Abstract: The blood pump (10) comprises an elongate drive portion (11) and a pump portion (12) lengthening the latter. Between the two portions, flow openings (17) are positioned. According to the invention, the flow openings (17) are covered by a screen (24) preventing the blood pump from sucking fast on tissue parts or cardiac valves or from sucking in endogenous tissue and being blocked thereby.

Abstract: The pump (10) comprises a drive portion (11) and a pump portion (12) which have such a small diameter that they can be pushed through a blood vessel (31). The pump portion (12) has a flexible cannula (18) connected thereto. In order to reduce the flow resistance of the cannula (18), the cannula (18) can be dilated to a diameter that is larger than that of the drive portion (11) and the pump portion (12), respectively. To be able to introduce the pump into the body by puncturing the blood vessel (31) according to the Seldinger technique, the cannula (18) is set into the constricted state in which it has a small diameter. In the blood vessel (31), it is dilated so that it offers a small flow resistance to the blood to be pumped there.

Abstract: An intravascular blood pump designed to be advanced through the blood vessel system of the patient, comprises a housing (15) accommodating an electric motor (12), the proximal end of the housing (15) being connected to a catheter (23) and the distal end thereof carrying a pump (11). The electric motor (12) includes a stator winding (17) forming a load-bearing component of the housing (15). The stator winding (17) is embedded in a matrix made of synthetic resin. The housing (15) is of an ironless design without any magnetic reflux device. The motor is operated with a rotational speed of about 50,000 upm. The magnetic stray field generated with such high frequencies does not disturb the cardiac rhythm of the patient. The motor can be given a compact size and thus has a high mechanical output power.

Abstract: An intracardiac rotary pump (10) is provided with a pressure differential sensor (18) for supporting the pumping heart. The pressure differential sensor measures the pressure differential between aorta (AO) and left ventricle (LV). This pressure differential must correspond to certain desired values at different speed stages. If the pressure differential deviates to too large an extent, the deviation is recognized as a drift of the pressure sensor, and a correction value is determined in dependence on the drift, the subsequently measured pressure values being corrected with the aid of this correction value. In this manner it is possible to carry out a drift correction on the sensor with the pump arranged in the heart and even with the pump in operation.

Abstract: The paracardiac blood pump is destined for protruding through the cardiac wall into the heart with a portion of its housing (10) and for suctioning blood from the heart. The blood is pumped into one of the blood vessels connected with the heart through a line that extends outside the heart. A cannula (30) is arranged in front of the inlet (17) of the pump ring (16). The housing (10) and the cannula (30) have approximately the same outer diameters of 13 mm at most. The housing, together with the cannula (30), can thus be inserted into the heart through a puncture hole that is produced in the cardiac wall without removing material.

Abstract: The micromotor serves to drive an impeller (12) rotating in a pump housing (14). The excitation winding of the micromotor is surrounded by an enveloping flux return structure (18) of ferromagnetic material divided into rings (35). The rings (35) are separated from each other by slots (25). The slots are produced by laser cutting of a continuous tube. The enveloping flux return structure has a small wall thickness of a few tenths of a millimeter. The rings (35) are mutually connected by bridges (26). The enveloping flux return structure (18) can be integrally formed with the pump housing (14) of the pump (11). The micromotor can be produced in a small format with a small diameter. It has a high flow rate at a correspondingly high rotational speed. The micromotor is particularly suitable for introducing blood pumps into the vascular system in a non-operative minimally invasive percutaneous manner.

Abstract: The blood pump comprises a pump casing (10) in which an impeller (16) is installed without any bearing. Said impeller (16) is rotated via a magnetic coupling (32,36) by an external magnetic driving means (33). The impeller is radially centered via the magnetic coupling (32,36). The lower side (30) of the blades (19) of the impeller is configured as supporting surface (30) sloping towards the trailing end. In this way a hydrodynamical supporting effect is attained during rotation such that the impeller (16) raises from the bottom surface (12) of the pump casing (10). Since no bearings and sealings are provided on the pump casing the danger of thrombosis and the danger of penetration of foreign bodies in the form of abrasive particles into the blood is reduced.

Abstract: The paracardiac blood pump is destined designed for protruding through the cardiac wall into the heart with a portion of its housing (10) and for suctioning blood from the heart. The blood is pumped into one of the blood vessels connected with the heart through a line that extends outside the heart. A cannula (30) is arranged in front of the inlet (17) of the pump ring (16). The housing (10) and the cannula (30) have approximately the same outer diameters of 13 mm at most. The housing, together with the cannula (30), can thus be inserted into the heart through a puncture hole that is produced in the cardiac wall without removing material.