Catheter pump arrangement and flexible shaft arrangement having a core

Abstract

The invention relates to a flexible shaft arrangement having a flexible hollow shaft (1, 2) which has an, end at the drive side and an end at the output side, wherein the hollow shaft is reinforced sectionally between these ends by a core (3, 4) extending in its interior. Stiffer and more flexible sections can hereby be selectively positioned within the shaft arrangement.

Claims

1. A flexible drive shaft, comprising: a shaft having a proximal end at a drive device and a distal end at an output side, the shaft formed as a hollow lumen; and at least one core positioned within the hollow lumen, wherein the core is configured to rotate with the shaft, wherein the at least one core is coupled to an inside of the hollow lumen.

2. The drive shaft of claim 1, wherein the shaft has a first flexibility in a region having a core and a second, larger flexibility in a region without a core.

3. The drive shaft of claim 1, wherein the at least one core has a first section having a first flexibility and a second section at a distal end of the core having a second flexibility greater than the first flexibility.

4. The drive shaft of claim 1, wherein the at least one core is held in the interior of the lumen by an axial spacer.

5. The drive shaft of claim 4, wherein a first core is held in a position relative to a second core by the axial spacer.

6. The drive shaft of claim 4, wherein the at least one core is held in a position with respect to the proximal end by the axial spacer.

7. The drive shaft of claim 4, wherein the axial spacer is a continuous strand coupled to the proximal end and the distal end of the shaft.

8. The drive shaft of claim 1, wherein the at least one core is rotationally fixed within the hollow lumen.

9. The drive shaft of claim 8, wherein the at least one core is welded to the inside of the hollow lumen.

10. The drive shaft of claim 1, wherein the at least one core is at least one of a metal body, a plastic body or a stranded body.

11. The drive shaft of claim 1, wherein the hollow lumen is defined by a wound helical spring, and wherein a first winding and a second winding of the wound helical spring directly contact each other.

12. The drive shaft of claim 1, wherein the shaft is configured from two coaxial wound helical springs, wherein a first helical spring is wound in a direction opposite a second helical spring.

13. The drive shaft of claim 1, wherein the proximal end of the shaft is stiffer than the distal end of the shaft.

14. The drive shaft of claim 1, wherein the distal end of the shaft is stiffer than the proximal end of the shaft.

15. The drive shaft of claim 1, wherein the stiffness of the shaft is variable along the length of the shaft.

16. The drive shaft of claim 1, wherein the hollow lumen is configured to be surrounded by a hollow catheter.

17. The drive shaft of claim 1, wherein the distal end of the hollow lumen is configured to be coupled to an intravascular blood pump.

18. A flexible drive shaft, comprising: a shaft having a proximal end at a drive device and a distal end at an output side, the shaft formed as a hollow lumen, the hollow lumen comprising an inner diameter; and at least one core positioned within the hollow lumen, a section of the at least one core having a diameter of about the inner diameter of the hollow lumen, wherein the core is configured to rotate with the shaft.

19. The flexible drive shaft of claim 18, wherein the section of the at least one core is a first section, the at least one core further comprising: a second section having a diameter smaller than the inner diameter of the hollow lumen.

20. The flexible drive shaft of claim 18, wherein the section of the at least one core is configured to reinforce the hollow lumen.

Description

(1) The invention will be shown and subsequently described in the following with reference to an embodiment in a drawing.

(2) There are shown

(3) FIG. 1 a shaft arrangement in accordance with the invention in a three-dimensional representation having a plurality of sections reinforced by a core;

(4) FIG. 2 a cross-section of the shaft arrangement of FIG. 1;

(5) FIG. 3 a further embodiment of the shaft arrangement in a schematic representation;

(6) FIG. 4 an embodiment of the shaft arrangement in accordance with the invention in bent form; and

(7) FIG. 5 the use of the shaft arrangement in accordance with the invention in a heart pump.

(8) FIG. 1 shows, in a three-dimensional view, a hollow shaft which comprises two helical screws 1, 2 which are wound in opposite senses and of which the first is shown as light and the second as dark. The winding in opposite senses of the two helical springs has the effect that one of the springs is compressed and the other is stretched in each direction of rotation. There is thus no deformation overall in the axial direction in dependence on the direction of rotation which is to be transferred.

(9) The density of the windings of the individual springs and the thickness of the spring wire determine, on the one hand, the flexibility or stiffness respectively of the hollow shaft and, on the other hand, the torque which can be transferred.

(10) Two core sections 3, 4 are furthermore shown in FIG. 1 which each stiffen the shaft arrangement in the axial sections 5, 6. The hollow shaft remains free in the axial section lying therebetween and is correspondingly more flexible there.

(11) The core sections 3, 4 can be made as solid bodies, for example as plastic bodies or metal bodies, which have a high spring elasticity and break resistance as well as a high resistance to fatigue.

(12) The core sections can, however, also be stranded cores which then comprise a plurality of strand elements, for example wires. This embodiment is shown in more detail in FIG. 2 where a section shows the radial arrangement of the two helical springs 1, 2 and of the core 3. It is also shown there that the core 3 comprises a plurality of strand elements 8, 9, whereby it becomes very flexibly and permanently deformable.

(13) The two helical springs 1, 2 are dimensioned and arranged such that they are assembled radially into one another and coaxially to one another in a press fit so that a distribution of the torque to be transferred takes place between them. In addition, bending loads are also taken up together by both helical springs. The corresponding loads are likewise taken up in the sections in which a core is located within the hollow space of the helical springs 1, 2 by said core since it fits tightly in the hollow space.

(14) It is shown with reference to FIG. 3 that the core sections each have an end converging to a taper, whereby the end region 10, 11 of the core 3 becomes more and more flexible toward the end. The stiffness is thereby not reduced abruptly to the degree of stiffness of the hollow shaft toward the end of each core section in the total observation of the shaft arrangement, but a constant transition rather takes place which results in a continuous distribution on a bending strain of the shaft arrangement to reduce the kinking strains and to reduce the risk of a tearing of the shaft arrangement.

(15) The result is, with a given bending strain, that the bending radius is considerably increased in those sections 5, 6 in which the hollow shaft is reinforced by a core or by a core section. A substantially smaller bending radius is achieved in those sections in which no core is present. The above-described design of the end region of the core sections is suitable to avoid kinks between these regions.

(16) In FIG. 4, a bent shaft arrangement in accordance with the invention is shown by way of example, with two cores 3, 4 being shown in sections 5, 6 which extend almost straight or have a large bending radius. The hollow shaft arrangement is particularly bent in the section 7, as it is in section 12.

(17) The general transition of the stiffness by a corresponding design of the ends of the cores 3, 4 in the regions 10, 13 has the effect that the risk of kinking is reduced.

(18) Spacers are shown by way of example between the cores 3, 4 in FIG. 4, just as between the core 3 and the end of the shaft arrangement at the drive side. The spacers are labeled by 14, 15 and can be made as more or less stiff, thin cores which have a substantially smaller diameter than the cores 3, 4, and equally a substantially smaller stiffness. The spacers 14, 15 can, however, simply be made only as a thread with negligible stiffness, with it being expedient in this case to fasten the spacers suitably at both ends of the hollow shaft arrangement to be able to keep the core sections 3, 4 tensioned as on a chain and to be able to keep them stable at preset spacings.

(19) This embodiment has the advantage that, depending on the demands on the distribution of different stiffnesses along the hollow shaft arrangement, a series of cores/core sections can be drawn into the existing hollow shaft with spacers, with the length of the individual spacers being individually adaptable in accordance with the purpose of the shaft arrangement.

(20) FIG. 5 schematically shows an application for the shaft arrangement in accordance with the invention, with the shaft arrangement there only being shown schematically and being labeled by 16. The shaft arrangement 16 is connected to a motor 17 at the drive side and extends in a hollow catheter 18 which can be introduced into a blood vessel 19 of a body, for example a human body, and can be introduced into a ventricle 20 via the path of this blood vessel.

(21) A heart pump 21 is located at the end of the hollow catheter 18 and is made as an axial pump and has a rotor in its interior which can be driven by means of the shaft arrangement 16 at high speeds, for example between 10,000 and 20,000 revolutions per minute.

(22) The advantages of the shaft arrangement in accordance with the invention are shown in that, on the one hand, the shaft arrangement can be easily inserted through the blood vessel 19 due to suitable stiff regions, but that in the distal region, viewed from the introduction point, that is in the region of the aortic arch toward the ventricle, a high flexibility of the shaft arrangement is given so that the heart pump 21 can be introduced into the ventricle there without the stiffness of the shaft arrangement or of the hollow catheter being able to result in injuries to the ventricle walls or to the aorta in the region of the aortic arch. A knocking of the shaft and acoustic resonance are reliably avoided by the suitable distribution of the core(s) along the shaft arrangement.