CN219332945U

CN219332945U - Paddle for blood pump and blood pump

Info

Publication number: CN219332945U
Application number: CN202223285086.6U
Authority: CN
Inventors: 高琪; 何博; 刘星利
Original assignee: Zhejiang Diyuan Medical Equipment Co ltd
Current assignee: Zhejiang Diyuan Medical Equipment Co ltd
Priority date: 2022-12-08
Filing date: 2022-12-08
Publication date: 2023-07-14
Anticipated expiration: 2032-12-08

Abstract

The application discloses a paddle and blood pump for blood pump, the paddle includes wheel hub, first blade and second blade, wheel hub's circumferential surface has first ring district and second ring district, first ring district is located second ring district along axial one end, a plurality of first blades set up in first ring district, the profile that extends of first blade on first ring district is crooked towards the first direction of circumference, a plurality of second blades, set up in the second ring district, the profile that extends of second blade on the second ring district is crooked towards the second direction of circumference, wherein, first direction is opposite with the second direction. The extension profile of this application first blade and second blade is crooked in opposite directions, reduces the too big production that causes the inside unnecessary vortex of blood pump of blade distortion, has improved blood pump performance.

Description

Paddle for blood pump and blood pump

Technical Field

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

Background

The blood pump device is used for being placed in a body, converting mechanical energy into kinetic energy and pressure potential energy of blood, and conveying the blood in the heart chamber into an artery, so that the normal blood circulation of a heart failure patient is maintained. The main components of the blood pump include a blood pump housing, rotatable paddles and a motor for driving.

Blood pumps are required to meet the blood flow or blood pressure required by the patient. In the related art, the flow of the blood pump is improved by increasing the rotating speed of the blade, but the too high rotating speed of the blade has higher requirements on the performance of the motor, and side effects such as heating, hemolysis and the like which are harmful to the human health are generated.

Disclosure of Invention

In view of the foregoing, it is desirable to provide a paddle for a blood pump and a blood pump that enhance the performance of the blood pump and improve hemolysis.

To achieve the above object, according to a first aspect of embodiments of the present application, there is provided a paddle for a blood pump, the paddle including:

a hub having a circumferential surface with a first annular region and a second annular region, the first annular region being located at one end of the second annular region in an axial direction;

a plurality of first blades arranged in the first annular region, wherein the extension profile of the first blades on the first annular region is bent towards a first circumferential direction;

and the plurality of second blades are arranged in the second annular region, and the extension outline of the second blades on the second annular region is bent towards a second circumferential direction, wherein the first direction is opposite to the second direction.

In some embodiments, the pitch angle of the first blade increases gradually along the inlet end to the outlet end of the first blade, and the pitch angle of the second blade decreases gradually along the inlet end to the outlet end of the second blade.

In some embodiments, the inlet angle of the first blade is from 30 ° to 50 °, and/or the outlet angle of the first blade is from 50 ° to 75 °, the inlet angle of the second blade is from 50 ° to 75 °, the outlet angle of the second blade is from 75 ° to 90 °, and the absolute value of the difference between the inlet angle of the first blade and the inlet angle of the second blade is no more than 3 °.

In some embodiments, the maximum outer diameter of the first blade is equal to the maximum outer diameter of the second blade.

In some embodiments, the ratio of the length of the first blade in the axial direction of the hub to the length of the second blade in the axial direction of the hub is 2 to 3.

In some embodiments, the outlet end of the first vane is connected to the inlet end of the second vane; or alternatively, the first and second heat exchangers may be,

the outlet end of the first blade is arranged at intervals with the inlet end of the second blade, and the interval distance between the outlet end of the first blade and the inlet end of the second blade in the axial direction of the hub is not more than 0.2 times of the length of the first blade in the axial direction of the hub.

In some embodiments, in a plane perpendicular to the axial direction of the hub, the central angle formed by the inlet end and the outlet end of the first blade is 60 ° to 90 °, the central angle formed by the inlet end and the outlet end of the second blade is 15 ° to 45 °, and the sum of the central angle formed by the inlet end and the outlet end of the first blade and the central angle formed by the inlet end and the outlet end of the second blade adjacent thereto is not more than 120 °.

In some embodiments, the inlet end of the second blade is located on an extension of the outlet end of the first blade adjacent to the second blade.

In a second aspect of embodiments of the present application, there is provided a blood pump comprising:

a motor;

a pump housing for transporting blood, having an inlet and an outlet;

and any one of the blades is arranged in the pump shell, and a power output shaft of the motor is connected with the hub so as to drive the blade to rotate in the pump shell.

In some embodiments, at least two of said blades are provided, said hub of each of said blades is axially connected, and a power output shaft of said motor is connected to said hub of one of said blades to drive each of said blades to rotate within said pump housing.

The paddle of this embodiment, wheel hub's circumference surface has first ring district and second ring district, and first ring district is located second ring district along axial one end, and a plurality of first blades set up in first ring district, and the profile that extends of first blade on first ring district is crooked towards the first direction of circumference, and a plurality of second blades set up in the second ring district, and the profile that extends of second blade on the second ring district is crooked towards the second direction of circumference. The extension profile of this application first blade and second blade is crooked in opposite directions, is different from the unidirectional extension of extension profile of traditional blade, reduces the too big production that causes the inside unnecessary vortex of blood pump of blade distortion, has improved the blood pump performance, and make full use of the axial space of blood pump simultaneously can not increase the difficulty of putting into of blood pump, has solved traditional blade because of crooked too big difficult processing problem that causes.

Drawings

FIG. 1 is a schematic structural view of a blade according to a first embodiment provided herein;

FIG. 2 is a circumferentially expanded view of the first ring and first blades of FIG. 1 along the hub;

FIG. 3 is a circumferentially expanded view of the second ring and second blade of FIG. 1 along the hub;

FIG. 4 is a view of a single streamlined blade deployed circumferentially around a hub;

FIG. 5 is a schematic structural view of a blade according to a second embodiment provided herein;

FIG. 6 is a schematic structural view of a blade according to a third embodiment provided herein;

fig. 7 is a schematic structural view of a blade according to a fourth embodiment provided in the present application;

fig. 8 is a schematic structural diagram of a blood pump according to an embodiment of the present disclosure;

FIG. 9 is a schematic view of the structure of FIG. 8 from another perspective;

FIG. 10 is a schematic view of the pump housing of FIG. 8;

FIG. 11 is a schematic diagram of the motor of FIG. 8;

FIG. 12 is a schematic diagram of another blood pump according to an embodiment of the present disclosure;

FIG. 13 is a schematic view of the gear assembly of FIG. 12;

FIG. 14 is a schematic view of a blade and gear assembly according to an embodiment of the present application;

fig. 15 is a schematic view of the gear assembly of fig. 14.

Description of the reference numerals

A blade 1; a hub 11; a first annular region 11a; a second annular region 11b; a first blade 12; a second blade 13; a motor 2; a power take-off shaft 21; a housing 22; a guide surface 22a; a pump housing 3; an inlet 3a; an outlet 3b; support columns 31; a gear assembly 4; a drive gear 41; a driven gear 42; a bearing gear 43; a rotating shaft 44; a support 45; a seal bearing 46; a protective case 47; the bearing 5 is fixed.

Detailed Description

Embodiments of the present application are described in further detail below with reference to the accompanying drawings and examples. The following examples are illustrative of the present application but are not intended to limit the scope of the present application.

In the description of the embodiments of the present application, the terms "first," "second," and "second" are used for descriptive purposes only and are not to be construed as indicating or implying relative importance.

In a first aspect of the embodiments of the present application, referring to fig. 1, a blade 1 for a blood pump is provided, the blade 1 including a hub 11, a plurality of first blades 12 and a plurality of second blades 13.

It should be noted that, in the embodiment of the present application, a plurality refers to not less than two.

The circumferential surface of the hub 11 has a first annular region 11a and a second annular region 11b, the first annular region 11a being located at one end of the second annular region 11b in the axial direction. That is, the first annular region 11a and the second annular region 11b are arranged along the axial direction of the hub 11.

It will be appreciated that the blood pump has an inlet from which blood within the heart is drawn into the blood pump and an outlet from which the paddle 1 drives blood out as the paddle 1 rotates. For convenience of description, the present application will be described by taking the example that the first annular region 11a is close to the inlet of the blood pump, that is, the second annular region 11b is close to the outlet of the blood pump.

The plurality of first blades 12 are provided in the first annular region 11a, and an extension profile of the first blades 12 on the first annular region 11a is curved toward the first direction in the circumferential direction. The plurality of second blades 13 are disposed in the second annular region 11b, and an extension profile of the second blades 13 on the second annular region 11b is curved toward a second direction in the circumferential direction, wherein the first direction is opposite to the second direction.

The number of the first blades 12 and the second blades 13 is not limited, and for example, the number of the first blades 12 may be 2, the number of the second blades 13 may be 2, the number of the first blades 12 may be 2, the number of the second blades 13 may be 4, or other number ratios may be used. For example, referring to fig. 5, the number of first blades 12 is 2, the number of second blades 13 is 4, and the 4 second blades 13 are spaced around the hub 11.

When the blood pump is in operation, blood flows through the first vane 12 and the second vane 13 along the axial direction of the hub 11, that is, the blood pump is an axial flow blood pump. The pushing force generated by the rotation of the first blade 12 and the second blade 13 enables the blood to obtain energy, and the pressure potential energy and the kinetic energy of the blood are increased. That is, the first blade 12 and the second blade 13 each have an inlet end and an outlet end, and blood can flow from the inlet end of the first blade 12 to the outlet end of the second blade 13 to enhance blood pump performance.

Note that, referring to fig. 2 and 3, the extending profile of the first blade 12 on the first ring area 11a is curved toward the first circumferential direction, which means that: the profile of the first blade 12 on the surface of the hub 11 is spread out circumferentially of the hub 11, the inlet end of the first blade 12 being curved towards the first direction. The curvature of the extension profile of the second blade 13 on the second ring zone 11b towards the circumferential second direction means that: the profile of the second blades 13 on the surface of the hub 11 is spread out circumferentially of the hub 11, the outlet ends of the second blades 13 being curved towards the second direction. The first direction is opposite to the second direction, that is, the first blade 12 and the second blade 13 fully utilize the axial length space of the hub 11, and when the blood pump works, the hub 11 rotates and drives the first blade 12 and the second blade 13 to rotate at the same rotating speed and in the same rotating direction, so that the contact area of the blades and blood is increased, and the blood flow and pressure of the blood pump are improved.

According to the blade 1 provided by the embodiment of the application, the extension profile of the first blade 12 and the extension profile of the second blade 13 are reversely bent, the blade is distinguished from unidirectional extension of the extension profile of the traditional blade, the generation of unnecessary vortex inside the blood pump caused by overlarge blade twisting is reduced, meanwhile, the axial space of the blood pump is fully utilized, the placement difficulty of the blood pump is not increased, the problem that the traditional blade is difficult to process and shape due to overlarge bending is solved, the pump blood flow and pressure of the blood pump can be improved, the required rotating speed of the blade 1 is reduced, the harm such as hemolysis is reduced, and the performance of the blood pump is improved.

It will be appreciated that, referring to fig. 2 to 4, it is known from the principle of speed triangle (described later), for the single streamline blade in the related art shown in fig. 4, if the circumferential component speed c of the absolute speed v'1 of the outlet angle is required to be larger, the outlet angle needs to be enough to be larger, and in the case that the flow and the rotation speed that the blood pump needs to provide are fixed, this will cause the blade of the blade to have larger bending, which may further generate various adverse effects, such as difficult processing and shaping or early flow separation of blood in the blood pump, and the generation of vortex further causes energy loss and performance degradation. As can be seen from fig. 2 and 3, the present application uses axial space to alleviate excessive bending of a single blade by reversely bending the extension profiles of the first blade 12 and the second blade 13, and improves the pump blood flow and pressure of the blood pump and the blood pump performance while solving the problem that the single streamline blade is difficult to process and form.

In an embodiment, the pitch angle of the first blade 12 gradually increases along the inlet end to the outlet end of the first blade 12, and the pitch angle of the second blade 13 gradually decreases along the inlet end to the outlet end of the second blade 13.

It should be noted that, the pitch angle of the first blade 12 refers to an angle between a tangent line of an airfoil bone line of the first blade 12 and a circumferential direction, and, for example, the pitch angle of the inlet end of the first blade 12 is an inlet end installation angle, that is, an angle between a tangent line of an airfoil bone line of the inlet end blade and a circumferential direction, and the pitch angle of the outlet end of the first blade 12 is an outlet end installation angle, that is, an angle between a tangent line of an airfoil bone line of the blade at the outlet end of the first blade 12 and a circumferential direction; the pitch angle of the second blade 13 refers to the angle between the tangent to the airfoil line of the second blade 13 and the circumferential direction.

That is, referring to fig. 2 and 3, the profile of the surface of the hub 11 is developed along the circumferential direction of the hub 11, and the first blades 12 and the second blades 13 are arc-shaped blades. Thus, when blood flows through the flow channel formed by the first blade 12 and the second blade 13, the arc-shaped blade gently changes the direction of blood flow, further changes the size of the outlet angle, improves the circumferential component speed c of the absolute speed v'1 of the outlet angle, improves the pump blood flow and pressure of the blood pump, and improves the blood pump performance.

It will be appreciated that the inlet angle of the first vane 12 is less than the outlet angle of the first vane 12 and that the inlet angle of the second vane 13 is less than the outlet angle of the second vane 13.

It should be noted that, the inlet angle of the first blade 12 refers to an angle between a relative velocity direction and a circumferential direction when blood flows into the inlet end of the first blade 12, and the outlet angle of the first blade 12 refers to an angle between a relative velocity direction and a circumferential direction when blood flows out of the outlet end of the first blade 12; the inlet angle of the second blade 13 refers to the angle between the relative velocity direction and the circumferential direction when blood flows into the outlet end of the second blade 13, and the outlet angle of the second blade 13 refers to the angle between the relative velocity direction and the circumferential direction when blood flows out of the outlet end of the second blade 13.

For example, referring to fig. 2, the movement of the blood relative to the hub 11 is referred to as the absolute speed of the first blade 12, and a vector diagram composed of the absolute speed, the relative speed and the circumferential speed vector of the first blade 12 is the speed triangle of the first blade 12. For convenience of description, the absolute speed of the inlet end is recorded as v0, and the relative speed is recorded as w0; the absolute speed of the outlet end is v1, the relative speed is w1, and the rotational speed of the hub 11 is unchanged, i.e. the circumferential speed is denoted as u. Referring to fig. 3, for convenience of description, the absolute velocity of the inlet end of the second blade 13 is v '0, and the relative velocity is w'0; the absolute speed of the outlet end is v '1, the relative speed is w'1, and the rotational speed of the hub 11 is unchanged, i.e. the circumferential speed is denoted as u.

It will be appreciated that the v0 direction flows axially into the inlet of the first vane 12. The absolute velocity v1 of the outlet end is synthesized by the relative velocity w1 and the peripheral velocity u. Where v1 can be further divided into a speed a in the axial direction and a speed b in the circumferential direction, it is known from conservation of mass that the partial speeds a and v0 are the same in magnitude and are related to the flow rate of the blood pump, that is, the volume flow rate flowing into the first blade 12 and the volume flow rate flowing out of the first blade 12 are equal, the volume flow rate is equal to the axial speed multiplied by the flow area, and thus the partial speeds a and v0 are the same in magnitude. The component speed b is related to the static pressure of the blood pump, the larger the value of b, the better the performance of the blood pump, and the positive correlation of b with the outlet angle is known from the speed triangle. Thus, by setting the magnitude of the inlet and outlet angles of the first blade 12, the separation velocity b and thus the performance of the blood pump is improved without excessive twisting of the outlet end of the first blade 12.

It will be appreciated that v'1 can be further divided into a speed a along the axial direction and a speed c along the circumferential direction, and that the mass conservation knows that the speeds a and v0 are the same, and are related to the flow rate of the blood pump, that is, the volume flow rate flowing into the first blade 12 and the volume flow rate flowing out of the second blade 13 are equal, and the volume flow rate is equal to the axial speed multiplied by the flow area, so that the speeds a and v0 are the same. The component speed c is related to the static pressure of the blood pump, the greater the value of c, the better the performance of the blood pump, while from the speed triangle, c is positively related to the outlet angle. Thus, by setting the inlet angle and the outlet angle of the second blade 13, the outlet angle of the second blade 13 is increased on the basis of the first blade 12, the inlet angle and the outlet angle of the second blade 13 are smaller in phase difference, the problem that the blade is too large in distortion and difficult to machine and shape is solved, and meanwhile, the performance of the blood pump is improved.

In one embodiment, the inlet angle of the first vane 12 is 30 ° to 50 °, the outlet angle of the first vane 12 is 50 ° to 75 °, the inlet angle of the second vane 13 is 50 ° to 75 °, and the outlet angle of the second vane 13 is 75 ° to 90 °.

Illustratively, the inlet angle of the first vane 12 may be 30 °, 40 °, 50 °, or the like.

Illustratively, the outlet angle of the first vane 12 is 50 °, 60 °, 75 °, or the like.

Illustratively, the inlet angle of the second vane 13 may be 50 °, 60 °, 75 °, or the like.

Illustratively, the outlet angle of the second vane 13 may be 75 °, 80 °, 90 °, or the like.

It will be appreciated that the movement of blood along the first blade 12 is a relative movement, the corresponding speed being a relative speed, the peripheral speed being the rotational speed of the hub 11. That is, the relative velocity direction of the inlet and outlet ends is determined by the inlet and outlet angles, respectively.

In an embodiment, the absolute value of the difference between the outlet angle of the first blade 12 and the inlet angle of the second blade 13 is not more than 3 °. Illustratively, the difference between the outlet angle of the first vane 12 and the inlet angle of the second vane 13 may be 0 °, 2 °, 3 °, or the like. That is, the outlet angle of the first blade 12 and the inlet angle of the second blade 13 are equal or approximately equal. Thus, the relative velocity w 0' of the inlet end of the second blade 13 is in the direction and magnitude consistent with the relative velocity w1 of the outlet end of the first blade 12, within the tolerance. Thus, by the reverse bending of the first blade 12 and the second blade 13, the component speed c of v'1 is greater than the component speed b of v1, and the performance of the blood pump is further improved.

In this embodiment, by reversely bending the first blade 12 and the second blade 13, the outlet angle of the first blade 12 and the inlet angle of the second blade 13 are designed to be approximately equal, so that the impact of blood is reduced, and the performance of the blood pump is improved.

Specifically, when the outlet angle of the first blade 12 and the inlet angle of the second blade 13 are equal, the data of the inlet-outlet pressure rise values of the multiple sets of pumps under the premise of the same rotation speed and the same blood flow value in the pump of the blade 1 in the embodiment of the present application are compared with the data of the following table:

it can be understood that under the condition that the rotation speed is unchanged and the blood flow value in the pump is increased simultaneously, the pump inlet and outlet pressure rise values corresponding to the blade 1 are all larger than the pump inlet and outlet pressure rise values corresponding to the single streamline blade, namely the performance of the blade 1 is better.

In one embodiment, the maximum outer diameter of the first blade 12 is equal to the maximum outer diameter of the second blade 13. Thus, blood at the inner edge of the pump casing of the blood pump can flow through the rotation of the first blade 12 and the second blade 13 when the blood pump works, the coagulation phenomenon at the inner edge of the pump casing caused by the overlarge radial space of the blood pump due to overlarge outer diameter of one blade is reduced, and the performance of the blood pump is improved.

The ratio of the lengths of the first blade 12 and the second blade 13 in the axial direction of the hub 11 is not limited.

In an embodiment, referring to fig. 7, the length of the first blade 12 in the axial direction of the hub 11 is approximately equal to the length of the second blade 13 in the circumferential direction of the hub 11, so that the blade 1 has an attractive appearance, and the first blade 12 and the second blade 13 have high ductility.

In another embodiment, referring to fig. 1, 5 and 6, the ratio of the length of the first blade 12 in the axial direction of the hub 11 to the length of the second blade 13 in the circumferential direction of the hub 11 is 2-3. For example, the ratio of the length of the first blade 12 in the axial direction of the hub 11 to the length of the second blade 13 in the circumferential direction of the hub 11 may be 2, 2.5, 3, or the like. In this way, the axial length ratio of the first blade 12 is increased, the time for blood to flow through the first blade 12 is longer than that for the second blade 13, and the impact of deflecting the absolute velocity v0 from the axial direction to v1 is smaller, thereby improving the performance of the blood pump.

The first blade 12 and the second blade 13 may be connected or spaced apart.

In one embodiment, referring to fig. 5 to 7, the outlet end of the first vane 12 is connected to the inlet end of the second vane 13. The whole structure is in an S-shaped design, and is convenient to process and shape. For example, referring to fig. 6, a rounded structure is disposed at the connection between the outlet end of the first blade 12 and the inlet end of the second blade 13, which further facilitates processing and reduces hemolysis.

In an embodiment, referring to fig. 1, the outlet end of the first blade 12 is spaced from the inlet end of the second blade 13, and the distance between the outlet end of the first blade 12 and the inlet end of the second blade 13 in the axial direction of the hub 11 is not more than 0.2 times the length of the first blade 12 in the axial direction of the hub 11. It will be appreciated that if the gap is too large, the output flow of the second vane 13 will decrease, thereby affecting the blood pump performance. Therefore, the material is saved and the manufacturing cost is reduced on the premise of not influencing the performance of the blood pump.

In some embodiments, referring to fig. 9, in a plane perpendicular to the axial direction of the hub 11, the inlet end and the outlet end of the first blade 12 form a central angle of 60 ° to 90 °, and the inlet end and the outlet end of the second blade 13 form a central angle of 15 ° to 45 °. That is, the projection of the first blade 12 in the top-bottom direction of the hub 11 forms a central angle of 60 ° to 90 ° at the inlet end and the outlet end. Illustratively, the central angle formed by the inlet end and the outlet end of the first vane 12 may be 60 °, 75 °, 90 °, or the like; the projection of the second blade 13 along the top and bottom directions of the hub 11, and the central angle formed by the inlet end and the outlet end is 15-45 degrees. Illustratively, the central angle formed by the inlet end and the outlet end of the second vane 13 may be 15 °, 30 °, 45 °, or the like.

It will be appreciated that the central angle formed by the inlet and outlet ends of the first vane 12 is the wrap angle of the first vane 12

The central angle formed by the inlet end and the outlet end of the second blade 13 is equal to the wrap angle of the second blade 13>

The wrap angle of the first and

second blades

12, 13 is substantially indicative of the extent of the diffusion of the blade flow path, given the determined projection of the blade axial plane and the number of blades. In general, the larger the wrap angle of the blade, the longer the blade, the smaller the load per unit length of the blade, and the smaller the equivalent diffusion angle of the flow channel, which is beneficial to the energy exchange between the blade and blood. However, if the wrap angle is too large, frictional losses of the blade with the blood increase. Thus, by setting the wrap angles of the first blade 12 and the second blade 13 within the above-described range, the performance of the blood pump is improved.

In an embodiment, in a plane perpendicular to the axial direction of the hub 11, the sum of the central angle formed by the inlet end and the outlet end of the first blade 12 and the central angle formed by the inlet end and the outlet end of the second blade 13 adjacent thereto is not more than 120 °. Thus, the friction loss between the blade and blood is reduced, and the performance of the blood pump is improved.

In one embodiment, referring to fig. 1 and 5 to 7, the inlet end of the second vane 13 is located on an extension line of the outlet end of the first vane 12 close to the second vane 13. That is, the first vane 12 and the second vane 13 form a continuous flow path to improve the performance of the blood pump.

In a second aspect of the embodiments of the present application, referring to fig. 8, there is provided a blood pump comprising a motor 2, a pump housing 3 and any one of the paddles 1 described above.

The pump housing 3 is for transporting blood, and has an inlet 3a and an outlet 3b.

The blade 1 is disposed within the pump housing 3, that is, the inlet 3a and the outlet 3b of the pump housing 3 are located on axially opposite sides of the blade 1.

The power take-off shaft 21 of the motor 2 is connected to the hub 11 to drive the blades 1 to rotate within the pump housing 3.

The motor 2 can drive the paddle 1 to rotate at a high speed in the pump shell 3 through the power output shaft 21, negative pressure is formed in the pump, blood in a ventricle smoothly enters the pump shell 3, mechanical energy is further converted into kinetic energy and pressure potential energy of the blood through the paddle 1 to be pumped downstream from the outlet 3b of the pump shell 3, and the purpose of ventricular assist is achieved.

The motor 2 is a built-in motor, and is placed in the patient along with the pump housing 3 and the paddle 1.

In an embodiment, referring to fig. 8 and 10, a plurality of support columns 31 are formed at one end of the pump casing 3 near the motor 2, the plurality of support columns 31 are arranged at intervals along the circumferential direction of the pump casing 3, the support columns 31 are connected with the casing 22 of the motor 2, and the interval between two adjacent support columns 31 forms an outlet 3b. In this way, the side wall of the pump housing 3 is formed with a plurality of outlets 3b, the axial or radial dimension of the pump housing 3 is not increased, and the placement difficulty of the blood pump is not increased.

The manner in which the support column 31 is connected to the housing 22 of the motor 2 is not limited. For example, the support column 31 and the housing 22 of the motor 2 can be integrally formed, so that the manufacturing cost is reduced; and the welding can be also adopted, so that the connection strength is improved.

In one embodiment, referring to fig. 11, an end face of the housing 22 of the motor 2 near one end of the pump housing 3 protrudes toward the inside of the pump housing 3 and protrudes toward the guide surface 22a. That is, the casing 22 of the motor 2 is shaped in a streamline form conforming to the hemodynamic characteristics, an effective flow guiding structure is formed, and after the pressure potential energy and the kinetic energy of blood are improved by the paddle 1, the blood is guided to the outlet 3b by the flow guiding surface 22a formed by the casing 22 of the motor 2, so that the loss of blood pressure potential energy is avoided, and the generation of coagulation at the outlet 3b is reduced.

The number of the blades 1 is not limited, and may be one or two. In some embodiments, the number of blades 1 is two, the hubs 11 of two blades 1 are connected in the axial direction, and the power output shaft 21 of the motor 2 is connected to the hub 11 of one of the blades 1, that is, the power output shaft 21 of the motor 2 is connected to the side of the hub 11 of one of the blades 1 facing away from the hub 11 of the other blade 1, so as to drive each blade 1 to rotate in the pump housing 3. That is, the hub 11 of the blade 1 close to the motor 2 is connected to the motor 2 at one end and to the hub 11 of the blade 1 far from the motor 2 at the other end.

The hubs 11 of the two blades 1 may be rigidly connected or assisted by other structures.

In one embodiment, referring to fig. 13 to 15, the blood pump includes a gear assembly 4 disposed between two paddles 1, and the gear assembly 4 is rotatably connected to hubs 11 of the paddles 1.

In some embodiments, referring to fig. 13, the gear assembly 4 includes a driving gear 41, a driven gear 42, a bearing gear 43, a rotating shaft 44, and a support 45. The gear assembly 4 is connected with the hub 11 of the two paddles 1 through two rotating shafts 44, wherein a driving gear 41 is arranged on the rotating shaft 44 close to the motor 2, a driven gear 42 is arranged on the rotating shaft 44 far away from the motor 2, and the driving gear 41 and the driven gear 42 are in meshed connection through two bearing gears 43. The two supporting pieces 45 are respectively penetrated on the two bearing gears 43, and one end of the supporting piece 45 away from the bearing gears 43 is fixedly connected with the pump shell 3 for fixing the gear assembly 4 in the pump shell 3.

It can be understood that when the blood pump works, the motor 2 can drive the blade 1 close to the motor 2 to rotate at a high speed in the pump shell 3 through the power output shaft 21, then the hub 11 drives the rotating shaft 44 to rotate, the rotating shaft 44 drives the driving gear 41 to rotate, the driving gear 41 is transmitted to the two bearing gears 43 and then drives the driven gear 42 to rotate, then the blade 1 far away from the motor 2 is driven to rotate through the rotating shaft 44, negative pressure is formed in the pump, blood in a ventricle smoothly enters the pump shell 3, further, the blade 1 does work, mechanical energy is converted into kinetic energy and pressure potential energy of the blood, and the kinetic energy and the pressure potential energy are pumped downstream from the outlet 3b of the pump shell 3, so that the purpose of ventricular assist is achieved.

In other embodiments, referring to fig. 14 and 15, the gear assembly 4 includes a rotating shaft 44, a driving gear 41, a driven gear 42, a bearing gear 43, a support 45, a seal bearing 46, and a protective housing 47. The gear assembly 4 is connected with the hubs 11 of the two paddles 1 through two rotating shafts 44, wherein a driving gear 41 is arranged on the rotating shaft 44 close to the motor 2, a driven gear 42 is arranged on the rotating shaft 44 far away from the motor 2, and the driving gear 41 and the driven gear 42 are in meshed connection through a bearing gear 43. The support 45 is arranged on the bearing gear 43 in a penetrating manner, and one end of the support 45 away from the bearing gear 43 is fixedly connected with the pump housing 3 for fixing the gear assembly 4 in the pump housing 3. The protective housing 47 is covered outside the driving gear 41, the driven gear 42, the bearing gear 43, the partial rotating shaft 44 and the partial supporting member 45, and is used for protecting gear transmission and reducing coagulation. The junction of pivot 44 and protective housing 47 surface is provided with sealed bearing 46 for sealed protective housing 47 reduces the blood inflow and influences gear drive in the protective housing 47.

It can be understood that when the blood pump works, the motor 2 can drive the blade 1 close to the motor 2 to rotate at a high speed in the pump shell 3 through the power output shaft 21, then the hub 11 drives the rotating shaft 44 to rotate, the rotating shaft 44 drives the driving gear 41 to rotate, the driving gear 41 is transmitted to the bearing gear 43 and then drives the driven gear 42 to rotate, then the blade 1 far away from the motor 2 is driven to rotate through the rotating shaft 44, negative pressure is formed in the pump, blood in a ventricle smoothly enters the pump shell 3, further, the blade 1 does work, mechanical energy is converted into kinetic energy and pressure potential energy of the blood, and the kinetic energy and the pressure potential energy are pumped downstream from the outlet 3b of the pump shell 3, so that the purpose of ventricular assist is achieved.

In an embodiment, referring to fig. 12, the blood pump includes a fixed bearing 5, which is disposed at an end of the blade 1 away from the motor 2 and away from the motor 2, and is fixedly connected with the pump housing 3. In this way, the blade 1 can be fixed in the pump shell 3, the influence of looseness of the blade 1 on blood transmission during operation of the blood pump is reduced, and the blood pumping capacity of the blood pump is improved.

The foregoing description is only of the preferred embodiments of the present application and is not intended to limit the same, but rather, various modifications and variations can be made by those skilled in the art. Any modification, equivalent replacement, improvement, etc. made within the spirit and principles of the present application should be included in the protection scope of the present application.

Claims

1. A paddle for a blood pump, the paddle comprising:

2. A blade according to claim 1, wherein the pitch angle of the first blade increases gradually along the inlet to the outlet end of the first blade and the pitch angle of the second blade decreases gradually along the inlet to the outlet end of the second blade.

3. The blade of claim 1, wherein the inlet angle of the first blade is 30 ° to 50 °, the outlet angle of the first blade is 50 ° to 75 °, the inlet angle of the second blade is 50 ° to 75 °, the outlet angle of the second blade is 75 ° to 90 °, and the absolute value of the difference between the outlet angle of the first blade and the inlet angle of the second blade is no more than 3 °.

4. A blade according to any one of claims 1 to 3, wherein the maximum outer diameter of the first blade is equal to the maximum outer diameter of the second blade.

5. A blade according to any one of claims 1-3, wherein the ratio of the length of the first blade in the axial direction of the hub to the length of the second blade in the axial direction of the hub is 2-3.

6. A blade according to any one of claims 1 to 3, wherein the outlet end of the first blade is connected to the inlet end of the second blade; or alternatively, the first and second heat exchangers may be,

7. A blade according to claim 1, wherein the inlet and outlet ends of the first blade form a central angle of 60 ° to 90 °, the inlet and outlet ends of the second blade form a central angle of 15 ° to 45 °, and the sum of the central angle of the inlet and outlet ends of the first blade and the central angle of the inlet and outlet ends of the second blade adjacent thereto does not exceed 120 °.

8. A blade according to any one of claims 1 to 3, wherein the inlet end of the second blade is located on an extension of the outlet end of the first blade adjacent the second blade.

9. A blood pump, comprising:

a motor;

a pump housing for transporting blood, having an inlet and an outlet;

and the blade according to any one of claims 1 to 8, which is arranged in the pump shell, wherein a power output shaft of the motor is connected with the hub so as to drive the blade to rotate in the pump shell.

10. The blood pump of claim 9, wherein there are at least two of said paddles, said hub of each of said paddles being connected in an axial direction, said power take-off shaft of said motor being connected to said hub of one of said paddles to drive each of said paddles to rotate within said pump housing.