阅读说明：本技术 血泵 (Blood pump ) 是由 托斯顿·西斯 克莱纳·斯帕尼尔 约尔格·舒马赫 于 2016-10-04 设计创作，主要内容包括：本发明涉及一种血泵。所述血泵包括在导管(2)中被引导的柔性驱动轴(3)、在驱动轴(3)的远端区域中连接到驱动轴(3)的输送元件(6)、以及电机(7),其中所述电机(7)包括定子(36)和可在定子(36)中移动地安装的转子(30)。所述定子(36)包括绕组(37),并且所述转子(30)包括转子磁体(31)。此外,驱动轴(3)在驱动轴(3)的近端处连接到转子(30)。所述定子(36)和所述转子(30)不可拆卸地彼此连接并形成由转子(30)和定子(36)限定的具有环形横截面的间隙(40)。(The invention relates to a blood pump. The blood pump comprises a flexible drive shaft (3) guided in a catheter (2), a conveying element (6) connected to the drive shaft (3) in the region of the distal end of the drive shaft (3), and a motor (7), wherein the motor (7) comprises a stator (36) and a rotor (30) mounted movably in the stator (36). The stator (36) comprises windings (37) and the rotor (30) comprises rotor magnets (31). Furthermore, the drive shaft (3) is connected to the rotor (30) at the proximal end of the drive shaft (3). The stator (36) and the rotor (30) are non-detachably connected to one another and form a gap (40) with an annular cross section which is delimited by the rotor (30) and the stator (36).)

1. A blood pump comprising a flexible drive shaft (3) guided in a catheter (2), a conveying element (6) connected to the drive shaft (3) in a distal region of the drive shaft (3), and a motor (7), wherein the motor (7) comprises a stator (36) and a rotor (30) rotatably mounted in the stator (36), wherein the stator (36) comprises windings (37) and the rotor (30) comprises a rotor magnet (31), wherein the drive shaft (3) is connected to the rotor (30) at a proximal end of the drive shaft (3), wherein the stator (36) and the rotor (30) form a gap (40) therebetween defined by the rotor (30) and the stator (36), the gap (40) having a minimum width of 0.05 mm.

2. The blood pump of claim 1, wherein the gap (40) has a width of at least 0.1 mm.

3. The blood pump according to claim 1 or 2, wherein the gap (40) has a width of at most 1 mm.

4. The blood pump according to any of claims 1 to 3, wherein the gap (40) has a width of at most 0.5mm, particularly preferably at most 0.25 mm.

5. The blood pump according to any of claims 1 to 4, wherein the flushing opening (41) is in fluid connection with the gap (40).

6. The blood pump according to claim 5, wherein the flushing opening (41) is connected with a flushing connection (42) provided at the proximal end of the motor (7).

7. The blood pump according to claim 5 or 6, wherein the gap (40) is in fluid connection with an intermediate space formed between the catheter (2) and the drive shaft (3).

8. The blood pump according to any of claims 1 to 7, wherein the windings (37) have an inner diameter which corresponds at most to 1.5 times, preferably at most to 1.25 times, particularly preferably at most to 1.15 times the outer diameter of the rotor magnets (31).

9. The blood pump according to any of claims 1 to 8, wherein the radial distance between the windings (37) and the rotor magnets (31) is at most 2mm, preferably at most 1.25mm, particularly preferably at most 0.75 mm.

10. The blood pump of any of claims 1 to 9, wherein the stator (36) comprises a fluid-tight sleeve (44) having a substantially annular cross-section, in such a way that the gap (40) is defined.

11. The blood pump of claim 10, wherein the extension of the sleeve (44) in the axial direction is less than 1.5 times the axial extension of the rotor magnet (31).

12. The blood pump according to any of claims 1 to 11, wherein the sleeve (44) comprises plastic, in particular polyetheretherketone or polyethylene or glass, and/or the sleeve (44) is formed from a resilient plastic.

13. The blood pump of any of claims 1 to 12, wherein the blood pump is configured to pump blood from a ventricle into a blood vessel of a patient when the motor (7) is arranged outside the body of the patient.

14. The blood pump according to any of claims 1 to 13, wherein the gap (40) has a width of at least 0.15mm, particularly preferably at least 0.2 mm.

15. The blood pump of any of claims 1 to 14, wherein the stator (36) and the rotor (30) are non-releasably connected to each other for a user.

16. Pump head (4) for a blood pump, comprising a housing (5) and a conveying element (6), the conveying element (6) is connected to the drive shaft (3) in the region of the distal end of the drive shaft (3), wherein the housing (5) is designed as a diamond lattice (19) and comprises an elastic cover layer (21), an inlet region (22) and an outlet region (24), the resilient cover layer (21) being in a fluid sealing region, neither the inlet region (22) nor the outlet region (24) being covered by the resilient cover layer (21), wherein during operation of the blood pump a motor (7) drives the drive shaft (3), the drive shaft (3) rotating the conveying element (6), in this way, blood is conveyed through the inlet region (22) to the housing (5) and flows out of the housing (5) through the outlet region (24).

17. Blood pump comprising a flexible drive shaft (3), a pump head (4) and an electric motor (7), the drive shaft (3) being guided in a conduit (2), the pump head (4) comprising a housing (5) and a delivery element (6) connected to the drive shaft (3) in a distal region of the drive shaft (3), the electric motor (7) comprising a stator (36) and a rotor (30), the drive shaft (3) being connected to the rotor (30) at a proximal end of the drive shaft (3), wherein the housing (5) is designed as a diamond-shaped lattice (19) and comprises an elastic covering layer (21), an inlet region (22) and an outlet region (24), the elastic covering layer (21) being in a fluid-tight region, neither the inlet region (22) nor the outlet region (24) being covered by the elastic covering layer (21), wherein during operation of the blood pump, the motor (7) drives the drive shaft (3), the drive shaft (3) rotating the delivery element (6) in such a way that blood is delivered to the housing (5) through the inlet region (22) and flows out of the housing (5) through the outlet region (24).

18. A blood pump comprising a flexible drive shaft (3) guided in a catheter (2), a conveying element (6) connected to the drive shaft (3) in a distal region of the drive shaft (3), and a motor (7), wherein the motor (7) comprises a stator (36) and a rotor (30) rotatably mounted in the stator (36), wherein the stator (36) comprises windings (37) and the rotor (30) comprises a rotor magnet (31), wherein the drive shaft (3) is connected to the rotor (30) at a proximal end of the drive shaft (3), wherein the windings (37) are infused into a biocompatible infusion compound.

19. A blood pump comprising a flexible drive shaft (3) guided in a catheter (2), a conveying element (6) connected to the drive shaft (3) in the region of the distal end of the drive shaft (3), and a motor (7), wherein the motor (7) comprises a stator (36) and a rotor (30) rotatably mounted in the stator (36), wherein the stator (36) comprises windings (37) and the rotor (30) comprises a rotor magnet (31), wherein the drive shaft (3) is connected to the rotor (30) at the proximal end of the drive shaft (3), wherein the stator (36) comprises a fluid-tight sleeve (44) having a substantially annular cross-section, by means of which the gap (40) is defined.

20. A blood pump comprising a flexible drive shaft (3) guided in a catheter (2), a conveying element (6) connected to the drive shaft (3) in the region of the distal end of the drive shaft (3), and a motor (7), wherein the motor (7) comprises a stator (36) and a rotor (30) rotatably mounted in the stator (36), wherein the stator (36) comprises windings (37) and the rotor (30) comprises a rotor magnet (31), wherein the drive shaft (3) is connected to the rotor (30) at the proximal end of the drive shaft (3), wherein the rotor (30) is radially mounted by means of at least one slide bearing or at least one ball bearing.

21. A blood pump comprising a flexible drive shaft (3) guided in a catheter (2), a conveying element (6) connected to the drive shaft (3) in the distal region of the drive shaft (3), and a motor (7), wherein the motor (7) comprises a stator (36) and a rotor (30) rotatably mounted in the stator (36), wherein the stator (36) comprises windings (37) and the rotor (30) comprises a rotor magnet (31), wherein the drive shaft (3) is connected to the rotor (30) at the proximal end of the drive shaft (3), wherein the rotor (30) has a coating and/or a cover for protecting the rotor magnet (31).

Technical Field

The present application relates to a blood pump. In particular, the present application relates to a blood pump having a motor.

Background

As is known from the prior art, this blood pump has a proximal end and a distal end and has a catheter arranged therebetween, with which a flexible drive shaft is guided inside the catheter. Such blood pumps typically comprise a pump head at its distal end, the pump head comprising a collapsible housing and a collapsible conveying element, wherein the conveying element is connected to the distal end region of the drive shaft. Such a pump head can be guided to difficult to access locations. For example, such a pump head can be inserted through the femoral artery via the aortic arch into the region of the aortic valve of a patient in order to transport blood from the left ventricle of the heart into the aorta. The drive shaft is driven at the proximal end of the blood pump by a motor, typically located outside the patient's body. Such a blood pump is described, for example, in document EP 2868331 a 2.

Document US 4,895,557 discloses a motor device for the drive of a blood pump. The motor device comprises a rotor shell which can sterilize and prevent water, and a rotor is positioned in the shell. For operation, the rotor housing is designed to be guided into a groove of the stator housing, so that the rotor is surrounded by the stator. After operation, the rotor housing can be pulled out of the groove of the stator housing and disposed of.

A disadvantage of such a motor device is that it has a considerable volume, which can lead to problems, in particular when fixing the motor device to the leg of a patient. Moreover, such an electromechanical device can lead to serious undesired heat generation during operation. Another disadvantage is that severe contamination of the stator can occur during assembly of the system, for example due to impurities on the user's gloves, which requires extensive cleaning and sterilization of the reusable stator.

Disclosure of Invention

The object of the present invention is to propose a blood pump which is simple to operate and which overcomes the drawbacks of the known devices described above.

The proposed blood pump comprises a flexible drive shaft guided in a catheter, a conveying element connected to the drive shaft in the region of its distal end, and a motor, wherein the motor comprises a stator and a rotor rotatably mounted therein. The stator includes windings and the rotor includes rotor magnets. Further, the drive shaft is connected to the rotor at a proximal end of the drive shaft. The stator and the rotor are non-releasably connected to each other and form a gap defined by the rotor and the stator.

The proposed blood pump can provide a compact construction, in particular in comparison with the modular construction of the motor for a blood pump known from the prior art, in which the rotor and the stator are designed in such a way that they can be detached by the user. With this proposed blood pump, the stator and the rotor form one unit and can be connected to one another by, for example, a friction or material bond. By the compact structure, the motor can be made lightweight, and in this way, when the motor is fixed on the leg of the patient, the motor contributes to the reduction of the load.

The inner diameter of the winding corresponds at most to 1.5 times, preferably at most 1.25 times, particularly preferably at most 1.15 times the outer diameter of the rotor magnet. The magnetic air gap is given by the distance between the windings and the rotor magnets. The small distance between the rotor magnets and the windings allows for an efficient conversion of electrical power into pump power, so that when operating at the desired pump power, heat losses in the motor can be kept low. In view of the fact that with the proposed electric machine, due to the single-part construction, no housing part needs to be provided in the magnetic air gap, so that a small distance between the winding and the rotor magnet can be achieved compared to constructions in which the stator and the rotor are designed in an independently accommodated manner. For example, given a winding with an inner diameter of 6mm, the outer diameter of the rotor magnet may be greater than 5.25 mm.

For example, the radial distance between the winding and the motor magnet may be at most 2mm, preferably at most 1.25mm, particularly preferably at most 0.75 mm.

The gap typically has a circular cross-section. The width of the gap corresponds to or is less than the width of the magnetic air gap. It is conceivable that the width of the gap is at most 1mm, preferably at most 0.5, particularly preferably at most 0.25 mm. It is also conceivable for the gap to have a width of at least 0.1mm, preferably at least 0.15mm, particularly preferably at least 0.2 mm.

Furthermore, a flushing opening can be provided which is in fluid connection with the gap. The flush opening may be fluidly connected to the flush connection. Such a flush connection may be arranged, for example, at the proximal end of the motor.

Furthermore, it is conceivable that the gap is fluidly connected to an intermediate space formed between the conduit and the drive shaft. In this way, flushing liquid can be flushed through the gap into the intermediate space between the drive shaft and the catheter by means of the flushing connection. In this way, lubrication of the drive shaft in the conduit may be achieved. Furthermore, the introduction of the rinsing liquid through the rinsing connection prevents blood from the patient from entering the motor, in particular the gap. Irrigation fluid may also be introduced into the patient through the irrigation connection, the gap, and the intermediate space between the catheter and the drive shaft. For example, a glucose solution is used as the rinsing liquid.

It is contemplated that the irrigation fluid may be washed around the rotor from the proximal end to the distal end. It is also contemplated that the irrigation fluid may be washed around the rotor from its distal end to its proximal end.

It is also possible to use a catheter with several lumens, so that a forward flush and a return flush can be achieved, as described for example in document US 4,895,557. Here, two or more connections for rinsing liquid can be provided on the motor.

It is conceivable that the gap has a minimum width of 0.05mm to ensure a reliable flow of flushing liquid through the gap.

It is envisaged that the windings are impregnated into the potting compound. The impregnation of the winding with the impregnating compound is suitable for closing and smoothing possible grooves on the winding surface. The potting compound may comprise a low viscosity material adapted to flow into and fill the grooves.

It is envisaged that the potting compound forms part of the stator defining the gap. A mostly smooth boundary surface of the gap may be achieved by pouring the compound. For example, the potting compound may comprise an epoxy resin. Furthermore, potting compounds containing, for example, alumina, iron powder or other thermally conductive substances are also contemplated to improve heat transfer. By pouring the compound, it is possible to achieve a reduction in the number of air bubbles adhering to the stator after the gap has been vented.

Damage or corrosion of the windings due to the flushing liquid or possibly due to particles transported by the flushing liquid can be prevented by the potting compound. Furthermore, by impregnating the compound, it is also possible to prevent particles from depositing on the winding.

Also, infusion compounds comprising biocompatible materials are envisaged. Generally, the potting compound herein is made entirely of biocompatible material, and therefore does not release toxic substances to the patient through the raised connection. For example, it is also conceivable to coat the winding with parylene.

It is also conceivable for the stator to comprise a fluid-tight sleeve with a substantially annular cross-section, by means of which the gap is defined. For example, the windings of the stator may be separated from the flushing liquid by a sleeve. In this way, damage to the winding due to the flushing liquid can be prevented. It is envisaged that the sleeve forms part of a stator defining a gap.

The sleeve can also be designed in such a way that, in addition to the windings, other motor components are also separated from the rinsing liquid by the sleeve and are therefore protected from damage. For example, welding locations that may be located in the motor may be protected from corrosion by the sleeve.

The sleeve may comprise, for example, plastic, in particular polyetheretherketone or polyethylene, or glass. It is also contemplated that the sleeve is formed of a resilient plastic, including, for example, polyethylene. The sleeve is used to guide the flushing liquid and not necessarily for mechanically stabilizing the motor. For this purpose, the sleeve can be manufactured in a thin-walled manner and/or in a flexible material. Furthermore, the outer shape of the motor or the outer shape of a part of the motor is not determined by the shape of the sleeve. For this reason, it may be advantageous for the sleeve to only slightly cover the windings and/or the rotor in the axial direction. For example, it is conceivable for the sleeve to have an extension in the axial direction which is less than 1.5 times the axial extension of the rotor magnet.

It is also conceivable that the rotor is mounted radially by means of at least one plain bearing. For example, the rotor may be mounted by two sliding bearings. The at least one plain bearing may comprise, for example, a non-magnetizable material and/or a ceramic material, in particular alumina, zirconia, yttrium-stabilized zirconia or silicon nitride. Furthermore, the plain bearing can comprise, for example, steel, in particular implant steel. For example, a biocompatible coating with diamond-like amorphous carbon may also be provided.

Furthermore, the rotor may be radially mounted by at least one ball bearing. It is envisaged that at least one of the ball bearings comprises a non-magnetisable material. In particular, it is conceivable that the part of the ball bearing which is worn down by operation of the electric machine comprises or is made of a non-magnetizable material. In this way it is achieved that the wear material of the ball bearing part does not stick to the ferromagnetic parts of the electrical machine. In this way, for example, it is possible to prevent ferromagnetic wear debris from remaining on the rotor and causing damage to the rotor. Also, ferromagnetic wear debris can be prevented from damaging the windings or other components of the motor.

For example, the at least one ball bearing may comprise balls comprising a ceramic material. Furthermore, the at least one ball bearing may comprise a cage comprising plastic. For example, the holder may comprise polyethylene or polytetrafluoroethylene. The balls may also be composed entirely of ceramic material. The holder may be constructed entirely of plastic.

Typically, the rotor includes a coating and/or covering for protecting the rotor magnets. It may be that the coating and/or the cover forms a part of the rotor, which part delimits the gap. The coating as well as the covering may comprise or consist of a biocompatible material. For example, a coating with parylene or a biocompatible epoxy may be provided. Coatings of diamond-like amorphous carbon may also be provided. The coating may have a thickness of less than 100 μm, preferably less than 10 μm. The rotor may comprise a covering of polyetheretherketone or stainless steel, for example.

The blood pump may comprise an expandable pump head comprising a transport element and a housing, wherein the transport element and the housing are designed in such a way that they automatically expand after being forced to contract. The expandable pump head allows for a larger design of the pump head and the delivery element, while allowing for a relatively small diameter opening for inserting the blood pump into the patient tissue.

Typically, the pump is configured to pump blood from the ventricle into a blood vessel of the patient when the motor is disposed outside the patient's body. The motor may be configured to be fastened to, for example, a thigh of a patient.

For this purpose, the flexible drive shaft has a sufficient length, depending on the anatomy of the patient. Typically, the flexible shaft herein has a length of at least 50 centimeters, preferably at least 90 centimeters. The maximum length of the flexible drive shaft is 200 cm, preferably 150 cm.

By using a blood pump driven by a motor located outside the patient's body, higher efficiency requirements may need to be met compared to a blood pump driven by a motor located inside the patient's body. For example, for a motor arranged inside the patient, it is advantageous to remove heat generated in the operation through the patient's blood system. In contrast, pumps that generate heat and are arranged outside the patient's body in certain cases require additional heat dissipating elements or a particularly efficient way of operation.

The application also relates to a method of operation for the proposed blood pump. When using this method of operation, the touchable surface of the housing of the motor is heated to a temperature of no more than 60 ℃, preferably no more than 48 ℃, particularly preferably no more than 43 ℃, during permanent operation at a speed of 15,000 r.p.m., preferably at least 30,000 r.p.m. Especially when fastening the motor to the thigh of a patient, it is important that the housing of the motor does not overheat during operation.

Furthermore, an operating method is envisaged in which the touchable surface of the housing of the motor is not heated to a temperature exceeding 60 ℃, preferably not exceeding 48 ℃, particularly preferably not exceeding 43 ℃, during permanent operation of the blood pump at a delivery rate of at least 1 liter/min, preferably at least 2 liters/min.

A blood pump comprising a cooling body, for example with cooling ribs or heat pipes connected in a heat-conducting manner to the motor, for dissipating heat generated during operation, is conceivable. It is also contemplated that the blood pump is configured to dissipate heat to the patient's tissue, for example, via the skin of the thighs.

The blood pump with all the components described can be delivered in sterile packaging. The blood pump may be sterilized, for example, by gamma sterilization or by using ethylene oxide. The blood pump may be discarded completely after use. In the case of the proposed blood pump, therefore, repeated cleaning or sterilization of the components of the blood pump, in particular of the motor, by the user can be dispensed with.

Drawings

Illustrative examples of the invention are described below with reference to the accompanying drawings. Shown in:

FIG. 1 is a schematic view of a pump apparatus;

FIG. 2 is a schematic view of a pump head;

fig. 3(a), 3(b) two further schematic views of the pump head;

FIG. 4 is a schematic view of the housing;

FIG. 5 is a schematic view of the motor; and

fig. 6 is a schematic view of another motor.

Detailed Description

Fig. 1 schematically shows a pump device 1. The pump device 1 comprises a conduit 2, in which conduit 2 a flexible drive shaft 3 is guided. The conduit 2 is connected to a pump head 4. The pump head 4 comprises a housing 5 and a transport element 6, which transport element 6 is arranged in the housing 5 and is drivable via the drive shaft 3 by a motor 7 connected to the proximal end of the drive shaft 3. The pump head 4, as well as the catheter 2 and the drive shaft 3, are introduced into the femoral artery 9 via the port 8 in such a way that the pump head 4 in the region of the left ventricle 10 is located in the region of the aortic valve 11. In operation, the drive shaft 3 is driven by the motor 7 and the pump device 1 delivers blood from the left ventricle 10 into the aorta 12. In the shown device for left heart assist, the delivery direction of the pump device 1 corresponds to the direction from the distal end 13 of the pump device 1 to the proximal end 14 of the pump device 1.

However, the pump device 1 may also be configured for transporting blood in a direction from the proximal end 14 to the distal end 13 of the pump device 1, which is suitable for right heart assist, for example.

The pump head 4 is shown schematically in fig. 2. Recurring features in this and subsequent figures are denoted by the same reference numerals. The pump head 4 comprises a transport element 6 and a housing 5. The conveying element 6 in the present example is designed as a pump rotor with two flexible sections in the form of rotor blades. In addition, the drive shaft 3 is shown mounted on the distal end region 15 of the pump head 4. At the distal end 16 of the pump head 4, a so-called tail (pigtail)17 made of an elastically deformable material is provided. The cylindrical element 18 is rigidly connected to the drive shaft 3. The conveying element 6 is fixed to the cylindrical element 18. The conveying elements 6 as well as the housing 5 are designed in such an expandable manner that they can expand automatically after being forced to contract. The conveying element 6 is made of plastic. The housing 5 is made of a shape memory material, nitinol. Since the transport element 6 as well as the housing 5 are designed in an expandable manner, the entire pump head 4 can be expanded.

The housing 5 is designed as a diamond lattice 19 and comprises an elastic covering layer 21 of polyurethane in the fluid-tight area 20. The elastic covering layer 21 covers the inside and outside of the diamond-shaped lattices 19 in such a manner that the diamond-shaped lattice openings formed by the lattices 19 in the fluid-tight region 20 can be closed in a fluid-tight manner by the elastic covering layer 21.

Furthermore, the housing 5 comprises an inlet area 22 which is not covered by the elastic cover layer 21. In the inlet region 22, the diamond-shaped grid openings form inlet openings, one of which is provided with the reference numeral 23, for example in fig. 2. The housing 5 also comprises an outlet area 24 which is likewise not covered by the elastic covering layer 21. In the outlet region 24, the diamond-shaped grid openings form outlet openings, one of which is shown by way of example and provided with the reference numeral 25.

In operation of the pump device 1, the drive shaft 3 is driven by the motor 7 such that the conveying element 6 connected to the drive shaft 3 rotates about the axis of the drive shaft 3. In this way, blood is conveyed into the housing 5 through the inlet opening of the inlet region 22 and subsequently flows out of the housing 5 through the outlet opening of the outlet region 24. In this way, the blood is conveyed by the pump device 1 in the conveying direction 26.

The elastic covering layer 21 does not extend completely around the axial direction of the conveying element 6. Instead, the conveying element 6 projects partially into the outlet region 24, so that at least an outlet opening with the reference number 25 is arranged laterally, i.e. in the radial direction, next to the conveying element 6. In contrast, the elastic covering layer 21 is designed at its distal end such that the conveying element 6 does not project or does not project significantly into the inlet region 22 and is therefore not laterally enclosed by the inlet opening.

The design of the elastic membrane 21 and the conveying element 6 and their arrangement relative to one another are such that approximately one third of the axial extension of the conveying element 6 is not surrounded by the elastic membrane 21 which forms the fluid-tight region 20. In the example shown, the same portion of the conveying element 6 extending axially is surrounded by an outlet region 24.

The pump head 4 additionally comprises an outflow element. This may be designed as an outflow shield 27 as shown in fig. 3(a), or as an outflow tube 27' as shown in fig. 3 (b).

The outflow shield 27 shown in fig. 3(a) is fixed to the housing 5 in the fluid-tight region 20 of the housing 5. The outflow shield 27 has the shape of a truncated-cone-shaped side surface and extends in the conveying direction 26 such that it widens in the conveying direction 26. The delivery element 6 and the outlet area 24 are surrounded by an outflow shroud 27. In another embodiment, it is also conceivable that the outlet area 24 is partially surrounded by the outflow shroud 27.

The pump head 4 in fig. 3(b) differs from the pump head 4 shown in fig. 3(a) only in that an outflow tube 27' is provided instead of the outflow shield 27. The outflow tube 27 is fixed to the housing 5 in the fluid-tight region 20 and extends therefrom in the conveying direction 26. The outflow tube 27 'is made of polyurethane and comprises openings 28, 28', 28 "in the area lying in the conveying direction 26. In the example shown, the outlet area 24 is completely surrounded by the outflow tube 27'. The outflow tube 27 'is flexible and automatically closes when blood flow occurs in a direction opposite to the delivery direction 26, as the outflow tube 27' is pressed onto the catheter 2 and/or the housing 5.

Fig. 4 schematically shows a diamond-shaped lattice 19 of the housing 5. Additionally shown are the fluid sealing region 20 with the elastomeric cover layer 21 and the inlet region 22 and the outlet region 24. The area of the inlet region 22 and the outlet region 24 has a conical shape, while the fluid seal region 20 is substantially tubular. The lattice 19 includes lattice struts, one of which is characterized, for example, by the reference numeral 45. The lattice struts 45 run in such a way that the substantially diamond-shaped lattice openings in the inlet region 22 and in the outlet region 24 are larger than the substantially diamond-shaped lattice openings in the fluid-tight region 20. The lattice struts arranged on the side of the housing 5 facing away from the observer are only indicated in fig. 4 by dashed lines in order to improve the overview.

In the fluid-tight region 20, the lattice struts 45 form a relatively thin lattice. The lattice 19 includes 32 struts along the outer periphery of the casing 5 in the fluid tight region 20, or the lattice 19 includes 16 nodes since the outer periphery is considered to have nodes at axial positions of the casing 5. By means of this tight lattice 19, a substantially circular cross section of the housing 5 in the fluid-tight region 20 is achieved.

The number of lattice struts 45 along the outer circumference of the housing 5 is halved from the fluid-tight region 20 in the direction of the inlet region 22 and in the direction of the outlet region 24 by combining the lattice struts in pairs, so that the housing 5 in the respective region comprises sixteen lattice struts 45 along the outer circumference, wherein no node points are present. The number of lattice struts 45 is then reduced again in the direction of the inlet region 22 and the outlet region 24 by combining the lattice struts in pairs, so that the housing 5 in these regions comprises eight lattice struts 45. The number of lattice struts 15 is further reduced in the outlet region 24 in the manner described above, so that the housing 5 in the region located further away in the conveying direction 26 has only four lattice struts 45 along the outer periphery.

Due to the described reduction in the number of lattice struts 45, a lattice 19 having a larger lattice opening than in the fluid-tight region 20 is formed in the inlet region 22 and the outlet region 22.

The lattice struts 45 in the tapered regions of the outlet region 24 and the inlet region 22 form a helical structure which results in a reliable deployment of the pump head 4 when the pump head 4 is pushed out of the sleeve.

Fig. 5 shows a schematic view of the motor 7. The motor 7 is connected to the pipe 2 in the region of a shaft head (shaft stub)29, said pipe 2 being glued into the shaft head 29. A flexible drive shaft 3 is guided in the catheter 2. Further, the motor 7 includes a rotor 30 having a rotor magnet 31.

The flexible drive shaft 3 is connected to the rotor 30 in such a way that, given a rotation of the rotor 30, a torque is transmitted from the rotor 30 to the flexible drive shaft 3. The torque is transmitted to the conveying element 6 via a flexible drive shaft, so that the pump device is driven by the motor 7.

The rotor 30 is mounted axially by means of two bearings 32, 33. One of these bearings 33 is biased for axial stabilization of the rotor 30 by a spring element 34. The spring element 34 can be designed, for example, as a helical spring or as a ring spring. The bearings 32, 33 can each be designed as ball bearings or slide bearings. If the bearings 32, 33 are designed as ball bearings, the bearings 32, 33 comprise ceramic balls and a plastic cage, so that the ball bearings are of non-magnetized material. The ring of the bearing may for example be designed from magnetizable metal or non-magnetizable material. If the bearings 32, 33 are designed as sliding bearings, they each comprise a friction complex of DLC-coated implant steel and yttrium-stabilized zirconia.

Rotor magnet 31 includes a biocompatible DLC coating. The electric machine 7 furthermore comprises a stator 36. The stator 36 comprises several windings 37 which are connected in an electrically conductive manner to electrical connections 38. The stator 36 also includes a back iron lamination 39. The windings 37 are impregnated with a biocompatible epoxy resin containing thermally conductive alumina.

A gap 40 having a circular cross section is formed between the inner side of the coating of the winding 37 and the outer side of the coating 35 of the rotor magnet 31. The gap 40 has a width of 0.2 mm. This gap 40 is in fluid connection with a flushing opening 41 connected to a flushing connection 42, wherein the flushing connection 42 is arranged at the proximal end of the motor 7. Furthermore, the gap 40 is in fluid connection with the intermediate space formed between the drive shaft 3 and the conduit 2. Thus, for example, the glucose solution can be flushed through the flushing opening 41 and the gap 40 and the intermediate space via the flushing connection 42. In this manner the glucose solution is flushed around the rotor 30 during operation. The radial distance between the outside of rotor magnet 31 and the inside of windings 37 is 0.5 mm. The inner diameter of the winding 37 corresponds here to 1.1 times the outer diameter of the rotor magnet 31.

The stator 36 and the rotor 30 are connected to each other in a manner that cannot be released by a user and are incorporated into a motor housing 43. The motor housing 43 may be connected to a handle or a cooling body, for example. Due to the small distance between the windings 37 and the rotor magnets 31, the motor can be operated in a very efficient manner, so that when the pump device 1 is operated at a speed of 32,000 r.p.m. and a delivery output of 2.5l per minute, the motor housing 43, and the handle or cooling body, which may be connected to the housing, is heated to below 40 ℃ at its exposed surface.

The electric machine 7' shown in fig. 6 differs from the electric machine 7 shown in fig. 6 only in that the stator 36 in this embodiment comprises a fluid tight sleeve 44 defining the gap 40. In this embodiment, the width of the gap 40 is, for example, 0.15mm or 0.22 mm. The sleeve 44 comprises polyetheretherketone and is magnetically inert. The sleeve 44 is arranged in such a way that, for example, the windings 37 and other parts of the stator 36 are separated by the sleeve 44 from flushing liquid that may flow through the gap 40. The extension of the sleeve 44 in the axial direction is approximately 1.2 times the axial extension of the rotor magnet 31.

Features of different embodiments disclosed only in the illustrative examples may be combined with each other and claimed separately.