Shear Stress Related Blood Damage in Laminar Couette Flow

Paul, Reinhard; Apel, Jörn; Klaus, Sebastian; Schügner, Frank; Schwindke, P.; Reul, H.

doi:10.1046/j.1525-1594.2003.07103.x

Cited by 251 publications

(231 citation statements)

References 14 publications

(29 reference statements)

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“…As mentioned previously, development of vortical flow depends strongly on the annular gap width and is inversely correlated to the radii [18]. Such vortices may either originate from the end walls (outer cylinder) and propagate inwards [38], or conversely, and may manifest other forms of instabilities [40], in the narrow gap limit.…”

Section: Design Optimization Of Couette Viscometersmentioning

confidence: 82%

“…The earliest rotational viscometers were designed and used to determine altered blood viscosity during pathological conditions, such as coronary occlusion and arterial thrombosis, and RBC aggregation, under different low shear rates [13][14][15]. Computer-controlled Couette viscometers were introduced in the early 1980s to investigate change in viscosity of blood with increasing shear rates [16,17], and also to investigate abrupt critical shear stress and exposure time limits that induce hemolysis of RBC [18]. While mostly restricted to clinical applications (measurement of blood viscosity), in vitro studies investigating platelet activation and the influence of RBC on the same further led to the development of oscillatory-flow and optically transparent Couette viscometers by which flow patterns and interaction between the blood constituents could be observed under physiological conditions [16,[19][20][21][22][23].…”

Section: Annular Couette Viscometers Backgroundmentioning

confidence: 99%

“…For the narrow gap limit (radius ratio → 1), the Taylor number may be approximated as [18,34]: (2) where R e is the Reynolds number and other parameters are as defined above. The critical Taylor number for the onset of secondary flow (or Taylor vortices) has been reported to be Tc = 1712 for water [35].…”

Section: Taylor Number and Annular Flowmentioning

confidence: 99%

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Biological effects of dynamic shear stress in cardiovascular pathologies and devices

Girdhar

Bluestein

2008

Expert Review of Medical Devices

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Altered and highly dynamic shear stress conditions have been implicated in endothelial dysfunction leading to cardiovascular disease, and in thromboembolic complications in prosthetic cardiovascular devices. In addition to vascular damage, the pathological flow patterns characterizing cardiovascular pathologies and blood flow in prosthetic devices induce shear activation and damage to blood constituents. Investigation of the specific and accentuated effects of such flow-induced perturbations on individual cell-types in vitro is critical for the optimization of device design, whereby specific design modifications can be made to minimize such perturbations. Such effects are also critical in understanding the development of cardiovascular disease. This review addresses limitations to replicate such dynamic flow conditions in vitro and also introduces the idea of modified in vitro devices, one of which is developed in the authors' laboratory, with dynamic capabilities to investigate the aforementioned effects in greater detail.Keywords cardiovascular disease; cone-plate viscometers; dynamic shear stress; platelet activation; prosthetic heart valves; turbulence Implantable blood recirculation devices, artificial hearts and heart valves, have long been used as life-saving alternatives for people with severe cardiovascular diseases. However, such devices require complex anticoagulation therapy and, as a consequence, are linked to postimplant complications, such as hemorrhage. Despite the anticoagulation therapy, the risk for cardioembolic stroke is not eliminated. Although biocompatibility of these recirculation devices is of utmost importance, optimizing the geometric design of these devices is also critical to avoid flow-induced trauma to blood. Over the years, a definite link between fluid shearstress-induced damage and activation of blood constituents such as platelets and red blood cells, has been established. Irregular flow patterns arising around complex geometries (e.g., the hinge regions of mechanical heart valves [MHV]) have been recently characterized by numerical calculations and noninvasive flow measurements, and are implicated in causing flow-induced thromboembolism (TE). For instance, the Medtronic Parallel™ valve exhibited regions of elevated turbulent stress around the hinges due to its specific geometry, which, in †Author for correspondence: Department of Biomedical Engineering, State University of New York at Stony Brook, Stony Brook, NY 11794-8181, USA, Tel.: +1 631 444 1259, Fax: +1 631 444 6646, danny.bluestein@sunysb.edu. Financial & competing interests disclosure:The authors have no relevant affiliations or financial involvement with any organization or entity with a financial interest in or financial conflict with the subject matter or materials discussed in the manuscript. This includes employment, consultancies, honoraria, stock ownership or options, expert testimony, grants or patents received or pending, or royalties. No writing assistance was utilized in the production of this manu...

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Section: Design Optimization Of Couette Viscometersmentioning

confidence: 82%

Section: Annular Couette Viscometers Backgroundmentioning

confidence: 99%

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Biological effects of dynamic shear stress in cardiovascular pathologies and devices

Girdhar

Bluestein

2008

Expert Review of Medical Devices

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“…According to [60], "up to now, neither the exact mechanisms of blood damage nor the tolerable shear loads have been explicitly defined". Hence, erythrocyte damage is commonly assessed by a correlation between the shear stress and exposure time.…”

Section: Hemolysis Modelingmentioning

confidence: 99%

Biofluid Flow and Heat Transfer

Thiriet¹,

Sheu²,

Garon³

2016

Handbook of Fluid Dynamics, Second Edition

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2nd EditionInternational audienceMajor moving biological fluids, or biofluids, are blood and air that cooperate to bring oxygento the body’s cells and eliminate carbon dioxide produced by these cells. Blood is conveyed ina closed network composed of 2 circuits in series — the systemic and pulmonary circulation—, each constituted by arteries, capillaries, and veins, under the synchronized action of theleft and right cardiac pumps, respectively. Air is successively inhaled from and exhaled to theatmosphere through the airway openings (nose and/or mouth). In the head, blood generatesthe cerebrospinal fluid in choroid plexi of all compartments of the ventricular system andreceives it in arachnoid villi. Other biofluids are either secreted, such as bile from the liverand breast milk that both transport released substances with specific tasks, or excreted,such as urine from kidneys or sweat from skin glands that both convey useless materials andwaste produced by the cell metabolism. In addition to the convective transport, peristalsis,which results from the radial contraction and relaxation of mural smooth muscles, propelsthe content of the lumen of the muscular bioconduit (e.g., digestive tract) in an anterogradedirection.Blood circulation and air flow in the respiratory tract are widely explored because oftheir vital functions. Note that inhaled air is transported through the respiratory tract bytwo processes: convection down to bronchioles and diffusion down to pulmonary alveoli.1Furthermore, investigations of these physiological flows in deformable bioconduits give riseto models such as the Starling resistance that themselves become object of new study fieldsin physics and mechanics (e.g., collapsible tubes) as well as of new developments in math-ematical modeling and scientific computing. Whereas fluid–structure interaction problemsin aeronautics and civil engineering deal with materials of distinct properties, blood streamand vessel wall correspond to two domains of nearly equal physical properties, as both bloodand vessels have densities close to that of water. New processing strategies must then beconceived

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“…the high shear rate limit viscosity of blood). Although real blood is a heterogeneous non-Newtonian fluid, the modeling of blood as a homogeneous Newtonian fluid for high shear rates is widely agreed upon for flow in large arteries and valves (Paul et al, 2003;Sotiropoulos et al, 2009). Nevertheless, it is important to keep in mind that when studying low levels of shear stresses, for example in the recirculation regions and vortices in the wake, the non-Newtonian effects could become important and should be taken into account when assessing the hemodynamics of the valve (Sotiropoulos et al, 2009).…”

Section: Three-dimensional Strongly Coupled Partitioned Fsi Simulatiomentioning

confidence: 99%