 140 mmHg for the gel LV. Calculations from the simulations resulted in a maximum pressure drop of 55 mmHg for the swell and 110 mmHg for the LV. This data serves as a first step in corroborating our methodology to utilize the information obtained from both methods to identify and better understand mutual sources of changes in flow patterns.

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.

Modeling of aortic valve stenosis using fluid-structure interaction method

Perfusion ◽  
2021 ◽  
pp. 026765912199854
Author(s):  
Mohammad Javad Ghasemi Pour ◽  
Kamran Hassani ◽  
Morteza Khayat ◽  
Shahram Etemadi Haghighi
Keyword(s):  
Blood Flow ◽  
Aortic Valve ◽  
Fluid Structure Interaction ◽  
Three Dimensional ◽  
Fluid Structure ◽  
Structure Interaction ◽  
Relaxation Phase ◽  
Exercise Condition ◽  
Time Dependent Domain ◽  
Comparison Of The Results

Background and objectives: Fluid structure interaction (FSI) is defined as interaction of the structures with contacting fluids. The aortic valve experiences the interaction with blood flow in systolic phase. In this study, we have tried to predict the hemodynamics of blood flow through a normal and stenotic aortic valve in two relaxation and exercise conditions using a three-dimensional FSI method. Methods: The aorta valve was modeled as a three-dimensional geometry including a normal model and two others with 25% and 50% stenosis. The geometry of the aortic valve was extracted from CT images and the models were generated by MMIMCS software and then they were implemented in ANSYS software. The pulsatile flow rate was used for all cases and the numerical simulations were conducted based on a time-dependent domain. Results: The obtained results including the velocity, pressure, and shear stress contours in different systolic time sequences were explained and discussed. The maximum blood flow velocity in relaxation phase was obtained 1.62 m/s (normal valve), 3.78 m/s (25% stenosed valve), and 4.73 m/s (50% stenosed valve). In exercise condition, the maximum velocities are 2.86, 4.32, and 5.42 m/s respectively. The maximum blood pressure in relaxation phase was calculated 111.45 mmHg (normal), 148.66 mmHg (25% stenosed), and 164.21 mmHg (50% stenosed). However, the calculated values in exercise situation were 129.57, 163.58, and 191.26 mmHg. The validation of the predicted results was also conducted using existing literature. Conclusions: We believe that such model are useful tools for biomechanical experts. The further studies should be done using experimental data and the data are implemented on the boundary conditions for better comparison of the results.

Axisymmetric fluid-structure interaction model of the left ventricle

2003 ◽  
pp. 1669-1672 ◽  
Author(s):  
Dimitri Deserranno ◽  
Zoran B. Popovic ◽  
Neil L. Greenberg ◽  
Mohammad Kassemi ◽  
James D. Thomas
Keyword(s):  
Left Ventricle ◽  
Fluid Structure Interaction ◽  
Interaction Model ◽  
Fluid Structure ◽  
Structure Interaction

PERSONALIZED FSI-MODELING OF THE AORTIC BULB AND ARCH TO PREDICT ITS MECHANICAL BEHAVIOR AND ASSESS THE LOADS DURING THE CARDIAC CYCLE

2021 ◽  
Vol 11 (2) ◽  
pp. 13-16
Author(s):  
Artur Ovsepyan ◽  
Alexander Smirnov ◽  
Sergey Dydykin ◽  
Yuriy Vasil'ev ◽  
Evgeniy Trunin ◽  
...  
Keyword(s):  
Blood Flow ◽  
Mechanical Behavior ◽  
Dynamic Model ◽  
Cardiac Cycle ◽  
Fluid Structure Interaction ◽  
Complex Dynamic ◽  
Fluid Structure ◽  
Structure Interaction ◽  
Dynamic Event

The interaction of the blood flow with the aorta is a complex dynamic event described in biomechanics as the Fluid-structure interaction. In this study we’ve developed a method for creation of a personalized 3D dynamic model of the aortic bulb and arch for the prediction of its mechanical behavior using FSI-analysis. We found that the accuracy of predicting geometric aortic deformities based on FSI modeling is on average 92%.

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