Fluid shear stress in prosthetic heart valves

Roschke, E. J.; Harrison, Earl C.

doi:10.1016/0021-9290(77)90003-3

Cited by 24 publications

(6 citation statements)

References 33 publications

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“…This was the conclusion reached by Blackshear. 1 Insofar as normally functioning prosthetic valves are concerned, particularly ball-and disk-type valves, a recent analysis by Roschke et al 20 suggests that red cells passing through such valves could be exposed to boundary layer stresses sufficiently high for sufficiently long times to cause lysis.…”

Section: Free Shear Layermentioning

confidence: 99%

Flow-induced trauma to blood cells.

Sutera¹

1977

Circulation Research

130

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Section: Free Shear Layermentioning

confidence: 99%

Flow-induced trauma to blood cells.

Sutera¹

1977

Circulation Research

130

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“…Identification of arterial regions of low wall shear stress (WSS) would predict progression of atherosclerosis [10], localization of high-risk coronary atherosclerotic plaques, vessel wall remodeling [11], and abdominal aortic aneurysm (AAA) [12], [13]. Furthermore, identification of specific regions in the prosthetic valve leaflets [14], the cardiopulmonary bypass machine [15], and left ventricular assist device (LVAD) would predict thrombus formation [16]. In this context, the ability to measure real-time shear stress would advance the field of cardiovascular research.…”

Section: Introductionmentioning

confidence: 99%

Real-Time Intravascular Shear Stress in the Rabbit Abdominal Aorta

Dai

et al. 2009

IEEE Trans. Biomed. Eng.

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Fluid shear stress is intimately linked with the biological activities of vascular cells. A flexible microelectromechanical system (MEMS) sensor was developed to assess spatial- and temporal-varying components of intravascular shear stress (ISS) in the abdominal aorta of adult New Zealand white (NZW) rabbits. Real-time ISS (ISSreal-time) was analyzed in comparison with computational fluid dynamics (CFD) simulations for wall shear stress (WSS). Three-dimensional abdominal arterial geometry and mesh were created using the GAMBIT software. Simulation of arterial flow profiles was established by FLUENT. The Navier–Stokes equations were solved for non-Newtonian blood flow. The coaxial-wire-based MEMS sensor was deployed into the abdominal arteries of rabbits via a femoral artery cutdown. Based on the CFD analysis, the entrance length of the sensor on the coaxial wire (0.4 mm in diameter) was less than 10 mm. Three-dimensional fluoroscope and contrast dye allowed for visualization of the positions of the sensor and ratios of vessel to coaxial wire diameters. Doppler ultrasound provided the velocity profiles for the CFD boundary conditions. If the coaxial wire were positioned at the center of vessel, the CFD analysis revealed a mean ISS value of 31.1 with a systolic peak at 102.8 dyn · cm−2. The mean WSS was computed to be 10.1 dyn · cm−2 with a systolic peak at 33.2 dyn · cm−2, and the introduction of coaxial wire increased the mean WSS by 5.4 dyn · cm−2 and systolic peak by 18.0 dyn · cm−2. Experimentally, the mean ISS was 11.9 dyn · cm−2 with a systolic peak at 47.0 dyn · cm−2. The waveform of experimental ISS was similar to that of CFD solution with a 30.2% difference in mean and 8.9% in peak systolic shear stress. Despite the difference between CD and experimental results, the flexible coaxial-wire-based MEMS sensors provided a possibility to assess real-time ISS in the abdominal aorta of NZW rabbits.

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“…Red cell tethering subsequently increases the vulnerability for shear stress or turbulence-related red cell fracture, which may occur at modest shear stresses. 18 Residual nativevalve fissuring and endothelial denudation after balloon dilatation and balloon-expandable transcatheter valve insertion likely served as an additional nidus for red cell tethering and subsequent hemolysis. This could partially explain the higher hemolysis rate post-TAVI compared with the traditionally lower hemolysis rates post-bioprosthetic SAVR.…”

Section: Discussionmentioning

confidence: 99%