A vascular coupling device for connecting an artificial heart pump to the vascular system of a subject is disclosed. The artificial heart pump may form part of a total artificial heart (TAH). The vascular coupling device comprises a first and a second coupling element, each one of said first and second coupling elements has a first end comprising a resilient coupling portion, a second end comprising a vascular grafting material, and a tubular midsection is arranged between said first and second ends. The vascular coupling device further comprises a coupling plate comprising a first receptor and a second receptor configured and adapted for receiving said resilient coupling portions of the first and second coupling elements. The vascular coupling device further comprises a docking plate, comprising a first and a second docking port configured to be arranged to an inlet channel and an outlet channel of said artificial heart pump and one or more fastening means for connecting said coupling plate to the docking plate. A method for connecting the vascular coupling device to the vascular system of a subject is also disclosed.

An integrated flow source is a limiting factor in numerous microfluidic applications. In addition to precise gradients and controlling molecular transports, a built-in source of stable and accurate flow can enable novel shear stress modulations for long-term cell culturing studies. The Tesla turbine, when used as a pump on the microfluidic regime, produces stable and accurate fluid gradients by utilizing laminar flow between its rotating discs Utilizing a stereolithography based 3D printer, a tesla pump (Ø10 cm) and associated housing capable of driving a microfluidic gradient is provided having a printed rotor surface topology of the pump in order to enhance pumping of biological fluids like blood at elevated viscosities. The surface topology is tuned via 3D pixilation, and this modulation completely recovered the pressure loss between pumping water at 1 cP versus glycerol solution at 3 cP. As a result, increased fluid viscosities, and even Non-Newtonian viscosities, can be used.

Devices for moving blood within a patient, and methods of doing so. The devices can include a pump portion that includes an impeller and a housing around the impeller, as well as a fluid lumen. The impeller can be activated to cause rotation of the impeller and thereby move fluid within the fluid lumen.

Devices for moving blood within a patient, and methods of doing so. The devices can include a pump portion that includes an impeller and a housing around the impeller, as well as a fluid lumen. The impeller can be activated to cause rotation of the impeller and thereby move fluid within the fluid lumen.

A controller for an implantable blood pump includes processing circuitry configured to initiate a suction response algorithm if a combination of a number of detected suction events multiplied by a suction event variable and a number of non-suction events multiplied by a non-suction event variable exceed a predetermined threshold.

A controller for an implantable blood pump includes processing circuitry configured to initiate a suction response algorithm if a combination of a number of detected suction events multiplied by a suction event variable and a number of non-suction events multiplied by a non-suction event variable exceed a predetermined threshold.

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.