An inlet cannula is provided for supplying a fluid from a human vessel to a fluid pump, the inlet cannula formed as a hollow structure suitable for conveying the fluid and a surface of the inlet cannula has an ingrowth zone and an inlet zone separated from each other by a tear-off edge extending in the circumferential direction of the inlet cannula, wherein a first tangent to the inlet zone on the tear-off edge has an angle to a longitudinal axis of the inlet cannula of >0° and <180°, and wherein a surface roughness in the ingrowth zone is greater than a surface roughness in the inlet zone, and wherein along the flow direction the ingrowth zone is concave, convex, or not curved and the inlet zone is convexly curved, and wherein the tear-off edge forms a curvature transition between the ingrowth zone and the inlet zone.

An inlet cannula is provided for supplying a fluid from a human vessel to a fluid pump, the inlet cannula formed as a hollow structure suitable for conveying the fluid and a surface of the inlet cannula has an ingrowth zone and an inlet zone separated from each other by a tear-off edge extending in the circumferential direction of the inlet cannula, wherein a first tangent to the inlet zone on the tear-off edge has an angle to a longitudinal axis of the inlet cannula of >0° and <180°, and wherein a surface roughness in the ingrowth zone is greater than a surface roughness in the inlet zone, and wherein along the flow direction the ingrowth zone is concave, convex, or not curved and the inlet zone is convexly curved, and wherein the tear-off edge forms a curvature transition between the ingrowth zone and the inlet zone.

Embodiments in the present disclosure relate to an anchoring and centering device for a circulatory support pump. An exemplary apparatus comprises an expandable anchoring device extending along a longitudinal axis, wherein the expandable anchoring device is arranged about a central axis. A distal portion of the expandable anchoring device defines an annulus through which the cardiac pump can be arranged and to which the cardiac pump can be releasable coupled. A proximal portion of the expandable anchoring device is configured to circumferentially expand to an unconstrained configuration that has a cross-sectional diameter greater than a diameter of the annulus. The exemplary apparatus also includes a constraining member arranged over the expandable anchoring device to constrain the expandable anchoring device in a constrained configuration for delivery of the anchoring apparatus.

A device and method for diverting a portion of oxygenated blood from a lower pressure region, e.g., left atrium or pulmonary vein, and providing it to the aorta, bypassing the left ventricle, operating at least in part, on the Venturi effect. The device includes a first conduit that diverts a portion of blood from the aorta to a parallel flow path. The device includes a second conduit that delivers blood from the lower pressure region to the first conduit. The blood from the lower pressure region in the second conduit is combined with the blood from the aorta in the first conduit and returned to the aorta. The second conduit is coupled to the first conduit at or near a narrow segment of the first conduit. A Venturi effect at or near the narrow segment draws the blood from the lower pressure region into the first and/or second conduit.

An intravascular blood pump having a rotatable shaft carrying an impeller and a housing with an opening through which the shaft extends with the impeller positioned outside the housing. The shaft and the housing have surfaces forming a circumferential gap which converges towards the impeller-side end of the gap and which has a minimum gap width of preferably no more than 5 μm, more preferably no more than 2 μm.

An intravascular blood pump having a rotatable shaft carrying an impeller and a housing with an opening through which the shaft extends with the impeller positioned outside the housing. The shaft and the housing have surfaces forming a circumferential gap which converges towards the impeller-side end of the gap and which has a minimum gap width of preferably no more than 5 μm, more preferably no more than 2 μm.

A control device (100) for controlling the rotational speed (n.sub.VAD(t)) of a non-pulsatile ventricular assist device, VAD, (50) uses an event-based within-a-beat control strategy, wherein the control device is configured to alter the rotational speed of the VAD within the cardiac cycle of the assisted heart and to synchronize the alteration of the rotational speed with the heartbeat by at least one sequence of trigger signals (σ(t)) that is related to at least one predetermined characteristic event in the cardiac cycle. Further, a VAD (50) for assistance of a heart comprises the control device (100) for controlling the VAD, wherein the VAD is preferably a non-pulsatile rotational, for example catheter-based, blood pump.

A control device (100) for controlling the rotational speed (n.sub.VAD(t)) of a non-pulsatile ventricular assist device, VAD, (50) uses an event-based within-a-beat control strategy, wherein the control device is configured to alter the rotational speed of the VAD within the cardiac cycle of the assisted heart and to synchronize the alteration of the rotational speed with the heartbeat by at least one sequence of trigger signals (σ(t)) that is related to at least one predetermined characteristic event in the cardiac cycle. Further, a VAD (50) for assistance of a heart comprises the control device (100) for controlling the VAD, wherein the VAD is preferably a non-pulsatile rotational, for example catheter-based, blood pump.

Provided herein are methods for in-vivo assessment of intraventricular flow shear stress, risk of hemolysis, also the location and extent of blood flow stasis regions and inside a cardiac chamber or blood vessel. Also provided herein are systems for performing such methods. Also provided herein are methods for assessing hemolysis and/or thrombosis risk in patients implanted with an LVAD. LVAD positioning and/or speed may be adjusted based on the results obtained by using methods described herein, and the risk for hemolysis and/or thrombosis can be minimized.

Provided herein are methods for in-vivo assessment of intraventricular flow shear stress, risk of hemolysis, also the location and extent of blood flow stasis regions and inside a cardiac chamber or blood vessel. Also provided herein are systems for performing such methods. Also provided herein are methods for assessing hemolysis and/or thrombosis risk in patients implanted with an LVAD. LVAD positioning and/or speed may be adjusted based on the results obtained by using methods described herein, and the risk for hemolysis and/or thrombosis can be minimized.