DEVICE TO ASSIST THE PERFORMANCE OF A HEART

Abstract

A device to assist the performance of a heart with at least one pump that is formed as a rotary pump and magnetically driven.

Claims

1. A heart assist pump device configured to be positioned within a patient's body and comprising: a blood flow path comprising: an inflow tube with a distal suction end configured to be inserted into a ventricle of a heart, wherein the inflow tube is substantially linear and comprises a central axis, wherein the distal suction end is aligned with the central axis; a first chamber comprising one or more walls and a substantially planar bottom wall having an inner surface that is located at a position that is axially opposite of the distal suction end, the first chamber fluid communication with the inflow tube, wherein the first chamber is aligned with the central axis; and a blood outflow path located downstream of the inflow tube and in fluid communication with the first chamber and with a blood vessel of the body, and configured to direct blood in at least one direction that is not aligned with the central axis; a magnetic rotor assembly comprising a rotor and a first magnetic device located within the first chamber, wherein the first magnetic device is a single magnetic device that is coupled to the rotor; a second magnetic device associated with, and sealed from, the magnetic rotor assembly and configured to rotate the magnetic rotor assembly by a magneto coupling with the magnetic rotor assembly, wherein the second magnetic device is a single magnetic device, wherein the magnetic rotor assembly and the second magnetic device are aligned with the central axis and wherein the magneto coupling is configured to control an axial and/or a radial position of the magnetic rotor assembly is controlled relative to the second magnetic device; a gap between a side wall of the first chamber and the magnetic rotor assembly, the gap axially aligned with the central axis, wherein the gap is defined by the controlled axial and/or radial position of the magnetic rotor assembly, wherein the gap comprises an inner diameter that is smaller than an inner diameter of the inflow tube; and guide surfaces on the magnetic rotor assembly in fluid communication with the blood flowing through the blood flow path, the guide surfaces configured to produce centrifugal components within the blood during rotation of the magnetic rotor assembly, wherein the guide surfaces are spaced axially away from the first magnetic device, and wherein the guide surfaces of the magnetic rotor assembly are configured to drive the blood flow along the blood outflow path.

2. The heart assist pump device of claim 1, further comprising a second chamber that surrounds the second magnetic device and comprises one or more walls that seal the second magnetic device from the magnetic rotor assembly.

3. The heart assist pump device of claim 1, wherein the guide surfaces are spaced axially away from the inner surface of the substantially planar bottom wall.

4. The heart assist pump device of claim 1, wherein the second magnetic device is axially closer to the first magnetic device than to the guide surfaces of the rotor.

5. (canceled)

6. The heart assist pump device of claim 1, wherein at least part of the blood outflow path is configured to direct the blood driven by the guide surfaces in a direction that is substantially perpendicular to the central axis.

7. The heart assist pump device of claim 1, wherein the guide surfaces are configured to drive the blood within the first chamber in a direction that is substantially perpendicular to the inflow tube and to the central axis.

8. The heart assist pump device of claim 1, wherein the second magnetic device is spaced axially from the guide surfaces of the rotor.

9. The heart assist pump device of claim 1, wherein the blood vessel is an artery.

10. The heart assist pump device of claim 1, wherein the blood vessel is an aorta.

11. The heart assist pump device of claim 1, wherein the ventricle is a left ventricle.

12. The heart assist pump device of claim 1, further comprising a control arrangement comprising at least one sensor configured to generate a control signal, and a controller configured to receive the generated control signal.

13. The heart assist pump device of claim 12, wherein the control arrangement is configured to control the heart assist pump device.

14. The heart assist pump device of claim 1, wherein the magneto coupling is configured to control an axial and/or a radial position of the magnetic rotor assembly relative to the second magnetic device and orient the magnetic rotor assembly such that the magnetic rotor assembly remains adjacent to, and spaced apart from, the side wall of the first chamber by the gap.

15. The heart assist pump device of claim 1, wherein the magneto coupling is configured to passively control an axial and/or radial position of the magnetic rotor assembly relative to the second magnetic device and orient the magnetic rotor assembly such that the magnetic rotor assembly remains adjacent to, and spaced apart from, the side wall of the first chamber by the gap.

16. The heart assist pump device of claim 1, wherein the magneto coupling is configured to magnetically control an axial and/or radial position of the magnetic rotor assembly relative to the second magnetic device and orient the magnetic rotor assembly such that the magnetic rotor assembly remains adjacent to, and spaced apart from, the side wall of the first chamber by the gap.

17. A heart assist pump device configured to be positioned within a patient's body and comprising: a blood flow path comprising: an inflow tube with a distal suction end configured to be inserted into a ventricle of a heart, wherein the inflow tube is substantially linear and comprises a central axis, wherein the distal suction end is aligned with the central axis; a first chamber comprising one or more walls and a substantially planar bottom wall having an inner surface that is located at a position that is axially opposite of the distal suction end, the first chamber in fluid communication with the inflow tube, wherein the first chamber is axially aligned with the central axis; and a blood outflow path located downstream of the inflow tube and in fluid communication with the first chamber and with a blood vessel of the body, and configured to direct blood in at least one direction that is not axially aligned with the central axis; a magnetic rotor assembly comprising a rotor and a first magnetic device located within the first chamber, wherein the first magnetic device is a single magnetic device that is coupled to the rotor; a second magnetic device associated with, and sealed from, the magnetic rotor assembly and configured to rotate the magnetic rotor assembly by a magneto coupling with the magnetic rotor assembly, wherein the second magnetic device is a single magnetic device, wherein the magnetic rotor assembly and the second magnetic device are aligned with the central axis and wherein the magneto coupling is configured to passively control an axial and/or a radial position of the magnetic rotor assembly relative to the second magnetic device a gap between a side wall of the first chamber and the magnetic rotor assembly, the gap axially aligned with the central axis and configured for blood flow therethrough, wherein the gap is defined by the controlled axial and/or radial position of the magnetic rotor assembly, wherein the gap comprises an inner diameter that is smaller than an inner diameter of the inflow tube; and guide surfaces on the magnetic rotor assembly in fluid communication with the blood flowing through the blood flow path, the guide surfaces configured to produce centrifugal components within the blood during rotation of the magnetic rotor assembly, wherein the guide surfaces are spaced axially away from the first magnetic device, and wherein the guide surfaces of the magnetic rotor assembly are configured to drive the blood flow along the blood outflow path.

18. The heart assist pump device of claim 17, further comprising a second chamber that surrounds the second magnetic device and comprises one or more walls that seal the second magnetic device from the magnetic rotor assembly.

19. The heart assist pump device of claim 17, wherein the guide surfaces are spaced axially away from the inner surface of the substantially planar bottom wall.

20. The heart assist pump device of claim 17, wherein the second magnetic device is axially closer to the first magnetic device than to the guide surfaces of the rotor.

21. (canceled)

22. The heart assist pump device of claim 17, wherein at least part of the blood outflow path is configured to direct the blood driven by the guide surfaces in a direction that is substantially perpendicular to the central axis.

23. The heart assist pump device of claim 17, wherein the guide surfaces are configured to drive the blood within the first chamber in a direction that is substantially perpendicular to the inflow tube and to the central axis.

24. The heart assist pump device of claim 17, wherein the second magnetic device is spaced axially from the guide surfaces of the rotor.

25. The heart assist pump device of claim 17, wherein the blood vessel is an artery.

26. The heart assist pump device of claim 17, wherein the blood vessel is an aorta.

27. The heart assist pump device of claim 17, wherein the ventricle is a left ventricle.

28. The heart assist pump device of claim 17, further comprising a control arrangement comprising at least one sensor configured to generate a control signal, and a controller configured to receive the generated control signal.

29. The heart assist pump device of claim 28, wherein the control arrangement is configured to control the heart assist pump device.

30. The heart assist pump device of claim 17, wherein the magnetic rotor assembly and the second magnetic device are axially aligned with the central axis and wherein the magneto coupling is configured to orient the magnetic rotor assembly such that the magnetic rotor assembly remains adjacent to, and spaced apart from, the side wall of the first chamber by the gap.

31. A method for assisting the blood circulation of a heart in a body, comprising: providing a heart assist device configured to be positioned within the body, comprising: a blood flow path comprising: an inflow tube with a distal suction end configured to be inserted into a left ventricle of a heart, wherein the inflow tube is substantially linear and comprises a central axis, and wherein the distal suction end is aligned with the central axis; a first chamber comprising one or more walls and a substantially planar bottom wall having an inner surface that is located at a position that is axially opposite of the distal suction end, the first chamber in fluid communication with the inflow tube, wherein the first chamber is aligned with the central axis; and a blood outflow path located downstream of the inflow tube and in fluid communication with the first chamber and with an aorta of the body, and configured to direct blood in at least one direction that is not axially aligned with the central axis; a magnetic rotor assembly comprising a rotor and a first magnetic device located within the first chamber, wherein the first magnetic device is a single magnetic device; a second magnetic device associated with, and sealed from, the magnetic rotor assembly and configured to rotate the magnetic rotor assembly by a magneto coupling with the magnetic rotor assembly, wherein the second magnetic device is a single magnetic device, wherein an axial position and/or a radial position of the magnetic rotor assembly is controlled relative to the second magnetic device by the magneto coupling, wherein the magnetic rotor assembly and the second magnetic device are aligned with the central axis; a gap between a side wall of the first chamber and the magnetic rotor assembly, the gap axially aligned with the central axis and configured for blood flow therethrough, wherein the gap comprises an inner diameter that is smaller than an inner diameter of the inflow tube; guide surfaces on the magnetic rotor assembly in fluid communication with the blood flowing through the defined blood flow path, the guide surfaces configured to produce centrifugal components within the blood during rotation of the magnetic rotor assembly, wherein at least the guide surfaces of the magnetic rotor assembly are configured to drive the blood flow along the blood outflow path; positioning the heart assist pump device within the body; inserting the suction end of the inflow tube into the left ventricle; orienting the magnetic rotor assembly via the magneto coupling such that the magnetic rotor assembly remains adjacent to, and entirely spaced from, the side wall of the first chamber to define and maintain the gap between the side wall of the first chamber and the magnetic rotor assembly; activating the heart assist pump device; rotating the magnetic rotor assembly via the magneto coupling; maintaining the orienting of the magnetic rotor assembly during the rotating of the magnetic rotor assembly; suctioning the blood from the ventricle and into the inflow tube; driving the blood through the blood outflow path; directing the blood through the blood outflow path to the aorta.

32. The method of claim 31, wherein the heart assist pump device further comprises a second chamber that surrounds the second magnetic device and comprises one or more walls that seal the second magnetic device from the magnetic rotor assembly.

33. The method of claim 31, wherein the guide surfaces are spaced axially away from the inner surface of the substantially planar bottom wall.

34. The method of claim 31, wherein the second magnetic device is axially closer to the first magnetic device than to the guide surfaces of the rotor.

35. (canceled)

36. The method of claim 31, further comprising configuring at least part of the blood outflow path to direct the blood driven by the guide surfaces in a direction that is substantially perpendicular to the central axis.

37. The method of claim 36, comprising configuring the guide surfaces to drive the blood within the first chamber in a direction that is substantially perpendicular to the inflow tube and to the central axis.

38. The method of claim 31, wherein the heart assist pump device further comprises a control arrangement comprising at least one sensor configured to generate a control signal, and a controller configured to receive the generated control signal.

39. The method of claim 38, controlling the heart assist pump device with the control arrangement.

40. The method of claim 31, further comprising passively controlling an axial position and/or a radial position of the magnetic rotor assembly relative to the second magnetic device.

41. The method of claim 31, further comprising magnetically controlling an axial position and a radial position of the magnetic rotor assembly relative to the second magnetic device.

42. The heart assist pump device of claim 1, wherein the first magnetic device comprises a bar magnet.

43. The heart assist pump device of claim 1, wherein the second magnetic device comprises a bar magnet.

44. The heart assist pump device of claim 17, wherein the first magnetic device comprises a bar magnet.

45. The heart assist pump device of claim 17, wherein the second magnetic device comprises a bar magnet.

46. The heart assist pump device of claim 31, wherein the first magnetic device comprises a bar magnet.

47. The heart assist pump device of claim 31, wherein the second magnetic device comprises a bar magnet.

Description

BRIEF DESCRIPTION OF DRA WINGS

[0009] The invention is explained in further detail below by use of an examplary embodiment which is illustrated diagrammatically in the drawings, in which FIG. 1 shows a diagrammatic illustration of the arrangement of the pump and of the drive, FIG. 2 shows a diagrammatic illustration of the distal end of a catheter which is used according to the invention, and FIG. 3 shows an enlarged illustration of the part of the catheter bearing the balloon, in section.

DETAILED DESCRIPTION

[0010] In FIG. 1, a heart is designated by 1, into which a heart ventricle catheter 2 is introduced. The catheter is introduced here for example via the femoral artery and the aortic arch 3 into the heart chamber and carries a series of sensors 4 via which the volume can be determined. The measurement signals are passed to a control arrangement 5. The heart ventricle catheter is formed with several lumina, as additionally illustrated below in further figures of the drawings, with fluid being supplied via such lumina to drive a rotor, arranged at the distal end, which forms the pump to assist the blood circulation and is designated by 6 in FIG. 1. The positioning of this rotor is indicated in FIG. 1 by the arrow 8. The driving medium for the rotor or the pump is guided in a circular flow by means of a fluid pump 7 which can be regulated in a synchronised manner as a function of the control signals generated in the control arrangement 5. The distal region in which the pump is arranged is designated diagrammatically by 8, the catheter 2 having at its distal end a tube 9 leading to the suction end 10. A reservoir for driving fluid is designated by 11, which provides additional driving medium for filling the balloon 12 serving for an occlusion of the artery, and which receives again the volume of driving medium occurring on deflation of the balloon.

[0011] The volumetric measurement in the cardiac chamber allows differences to be reliably detected between the diastolic and systolic volume and allows corresponding correction signals to be made available for the output of the synchronised fluid pump 7. Furthermore, in the control circuit 5, corresponding fixed values can be provided, such as for example a defined cardiac output, which is referred to on deviation of the measured cardiac output to control the pump.

[0012] A retroperfusion can take place via a conventional balloon catheter which is occluded in a correspondingly synchronized manner, so that the directed return is in fact guaranteed during the diastole. Hereby the corresponding measurement values for the heart rate or for the correct moment of the diastole can be obtained from ECG data.

[0013] In FIG. 2, the distal end of a modified catheter 2 is now illustrated. The end side 13 of this catheter has two pocket-shaped chambers 14 and 15, in which bar magnets are respectively arranged. The bar magnet 16 is connected here at the distal end outwards via a shaft 17 with a rotor 18, whereas the bar magnet 19 lying on the inside is connected via a shaft 20 with a drive wheel 21. The drive wheel 21 is formed here as a paddle wheel and is acted upon with fluid via a lumen 22, this fluid flowing off again via the lumen 23 of the catheter. The rotation of the paddle wheel 21 is regulated here accordingly by corresponding control of the fluid pressure in the lumen 22 serving for the supply of fluid, in which the magnet 19, which is connected so as to be locked against relative rotation with the paddle wheel 21, is set into corresponding rotation. At the outer side, which is completely sealed with respect to the lumina 22 and 23, the magnet 16 is subsequently entrained accordingly and drives the rotor 18 via the shaft 17, whereby a flow is formed in the region of the tube 9, as is indicated by the arrows 24, and which assists the natural blood flow in the vessel 26, illustrated by the arrow 25.

[0014] In FIG. 3, the partial region of the balloon 12, which is connected in a sealing manner to the catheter 2, is illustrated on an enlarged scale. The two lumina leading away from the fluid pump 7 and back to the fluid pump 7 are designated in turn by 22 and 23. In the region of the balloon 12, the wall of these lumina is provided with valves which can be actuated magnetically for example. The valves are indicated diagrammatically by 27 and An opening of the valve 27 leads to the fluid, coming from the fluid pump 7, which is under pressure, which is indicated by the + sign, being pumped into the balloon 12, with which the overall quantity of the circulating driving fluid would of course be reduced, in so far as the reservoir 11, indicated diagrammatically in FIG. 1, is not provided. By closing the valve 27, the occlusion is closed off, the collapsing of the balloon 12 being able to be brought about by opening the valve 28 and the fluid now being drawn off via the lumen 23, leading back to the pump, which lumen 23 is at a slightly lower pressure which is indicated by the sign. As the overall volume of the fluid in the circulating system is now to be reduced, a portion of this volume must be pumped back again into the reservoir 11 according to FIG. 1.