CN117398597A

CN117398597A - Blood pump

Info

Publication number: CN117398597A
Application number: CN202311431877.1A
Authority: CN
Inventors: 谢端卿; 余顺周; 邓达钊; 黄嘉铭
Original assignee: Shenzhen Core Medical Technology Co Ltd
Current assignee: Shenzhen Core Medical Technology Co Ltd
Priority date: 2023-10-31
Filing date: 2023-10-31
Publication date: 2024-01-16

Abstract

The present application relates to a blood pump comprising a housing tube and a drive unit; the proximal end of the shell tube is provided with a liquid inlet, and the distal end of the shell tube is provided with a liquid outlet; the driving unit is arranged in the shell tube and is radially spaced from the inner wall surface of the shell tube to form a blood flow channel, and the blood flow channel is communicated with the liquid inlet and the liquid outlet. Wherein the driving unit comprises a motor and an impeller connected with the motor; the proximal end of the shell tube is fixedly connected with the proximal end of the motor or the catheter of the blood pump. By the arrangement, the axial dimension of the pump body of the blood pump can be designed to be smaller, so that the blood pump can pass through a pushing path from a inferior vena cava (or superior vena cava) to a pulmonary artery, thereby assisting a right ventricle to pump blood into the pulmonary artery, and reducing the risk of over-expansion and expansion in the process of right ventricular congestion.

Description

Blood pump

Technical Field

The application relates to the technical field of medical equipment, in particular to a blood pump.

Background

Interventional blood pumps, also known as endocardial or intravascular blood pumps, may be inserted into a blood vessel and advanced into the patient's heart to function as left or right ventricular assist pumps.

When the right heart auxiliary pump serving as the right heart auxiliary pump in the traditional technology is used for assisting the heart to pump blood, the problem of excessive expansion and expansion of the right heart chamber easily occurs, and the health of a patient is not facilitated.

Disclosure of Invention

Based on the above, the application provides a blood pump which aims at assisting the right ventricle to circulate blood and solving the problem of over-expanding and expanding the right ventricle.

In one aspect, the present application provides a blood pump comprising:

the shell tube is provided with a liquid inlet at the proximal end and a liquid outlet at the distal end; and

the driving unit is arranged in the shell tube, and is radially spaced from the inner wall surface of the shell tube to form a blood flow channel which is communicated with the liquid inlet and the liquid outlet;

wherein the driving unit comprises a motor and an impeller connected with the motor; the proximal end of the shell tube is fixedly connected with the proximal end of the motor or the catheter of the blood pump; the shell tube comprises:

the proximal end of the outlet pipe is fixedly connected with the distal end of the motor, a communication port is arranged on the side wall of the proximal end of the outlet pipe, and the liquid outlet is arranged at the distal end of the outlet pipe; and

the inlet pipe is sleeved on the periphery of the motor, the liquid inlet is formed in the proximal end of the inlet pipe, and the proximal end of the inlet pipe is fixedly connected with the motor or the guide pipe; the far end of the inlet pipe is fixedly connected with the peripheral wall of the outlet pipe so that the communication port is contained in the inlet pipe;

The impeller is accommodated in the outlet pipe; a gap is arranged between the motor and the inner wall surface of the inlet pipe, and the gap is communicated with the communication port and the inner cavity of the outlet pipe to form the blood flow channel;

the distal end of the motor stretches into the outlet pipe, the distal end of the motor is provided with a first reducing surface, the first reducing surface is positioned at the inner side of the communication port, and the diameter of the first reducing surface is gradually reduced along the direction from the motor to the impeller.

In one embodiment, the motor includes a motor body and a shaft support; wherein the motor body is housed within the inlet tube; the shaft support seat is connected to the distal end of the motor main body and extends into the outlet pipe, and the outer peripheral wall of the shaft support seat forms the first reducing surface.

In one embodiment, the inlet pipe comprises a main body section and a first necking section connected with the distal end of the main body section, and the distal end of the first necking section is fixedly connected with the outer peripheral surface of the outlet pipe; the first reducing section is provided with an inner reducing surface, the inner reducing surface is positioned at the outer side of the communication port, and the diameter of the inner reducing surface and the diameter of the first reducing surface are gradually reduced along the same direction.

In one embodiment, the distance between the inner reducing surface of the first reducing section and the first reducing surface is gradually increased along the direction from the motor to the impeller.

In one embodiment, the first necked section further has an outer tapered surface facing away from the inner tapered surface, the outer tapered surface being receivable within a right ventricle for contact engagement by a surface of a pulmonary valve facing the right ventricle.

In one embodiment, the first necked-down section has a first axial length D ₁ The body section has a second axial length D ₂ The first axial length D ₁ And the second axial length D ₂ The ratio of (C) to (D) is 1/4 or less ₁ /D ₂ ≤1/3。

In one embodiment, the inlet pipe comprises a main body section and a second necking section connected with the proximal end of the main body section, the proximal end of the second necking section is fixedly connected with the motor or the guide pipe, the diameter of the second necking section gradually increases along the direction from the motor to the impeller, and the liquid inlet axially extends from the second necking section to the main body section.

In one embodiment, the liquid inlet includes a first inlet region on the second necked section and a second inlet region on the main body section; wherein the first inlet zone has a first width along the circumference of the inlet pipe and the second inlet zone has a second width along the circumference of the inlet pipe, the second width being greater than the first width; the first width gradually increases in a direction from the conduit to the motor.

In one embodiment, the motor includes a motor body and a proximal end cap; the proximal end cover is arranged at the proximal end of the motor main body and fixedly connected with the guide pipe, the outer circumferential surface of the proximal end cover is provided with a second reducing surface, and the diameter of the second reducing surface is gradually increased along the direction from the guide pipe to the motor;

the second reducing surface extends from the interior of the main body section to the interior of the second reducing section such that a proximal portion of the second reducing surface is radially opposite the liquid inlet and a distal portion of the second reducing surface is radially opposite the inner wall surface of the main body section.

In one embodiment, the outlet pipe comprises a first pipe section and a second pipe section connected with the first pipe section, the first pipe section is provided with the liquid outlet, the second pipe section stretches into the inlet pipe, and the second pipe section is provided with the communication port; wherein,

the outer diameter of the second pipe section is larger than that of the first pipe section, so that a step part is formed between the outer peripheral surface of the second pipe section and the outer peripheral surface of the first pipe section; the far end of the inlet pipe is provided with a first inserting part, the end face of the first inserting part is in abutting connection with the step part, and the outer surface of the first inserting part is flush with the outer peripheral surface of the second pipe section;

And/or the distal end of the motor is provided with a shaft shoulder part, the proximal end of the second pipe section is provided with a second plug-in connection part, the end face of the second plug-in connection part is in butt joint with the shaft shoulder part, and the outer peripheral surface of the second plug-in connection part is flush with the outer peripheral surface of the motor.

In one embodiment, the thickness of the second plug portion is greater than the thickness of the second tube segment; and/or the connection part of the inner wall surface of the second plug-in connection part and the inner wall surface of the second pipe section is provided with a rounding angle.

In one embodiment, the liquid outlet comprises a plurality of second openings, and the second openings are arranged at intervals along the circumferential direction of the shell tube; each second opening is in a strip shape and extends along the axial direction of the shell tube.

In one embodiment, the inlet tube is made of a hard material such that the inlet tube is in a non-expandable configuration; and/or the outlet tube is made of a hard material such that the outlet tube is in a non-expandable configuration.

In one embodiment, the outlet pipe comprises a first pipe section and a second pipe section connected with the first pipe section, the first pipe section is provided with the liquid outlet, the second pipe section stretches into the inlet pipe, and the second pipe section is provided with the communication port;

The proximal end portion of the impeller is housed within the second tube segment such that a side surface of the proximal end portion of the impeller is opposite to the communication port; the distal portion of the impeller is received within the first tube section and is adjacent or near the liquid outlet.

In one embodiment, the inner wall surface of the inlet pipe is convexly provided with a plurality of guide fins, the guide fins are arranged at intervals along the circumferential direction of the inlet pipe, and each guide fin extends along the axial direction of the inlet pipe.

In one embodiment, the liquid inlet comprises a plurality of first openings arranged at intervals along the circumferential direction of the inlet pipe, and a partition wall is formed between two adjacent first openings; the guide fins are respectively in one-to-one correspondence with the separation walls, and the proximal ends of the guide fins at least partially extend to the inner wall surfaces of the separation walls;

and/or, the proximal end of the guide fin protrudes from the inner wall surface of the inlet pipe to a first height, and gradually increases along the direction from the guide pipe to the motor; the distal ends of the guide fins protrude from the inner wall surface of the inlet pipe by a second height, and gradually decrease in the direction from the guide pipe to the motor.

In one embodiment, the casing has a first length in an axial direction of the drive unit; the first length is such that the blood pump is capable of passing from the right atrium, right ventricle, pulmonary valve to extend into the pulmonary artery such that the fluid inlet is in the right ventricle and the fluid outlet is in the pulmonary artery.

In one embodiment, the first length is 20mm-32mm.

According to the blood pump, the liquid inlet and the liquid outlet are formed in the shell tube, the driving unit is arranged in the shell tube, so that the inner wall surface of the shell tube and the driving unit are formed with the blood flow channel along the radial interval of the driving unit, and the liquid inlet and the liquid outlet are communicated through the blood flow channel; the driving unit comprises a motor and an impeller connected with the motor; the proximal end of the shell tube is fixedly connected with the proximal end of the motor or the catheter of the blood pump, so that the axial length of the pump body of the blood pump can be effectively shortened, and the blood pump can be suitable for a pushing path from a inferior vena cava (or superior vena cava) to a pulmonary artery. When the blood pump is used as the right ventricle of an interventional patient, the blood pump may pass from the right atrium through the tricuspid valve into the right ventricle and through the pulmonary valve to partially extend into the pulmonary artery such that the inlet of the blood pump is in the right ventricle and the outlet of the blood pump is in the pulmonary artery.

After the blood pump is started, the motor of the driving unit drives the impeller to rotate, so that the blood in the right atrium flows into the right ventricle, and the blood in the right ventricle is sucked into the blood flow channel in the blood pump through the liquid inlet of the blood pump and then is discharged into the pulmonary artery from the liquid outlet of the blood pump under the driving of the impeller. Therefore, compared with the mode that the liquid inlet and the liquid outlet of the traditional blood pump are all arranged in the inferior vena cava in a penetrating mode, so that the right ventricle is at a transitional expansion risk, the blood pump can penetrate through the pulmonary artery from the right ventricle to assist the pressure release of the right ventricle, so that the risk of excessive expansion in the process of congestion of the right ventricle can be reduced, and the use safety of the blood pump is improved.

Drawings

Fig. 1 is a schematic representation of a human heart anatomy.

Fig. 2 is a schematic diagram of a blood pump according to an embodiment of the present application applied to assist the right ventricle in pumping blood.

Fig. 3 is an isometric view of the blood pump of fig. 2.

Fig. 4 is a cross-sectional view of the blood pump of fig. 3 taken along line A-A.

Fig. 5 is an enlarged view of a portion of the outlet tube at B of fig. 4.

Fig. 6 is an enlarged view of a portion of the blood pump at C shown in fig. 4.

Fig. 7 is a schematic view of the blood pump of fig. 4 with blood flowing through the channels.

Fig. 8 is an exploded view of the blood pump of fig. 3.

Fig. 9 is a cross-sectional view of an inlet tube in the blood pump of fig. 4.

Fig. 10 is a cross-sectional view of a blood pump according to another embodiment of the present application.

Fig. 11 is a partial enlarged view of the blood pump shown in fig. 10 at D.

Fig. 12 is a cross-sectional view of the drive unit in the blood pump of fig. 4.

Fig. 13 is a cross-sectional view of an outlet tube of the blood pump of fig. 4.

Fig. 14 is an enlarged view of a portion of the blood pump shown in fig. 13 at E.

Fig. 15 is a schematic view of a blood pump according to yet another embodiment of the present application being inserted into the right ventricle of a heart.

Reference numerals: 10. a blood pump; 11. a pump body; 12. a conduit; 100. a driving unit; 110. a motor; 111. a motor main body; 101. a cylindrical shell; 102. a shaft shoulder; 103. a first rotor; 104. a stator; 105. a second rotor; 106. a rotating shaft; 112. a shaft support base; 112a, a first reducing surface; 113. a proximal cap; 113a, a second reducing surface; 120. an impeller; 200. a shell tube; 210. an inlet pipe; 211. a first necked section; 211a, inner reducing surfaces; 211b, outer A reducing surface; 212. a second necked section; 213. a main body section; 214. a liquid inlet; 214a, a first inlet zone; 214b, a second inlet zone; 214c, a first opening; 215. a first plug-in connection; 216. a deflector fin; 217. a partition wall; 220. an outlet tube; 220a, a liquid outlet; 220b, a second opening; 221. a first pipe section; 222. a second pipe section; 222a, a communication port; 222b, a second plug-in part; 223. a step portion; 224. a fixing part; 224a, a glue containing groove; 400. a blood flow path; 410. a gap; 411 a first guide flow path; 412. a second guide flow path; 413. a first delivery flow path; 420. a second delivery flow path; 20. a heart; 21. right atrium; 22. a right ventricle; 23. tricuspid valve; 24. pulmonary valve; 31. superior vena cava; 32. inferior vena cava; 33. pulmonary artery; l (L) ₁ The width of the first guide flow channel; d (D) ₁ A first axial length; d (D) ₂ A second axial length; s is S ₁ A first width; s is S ₂ A second width; r, rounded corners; h ₁ A first height; h ₂ A second height.

20. Inferior vena cava; 21. superior vena cava; 22. right atrium; 23. tricuspid valve; 24. a right ventricle; 25. pulmonary valve; 25a, inner side; 26. pulmonary artery; 27. pulmonary veins; 28. the left atrium; 29. mitral valve, 30, left ventricle; 31. an aortic valve; 32. the aorta.

Detailed Description

In order to make the above objects, features and advantages of the present application more comprehensible, embodiments accompanied with figures are described in detail below. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present application. This application is, however, susceptible of embodiment in many other forms than those described herein and similar modifications can be made by those skilled in the art without departing from the spirit of the application, and therefore the application is not to be limited to the specific embodiments disclosed below.

In the description of the present application, it should be understood that, if there are terms such as "center", "longitudinal", "transverse", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential", etc., these terms refer to the orientation or positional relationship based on the drawings, which are merely for convenience of description and simplification of description, and do not indicate or imply that the apparatus or element referred to must have a specific orientation, be configured and operated in a specific orientation, and therefore should not be construed as limiting the present application.

Furthermore, the terms "first," "second," and the like, if any, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include at least one such feature. In the description of the present application, the terms "plurality" and "a plurality" if any, mean at least two, such as two, three, etc., unless specifically defined otherwise.

In this application, unless explicitly stated and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly. For example, the two parts can be fixedly connected, detachably connected or integrated; can be mechanically or electrically connected; either directly or indirectly, through intermediaries, or both, may be in communication with each other or in interaction with each other, unless expressly defined otherwise. The specific meaning of the terms in this application will be understood by those of ordinary skill in the art as the case may be.

In this application, unless expressly stated or limited otherwise, the meaning of a first feature being "on" or "off" a second feature, and the like, is that the first and second features are either in direct contact or in indirect contact through an intervening medium. Moreover, a first feature being "above," "over" and "on" a second feature may be a first feature being directly above or obliquely above the second feature, or simply indicating that the first feature is level higher than the second feature. The first feature being "under", "below" and "beneath" the second feature may be the first feature being directly under or obliquely below the second feature, or simply indicating that the first feature is less level than the second feature.

It will be understood that if an element is referred to as being "fixed" or "disposed" on another element, it can be directly on the other element or intervening elements may also be present. If an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present. The terms "vertical," "horizontal," "upper," "lower," "left," "right," and the like as used herein, if any, are for descriptive purposes only and do not represent a unique embodiment.

In the related art, an interventional assistance device, also called a blood pump, is mainly applied to an intervention into a blood vessel of a patient to assist the blood circulation of the patient. In order to facilitate understanding of the application of the blood pump, the heart structure and blood flow direction will be briefly described. Referring to fig. 1, fig. 1 is an anatomical structure of a human heart. The blood circulation of the human body includes the systemic circulation and the pulmonary circulation. Wherein blood is ejected from the left ventricle 30 through the aortic valve 31 to the aorta 32, and the substance exchange is performed in capillaries flowing through the aorta 32 to the whole body, so that arterial blood becomes venous blood, and the venous blood flows back to the right atrium 22 through the superior vena cava 21 and the inferior vena cava 20, and this cycle is called the systemic circulation. Next, the blood from the right atrium 22 enters the right ventricle 24 through the tricuspid valve 23, is ejected from the right ventricle 24 through the pulmonary valve 25 to the pulmonary artery 26, and flows through the pulmonary artery 26 to the pulmonary capillaries of each stage for gas exchange, so that the venous blood becomes arterial blood, the arterial blood finally flows back from the pulmonary vein 27 to the left atrium 28, and the blood from the left atrium 28 enters the left ventricle 30 from the mitral valve 29, and this cycle is called pulmonary circulation.

A relatively common type of blood pump is the left ventricular assist pump. Such left ventricular assist pumps generally include a drive unit and a cannula assembly; wherein, the proximal end of the sleeve component is provided with a liquid outlet, and the distal end of the sleeve component is provided with a liquid inlet; the motor of the driving unit is fixedly connected with the proximal end of the sleeve assembly, and the impeller of the driving unit is arranged in the sleeve assembly and is connected with the rotating shaft of the motor. The length of such a cannula assembly is typically more than several times the length of the drive unit, so that the axial length of the pump body of the left ventricular assist pump is long. When a left ventricular assist pump is applied to the left ventricle 30, it is common to pass the left ventricular assist pump from the aorta 32 through the aortic valve 31 such that the inlet of the left ventricular assist pump extends into the left ventricle 30 and the outlet of the left ventricular assist pump is located within the aorta 32, i.e. only the distal portion of the left ventricular assist pump extends into the left ventricle 30. Thus, the left ventricular assist pump is capable of assisting the left ventricle 30 to pump blood from the left ventricle 30 to the aorta 32. The path of the left ventricular assist pump from the ascending portion of the aorta 32 through the aortic valve 31 to enter the left ventricle 30 is relatively similar to the same axial direction, so that the left ventricular assist pump having the pump body with a longer axial length can adapt to the pushing path of the left ventricle 30.

If the patient's right ventricle 24 is dysfunctional, a blood pump is also required to assist the right ventricle 24 in pumping blood. Therefore, it is also contemplated to apply a left ventricular assist pump to assist the right ventricle 24 in pumping blood. However, the push path of the blood pump implanted in the right ventricle passes through the right atrium, the tricuspid valve 23, the right ventricle 24 and the pulmonary valve 25 in sequence from the inferior vena cava 20 or the superior vena cava 21 to the pulmonary artery 26, and thus, the push path of the blood pump implanted in the right ventricle is short, and the blood pump implanted in the right ventricle has a large number of bends and a complex internal structure. Such a left ventricular assist pump is difficult to apply to the right ventricle 24 because of the excessive axial length of the pump body of the conventional left ventricular assist pump, which is difficult to pass through the push path of the right ventricle 24.

Thus, there is a right ventricular assist pump available on the market that can be used to assist the flow of blood in the right ventricle 24, which is adapted to be introduced from a wound in the waist or thigh of a patient to the inferior vena cava 20 with both the inlet and outlet of the right ventricular assist pump positioned in the inferior vena cava 20, i.e. without the outlet of the right ventricular assist pump extending into the pulmonary artery 26. When the right ventricular assist pump is started, the right ventricular assist pump can only drive blood in the lower vena cava 20 to accelerate to flow to the right atrium, and then enter the right ventricle 24 through the right atrium, but can not assist the right ventricle 24 to pump the blood into the pulmonary artery 26 for decompression, so that the right ventricular assist pump has an obvious defect that excessive expansion is easily generated in the process of congestion of the right ventricle 24, and a certain potential safety hazard is generated for health of patients.

Referring to fig. 1, in order to solve the above-mentioned problems, the present application provides a blood pump 10, and the blood pump 10 is mainly used as a right ventricular assist pump. The blood pump 10 can be threaded from the right ventricle 24 into the pulmonary artery 26 to assist the right ventricle 24 in pumping blood into the pulmonary artery 26 for decompression of the right ventricle 24. Of course, in other embodiments, the blood pump 10 may also be used as a left ventricular assist pump. In the field of medical device technology, the medical device is generally referred to as a proximal end at the end close to a doctor or an operator and a distal end at the end far from the doctor or the operator.

Referring to fig. 2 to 4, a blood pump 10 according to an embodiment of the present disclosure includes a driving unit 100 and a casing 200. The proximal end of the shell tube 200 is provided with a liquid inlet 214, and the distal end of the shell tube 200 is provided with a liquid outlet 220a; the driving unit 100 is disposed inside the casing 200, and a blood flow path 400 is formed by the driving unit 100 being spaced apart from the inner wall surface of the casing 200 in the radial direction, and the blood flow path 400 communicates the liquid inlet 214 with the liquid outlet 220 a. The radial direction refers to the radial direction of the driving unit 100. Wherein the driving unit 100 includes a motor 110 and an impeller 120 connected to the motor 110; the proximal end of the housing tube 200 is fixedly connected with the motor 110 or the catheter 12 of the blood pump 10, so that the driving unit 100 is stably positioned in the housing tube 200.

Specifically, the drive unit 100 and the casing 200 constitute the pump body 11 of the blood pump 10, and the axial length of the blood pump 10 refers to the length of the pump body 11. Here, by disposing both the motor 110 and the impeller 120 of the driving unit 100 inside the casing 200, that is, accommodating the driving unit 100 as a whole inside the casing 200, instead of arranging the motor 110 and the casing 200 in the axial direction (such as the arrangement of the motor and the sleeve assembly of the conventional left heart assist pump), the axial length of the pump body 11 of the blood pump 10 can be greatly shortened, so that the pump body 11 of the blood pump 10 can pass through a short and much-curved pushing path from the inferior vena cava 20 (or the superior vena cava 21) to the pulmonary artery 21, so that the liquid inlet 214 is located in the right ventricle 24, and the liquid outlet 220a is located in the pulmonary artery 26.

Specifically, as shown in fig. 2, fig. 2 shows a schematic diagram in which the blood pump 10 of the present application is applied as a right ventricle auxiliary pump for assisting the right ventricle in pumping blood, and a dashed arrow F is indicated as a blood flow direction in fig. 2. One of the route of delivery of the blood pump 10 is for the pump body 11 of the blood pump 10 to pass from the inferior vena cava 20 into the right atrium 22, then from the right atrium 22 through the tricuspid valve 23 into the right ventricle 24, and then from the right ventricle 24 through the pulmonary valve 25 to extend partially into the pulmonary artery 26, ensuring that the inlet port 214 of the blood pump 10 is located within the right ventricle 24 and the outlet port 220a of the blood pump 10 is located within the pulmonary artery 26. Another route of delivery for the blood pump 10 is for the body 11 of the blood pump 10 to enter the right atrium 22 from the superior vena cava 21, then pass from the right atrium 22 through the tricuspid valve 23 into the right ventricle 24, and then pass from the right ventricle 24 through the pulmonary valve 25 to extend partially into the pulmonary artery 26, ensuring that the inlet 214 of the blood pump 10 is located in the right ventricle 24 and the outlet 220a of the blood pump 10 is located in the pulmonary artery 26.

As can be seen from fig. 1 and 2, the pushing path of the blood pump 10 from the inferior vena cava 20 or the superior vena cava 21 to the pulmonary artery 26 has the characteristics of short path, more curved openings, complex internal tissues, and the like. Because the axial length of the pump body 11 of the blood pump 10 is shorter, the pump body 11 can pass through each bending port of the pushing path with a shorter path and enter the pulmonary artery 26 after turning upwards (or deflecting) in the narrow right ventricle 24, so that the difficulty of the blood pump 10 entering the right ventricle 24 is greatly reduced, and the smoothness of the blood pump 10 passing through the pushing path is improved.

When the blood pump 10 is turned on, the motor 110 of the driving unit 100 drives the impeller 120 to rotate, so that blood enters the right ventricle 24 through the right atrium, and the blood in the right ventricle 24 is sucked into the blood flow path 400 by the liquid inlet 214 of the blood pump 10; the blood in the blood flow path 40 continues to be driven by the impeller 120 to flow toward the fluid outlet 220a, and finally the blood is discharged from the fluid outlet 220a to the pulmonary artery 26. It can be seen that the blood pump 10 of the present application is capable of penetrating from the right ventricle 24 to the pulmonary artery 26 to assist the decompression of the right ventricle 24, thereby reducing the charging of the right ventricle 24The risk of over-distension and swelling during blood processing increases the safety of the blood pump 10 in use. M in FIGS. 4 to 5 ₁ And M ₂ Is two points on the axis (i.e. axial) of the blood pump 10, namely the dashed line M ₁ M ₂ May represent the axis of the blood pump 10; from M ₁ To M ₂ Is along the axis of the blood pump 10 and is directed distally from the proximal end; conversely, from M ₂ To M ₁ Is along the axis of the blood pump 10 and is directed proximally from the distal end.

It will be appreciated that since the driving unit 100 is accommodated inside the casing 200, and the blood flow channel 400 is formed between the inner circumferential wall of the casing 200 and the driving unit 100, the length of the casing 200 is equivalent to the axial length of the pump body 11, and the length of the casing 200 may be designed to be only slightly longer than the driving unit 100 (in order to be able to accommodate the driving unit and make the driving unit work normally), without the need to design the length to be several times as long as the driving unit 100 as in the conventional cannula assembly.

Referring to fig. 3 and 4, the blood pump 10 further includes a catheter 12, wherein a distal end of the catheter 12 is fixedly connected with a proximal end of the motor 110, and supply lines (not shown) such as a wire and a flushing line are disposed in the catheter 12. The proximal end of the housing tube 200 may be directly affixed to the catheter 12, or the proximal end of the housing tube 200 may be affixed to the proximal end of the motor 110. Since the catheter 12 is typically of a deformable nature to fit into a blood vessel, the axial dimensions of the catheter 12 generally have little effect on the difficulty of implantation of the blood pump 10 within the heart 20. That is, the above-described possibility of designing the axial dimension of the blood pump 10 smaller mainly refers to the axial dimension of the pump body 11 of the blood pump 10. The portion of the blood pump 10 located in the heart 20 is mainly referred to as the pump body 11. The present application is configured such that the axial length of the pump body 11 of the blood pump 10 can be designed to be smaller so that the pump body 11 of the blood pump 10, after entering the right ventricle 24, can bend (or deflect) upward in the right ventricle 24 to pass through the pulmonary valve 25 so that the inlet port 214 of the blood pump 10 is within the right ventricle 24 and the outlet port 220a of the blood pump 10 can pass from the pulmonary valve 25 into the pulmonary artery 26.

Referring to fig. 4 to 8, in one embodiment, the housing tube 200 includes an inlet tube 210 and an outlet tube 220, and the inlet tube 210 is connected to the outlet tube 220. The proximal end of the outlet pipe 220 is fixedly connected with the distal end of the motor 110, and a communication port 222a is also formed in the side wall of the proximal end of the outlet pipe 220; the distal end of the outlet tube 220 is provided with a liquid outlet 220a; the inlet pipe 210 is sleeved on the outer periphery of the motor 110, the proximal end of the inlet pipe 210 is provided with a liquid inlet 214, the proximal end of the inlet pipe 210 is fixedly connected with the motor 110 or the conduit 12, and the distal end of the inlet pipe 210 is fixedly connected with the outer peripheral wall of the outlet pipe 220, so that the communication port 222a is accommodated in the inlet pipe 210. Wherein the impeller 120 is housed within the outlet tube 220; a gap 410 is provided between the motor 110 and the inner wall surface of the inlet tube 210, and the gap 410 communicates with the communication port 222a and the inner cavity of the outlet tube 220 to form a blood flow path 400.

Specifically, the catheter 12 is axially and proximally-to-distally oriented (i.e., from M) along the blood pump 10 with the motor 110, the outlet tube 220 ₁ To M ₂ Direction of (c) are sequentially arranged and connected. The proximal end of the inlet tube 210 is fixedly connected to the distal end of the catheter 12 or the proximal end of the motor 110 to support the proximal end of the motor 110; the distal end of the inlet pipe 210 is connected to the outer peripheral wall of the outlet pipe 220, and the connection between the outlet 220a and the communication port 222a of the outlet pipe 220 is located on the outer peripheral wall, so that the proximal end of the outlet pipe 220 extends into the inlet pipe 210 and is fixedly connected to the distal end of the motor 110 to support the distal end of the motor 110. That is, the inlet tube 210 and the outlet tube 220 support the proximal end and the distal end of the motor 110, respectively, thereby stably supporting the motor 110 within the housing tube 200, and further stably defining the gap 410 between the outer circumferential surface of the motor 110 and the inner wall surface of the inlet tube 210.

The inlet pipe 210 and the outlet pipe 220 are hollow tubular structures; the communication port 222a at the proximal end of the outlet tube 220 can communicate the gap 410 at the outer periphery of the motor 110 with the inner cavity of the outlet tube 220 to form the blood flow path 400. Blood enters the gap 410 from the inlet port 214 (see the blood flow direction indicated by the broken line arrow F in fig. 7), then flows from the gap 410 to the communication port 222a, enters the inner cavity of the outlet tube 220 from the communication port 222a, and finally is discharged from the outlet port 220a of the outlet tube 220. Therefore, the casing 200 can cooperate with the driving unit 100 to form the blood flow channel 400 through which blood flows smoothly, so as to provide a basis for shortening the axial dimension of the pump body 11 of the blood pump 10, thereby improving the ability of the blood pump 10 to traverse complex paths, and facilitating the distal end of the blood pump 10 with the liquid outlet 220a to penetrate into the pulmonary artery 26 more smoothly.

Referring to fig. 4 to 8, in one embodiment, the distal end of the motor 110 extends into the outlet pipe 220, and the distal end of the motor 110 has a first reducing surface 112a, the first reducing surface 112a is located inside the communication port 222a, and the diameter of the first reducing surface 112a is gradually reduced along the direction from the motor 110 to the impeller 120. With this arrangement, after the blood enters the proximal end of the outlet tube 220 from the communication port 222a, the blood contacts the first tapered surface 112a of the motor 110, so that at least a portion of the blood flows along the first tapered surface 112a, and flows from the direction guided by the first tapered surface 112a toward the outlet 220a of the outlet tube 220, thereby improving the smoothness of the blood flowing from the inlet tube 210 into the outlet tube 220 through the communication port 222a and accelerating the blood flow.

It is understood that the first tapered surface 112a is the outer circumferential surface of the distal end of the motor 110. Alternatively, the motor 110 includes a motor body 111 and a shaft support 112. The shaft support 112 is connected to the distal end of the motor body 110. The motor main body 111 has a rotation shaft 106, the rotation shaft 106 penetrates through the shaft support base 112 along the axial direction to be fixedly connected with the impeller 120, and the shaft support base 112 can support the rotation shaft 106, so that the rotation shaft 106 stably drives the impeller 120 to rotate. The outer diameter of the shaft support 112 is gradually reduced along the direction from the motor 110 to the impeller 120, so that the shaft support 112 is generally arranged in a frustum shape.

Optionally, the shaft support base 112 extends into the outlet pipe 220, the outer peripheral wall of the shaft support base 112 forms a first reducing surface 112a, the first reducing surface 112a is located inside the communication port 222a, and the diameter of the first reducing surface 112a is in the direction from the motor 110 to the impeller 120 (i.e., from M ₁ To M ₂ Direction of (c) gradually decreases. After entering the proximal end of the outlet tube 220 from the communication port 222a, the blood first contacts the first tapered surface 112a of the shaft support 112, so that at least a portion of the blood flows along the first tapered surface 112a while being coanda-flowed, and flows from being guided by the first tapered surface 112a toward the outlet 220a of the outlet tube 220, to thereby enhance the flow of the blood from the inlet tube 210 into the outlet tube 220 through the communication port 222a And accelerating blood flow.

Referring to fig. 3 and 9, in one embodiment, the inlet tube 210 includes a main body section 213 and a first necked-down section 211; the first necked-down section 211 is connected to the distal end of the main body section 213 and fixedly connected to the outer peripheral wall of the outlet tube 220. The inlet tube 210 may also include a second necked-down section 212, the second necked-down section 212 being connected to the proximal end of the main body section 213 and fixedly connected to the motor 110 or the catheter 12. That is, the inlet tube 210 may include a body section 213 and at least one of a first necked-down section 211 and a second necked-down section 212.

Referring to fig. 4, 5 and 9, in one embodiment, the inlet tube 210 includes a main body section 213 and a first necked-down section 211. The distal end of the first reducing section 211 is fixedly connected with the outer peripheral wall of the outlet pipe 220, the first reducing section 211 has an inner reducing surface 211a positioned outside the communication port 222a, the diameter of the inner reducing surface 211a gradually decreases in the same direction as the diameter of the first reducing surface 112a, i.e. the diameter of the inner reducing surface 211a also decreases in the direction from the motor 110 to the impeller 120 (i.e. from M ₁ To M ₂ Is provided) such that the inner tapered surface 211a is inclined relatively toward the communication port 222a from the proximal end to the distal end.

It will be appreciated that the first necked-down section 211 serves as the distal end portion of the inlet tube 210, since the inner tapered surface 211a of the first necked-down section 211 is located outside the communication port 222a, the spaced region between the inner tapered surface 211a of the first necked-down section 211 and the outer peripheral wall of the proximal end of the outlet tube 220 forms the distal end of the gap 410. Thus, when the blood in the gap 410 flows to the distal end of the gap 410, at least part of the blood flows along the inner reducing surface 211a of the first reduced port section 211 with the wall, so as to be guided by the inner reducing surface 211a obliquely to the communication port 222a of the outlet pipe 220, so that the blood in the gap 410 passes more smoothly from the communication port 222a to enter the proximal end of the outlet pipe 220.

Obviously, the proximal blood entering the outlet tube 220 from the communication port 222a is further guided by the first tapered surface 112a of the shaft support 112 to flow in the distal direction of the outlet tube 220. That is, the inner tapered surface 211a of the first reduced section 211 and the first tapered surface 112a of the shaft support 112 are respectively engaged on the inner and outer sides of the communication port 222a to guide the blood flow, so that the blood can smoothly flow from the communication port 222a into the outlet pipe 220 from the gap 410, not only the blood flow can be accelerated, but also the blood collision damage can be reduced.

Referring to fig. 4, 5 and 7, a flow path formed by the first reducing surface 112a and the inner reducing surface 211a of the first reducing section 211 is referred to as a first guide flow path 411, and the first guide flow path 411 is a part of the gap 410. In one embodiment, the spacing L between the first tapered surface 112a and the inner tapered surface 211a ₁ In a direction along the outlet tube 220 to the motor 110 to the impeller 120 (i.e., from M ₁ To M ₂ The direction of (c) is arranged to be gradually increased. Pitch L ₁ And also corresponds to the width of the first guide flow passage 411. Thus, the first guide flow passage 411 has a cross section similar to a diverging horn shape, so that blood is easily guided from the inside of the inlet tube 210 to the inside of the outlet tube 220 through the communication port 222 a.

Referring to fig. 4, 5 and 15, the first reducing section 211 further has an outer reducing surface 211b opposite to the inner reducing surface 211a, and the diameter of the outer reducing surface 211b of the first reducing section 211 decreases along the same direction as the inner reducing surface 211 a. The outer tapered surface 211b can be received within the right ventricle 24 for contact engagement by the surface of the pulmonary valve 25 facing the right ventricle 24. That is, when the blood pump 10 is inserted into the right ventricle 24, the first necked-down section 211 of the inlet tube 210 of the blood pump 10 is positioned within the right ventricle 24. The pulmonary valve 25 has a valve side 25a facing the right ventricle 24; the outer reducing surface 211b of the first reducing section 211 has a shape similar to the valve side surface 25a of the pulmonary valve 25, so that the valve side surface 25a can be attached and clamped, and the stability of the blood pump 10 penetrating the pulmonary valve 25 can be improved. Furthermore, the distal end of the first necked down section 211 or the outlet tube 220 has a smaller diameter at a location adjacent to the first necked down section 211 and is also less subject to force at the location where the pulmonary valve 25 is clamped, thereby reducing the force on the pulmonary valve 25 and reducing damage to the pulmonary valve 25.

With continued reference to fig. 7, the flow path formed by the motor main body 111 and the inlet pipe 210 arranged at intervals in the radial direction is denoted as a first conveying flow path 413, and the first conveying flow path 413 is also one of the components of the gap 410. In one embodiment, the first necked-down section 211 has First axial length D ₁ The body section 213 has a second axial length D ₂ ，1/4D ₂ ≤D ₁ ≤1/3D ₂ . I.e. the axial length of the first guide flow channel 411 is between 1/4 and 1/3 of the axial length of the first delivery flow channel 413. This ensures that the first guide flow passage 411 has a sufficient length to drain blood so that blood can be effectively drained from both the inner and outer sides of the communication port 222a, and the smoothness of the blood turning from the first delivery flow passage 413 into the outlet pipe 220 through the first guide flow passage 411 is improved.

Referring to fig. 4 and 9, in one embodiment, the inlet tube 210 includes a main body 2133 and a second necking segment 212 disposed at a proximal end of the main body 2133, wherein the proximal end of the second necking segment 212 is fixedly connected with the motor 110 or the catheter 12, and a diameter of the second necking segment 212 is along a direction from the motor 110 to the impeller 120 (i.e. from M ₁ To M ₂ Direction of (c) increases gradually. Wherein the liquid inlet 214 extends from the second necked-down section 212 to the main section 213 in the axial direction. Thus, on the one hand, the inlet 214 is made to have a large dimension in the axial direction to facilitate inflow of blood. On the other hand, since the gap 410 is located substantially at the outer periphery of the blood pump 10, providing the second constriction 212 with a diameter gradually increasing in the direction from the proximal end toward the distal end enables the inner wall surface of the second constriction 212 to guide blood located at the radially opposite inner side to flow into the gap 410 located near the outer periphery, so as to improve the blood flow smoothness at the liquid inlet 214.

Referring to fig. 4, 7 and 9, in one embodiment, the liquid inlet 214 includes a first inlet region 214a and a second inlet region 214b, the first inlet region 214a is located on the second necking segment 212, and the second inlet region 214b is located on the main body segment 213. Wherein the first inlet zone 214a has a first width S along the circumference of the inlet tube 210 ₁ The second inlet zone 214b has a second width S along the circumference of the inlet tube 210 ₂ Second width S ₂ Is greater than the first width S ₁ And a first width S ₁ In the direction of the conduit 12 to the motor 110 (i.e., from M ₁ To M ₂ Direction of (c) increases gradually. In this way, the inlet area of the liquid inlet 214 is gradually increased along the blood flow direction, which is not only beneficial to guiding bloodThe inflow into the inlet 214 gradually from near to far may also increase the inlet area of the inlet 214.

Referring to fig. 4, 7 and 8, in one embodiment, the motor 110 further includes a proximal cover 113, and the proximal cover 113 is disposed at a proximal end of the motor body 111 and connects the motor body 111 and the catheter 12 to accommodate a connection between the motor body 111 and the catheter 12 therein. The proximal cap 113 is located inside the inlet 214, and the proximal cap 113 has a function of guiding blood entering from the inlet 214 to the gap 410.

Specifically, the motor body 111 may be housed within the body section 213. The proximal cap 113 is fixedly connected to the catheter 12, and the proximal cap 113 may be connected to the proximal end of the inlet tube 210 via the catheter 12. The outer peripheral surface of the proximal cap 113 is provided with a second tapered surface 113a, and the diameter of the second tapered surface 113a is in the direction from the catheter 12 to the motor 110 (i.e., from M ₁ To M ₂ Direction of (c) increases gradually. The second reducing surface 113a is located inside the liquid inlet 214, the second reducing surface 113a is radially opposite to the second reducing section 212, and a second guide flow passage 412 is formed therebetween, and the second guide flow passage 412 is a front end of the gap 410.

After the blood enters the second guide flow passage 412 of the gap 410 from the inlet 214, at least part of the blood contacts the second reducing surface 113a, and under the suction action of the impeller 120, the part of the blood is driven to flow along the wall of the second reducing surface 113a to the first conveying flow passage 413 of the gap 410, so as to effectively guide the blood just flowing into the blood pump 10 to flow to the distal end, improve the blood flow smoothness at the inlet 214, and reduce the risk of blocking the blood at the inlet 214.

Further, the second tapered surface 113a extends from the inside of the main body section 213 to the inside of the second reduced port section 212 such that a proximal end portion of the second tapered surface 113a is radially opposed to the liquid inlet 214, and a distal end portion of the second tapered surface 113a is radially opposed to the inner wall surface of the main body section 213. I.e., the inner wall surface of the main body section 213 shields the distal end portion of the second tapered surface 113a in the radial direction. The purpose of this arrangement is that the blood just derived from the distal end portion of the second tapered surface 113a has a tendency to flow obliquely in the radial direction; by radially opposing the distal end portion of the second tapered surface 113a to the inner wall surface of the main body section 213, when blood led out of the distal end portion of the second tapered surface 113a flows obliquely in the radial direction to contact with the inner wall surface of the main body section 213, it can be blocked by the inner wall surface of the main body section 213 and guided to flow into the first delivery flow path 413 in the axial direction, and the resistance of blood entering the first delivery flow path 413 can be reduced.

Referring to fig. 10 and 11, in one embodiment, a plurality of fins 216 are protruding from an inner wall surface of the inlet tube 210, the fins 216 are arranged at intervals along a circumferential direction of the inlet tube 210, each fin 216 extends along an axial direction of the inlet tube 210, and blood around a circumferential direction of the gap 410 can be guided to flow distally along the axial direction by the fin 216.

With continued reference to fig. 10 and 11, in one embodiment, the liquid inlet 214 includes a plurality of first openings 214c arranged at intervals along the circumferential direction of the inlet pipe 210, and a partition wall 217 is formed between two adjacent first openings 214 c. The plurality of guide fins 216 are respectively in one-to-one correspondence with the plurality of partition walls 217, and proximal ends of the guide fins 216 extend at least partially onto inner wall surfaces of the partition walls 217. Since the proximal end of the fin 216 extends at least partially onto the inner wall surface of the partition wall 217, blood entering the blood pump 10 from the first opening 214c can first contact the fin 216. Thus, the fin 216 can guide and limit the blood flowing into the blood pump 10 from the first opening 214c to flow to the distal end along the axial direction, so as to reduce the occurrence of blocking of the blood caused by mutual opposite interference of the blood flowing into the blood pump 10 from each opening in the circumferential direction, and improve the blood flow smoothness at the liquid inlet 214. Meanwhile, providing the guide fins 216 in one-to-one correspondence with the partition walls 217 can also increase the structural strength of the partition walls 217.

Referring also to fig. 10 and 11, in one embodiment, the proximal end of the fin 216 protrudes from the inner wall surface of the inlet tube 210 by a first height H ₁ Gradually increasing in the direction of the catheter 12 to the motor 110. Thus, when blood flows into the inlet 214 from the proximal end to the distal end, the guide fins 216 can gradually provide a separation effect to the blood, so as to gradually provide a separation guiding effect to the blood, and reduce the occurrence of a situation that blood flow is blocked due to abrupt limit blocking. The distal end of the fin 216 protrudes from the inner wall surface of the inlet tube 210 by a second height H ₂ From one to the next along the direction of the catheter 12 to the motor 110Is tapered to relatively increase the space available for blood flow within gap 410 and to facilitate blood flow pooling.

Referring to fig. 12, in one embodiment, the motor main body 111 includes a cylindrical shell 101, a first rotor 103, a second rotor 105, a stator 104 and a rotating shaft 106, wherein the first rotor 103, the second rotor 105 and the stator 104 are disposed in the cylindrical shell 101, and the rotating shaft 106 is disposed through the cylindrical shell 101. The distal end of the cylindrical shell 101 is connected to the shaft support 112 and the proximal end of the cylindrical shell 101 is connected thereto. The rotating shaft 106 passes through the shaft supporting seat 112 and is connected with the impeller 120, and the motor 110 drives the impeller 120 to rotate so as to drive blood to flow. The first rotor 103, the second rotor 105, the stator 104, and the shaft 106 are provided in the motor main body 111. The first rotor 103, the stator 104 and the second rotor 105 are sequentially sleeved on the rotating shaft 106, and the first rotor 103 and the second rotor 105 are fixedly connected with the rotating shaft 106. The stator 104 can generate and drive the first rotor 103 and the second rotor 105 to rotate, and the first rotor 103 and the second rotor 105 are used for driving the rotating shaft 106 to rotate when rotating. The rotating shaft 106 is connected to the impeller 120 to drive the impeller 120 to rotate.

Referring to fig. 11, in one embodiment, cylindrical shell 101 forms a first delivery flow path 413 with body section 213 of inlet tube 210. The radial dimension of the cylindrical shell 101 is substantially the same throughout the axial direction of the blood pump 10, as is the radial dimension of the body segment 213 throughout. The width of the first delivery flow path 413 formed by the cylindrical shell 101 and the main body segment 213 is substantially constant in the axial direction of the blood pump 10, and blood can be stably delivered.

Referring to fig. 13, in one embodiment, the outlet pipe 220 includes a first pipe section 221 and a second pipe section 222 connected to the first pipe section 221, the first pipe section 221 is provided with the liquid outlet 220a, the second pipe section 222 extends into the inlet pipe 210, and the second pipe section 222 is provided with a communication port 222a. The second tube segment 222 is adapted to be coupled to the motor 110. The inner cavity of the outlet pipe 220 is denoted as a second delivery flow path 420, and the communication port 222a communicates with the second delivery flow path 420, and the second delivery flow path 420 communicates with the gap 410 through the communication port 222a. Thus, the liquid inlet 214 communicates with the liquid outlet 220a through the gap 410 and the second transfer flow path 420, and the blood flow path 400 in the blood pump 10 is formed.

Referring to fig. 4 and 6, in one embodiment, the second pipe section 222 has an outer diameter larger than that of the first pipe section 221 such that a stepped portion 223 is formed between the outer circumferential surface of the second pipe section 222 and the outer circumferential surface of the first pipe section 221. The distal end of the inlet pipe 210 is provided with a first plug-in part 215, the end surface of the first plug-in part 215 is abutted against the step part 223, and the first plug-in part 215 can be quickly plugged in place through the positioning function of the step part 223, so that the efficiency and the accuracy of the connection between the inlet pipe 210 and the outlet pipe 220 are improved. The outer surface of the first plug portion 215 is flush with the outer circumferential surface of the second tube segment 222, so that the outer circumferential surface of the entire shell tube 200 is smooth and regular, and is convenient for moving in the blood vessel and the heart 20. Referring to fig. 9 and 6, in one embodiment, the first plugging portion 215 may be disposed at a distal end of the first necking section 211.

Referring to fig. 5, 13 and 14, in one embodiment, the distal end of the motor 110 is provided with a shaft shoulder 102. The proximal end of the second pipe section 222 is provided with a second plugging portion 222b, and the end face of the second plugging portion 222b abuts against the shaft shoulder 102, so that the second pipe section 222 and the motor 110 can be quickly plugged in place through the positioning function of the shaft shoulder 102, and the assembly efficiency and accuracy of the outlet pipe 220 and the motor 110 are improved. The outer peripheral surface of the second insertion portion 222b is flush with the outer peripheral surface of the motor 110, and since the outer peripheral surface of the motor 110 forms a part of the blood flow path 400 as a surrounding, the outer peripheral surface of the motor 110 will be used for contacting with blood; the second insertion portion 222b is inserted into the motor 110, so that the outer peripheral surface of the second insertion portion 222b can also contact blood. Thus, by providing the outer peripheral surface of the second insertion portion 222b flush with the outer peripheral surface of the motor 110, the blood flow resistance can be reduced, and the blood flow smoothness can be improved.

Further, the thickness of the second plugging portion 222b is greater than the thickness of the second pipe segment 222. In this way, the stability of the connection of the second tube section 222 with the drive unit 100 can be improved, and the weakening of the structural strength of the proximal end of the outlet tube 220 by the communication port 222a can also be balanced, so that a larger communication port 222a can be provided.

Optionally, in one embodiment, a rounded corner R is provided at the connection between the inner wall surface of the second plug portion 222b and the inner wall surface of the second pipe segment 222, so that the second plug portion 222b is smooth in appearance and facilitates guiding the blood flow at the communication port 222 a.

Referring to fig. 13, in one embodiment, the liquid outlet 220a includes a plurality of second openings 220b, and the plurality of second openings 220b are arranged at intervals along the circumference of the casing 200, so that blood flows from the circumference of the casing 200 to the blood pump 10, thereby improving the outflow efficiency of the blood pump 10. Each of the second openings 220b extends in a bar shape along the axial direction of the casing 200 so as to facilitate the blood flowing in the axial direction to sufficiently flow the blood pump 10, thereby reducing the risk of occurrence of the fluid blocking phenomenon.

In one embodiment, the inlet tube 210 is made of a hard material such that the inlet tube 210 is in a non-expandable configuration, on the one hand, the inlet tube 210 is provided with a strong resistance against blood flow impact to stably assist in blood transport. On the other hand, the blood flow path 400 formed by the inlet tube 210 and the driving unit 100 is stabilized in shape to stably convey blood. The hard material may be a metal.

Similarly, in one embodiment, the outlet tube 220 may also be made of a hard material, such that the outlet tube 220 is in a non-expandable configuration, which provides the outlet tube 220 with a relatively strong resistance to blood flow impact to aid in blood delivery in a stable manner. On the other hand, the partial blood flow path 400 formed by the outlet tube 220 is structurally stabilized in shape to stably convey blood. The hard material may be a metal.

In one embodiment, the proximal portion of the impeller 120 is received within the second tube segment 222 such that a side of the proximal portion of the impeller 120 is opposite the communication port 222 a. Thus, the impeller 120 can more effectively guide the blood flowing from the inlet tube 210 into the outlet tube 220 through the communication port 222a when rotating. Further, a distal portion of impeller 120 is received within first tube segment 221 and is adjacent or near outlet 220a. I.e., the impeller 120 extends from the second tube section 222 into the first tube section 221. Therefore, the impeller 120 can more effectively guide the blood to flow from the liquid outlet 220a to the blood pump 10 when rotating, so as to improve the outflow efficiency of the blood.

Referring to fig. 13, in one embodiment, the blood pump 10 further includes a tail tube (not shown), and the distal end of the outlet tube 220 is provided with a fixing portion 224, and the tail tube is connected to the fixing portion 224, so as to facilitate fixing the distal end of the blood pump 10. The fixing portion 224 may be fixedly connected with the tail pipe by gluing. The distal end of the blood pump 10 can be conveniently secured in the pulmonary artery 26 by a pigtail.

In one embodiment, the fixing portion 224 is provided with a glue receiving groove 224a at the outer periphery, the glue receiving groove 224a is used for receiving glue solution, and the pigtail tube is sleeved at the outer periphery of the fixing portion 224 and covers the glue receiving groove 224a. The glue content between the fixing portion 224 and the tail pipe can be improved through the glue containing groove 224a, so that the stability of the adhesive connection between the fixing portion 224 and the tail pipe is improved.

Referring to fig. 3, in one embodiment, the casing 200 has a first length L along the axial direction of the driving unit 100. The first length L enables the blood pump 10 to pass from the right atrium 22, the right ventricle 24, the pulmonary valve 25 to extend into the pulmonary artery 26 such that the fluid inlet 214 is located in the right ventricle 24 and the fluid outlet 220A is located in the pulmonary artery 26. Since the driving unit 100 and the casing 200 constitute the pump body 11 of the blood pump 10 and the driving unit 100 is located inside the casing 200, the first length L of the casing 200 corresponds to the axial length of the pump body 11 of the blood pump 10. It will be appreciated that the first length L may be different from one patient to another by slightly differing the size or anatomical shape of the tissue within the delivery path of the right ventricle 24, e.g., by differing the size or distance of the tissue within the delivery path of the right ventricle from a young patient to an old patient. Therefore, in practical application, the length of the first length L should be set according to the actual situation of the patient.

Optionally, the first length L is 20mm-32mm. The first length L may be, but is not limited to, 22mm, 25mm, 28mm, 30mm, 31mm, etc. The design can be reasonably designed according to patients with different ages, different body types or different symptoms, and the details are not repeated here.

The technical features of the above-described embodiments may be arbitrarily combined, and all possible combinations of the technical features in the above-described embodiments are not described for brevity of description, however, as long as there is no contradiction between the combinations of the technical features, they should be considered as the scope of the description.

The above examples only represent a few embodiments of the present application, which are described in more detail and are not to be construed as limiting the scope of the claims. It should be noted that it would be apparent to those skilled in the art that various modifications and improvements could be made without departing from the spirit of the present application, which would be within the scope of the present application. Accordingly, the scope of protection of the present application is to be determined by the claims appended hereto.

Claims

1. A blood pump, the blood pump comprising:

Wherein the driving unit comprises a motor and an impeller connected with the motor; the shell tube comprises:

2. The blood pump of claim 1, wherein the motor comprises a motor body and a shaft support; the shaft supporting seat is connected to the far end of the motor main body so as to enable a rotating shaft of the motor main body to pass through; the shaft support seat extends into the outlet pipe, and the outer peripheral wall of the shaft support seat forms the first reducing surface.

3. The blood pump of claim 1, wherein the inlet tube comprises a main body section and a first necked-down section connected to a distal end of the main body section, the distal end of the first necked-down section being fixedly connected to a peripheral wall of the outlet tube; the first reducing section is provided with an inner reducing surface, the inner reducing surface is positioned at the outer side of the communication port, and the diameter of the inner reducing surface and the diameter of the first reducing surface are gradually reduced along the same direction.

4. A blood pump according to claim 3, wherein the spacing between the inner reducing surface of the first reduced section and the first reducing surface is progressively greater in a direction along the motor to the impeller; and/or the first reducing section also has an outer reducing surface facing away from the inner reducing surface, the outer reducing surface being receivable within a right ventricle for contact fit of a valve side of a pulmonary valve facing the right ventricle; and/or the first necking section has a first axial length D ₁ The body section has a second axial length D ₂ The first axial length D ₁ And the second axial length D ₂ The ratio of (C) to (D) is 1/4 or less ₁ /D ₂ ≤1/3。

5. The blood pump of claim 1, wherein the inlet tube comprises a main body section and a second reduced mouth section connected to a proximal end of the main body section, the proximal end of the second reduced mouth section being fixedly connected to the motor or the catheter, the diameter of the second reduced mouth section increasing in a direction from the motor to the impeller, the inlet extending axially from the second reduced mouth section onto the main body section;

The liquid inlet comprises a first inlet area positioned on the second necking section and a second inlet area positioned on the main body section; wherein the first inlet zone has a first width along the circumference of the inlet pipe and the second inlet zone has a second width along the circumference of the inlet pipe, the second width being greater than the first width; the first width gradually increases in a direction from the conduit to the motor.

6. The blood pump of claim 5, wherein the motor comprises a motor body and a proximal cap; the proximal end cover is arranged at the proximal end of the motor main body and fixedly connected with the guide pipe, the outer circumferential surface of the proximal end cover is provided with a second reducing surface, and the diameter of the second reducing surface is gradually increased along the direction from the guide pipe to the motor;

the second tapered surface extends from the interior of the main body section to the interior of the second reduced section such that a proximal portion of the second tapered surface is radially opposite the liquid inlet and a distal portion of the second tapered surface is radially opposite the inner wall surface of the main body section.

7. The blood pump of any one of claims 1 to 6, wherein the inlet tube is made of a hard material such that the inlet tube is in a non-expandable configuration; and/or the outlet tube is made of a hard material such that the outlet tube is in a non-expandable configuration.

8. The blood pump according to any one of claims 1 to 6, wherein the outlet tube comprises a first tube section and a second tube section connected to the first tube section, the first tube section is provided with the liquid outlet, the second tube section extends into the inlet tube, and the second tube section is provided with the communication port;

9. The blood pump according to any one of claims 1 to 6, wherein a plurality of guide fins are provided on an inner wall surface of the inlet tube in a protruding manner, the guide fins being arranged at intervals in a circumferential direction of the inlet tube, each guide fin extending in an axial direction of the inlet tube; wherein,

the liquid inlet comprises a plurality of first openings which are arranged at intervals along the circumferential direction of the inlet pipe, and a partition wall is formed between every two adjacent first openings; the guide fins are respectively in one-to-one correspondence with the separation walls, and the proximal ends of the guide fins at least partially extend to the inner wall surfaces of the separation walls;

10. The blood pump according to any one of claims 1 to 6, wherein the outlet tube comprises a first tube section and a second tube section connected to the first tube section, the first tube section is provided with the liquid outlet, the second tube section extends into the inlet tube, and the second tube section is provided with the communication port; wherein,

and/or the distal end of the motor is provided with a shaft shoulder part, the proximal end of the second pipe section is provided with a second plug-in connection part, the end face of the second plug-in connection part is in butt joint with the shaft shoulder part, and the outer peripheral surface of the second plug-in connection part is flush with the outer peripheral surface of the motor;

And/or the thickness of the second plug-in connection part is larger than that of the second pipe section; and/or the connection part of the inner wall surface of the second plug-in connection part and the inner wall surface of the second pipe section is provided with a rounding angle.

11. The blood pump of any one of claims 1 to 6, wherein the housing tube has a first length in an axial direction of the drive unit; the first length is such that the blood pump is capable of passing from the right atrium, right ventricle, pulmonary valve to extend into the pulmonary artery such that the fluid inlet is in the right ventricle and the fluid outlet is in the pulmonary artery.

12. The blood pump of claim 11, wherein the first length is 20mm-32mm.