A collapsible impeller and a ventricular assist blood pumping device

Abstract

The present invention relates to a foldable impeller, which comprises: a telescopic shaft including a plurality of shaft segments arranged at intervals along the axial direction, and a spring is connected between adjacent shaft segments; an impeller skeleton including at least two spiral blade groups that can be compressed radially inward along the telescopic shaft, different spiral blade groups are arranged in sequence from inside to outside along the radial direction of the telescopic shaft, and each spiral blade group has at least two spiral blades evenly distributed circumferentially. It solves the technical problem in the prior art that during the rotation of the impeller, the outer diameter extends outward and becomes larger, resulting in a smaller gap between the impeller and the outer conduit, preventing the phenomenon that the outer diameter of the impeller extends excessively outward, resulting in a smaller or no gap between the impeller and the peripheral components, ensuring the gap between the impeller and the peripheral components, and effectively avoiding the increase of the hemolysis index.

Description

Technical Field

[0001] The present invention relates to the field of medical devices, and particularly to a foldable impeller and a ventricular assist blood pump device. Background Art

[0002] A ventricular assist device is a device that provides effective circulatory support for high-risk coronary heart disease patients and acute myocardial infarction patients. For percutaneous coronary intervention (PCI) in high-risk coronary heart disease patients, the clinical goal of an ideal ventricular assist device is to maintain systemic hemodynamic stability while preventing interruption of cardiac output; reduce the level of myocardial ischemia and minimize myocardial cell damage; and reduce complications such as bleeding and peripheral tissue embolism. Therefore, an ideal ventricular assist device can provide systemic hemodynamic support and myocardial protection, and at the same time it is safe and simple.

[0003] The ability of a ventricular assist device to provide systemic hemodynamic support and myocardial protection is based on the basic principle that it replicates the original function of the heart: pumping blood out of the ventricle, entering the aortic root through the aortic valve, flowing from the aortic root through the aorta to the whole body, and supplying the myocardial circulation through the coronary artery inlet at the same time.

[0004] In the prior art, a blood pump includes a pump head and a drive assembly connected to the pump head. The impeller is an important component of the pump head and has a folded state and an unfolded state. It folds during intervention or removal and unfolds after the intervention is in place, thereby reducing the intervention size and preventing damage to blood vessels or corresponding organs.

[0005] In some current ventricular blood pump devices, when the foldable impeller rotates at high speed, due to the centrifugal force, the outer diameter of the impeller will extend outward and become larger, resulting in a smaller gap between the impeller and the outer catheter, leading to an increase in the hemolysis index and even causing the motor to jam. Summary of the Invention

[0006] Based on the above description, the present invention provides a foldable impeller to solve the technical problem in the prior art that during the rotation of the impeller, the outer diameter extends outward and becomes larger, resulting in a smaller gap between the impeller and the outer catheter.

[0007] The technical solution of the present invention to solve the above technical problem is as follows:

[0008] A foldable impeller, which comprises:

[0009] A telescopic shaft, including a plurality of shaft segments arranged at intervals along the axial direction, and a spring is connected between adjacent shaft segments;

[0010] The impeller skeleton includes at least two sets of spiral blades that can be compressed radially inward along the telescopic shaft. Different said sets of spiral blades are arranged in sequence from the inside to the outside along the radial direction of the telescopic shaft, and each said set of spiral blades has at least two spiral blades evenly distributed circumferentially.

[0011] Compared with the prior art, the technical solution of the present application has the following beneficial technical effects:

[0012] When the impeller provided by the present application rotates at a high speed, a binding force is formed between the shaft segments, preventing the phenomenon that the outer diameter of the impeller formed by the spiral blades extends excessively outward due to the centrifugal force, resulting in a smaller or no clearance between the impeller and the peripheral components, ensuring the clearance between the impeller and the peripheral components, effectively avoiding the increase of the hemolysis index, preventing the device from jamming. In addition, compared with the traditional impeller structure, the impeller skeleton structure provided by the present application has a larger size and can provide a larger pump blood volume.

[0013] On the basis of the above technical solution, the present invention can be further improved as follows.

[0014] Further, the telescopic shaft includes at least three shaft segments, and both ends of the outermost set of spiral blades are respectively connected to the outermost two shaft segments.

[0015] Further, when the number of shaft segments of the telescopic shaft is greater than 3, the spring includes at least one compression spring and at least two buffer springs. At least one buffer spring is arranged at both ends of the compression spring, and the length of the compression spring is greater than the length of the buffer spring.

[0016] Further, the number of shaft segments of the telescopic shaft is six. The six shaft segments are respectively two outer shaft segments, two secondary shaft segments and two inner shaft segments. The two outer shaft segments are arranged close to the outermost side. The two secondary shaft segments are respectively located on the inner side of the two outer shaft segments. The two inner shaft segments are respectively located on the inner side of the two secondary shaft segments. The compression spring is arranged between the two inner shaft segments. The buffer springs are arranged between the outer shaft segments and the secondary shaft segments and between the secondary shaft segments and the inner shaft segments;

[0017] The impeller skeleton includes an outer spiral blade group, a middle spiral blade group and an inner spiral blade group. The outer spiral blade group includes outer spiral blades whose two ends are respectively correspondingly connected to the two outer shaft segments. The middle spiral blade group includes middle spiral blades whose two ends are respectively correspondingly connected to the two secondary shaft segments. The inner spiral blade group includes inner spiral blades whose two ends are respectively correspondingly connected to the two inner shaft segments.

[0018] The present application provides a ventricular assist blood pumping device, which includes a transmission component, a support skeleton, a contraction catheter and the impeller as described above;

[0019] The transmission assembly includes an outer tube and a transmission shaft. The transmission shaft is disposed inside the outer tube, and one end of the transmission shaft is connected to a motor.

[0020] The support skeleton is disposed at the distal end of the outer tube. The support skeleton is a compressible and foldable structure, and a cavity is formed inside the support skeleton.

[0021] The impeller is drivingly connected to the transmission shaft and is disposed inside the cavity.

[0022] The contraction catheter is slidably disposed outside the outer tube. The contraction catheter has a compression cavity with an open distal end. The support skeleton and the impeller can be received into the compression cavity along with the movement of the contraction catheter.

[0023] Further, the motor connected to the transmission shaft is externally disposed outside the device, and the motor drives the impeller to rotate through a magnetic coupling manner.

[0024] Further, the transmission shaft includes a magnetic shaft portion at the distal end and a flexible portion at the proximal end of the magnetic shaft portion. The transmission assembly further includes a magnetic ring. The magnetic ring is rotatably disposed relative to the magnetic shaft portion. The magnetic shaft portion drives the magnetic ring to rotate through a magnetic coupling manner, and the impeller is mounted on the magnetic ring.

[0025] Further, the magnetic ring includes a connecting shaft at the distal end and a sleeve at the proximal end of the connecting shaft. The proximal end of the sleeve is open. At least a part of the magnetic shaft portion near the distal end is disposed inside the sleeve, and the impeller is mounted on the connecting shaft.

[0026] Further, the transmission assembly further includes an inner tube and a housing. The inner tube is sleeved outside the transmission shaft and is located inside the outer tube. The sleeve is rotatably sleeved at the distal end of the inner tube. The part of the magnetic shaft portion disposed inside the sleeve does not contact the inner tube. The housing is connected to the outer tube and wraps the sleeve, and the connecting shaft extends out from the distal end of the housing.

[0027] Further, the support skeleton includes a skeleton main body and a skeleton film. The skeleton main body is a bracket structure with a grid-shaped side wall. The skeleton film is covered on the skeleton main body. The distal end of the skeleton film encloses to form a flow inlet and the proximal end forms a flow outlet. The caliber size of the flow inlet is larger than that of the flow outlet. The skeleton main body is a nickel-titanium braided structure or a nickel-titanium tube laser cutting structure. Description of the Drawings

[0028] Figure 1 It is a schematic structural diagram of a foldable impeller provided by the present application.

[0029] Figure 2Schematic diagram of the impeller provided in the first embodiment of the present application;

[0030] Figure 3 Schematic diagram of the impeller provided in the second embodiment of the present application;

[0031] Figure 4 Schematic diagram of the impeller provided in the third embodiment of the present application;

[0032] Figure 5 Schematic diagram of a ventricular assist blood pumping device provided in the fourth embodiment of the present application;

[0033] Figure 6 Schematic diagram of the connection between the motor and the transmission shaft in the embodiment of the present application;

[0034] Figure 7 Schematic diagram of the support skeleton in the embodiment of the present application;

[0035] Figure 8 External schematic diagram of the transmission component in the embodiment of the present application;

[0036] Figure 9 For Figure 8 Schematic diagram of the A-A sectional view in

[0037] Figure 10 Schematic diagram of the magnetic ring in the embodiment of the present application;

[0038] Figure 11 Schematic diagram of the transmission shaft in the embodiment of the present application. Detailed implementation manners

[0039] To facilitate the understanding of the present application, the present application will be described more comprehensively below with reference to the relevant drawings. Embodiments of the present application are given in the drawings. However, the present application can be implemented in many different forms and is not limited to the embodiments described herein. On the contrary, the purpose of providing these embodiments is to make the disclosure of the present application more thorough and comprehensive.

[0040] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by those of ordinary skill in the technical field to which the present application belongs. The terms used herein in the specification of the present application are only for the purpose of describing specific embodiments and are not intended to limit the present application.

[0041] It will be understood that spatial relationship terms such as "under", "below", "lower", "beneath", "above", "upper", etc. may be used herein to describe the relationship of one element or feature shown in the figures to other elements or features. It should be understood that, in addition to the orientation shown in the figures, spatial relationship terms also include different orientations of the device in use and operation. For example, if the device in the drawings is flipped, an element or feature described as "under other elements" or "beneath them" or "underneath them" will be oriented "above" the other elements or features. Thus, the exemplary terms "under" and "beneath" can include both an upper and a lower orientation. In addition, the device may also include additional orientations (such as, rotated 90° or other orientations), and the spatial descriptors used herein are to be interpreted accordingly.

[0042] It should be noted that when an element is considered to be "connected" to another element, it may be directly connected to the other element or connected to the other element through an intermediate element. In the following embodiments, "connection", if there is a transfer of electrical signals or data between the connected circuits, modules, units, etc., should be understood as "electrically connected", "communicatively connected", etc.

[0043] As used herein, the singular forms "a", "an" and "the" may also include the plural forms unless the context clearly dictates otherwise. It should also be understood that the terms "comprises / include" or "has" etc. specify the presence of the stated features, wholes, steps, operations, components, parts or combinations thereof, but do not preclude the presence or addition of one or more other features, wholes, steps, operations, components, parts or combinations thereof.

[0044] As Figure 1 shown, the present application provides a collapsible impeller 30, which includes a telescopic shaft 31 and an impeller skeleton 32.

[0045] Wherein, the telescopic shaft 31 includes a plurality of shaft segments 310 arranged at intervals along the axial direction, and a spring 33 is connected between adjacent shaft segments;

[0046] The impeller skeleton 32 includes at least two spiral blade groups that can be compressed radially inward along the telescopic shaft. Different spiral blade groups are arranged in sequence from the inside to the outside along the radial direction of the telescopic shaft 31, and each spiral blade group has at least two spiral blades evenly distributed in the circumferential direction.

[0047] As an alternative embodiment, the number of the shaft segments 310 in the telescopic shaft 31 can be set according to actual circumstances. Preferably, the number is three or more. It can be understood that the different spiral blade groups expressed in this application are arranged in sequence from the inside to the outside along the radial direction of the telescopic shaft 31. It can be understood that the spatial curved surface structures formed when different spiral blade groups rotate do not interfere with each other and corresponding inner and outer layer relationships are formed between these spatial curved surfaces, that is, the spatial curved surface formed when the spiral blade group located on the radial inner side rotates is contained inside the spatial curved surface formed when the spiral blade group on the radial outer side rotates.

[0048] As a preferred technical solution of this application, the telescopic shaft 31 includes at least three shaft segments, and both ends of the outermost spiral blade group are respectively connected to the two outermost shaft segments.

[0049] In the first specific embodiment of this application, the telescopic shaft 31 has three shaft segments, namely an outer shaft segment 311 and an inner shaft segment 312.

[0050] The impeller skeleton 32 includes three spiral blade groups, namely an outer spiral blade group 32a, an inner spiral blade group 32b, and a middle spiral blade group 32c.

[0051] Among them, the outer spiral blade group 32a includes three outer spiral blades 321. The three outer spiral blades 321 are evenly distributed in the circumferential direction of the telescopic shaft 31 and are arranged in a spiral shape. Both ends of each outer spiral blade 321 are respectively connected to positions close to the outside of the two outer shaft segments 311; the inner spiral blade group 32b includes three inner spiral blades 322. The inner spiral blades 322 are evenly distributed in the circumferential direction of the telescopic shaft 31 and are arranged in a spiral shape. Both ends of each inner spiral blade 322 are respectively connected to positions close to both ends of the inner shaft segment 312; the middle spiral blade group 32c includes three middle spiral blades 323. The three middle spiral blades 323 are evenly distributed in the circumferential direction of the telescopic shaft 31 and are arranged in a spiral shape. Both ends of each outer spiral blade 321 are respectively connected to positions close to the inside of the two outer shaft segments 311.

[0052] As a more preferred technical solution of this application, when the number of shaft segments of the telescopic shaft 31 is greater than 3, the spring 33 includes at least one compression spring 331 and at least two buffer springs 332, and at least one buffer spring 332 is arranged at both ends of the compression spring 331, and the length of the compression spring 331 is greater than the length of the buffer spring 332.

[0053] In the second specific embodiment of this application, the telescopic shaft 31 has four shaft segments, namely two outer shaft segments 311 close to the outside and two inner shaft segments 312 close to the inside.

[0054] The impeller skeleton 32 includes an outer spiral blade group 32a, a middle spiral blade group 32c, and an inner spiral blade group 32b.

[0055] Among them, the outer spiral blade group 32a includes three outer spiral blades 321. The three outer spiral blades 321 are evenly distributed in the circumferential direction of the telescopic shaft 31 and are arranged in a spiral shape. The two ends of each outer spiral blade 321 are respectively connected to positions near the outer sides of the two outer shaft segments 311; the inner spiral blade group 32b includes three inner spiral blades 322. The inner spiral blades 322 are evenly distributed in the circumferential direction of the telescopic shaft 31 and are arranged in a spiral shape. The two ends of each inner spiral blade 322 are respectively connected to the two inner shaft segments 312; the middle spiral blade group 32c includes three middle spiral blades 323. The three middle spiral blades 323 are evenly distributed in the circumferential direction of the telescopic shaft 31 and are arranged in a spiral shape. The two ends of each outer spiral blade 321 are respectively connected to positions near the inner sides of the two outer shaft segments 311.

[0056] In the third specific embodiment of the present application, the number of shaft segments of the telescopic shaft 31 is six. The six shaft segments are two outer shaft segments 311, two secondary shaft segments 313, and two inner shaft segments 312. The two outer shaft segments 311 are arranged near the outermost side. The two secondary shaft segments 313 are respectively located on the inner sides of the two outer shaft segments 311. The two inner shaft segments 312 are respectively located on the inner sides of the two secondary shaft segments 313.

[0057] The compression spring 331 is arranged between the two inner shaft segments 312. The buffer spring 332 is arranged between the outer shaft segment 311 and the secondary shaft segment 313 and between the secondary shaft segment 313 and the inner shaft segment 312.

[0058] The impeller skeleton 32 includes an outer spiral blade group 32a, a middle spiral blade group 32c, and an inner spiral blade group 32b. The outer spiral blade group 32a includes outer spiral blades 321 whose two ends are respectively connected to the two outer shaft segments 311 correspondingly. The middle spiral blade group 32c includes middle spiral blades 323 whose two ends are respectively connected to the two secondary shaft segments 313 correspondingly. The inner spiral blade group 32b includes inner spiral blades 322 whose two ends are respectively connected to the two inner shaft segments 312 correspondingly.

[0059] When the impeller 30 provided in the present application rotates at a high speed, a binding force is formed between the shaft segments, preventing the outer diameter of the impeller formed by the spiral blades from extending outwards due to the centrifugal force, and preventing the phenomenon that the outer diameter of the impeller extends outwards excessively, resulting in a smaller or no gap between the impeller and the peripheral components. It ensures the gap between the impeller and the peripheral components, effectively avoids the increase of the hemolysis index, and prevents the device from getting stuck. In addition, compared with the traditional impeller structure, the impeller skeleton structure provided in the present application has a larger size and can provide a larger pump blood flow.

[0060] Based on the above impeller, in the fourth embodiment of the present application, a ventricular assist blood pumping device is disclosed, which includes a transmission assembly 10, a support skeleton 20, an impeller 30 as provided in the above third embodiment, and a contraction catheter 40.

[0061] Among them, as shown in Figure 5- Figure 9 The transmission assembly 10 includes an outer tube 11 and a transmission shaft 12. The transmission shaft 12 is arranged inside the outer tube 11, and one end of the transmission shaft 12 is connected to the motor 50.

[0062] The support skeleton 20 is arranged at the distal end of the outer tube 11. The support skeleton 20 is a compressible and foldable structure, and there is a cavity inside the support skeleton 20.

[0063] In a preferred embodiment of the present application, the support skeleton 20 includes a skeleton main body 21 and a skeleton film 22. The skeleton main body 21 is a support structure with a grid-shaped side wall. The skeleton film 22 is covered on the skeleton main body 21. The skeleton main body 21 is a nickel-titanium braided structure or a nickel-titanium tube laser cutting structure. The distal end of the skeleton film 22 encloses to form an inflow port 201 and the proximal end forms an outflow port 202. The caliber size of the inflow port 201 is larger than that of the outflow port 202, and the purpose is to ensure that enough blood flows in through the inflow port 201 during the operation of the device and improve the pump blood volume.

[0064] The impeller 30 is drivingly connected to the transmission shaft 12 and is arranged inside the cavity. The impeller is a compressible and foldable structure. In the embodiment of the present application, the impeller 30 is arranged near the proximal end of the support skeleton 20. It can be understood that in other embodiments of the present application, the impeller 30 can also be located in the middle of the support skeleton 20 or near its distal end, which can be freely selected and designed by those skilled in the art and will not be elaborated here. It should be noted that the position of the impeller 30 on the support skeleton 20 and the number of the impellers 30 are not limited. That is to say, the impeller can be single and located at the proximal end or the distal end of the support skeleton 20. At the same time, the impeller 30 can also be multiple, preferably 2, and are respectively located at the front end and the rear end of the support skeleton 20.

[0065] The motor 50 can be driven by an internal motor or an external motor through magnetic coupling. The internal micro-motor directly drives the impeller 300 to work to achieve the purpose of pumping blood. Currently, ventricular assist blood pumping devices generally use internal motors for driving. When starting the device during surgery, due to the high-speed rotation of the internal motor, the motor housing has a heat generation problem, resulting in an increase in the hemolysis index and an increase in the surgical risk for the patient. In addition, due to the limitations of the internal motor in terms of size, the motor torque and the impeller size are limited, and the inflow and outflow areas matching them are also limited, resulting in limited flow rate. Therefore, in the preferred embodiment of the present application, the motor 50 connected to the transmission shaft 12 is disposed outside the device, and the motor 50 drives the impeller 30 to rotate through magnetic coupling. By using an external motor 50 and driving through magnetic coupling, the external motor uses an external body motor method, and the motor does not enter the human body, which can effectively solve the problem of heat generation in the body. In addition, within the allowable range of size, the external motor 50 can freely set its torque, and the impeller can fully expand under the drive of the torque, ensuring the blood pumping volume.

[0066] The motor 50 drives the impeller 30 to rotate through magnetic coupling, and the following method is adopted in this embodiment:

[0067] Combined with Figure 11 As shown, the transmission shaft 12 includes a magnetic shaft portion 121 at the distal end and a flexible portion 122 at the proximal end of the magnetic shaft portion 121. The transmission assembly 10 further includes a magnetic ring 13. The magnetic ring 13 is rotatably disposed relative to the magnetic shaft portion 121. The magnetic shaft portion 121 drives the magnetic ring 13 to rotate through magnetic coupling, and the magnetic ring 13 is connected to the impeller 30.

[0068] Specifically, the magnetic ring 13 is entirely made of a magnetic material. As Figure 10 shown, it includes a connecting shaft 131 at the distal end and a sleeve 132 at the proximal end of the connecting shaft 131. The proximal end of the sleeve 132 is open, and at least a part of the magnetic shaft portion 121 near the distal end is disposed inside the sleeve 132. The impeller 30 is installed on the connecting shaft 131.

[0069] When the motor 50 drives the transmission shaft 12 to rotate, the sleeve 132 and the magnetic shaft portion 121 of the transmission shaft 12 achieve rotation through magnetic coupling, thereby driving the impeller 30 to rotate and achieving the purpose of pumping blood.

[0070] In the preferred embodiment of the present application, the transmission assembly 10 further includes an inner tube 14. The inner tube 14 is sleeved outside the transmission shaft 12 and is located inside the outer tube 11. The sleeve 132 is rotatably sleeved on the distal end of the inner tube 14. The part of the magnetic shaft portion 121 disposed inside the sleeve 132 does not contact the inner tube 14. More preferably, the entire transmission shaft 12 is wrapped by the inner tube 14 and does not directly contact the magnetic ring 13, reducing friction and heat generation.

[0071] Among them, the transmission component 10 further includes a housing 15. The housing 15 is connected to the outer tube 11 and wraps the sleeve 132. The connecting shaft 131 extends from the distal end of the housing 15.

[0072] The retractable catheter 40 is slidably disposed outside the outer tube 11. The retractable catheter 40 has a compression chamber 41 and the distal end of the compression chamber 41 is open. The support frame 20 and the impeller 30 can be received into the compression chamber 41 along with the movement of the retractable catheter 40. The entire device is recovered and released by the forward and backward movement of the retractable catheter 40. When the device is delivered to the appropriate position in the heart and released, the transmission component 10 drives the impeller 30 to rotate, thereby realizing the blood pumping function. Figure 5 This is the state when released.

[0073] In a preferred embodiment of the present application, a protection head 60 is provided at the distal end of the support frame 20. The protection head 60 is configured to be soft so as not to harm the patient's organ tissue. The protection head 60 can be made of a flexible material. Specifically, the protection head 6 is a flexible protrusion with an arc-shaped or wound end. The flexible end supports on the inner wall of the ventricle in a non-invasive or non-damaging manner, separating the inflow port 201 from the inner wall of the ventricle, and preventing the inflow port 201 from adhering to the inner wall of the ventricle due to the reaction force of the fluid (blood) during the operation of the device, ensuring the effective area of pumping and suction.

[0074] It can be understood that the materials used in the structures in the present application are all medical-grade materials, mainly processed from medical-grade polymers such as TPU / ABS / TPE / PTFE / PEEK and nickel-titanium and stainless steel alloys, and have good structural strength on the premise of ensuring their safety.

[0075] The above are only the preferred embodiments of the present invention and are not intended to limit the present invention. Any modifications, equivalent replacements, improvements, etc. made within the spirit and principle of the present invention shall be included in the protection scope of the present invention.

Claims

1. A collapsible impeller for pumping blood, characterized in that, Comprising: A telescopic shaft, including a plurality of shaft segments arranged at intervals along the axial direction, and springs are connected between adjacent said shaft segments; An impeller skeleton, which includes at least two sets of helical blades that can be compressed inwardly along the radial direction of the telescopic shaft. Different said sets of helical blades are arranged in sequence from the inside to the outside along the radial direction of the telescopic shaft, and each said set of helical blades has at least two helical blades evenly distributed circumferentially; Said telescopic shaft includes at least three shaft segments, and both ends of the outermost said set of helical blades are respectively connected to the outermost two shaft segments; the impeller skeleton includes three sets of helical blades, namely an outer helical blade set, an inner helical blade set and a middle helical blade set; Wherein, each outer helical blade of the outer helical blade set is evenly distributed circumferentially on the telescopic shaft and is arranged in a helical shape, and both ends of each said outer helical blade are respectively connected to positions close to the outside of two outer shaft segments; each inner helical blade of the inner helical blade set is evenly distributed circumferentially on the telescopic shaft and is arranged in a helical shape, and both ends of each said inner helical blade are respectively connected to positions close to both ends of the inner shaft segment; each middle helical blade of the middle helical blade set is evenly distributed circumferentially on the telescopic shaft and is arranged in a helical shape, and both ends of each said outer helical blade are respectively connected to positions close to the inside of two outer shaft segments.

2. The collapsible impeller for pumping blood according to claim 1, wherein, When the number of shaft segments of the telescopic shaft is greater than 3, said spring includes at least one compression spring and at least two buffer springs, and at least one buffer spring is arranged at both ends of the compression spring.

3. The collapsible impeller for pumping blood according to claim 2, wherein The number of shaft segments of the telescopic shaft is six, and the six said shaft segments are respectively two outer shaft segments, two secondary shaft segments and two inner shaft segments. The two said outer shaft segments are arranged close to the outermost side, the two said secondary shaft segments are respectively located on the inner side of the two outer shaft segments, and the two said inner shaft segments are respectively located on the inner side of the two secondary shaft segments. The compression spring is arranged between the two said inner shaft segments, and the buffer springs are arranged between the outer shaft segment and the secondary shaft segment and between the secondary shaft segment and the inner shaft segment; The impeller skeleton includes an outer helical blade set, a middle helical blade set and an inner helical blade set. The outer helical blade set includes outer helical blades whose two ends are respectively connected to two outer shaft segments correspondingly. The middle helical blade set includes middle helical blades whose two ends are respectively connected to two secondary shaft segments correspondingly. The inner helical blade set includes inner helical blades whose two ends are respectively connected to two inner shaft segments correspondingly.

4. A ventricular assist blood pumping device, characterized in that, Comprising a transmission component, a support skeleton, a contraction catheter and the impeller according to any one of claims 1 - 3; The transmission component includes an outer tube and a transmission shaft. The transmission shaft is arranged inside the outer tube, and one end of the transmission shaft is connected to a motor; The support skeleton is arranged at the distal end of the outer tube. The support skeleton is a compressible and foldable structure, and a cavity is provided inside the support skeleton; The impeller is drivingly connected to the transmission shaft and is arranged inside the cavity; The shrinkable catheter is slidably disposed outside the outer tube. The shrinkable catheter has a compression cavity with an open distal end of the compression cavity. The support framework and the impeller can be received into the compression cavity along with the movement of the shrinkable catheter.

5. The ventricular assist pumping device according to claim 4, wherein The motor connected to the transmission shaft is disposed outside the device, and the motor drives the impeller to rotate through a magnetic coupling manner.

6. The ventricular assist pumping device according to claim 5, characterized in that, The transmission shaft includes a magnetic shaft portion at the distal end and a flexible portion at the proximal end of the magnetic shaft portion. The transmission assembly further includes a magnetic ring. The magnetic ring is rotatably disposed relative to the magnetic shaft portion. The magnetic shaft portion drives the magnetic ring to rotate through a magnetic coupling manner, and the impeller is mounted on the magnetic ring.

7. The ventricular assist pumping device according to claim 6, wherein The magnetic ring includes a connecting shaft at the distal end and a sleeve at the proximal end of the connecting shaft. The proximal end of the sleeve is open. At least a part of the magnetic shaft portion near the distal end is disposed inside the sleeve, and the impeller is mounted on the connecting shaft.

8. The ventricular assist blood pumping device according to claim 7, wherein The transmission assembly further includes an inner tube and a housing. The inner tube is sleeved outside the transmission shaft and is located inside the outer tube. The sleeve is rotatably sleeved on the distal end of the inner tube. The portion of the magnetic shaft portion disposed inside the sleeve does not contact the inner tube. The housing is connected to the outer tube and wraps the sleeve, and the connecting shaft extends out from the distal end of the housing.

9. The ventricular assist pumping device according to claim 4, characterized in that, The support framework includes a framework main body and a framework film. The framework main body is a bracket structure with a grid-shaped side wall. The framework film is covered on the framework main body. The distal end of the framework film encloses to form a fluid inlet and the proximal end forms a fluid outlet. The caliber size of the fluid inlet is larger than the caliber size of the fluid outlet. The framework main body is a nickel-titanium braided structure or a nickel-titanium tube laser cutting structure.

Images