Development of the MEDOS/HIA DeltaStream Extracorporeal Rotary Blood Pump

Göbel, Carolin; Arvand, Arash; Eilers, Rolf; Marseille, O; Bals, Christoph; Meyns, Bart; Flameng, Willem; Rau, G.; Reul, H.

doi:10.1046/j.1525-1594.2001.025005358.x

Cited by 45 publications

(35 citation statements)

References 12 publications

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“…It is sometimes formed in a narrow gap and by hemolysis. At present, CFD of thrombus formation is only analyzed by calculating the velocity distribution in the gap (Gobel et al 2001;Tsukamoto et al 2001;Burgreen et al 2004) and shear stress Nishida et al 2006a). Figure 13.15 shows the example of geometric optimization of the blood pump using CFD analysis and antithrombogenicity.…”

Section: Cfd Of Thrombus Formationmentioning

confidence: 99%

Vascular Engineering of Circulatory Assist Devices

Nishida

2016

Vascular Engineering

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Heart failure is a condition in which the heart cannot pump sufficiently because its contractile force has deteriorated. Patients with heart failure can sometimes undergo heart transplantation, but in number these patients comprise less than 10 % of patients actually requiring heart transplantation. Thus, mechanical circulatory assistance plays an important role in substituting for heart transplantation wherein the pump function of the heart is assisted by an artificial blood pump called a ventricular assist device. On the other hand, cardiopulmonary bypass is a form of extracorporeal circulation that temporarily takes over the function of the heart and lungs to maintain the circulation of blood and the oxygen content of the body during surgery for heart failure and aneurysms of the thoracic aorta. This chapter describes the vascular engineering of circulatory assist devices. Particular emphasis is placed on recent progress in ventricular assist devices and cardiopulmonary bypass pumps. These important medical devices assist with human circulation at either the chronic or the acute phase. Because these devices are derived from an industrial pump, a great many studies have been conducted not only from the medical perspective but also from industrial and engineering perspectives. In this chapter, current ventricular assist devices and cardiopulmonary bypass pumps, their specifications, their classifications, and methods for their design and evaluating are presented, including flow analysis inside the pump to optimize the geometry.

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Section: Cfd Of Thrombus Formationmentioning

confidence: 99%

Vascular Engineering of Circulatory Assist Devices

Nishida

2016

Vascular Engineering

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“…Model parameters for (2)- (6) were obtained in experiments and fitted to the rotary blood pump model, which is a rotary (centrifugal) pump with diagonally streamed rotor (GOBEL et al, 2001). For rotational motor speed control of the blood pump, the angular velocity system state ~o was fed back to form the error of angular motor velocities eM…”

Section: Medical and Biological Engineering And Computing 2005 Vol 43 -mentioning

confidence: 99%

Robust and self-tuning blood flow control during extracorporeal circulation in the presence of system parameter uncertainties

Misgeld

Werner

Hexamer

2005

Med. Biol. Eng. Comput.

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Three different discrete controllers were designed and tuned to be used in conjunction with a rotary blood pump during cardiopulmonary heart-lung support. The controllers were designed to operate in both steady and pulsatile modes. The system and methods were tested in a circulatory haemodynamic simulator. To guarantee stable control of the non-linear circulatory system in the presence of patient parameter uncertainties, a proportional plus integral (PI) and an H infinity controller were robustly tuned, using a non-linear time-varying model. (H infinity refers to the Hardy space, the set of bounded functions, analytic in the right half plane. The H infinity controller is the solution to the H infinity norm optimisation problem.) A self-tuning general predictive controller (GPC), together with an adaptive Kalman filter (KF) estimator, was compared with the two robustly tuned controllers. The closed-loop blood flow control circuit was set up in simulation routines first. The blood flow controllers were validated in a circulatory hydrodynamic simulator (MOCK) combined with a rotary blood pump. Parameters of the system simulator were changed continuously, and the controllers were tested over a wide range of different operating points. Disturbances in the form of discontinuous additive parameter uncertainties were applied. The closed-loop systems remained robustly stable. The robustly tuned H infinity controller showed the best control performance, in contrast to the GPC controller, which was near instability in regions of strongly varying non-linear system gain. Compared with the H infinity controller, the PI controller showed slightly worse behaviour, but the closed-loop response was acceptable, even in regions of strongly varying non-linear system gain and during pulsatile perfusion. The rotary blood pump could provide stationary and pulsatile perfusion under control conditions. Controlled variables were hereby mean blood flow, pulsatility index and heart rate. All three controllers were developed for an arterial mean flow of 0-6 l min(-1) and a heart rate of up to 70 beats per minute. Pulsatile closed-loop perfusion could provide up to 30 mmHg pressure variation in the simulated ascending aorta at a mean flow of 3 l min(-1).

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“…Um diese Nachteile zu reduzieren, wurden miniaturisierte Herz-Lungen-Maschinen entwickelt [4,5]. Außerdem lassen sich durch diese Systeme gravierende hämodynamische Beeinträchtigungen oder myokardiale Ischämien, wie sie bei Operationen ohne Herz-Lungen-Maschine vorkommen können [1], vermeiden.…”

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