A numerical simulation of steady flow fields in a bypass tube

Lee, Denz; Su, J.; Liang, H. Y.

doi:10.1016/s0021-9290(01)00131-2

Cited by 45 publications

(31 citation statements)

References 23 publications

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“…The higher the Reynolds number and anastomosis angle, the more the flow is skewed towards the anastomosis floor and the higher the observed shear rates. 45 The hemodynamic parameters are also strongly dependent on the graft end design: extreme hemodynamic factors are noticed in grafts when bulges are present. 54 The vessel geometry also influences the WSS values importantly.…”

Section: Computational Studiesmentioning

confidence: 99%

Hemodynamics and Complications Encountered with Arteriovenous Fistulas and Grafts as Vascular Access for Hemodialysis: A Review

et al. 2005

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This review article describes the current state of affairs concerning in vivo, in vitro and in numero studies on the hemodynamics in vascular access for hemodialysis. The use and complications of autogenous and non-autogenous fistulas and catheters and access port devices are explained in the first part. The major hemodynamic complications are stenosis, initiated by intimal hyperplasia development, and thrombosis. The different in literature proposed conceivable causes of intimal hyperplasia development like surgical interventions, compliance mismatch, wall shear stress (WSS) and shear rate, vessel wall thrill and blood pressure are discussed on the basis of in vivo, in vitro and in numero studies.

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Section: Computational Studiesmentioning

confidence: 99%

Hemodynamics and Complications Encountered with Arteriovenous Fistulas and Grafts as Vascular Access for Hemodialysis: A Review

et al. 2005

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“…Studies on idealized three-dimensional models were carried out under steady-state conditions and pulsatile conditions. Steady analyses were performed by Henry et al (1996), by Kute and Vorp (2001) to investigate the effects of the flow at the proximal anastomosis on the fluid dynamics at the distal one and by Lee et al (2001) to explore the effects of the Reynolds number (in the range 100-400) as well as of the anastomosis angle, although in a rather simplistic model. Transient analyses were carried out by Kleinstreuer et al (1996) and Lei et al (1996Lei et al ( , 1997a to compare the effects of a standard anastomosis, a Taylor patch technique (where an autologous vein patch is inserted at the distal end of the PTFE graft) and an optimized geometry on distal temporal and time-averaged wall shear stress gradients.…”

Section: Peripheral Bypass Anastomosesmentioning

confidence: 99%

Computational modeling of vascular anastomoses

Migliavacca

Dubini

2005

Biomech Model Mechanobiol

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Recent development of computational technology allows a level of knowledge of biomechanical factors in the healthy or pathological cardiovascular system that was unthinkable a few years ago. In particular, computational fluid dynamics (CFD) and computational structural (CS) analyses have been used to evaluate specific quantities, such as fluid and wall stresses and strains, which are very difficult to measure in vivo. Indeed, CFD and CS offer much more variability and resolution than in vitro and in vivo methods, yet computations must be validated by careful comparison with experimental and clinical data. The enormous parallel development of clinical imaging such as magnetic resonance or computed tomography opens a new way toward a detailed patient-specific description of the actual hemodynamics and structural behavior of living tissues. Coupling of CFD/CS and clinical images is becoming a standard evaluation that is expected to become part of the clinical practice in the diagnosis and in the surgical planning in advanced medical centers. This review focuses on computational studies of fluid and structural dynamics of a number of vascular anastomoses: the coronary bypass graft anastomoses, the arterial peripheral anastomoses, the arterio-venous graft anastomoses and the vascular anastomoses performed in the correction of congenital heart diseases.

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“…The In the near future I would like to apply the developed numerical code for the numerical simulation of a steady flow in a complete bypass tube following study [2], but with respect to a non-Newtonian character of the blood.…”

Section: Numerical Results and Conclusionmentioning

confidence: 99%

“…[2], but with respect to non-Newtonian character of the blood. Blood flow can be assumed to behave as an incompressible continuum.…”

Section: Introductionmentioning

confidence: 99%

Modelling of Newtonian and Non‐Newtonian Incompressible Fluid Flow

Vimmr

2006

Proc Appl Math and Mech

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This paper deals with numerical simulation of steady laminar incompressible Newtonian and non-Newtonian fluid flow. The viscosity of non-Newtonian fluid is modelled using the fluid power law. The mathematical model is described by the non-linear conservative system of the incompressible Navier-Stokes equations that is solved using the explicit two-step MacCormack scheme with artificial viscosity together with the pseudo-compressibility method. The spatial discretization is performed by the cell-centred finite volume method on a structured quadrilateral grid.

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A numerical simulation of steady flow fields in a bypass tube

Cited by 45 publications

References 23 publications

Hemodynamics and Complications Encountered with Arteriovenous Fistulas and Grafts as Vascular Access for Hemodialysis: A Review

Hemodynamics and Complications Encountered with Arteriovenous Fistulas and Grafts as Vascular Access for Hemodialysis: A Review

Computational modeling of vascular anastomoses

Modelling of Newtonian and Non‐Newtonian Incompressible Fluid Flow

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