CN120346442A

CN120346442A - Blood pumping device and motor

Info

Publication number: CN120346442A
Application number: CN202410661543.1A
Authority: CN
Inventors: 潘丽春; 李寒松
Original assignee: Fengkaili Medical Instrument Shanghai Co ltd
Current assignee: Fengkaili Medical Instrument Shanghai Co ltd
Priority date: 2024-05-24
Filing date: 2024-05-24
Publication date: 2025-07-22
Also published as: WO2025242223A1

Abstract

The present application discloses a blood pumping device and a motor, wherein the blood pumping device is used to transport blood, the blood pumping device comprises a motor, a first pipeline and a second pipeline, the motor comprises a stator assembly, the stator assembly comprises an iron core, the iron core encloses a receiving cavity, a first flow cavity is arranged in the iron core, a second flow cavity connected to the first flow cavity is arranged in the iron core and/or in the receiving cavity; the first pipeline is connected to the first flow cavity; the second pipeline is connected to the second flow cavity, one of the first pipeline and the second pipeline is a perfusion pipeline, and the other is a reflux pipeline, the perfusion pipeline is used to transport perfusion liquid to the motor, and the reflux pipeline is used to discharge the perfusion liquid in the motor.

Description

Blood pumping device and motor

Technical Field

The application belongs to the technical field of medical appliances, and particularly relates to a blood pumping device and a motor.

Background

In cardiac surgery, the heart function of a patient is weakened and the pumping capacity is insufficient due to the disease of the patient or the operation requirement. In this case, an active interventional medical device such as a ventricular assist device is required to assist the heart in pumping blood. The existing ventricular assist device utilizes the heart pumping principle to pump blood in the heart through a pumping mechanism and guide the blood to the aorta outside the heart to flow to the whole body.

In some cases, the existing ventricular assist device includes a catheter and a blood pumping device, the blood pumping device is disposed at a distal end of the catheter (an end far away from an operator or a doctor), the blood pumping device can be inserted through femoral artery or axillary artery or carotid artery by pushing the catheter, at this time, a suction window of the ventricular assist device is located in a left ventricle, an outflow window is located in an aorta, and blood in the left ventricle is pumped into the aorta through the suction window and the outflow window when the blood pumping device is started, so as to realize a blood pumping function of the ventricular assist device. Similarly, the blood pumping device may be inserted through a vein such as a femoral vein by pushing the catheter. Heat is generated when the blood pumping device is in operation, and damage to the patient can occur if the blood pumping device is too hot.

Disclosure of Invention

The embodiment of the application provides a blood pumping device which can improve the effective heat dissipation of the blood pumping device and a motor.

The embodiment of the application provides a blood pumping device which is used for conveying blood and comprises a motor, a first pipeline and a second pipeline, wherein the motor comprises a stator assembly, the stator assembly comprises an iron core, an accommodating cavity is formed by enclosing the iron core, a first circulation cavity is formed in the iron core, a second circulation cavity communicated with the first circulation cavity is formed in the iron core and/or the accommodating cavity, the first pipeline is communicated with the first circulation cavity, the second pipeline is communicated with the second circulation cavity, one of the first pipeline and the second pipeline is a perfusion pipeline, the other of the first pipeline and the second pipeline is a backflow pipeline, the perfusion pipeline is used for conveying perfusate to the motor, and the backflow pipeline is used for discharging perfusate in the motor.

The first flow lumen is a strip lumen extending along a first direction, wherein the first direction is a direction in which a distal end of the motor is directed proximally.

According to the first aspect of the application, the iron core comprises an inner iron core and an outer iron core sleeved outside the inner iron core, the outer peripheral surface of the inner iron core is attached to the inner peripheral surface of the outer iron core, a groove is formed in the peripheral surface of the inner iron core facing the outer iron core, a first flow cavity is formed between the groove and the outer iron core, or a groove is formed in the peripheral surface of the outer iron core facing the inner iron core, a first flow cavity is formed between the groove and the inner iron core, or grooves are formed in the peripheral surface of the inner iron core facing the outer iron core and the peripheral surface of the outer iron core facing the inner iron core, and a first flow cavity is formed between the groove on the inner iron core and the groove on the outer iron core.

According to an embodiment of the first aspect of the application, the first flow chamber extends helically in a first direction within the core.

According to the embodiment of the first aspect of the application, the motor further comprises a rotor assembly, the rotor assembly comprises a rotating shaft and magnetic steel, the rotating shaft extends along the first direction, at least part of the rotating shaft is located in the accommodating cavity, the magnetic steel is located in the accommodating cavity and sleeved on the rotating shaft, the pole pair number of the magnetic steel is P, the first circulation cavity is spirally wound on the rotating shaft, and the winding number T=1/P or T=1/(2P) of the single first circulation cavity.

According to the embodiment of the first aspect of the application, the stator assembly further comprises a winding in the accommodating cavity, the winding is sleeved outside the magnetic steel, a second circulation cavity is formed by a gap between the winding and the rotor assembly, the length of the winding in the first direction is L, the pitch H=PL of the first circulation cavity when the circle number T=1/P of the first circulation cavity is rounded, and the pitch H=2PL of the first circulation cavity when the circle number T=1/(2P) of the first circulation cavity is rounded.

According to the embodiment of the first aspect of the application, the motor further comprises a distal end bearing sleeved on the rotating shaft, wherein the distal end bearing is communicated with the first flow cavity and the second flow cavity, a proximal end bearing sleeved on the rotating shaft, the rotating shaft is rotationally connected with the stator assembly through the distal end bearing and the proximal end bearing, the distal end bearing is positioned on one side, away from the first pipeline, of the proximal end bearing, a distal end sealing cover is connected with the distal end of the stator assembly, a first through hole penetrating the distal end sealing cover in a first direction is formed in the distal end sealing cover, at least part of the rotating shaft extends out of the first through hole to form a containing cavity, the distal end sealing cover is used for sealing the distal end of the containing cavity, the proximal end sealing cover is connected with the proximal end of the stator assembly, a second through hole penetrating the distal end sealing cover in the first direction is formed in the proximal end sealing cover, and the second through hole is used for communicating the second flow cavity and the second pipeline.

According to the embodiment of the first aspect of the application, the motor further comprises a proximal bearing seat, the proximal bearing seat is connected with the proximal end of the stator assembly, a first mounting hole penetrating the proximal bearing seat along a first direction is formed in the proximal bearing seat, the proximal bearing and the proximal sealing cover are embedded in the first mounting hole, the proximal sealing cover is located at one end, deviating from the distal bearing, of the proximal bearing, the distal bearing seat is connected with the distal end of the stator assembly, a second mounting hole penetrating the distal bearing seat along the first direction is formed in the distal bearing seat, and the distal bearing is embedded in the second mounting hole.

According to an embodiment of the first aspect of the application, the distal cover and the distal bearing seat have a gap in the first direction, and the gap between the distal cover and the distal bearing seat forms a third flow chamber, which third flow chamber communicates the first flow chamber and the second flow chamber.

According to an embodiment of the first aspect of the application, the first conduit is a perfusion conduit and the second conduit is a return conduit.

According to an embodiment of the first aspect of the present application, the proximal bearing block is further provided with a first communication hole, and the first communication hole communicates with the first communication cavity and the first pipe.

According to an embodiment of the first aspect of the application, one of the openings of the first communication hole is located on the end face of the proximal bearing seat facing away from the distal bearing seat and communicates with the first conduit, and the other opening is located on the circumferential face of the proximal bearing seat facing away from the first mounting hole and communicates with the first communication chamber.

According to an embodiment of the first aspect of the present application, the iron core includes an inner iron core and an outer iron core sleeved outside the inner iron core, the outer iron core is disposed in a gap with the inner iron core, and a gap between the inner iron core and the outer iron core forms a first flow cavity.

A second aspect of the present application provides an electric machine, comprising a stator assembly, the stator assembly comprising an iron core, the iron core enclosing to form a containment cavity, a first circulation cavity being provided in the iron core, a second circulation cavity being provided in the iron core and/or in the containment cavity, the second circulation cavity being in communication with the first circulation cavity, one of the first circulation cavity and the second circulation cavity being for communication with a perfusion conduit, the other being for communication with a return conduit.

It will be appreciated that the motor provided in the second aspect of the present application may be any motor provided in the blood pumping device of the first aspect of the present application, and will not be described here again. The motor can be used for pumping blood, tissue fluid, digestive fluid and other application scenes.

The blood pumping device comprises a motor, a first pipeline and a second pipeline, wherein the motor comprises a stator assembly, the stator assembly comprises an iron core, an accommodating cavity is formed by enclosing the iron core, a first circulation cavity is arranged in the iron core, a second circulation cavity communicated with the first circulation cavity is arranged in the iron core and/or the accommodating cavity, the first pipeline is communicated with the first circulation cavity, the second pipeline is communicated with the second circulation cavity, one of the first pipeline and the second pipeline is a perfusion pipeline, the other one of the first pipeline and the second pipeline is a backflow pipeline, the perfusion pipeline is used for conveying perfusate to the motor, and the backflow pipeline is used for discharging perfusate in the motor. According to the application, the first pipeline and the second pipeline are communicated with the interior of the motor, and the perfusate flows through the first circulation cavity and the second circulation cavity after flowing to the motor through one pipeline, takes away heat generated by the motor, and flows out from the other pipeline, so that the effective heat dissipation of the blood pumping device is improved, and the damage of the blood pumping device to a patient is reduced. Through set up the first circulation chamber with first pipeline intercommunication in the iron core, need not to establish the pipeline in addition in the motor outside, reduce the motor external diameter, and then reduce the intervention degree of difficulty.

Drawings

In order to more clearly illustrate the technical solution of the embodiments of the present application, the drawings that are needed to be used in the embodiments of the present application will be briefly described, and it is possible for a person skilled in the art to obtain other drawings according to these drawings without inventive effort.

FIG. 1 is a schematic diagram of a ventricular assist device including a pumping device according to some embodiments of the present application;

FIG. 2 illustrates a schematic longitudinal cross-sectional structural view of an example ventricular assist device of FIG. 1;

FIG. 3 illustrates a schematic structural view of an example inner core and proximal bearing housing;

FIG. 4 shows a schematic perspective view of an exemplary inner core and proximal bearing housing of FIG. 3;

FIG. 5 shows a schematic cross-sectional view of an exemplary ventricular assist device of FIG. 2 in the A-A position;

FIG. 6 shows a schematic cross-sectional view of the ventricular assist device of FIG. 2 in the A-A position in another example;

FIG. 7 shows a schematic cross-sectional view of the ventricular assist device of FIG. 2 in the A-A position, FIG. 8 shows a schematic view of an exemplary proximal cap;

FIG. 9 shows a schematic structural view of an exemplary outer core and distal end cap;

FIG. 10 illustrates a schematic structural view of an exemplary distal bearing housing;

FIG. 11 shows a schematic structural view of another example inner core and proximal bearing housing;

FIG. 12 shows a schematic cross-sectional structural view of the inner core and proximal bearing housing of FIG. 11 for one example;

fig. 13 shows a schematic structural diagram of an exemplary second pipe.

Reference numerals:

10. Motor, 11, stator assembly, 111, core, 1111, housing cavity, 1112, first flow cavity, 1113, second flow cavity, 112, inner core, 1121, first step face, 1122, second step face, 113, outer core, 114, groove, 115, winding, 12, rotor assembly, 121, shaft, 122, magnet steel, 13, distal bearing, 14, proximal bearing, 15, distal cover, 151, first through hole, 16, proximal cover, 161, second through hole, 17, proximal bearing housing, 171, first mounting hole, 172, first through hole, 173, third step face, 174, fourth step face, 18, distal bearing housing, 181, second mounting hole, 182, fifth step face, 183, sixth step face, 19, third flow cavity;

20. 21, a notch;

30. An interventional catheter;

40. an outflow channel 41, an outflow window 42, an impeller;

x, first direction.

Detailed Description

Features and exemplary embodiments of various aspects of the present application will be described in detail below, and in order to make the objects, technical solutions and advantages of the present application more apparent, the present application will be described in further detail below with reference to the accompanying drawings and the detailed embodiments. It should be understood that the particular embodiments described herein are meant to be illustrative of the application only and not limiting. It will be apparent to one skilled in the art that the present application may be practiced without some of these specific details. The following description of the embodiments is merely intended to provide a better understanding of the application by showing examples of the application.

It is noted that relational terms such as first and second, and the like are used solely to distinguish one entity or action from another entity or action without necessarily requiring or implying any actual such relationship or order between such entities or actions. Moreover, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or apparatus. Without further limitation, an element defined by the phrase "comprising" does not exclude the presence of additional identical elements in a process, method, article, or apparatus that comprises the element.

In order to solve the technical problems involved in the background technology, the applicant provides a blood pumping device, which comprises a motor, a first pipeline and a second pipeline, wherein the motor comprises a stator assembly, the stator assembly comprises an iron core, the iron core is enclosed to form a containing cavity, a first circulation cavity is arranged in the iron core, a second circulation cavity communicated with the first circulation cavity is arranged in the iron core and/or the containing cavity, the first pipeline is communicated with the first circulation cavity, the second pipeline is communicated with the second circulation cavity, one of the first pipeline and the second pipeline is a perfusion pipeline, the other one of the first pipeline and the second pipeline is a backflow pipeline, the perfusion pipeline is used for conveying perfusate to the motor, and the backflow pipeline is used for discharging perfusate in the motor.

According to the blood pumping device, the first pipeline and the second pipeline are communicated with the inside of the motor, perfusate flows through the first circulation cavity and the second circulation cavity after flowing to the motor through one pipeline, takes away heat generated by the motor, and flows out of the other pipeline, so that the effective heat dissipation of the blood pumping device and the motor is improved, and the damage of the blood pumping device to a patient is reduced. Through set up the first circulation chamber with first pipeline intercommunication in the iron core, need not to establish the pipeline in addition in the motor outside, reduce the motor external diameter, and then reduce the intervention degree of difficulty.

It is understood that the motor of the present application may be applied to an application scenario of a blood pumping device, a tissue fluid pumping device, a digestive juice pumping device, etc. to achieve the purpose of pumping fluids such as blood, tissue fluid, digestive juice, etc., and for convenience of understanding and description, the application scenario of the motor applied to the blood pumping device will be described below.

Before describing the specific structure of the pumping device, a ventricular assist device including the pumping device will be briefly described with reference to the accompanying drawings in order to understand the working environment of the pumping device. Fig. 1 is a schematic diagram of a ventricular assist device including a pumping device according to some embodiments of the present application. Fig. 2 shows a schematic longitudinal sectional view of an exemplary ventricular assist device of fig. 1, wherein the first conduit is not shown. As can be seen in fig. 1 and 2, the present application provides a ventricular assist device comprising a blood pumping device, the ventricular assist device comprising a blood pumping device (not shown), an outflow channel 40 and an interventional catheter 30, the interventional catheter 30 being connected to a proximal end of the blood pumping device, the outflow channel 40 being connected to a distal end of the blood pumping device. The blood pumping device comprises a motor 10, and an outflow channel 40 is provided with a suction window (not shown) and an outflow window 41. The blood pumping device and outflow channel 40 are, in use, advanced through the patient's blood vessel by means of the interventional catheter 30 until the blood pumping device and outflow channel 40 are located at a designated location in the patient's blood circulation system. At this time, the outflow window 41 and the suction window are located at different positions of the blood circulation system. When the motor 10 in the pumping device is started, the motor 10 drives blood to enter the outflow channel 40 from the suction window and flow out from the outflow window 41, so that the pumping function of the ventricular assist device is realized.

When the blood pumping device, the interventional catheter 30 and the outflow channel 40 are inserted into the patient, the end of the interventional catheter 30 facing away from the motor 10 extends out of the patient and is connected to a reservoir (not shown), a power supply device, a control switch or the like, and at least part of the first and second pipes 20 are located in the interventional catheter 30. The liquid storage tank conveys and discharges perfusate into the motor through a pipeline, and the perfusate flows through the motor 10 to take away heat generated during operation of the motor 10. Wherein, the perfusate comprises normal saline and anticoagulant, and the anticoagulant can be heparin. The anticoagulant in the perfusate reduces the probability of blood clotting, thereby reducing the probability of failure of the pumping function of the motor 10 due to clotting.

It will be appreciated that in the present application, proximal refers to the end facing the operator or physician and distal refers to the end facing away from the operator or physician. The proximal end of the motor 10 is directed towards the interventional catheter 30 and the distal end of the motor 10 is directed towards the outflow channel 40.

Having described the structure of the ventricular assist device, a description is given below of a blood pumping device according to an embodiment of the present application with reference to the accompanying drawings. In this description, the direction along the line connecting the proximal end and the distal end of the motor and pointing from the distal end to the proximal end is referred to as the first direction and is denoted as x. In the drawings, the dimensions in the drawings are not necessarily to scale with real dimensions for convenience in drawing.

As can be seen from fig. 1 and 2, the present application provides a blood pumping device for conveying blood, the blood pumping device includes a motor 10, a first pipe (not shown) and a second pipe 20, the motor 10 includes a stator assembly 11, the stator assembly 11 includes an iron core 111, the iron core 111 encloses a containing cavity 1111, a first circulation cavity 1112 is disposed in the iron core 111, and a second circulation cavity 1113 communicating with the first circulation cavity 1112 is disposed in the iron core 111 and/or the containing cavity 1111. It is understood that the first flow chamber 1112 provided in the core 111 means that a cavity or a gap is formed in a solid structure of the core 111 to form the first flow chamber 1112. The first conduit communicates with the first flow chamber 1112 and the second conduit 20 communicates with the second flow chamber 1113, one of the first conduit and the second conduit 20 being a perfusion conduit and the other being a return conduit. Wherein the perfusion tube is used for conveying perfusion liquid to the motor 10, and the reflux tube is used for discharging the perfusion liquid in the motor 10.

In some of these implementations, the walls of the first flow-through chamber 1112 have a high finish, a low roughness, and the walls of the first flow-through chamber 1112 are hydrophilically coated.

It will be appreciated that the manner in which the second flow-through chamber 1113 is disposed within the core 111 and/or within the receiving chamber 1111 in the present application will be described in detail below and will not be described herein.

In some of these embodiments, the first and second flow-through cavities 1112, 1113 are in direct communication or in indirect communication, meaning that the first and second flow-through cavities 1112, 1113 communicate through at least one other cavity, gap, or spatial structure. The present embodiment describes an application scenario in which the first flow chamber 1112 and the second flow chamber 1113 are indirectly connected.

The blood pumping device provided in this embodiment is communicated with the motor 10 through the first pipeline and the second pipeline 20, and the perfusate flows through the first circulation cavity 1112 and the second circulation cavity 1113 after flowing to the motor 10 through one of the pipelines and takes away the heat generated by the motor 10, and then flows out from the other pipeline, so that the effective heat dissipation of the blood pumping device is improved, and the damage of the blood pumping device to a patient is reduced. Through set up in iron core 111 with first pipeline intercommunication's first circulation chamber 1112, need not to set up the pipeline in addition in the motor outside, reduce motor 10 external diameter, and then reduce the intervention degree of difficulty.

Having described the overall structure of the pumping device, several implementations of a first flow-through chamber in a pumping device are described below in connection with the accompanying drawings. In some of these embodiments, the first flow-through chamber 1112 is a strip-shaped chamber extending along the first direction x. Wherein the first direction x is the direction in which the distal end of the motor 10 points proximally.

It is understood that the first flow chamber 1112 is a strip chamber extending along the first direction x in the present application, and does not mean that the first flow chamber 1112 is a linear cavity, and a center line of the linear cavity is a straight line parallel to the first direction x. Rather, first flow lumen 1112 has opposite ends with one end facing the proximal side and the other end facing the distal side, but the locus of first flow lumen 112 extending from one end to the other end is not particularly limited.

As can be seen in conjunction with fig. 2, in some of the embodiments, the core 111 includes an inner core 112 and an outer core 113 sleeved outside the inner core 112, and an outer circumferential surface of the inner core 112 is fitted to an inner circumferential surface of the outer core 113. The gap between the inner core 112 and the outer core 113 forms a first flow chamber 1112, and the inner core 112 encloses a receiving chamber 1111.

In some embodiments, the inner core 112 and the outer core 113 may be cylinders, or may be polygonal tubular structures such as square cylinders. The present embodiment is exemplified with the inner core 112 and the outer core 113 each being a cylinder.

Here, since the inner core 112 and the outer core 113 are each in an axisymmetric pattern, the inner core 112 and the outer core 113 each have a central axis, and the central axis extends in a direction coincident with a connecting line direction of the proximal end and the distal end of the motor, i.e., in a direction x in the drawing. The inner core 112 and the outer core 113 have a cylindrical structure, and thus have two circumferential surfaces, the circumferential surface of the cylinder outer wall being the outer circumferential surface, and the circumferential surface of the cylinder inner wall being the inner circumferential surface. Further, the axial direction of the inner core 112 refers to the direction in which the central axis extends. The circumferential direction of the inner core 112 refers to the circumferential direction of the outer periphery of the cylinder. Radial refers to a direction through the central axis in a radial plane, and generally also refers to a straight direction along a diameter or radius, or a straight direction perpendicular to the central axis. Radial dimensions generally refer to the radius or diameter of an axisymmetric part. It is to be understood that other components of the present application may be axially, circumferentially, radially, and circumferentially oriented as described above with respect to the inner core 112.

Fig. 3 shows a schematic structural view of an example inner core and a proximal bearing housing, fig. 4 shows a schematic perspective structural view of an example inner core and a proximal bearing housing of fig. 3, fig. 5 shows a schematic structural view of a cross-section of a ventricular assist device of fig. 2 in A-A position, fig. 6 shows a schematic structural view of a cross-section of a ventricular assist device of fig. 2 in A-A position, and fig. 7 shows a schematic structural view of a cross-section of a ventricular assist device of fig. 2 in A-A position. In fig. 5-7, the dimensions of each of the structures in the figures are not necessarily to scale relative to the structures in the other figures for convenience in illustrating the structure of the flow-through chamber.

As can be seen from fig. 2 to 5, in some embodiments, the outer core 113 is sleeved outside the inner core 112, and the inner peripheral surface of the outer core 113 is attached to the outer peripheral surface of the inner core 112, the circumferential surface of the inner core 112 facing the outer core 113 is provided with a groove 114a recessed into the accommodating cavity 1111, and a gap between the groove 114a and the outer core 113 forms a first circulation cavity 1112.

In some of these implementations, the walls of grooves 114a have a high finish, low roughness, and are hydrophilically coated.

As can be seen from fig. 2 and 6, in other embodiments, a circumferential surface of the outer core 113 facing the inner core 112 is provided with a groove 114b recessed in a direction away from the accommodating chamber 1111, and a gap between the groove 114b and the inner core 111 forms a first flow chamber 1112.

As can be seen from fig. 2 and 7, in other embodiments, the outer core 113 is sleeved outside the inner core 112, and the inner peripheral surface of the outer core 113 is attached to the outer peripheral surface of the inner core 112, the circumferential surface of the inner core 112 facing the outer core 113 and the circumferential surface of the outer core 113 facing the inner core 112 are both provided with grooves 114c, and a first flow chamber 1112 is formed between the grooves 114c on the inner core 112 and the grooves 114c on the outer core 113. The grooves 114c on the inner core 112 and the outer core 113 may be aligned and combined to form a groove with a larger cross-sectional area, or the grooves 114c on the inner core 112 and the outer core 113 may be offset, so that the number of the first circulation cavities 1112 is multiple. In this embodiment, only the inner core 112 is provided with the groove 114 a.

In some of these embodiments, the number of grooves 114 may be one or more. The depth of the groove 114 is 0.05mm to 0.5mm, for example, the depth of the groove 114 may be any one of 0.05mm, 0.1mm, 0.15mm, 0.2mm, 0.25mm, 0.3mm, 0.35mm, 0.4mm, 0.45mm, and 0.5 mm. The depth of the groove 114 may refer to the dimension of the groove 114 along the radial direction.

According to the blood pumping device provided by the embodiment, the grooves 114 are formed in the inner iron core 112 and/or the outer iron core 113, the grooves 114 form the first circulation cavity 1112, and the perfusate is conveyed along the extending direction of the grooves 114, because the first circulation cavity formed by the grooves 114 is a strip cavity, compared with the annular cavity with larger cross section, the strip cavity is similar in perfusate pressure at each position of the first circulation cavity 1112 due to smaller cross section, and bubble residues are not easy to occur in the first circulation cavity 1112. The residual air bubbles in the perfusion pipeline may cause the following consequences that 1) because the air bubbles are compressible, high-pressure pulsation in the aorta can cause blood to flow back into the catheter, so that the catheter fails (the working environment at the far end of the perfusion device is the arterial pressure of a human body, the pulsation pressure is changed continuously along with time, if the air bubbles remain in the perfusion device, the volume of air can be changed along with the change of the pressure, the instant flowing direction of the perfusion liquid at the furthest end face can be influenced, and when the volume of the air bubbles is reduced along with the increase of the environmental arterial pressure, the blood can flow back into the perfusion system, so that the reliability of the blood pumping catheter is influenced. Blood is easy to form thrombus in a transmission area, particularly in a bearing position, the transmission friction coefficient is increased, the service life of a transmission system is reduced, and meanwhile, the temperature is easy to rise too much, 2) bubbles are not discharged completely, and a certain probability of entering a blood vessel can be caused later, so that air embolism is caused.

As can be seen in conjunction with fig. 2-4, in some of these embodiments, the first flow chamber 1112 extends helically within the core 111 in a first direction x, wherein the first direction x is the direction in which the distal end of the motor 10 is pointing proximally. Wherein, the first flow chamber 1112 extends spirally means that the center point of the first flow chamber 1112 extends spirally along the first direction x. It is easy to understand that when the core 111 is formed by combining the inner core 112 and the outer core 113, and the inner core 112 and/or the outer core 113 are provided with the grooves 114, the grooves 114 also extend spirally in the first direction x.

It will be appreciated that in the present application, the first flow chamber 1112 extends helically in the first direction x within the core 111, which may mean that the first flow chamber 1112 has opposite ends and that a locus of one end of the first flow chamber 1112 extending to the other end within the core 111 extends helically around an axis parallel to the first direction.

Compared with the scheme of opening the linear circulation cavity along the first direction x, in the blood pumping device provided by the embodiment, the first circulation cavity 1112 in the scheme is arranged in a spiral extending manner, so that the entity thicknesses of the inner iron core 112 and the outer iron core 113 in the first direction x are more uniform, the first circulation cavity 1112 is positioned at different positions of the iron core 111 in the circumferential direction in the extending manner along the first direction x, the situation that one side of the iron core 111 is thinned is avoided, and the magnetic field distribution uniformity of the motor 10 is improved.

In some embodiments, the motor 10 further includes a rotor assembly 12, the rotor assembly 12 includes a rotating shaft 121 and a magnetic steel 122, the rotating shaft 121 extends along the first direction x, at least a portion of the rotating shaft 121 is located in the accommodating cavity 1111, and the magnetic steel 122 is located in the accommodating cavity 1111 and is sleeved on the rotating shaft 121. The pole pair number of the magnetic steel 122 is P, the first flow cavity 1112 is spirally wound around the rotating shaft 121, and the winding number t=1/P or t=1/(2P) of the single first flow cavity 1112.

The pole pair number P refers to the number of pairs of magnetic poles in the magnetic steel 122, and the magnetic steel 122 includes one or more N poles and S poles arranged around the rotation shaft 121 in a spacing ring, where the number of N poles is equal to the number of S poles, i.e., the number of N poles is the pole pair number P of the magnetic steel 122. Taking the formula t=1/P as an example, when the pole pair number P is 1, the first flow-through chamber 1112 is wound around the number T of turns 1, and when the pole pair number P is 2, the first flow-through chamber 1112 is wound around the number T of turns 0.5. Taking the formula t=1/(2P) as an example, the first flow-through chamber 1112 encircles the number of turns T0.5 when the pole pair number P is 1, and the first flow-through chamber 1112 encircles the number of turns T0.25 when the pole pair number P is 2. When the number of the first circulation cavities 1112 is plural, the number of the surrounding turns T of each first circulation cavity 1112 is equal, and the angle between the connecting lines of any two adjacent first circulation cavities 1112 and the axis of the rotating shaft 121 is equal when each first circulation cavity 1112 is spirally wound along the axis of the rotating shaft 121. Preferably, the number of pole pairs P is 1, the number of first flow-through cavities 1112 is 1 around the circle T, and the number of first flow-through cavities 1112 is 1.

The motor 10 is characterized as cogging because of uneven magnetic field distribution and magnetic field torque due to teeth (not shown) and slots (not shown) on the core 111, which cause the core to vibrate and produce noise, and reduce the efficiency of the motor 10. The slots on the core 111 are used for connection with windings, and the teeth are used for separating adjacent slots. Since the pole pair number P is related to the magnetic field distribution and the rotation speed of the motor 10, according to the simulation test and the physical verification, the pumping device provided in the embodiment uses the perfusate spirally conveyed in the first circulation chamber 1112 to offset the cogging of the motor 10 so as to reduce the magnetic field torque and improve the efficiency of the motor 10 by making the first circulation chamber 1112 surround the number of turns t=1/P or t=1/(2P).

In some of these embodiments, stator assembly 11 further includes windings 115 positioned within receiving cavities 1111, the windings being sleeved outside of magnetic steel 122. The length of the winding 115 in the first direction x is L, and when the number of turns t=1/P of the first flow-through chamber 1112, the pitch h=pl of the first flow-through chamber 1112. When the number of windings t=1/(2P) of the first flow chamber 1112, the pitch h=2pl of the first flow chamber 1112.

The winding 115 is fixedly connected to the slot portion of the core 111, and when the winding 115 is energized, the winding 115 generates a magnetic field and interacts with the magnetic field of the magnetic steel 122 and causes the magnetic steel 122 to rotate synchronously with the rotating shaft 121.

The pitch H of the groove 114 is understood with reference to the pitch of the bolt, i.e., the distance between adjacent threads measured along the axis of the bolt, generally refers to the axial distance between corresponding points on the pitch line of adjacent threads on a single thread. In the present embodiment, the pitch of the grooves 114 is understood to be the distance between two adjacent positions in the first direction x on a single groove 114 when the number of turns of the groove 114 is greater than 1.

Since the cogging is also related to the length of the winding 115 in the first direction x, according to the simulation test and the physical verification, the pumping device provided in the present embodiment further improves the efficiency of the motor 10 by making the pitch h=pl or h=2pl of the first circulation cavity 1112, and using the perfusate spirally conveyed in the first circulation cavity 1112 to offset the cogging of the motor 10, thereby reducing the magnetic field torque.

In some embodiments, the inner core 112 and the outer core 113 are both cylindrical, and the inner diameter of the inner peripheral surface of the outer core 113 is larger than the inner diameter of the outer peripheral surface of the inner core 112, that is, the inner core 112 and the outer core 113 are disposed with a gap therebetween, such that a gap for forming the first flow chamber 1112 is formed between the inner core 112 and the outer core 113, and the first flow chamber 1112 is an annular chamber extending along the first direction x.

According to the blood pumping device provided by the embodiment, the first circulation cavity 1112 is the annular cavity extending along the first direction x, the interception area of the first circulation cavity 1112 is increased, and because the first circulation cavity 1112 is the annular cavity, the connection openings of the first circulation cavity 1112, the first pipeline and the second circulation cavity 1113 can be designed at any positions on the annular cavity according to actual needs, so that the suitability of the first circulation cavity 1112 is improved, and the design difficulty is reduced.

In other embodiments, the iron core 111 is integrally formed by powder metallurgy, 3D printing, or the like, and the first flow chamber 1112 is naturally formed inside the iron core 111 during the forming process, or the iron core 111 is manufactured on the iron core 111 by a processing process after the integral forming.

Having described the implementation of a first flow lumen in a blood pumping device, several implementations of a second flow lumen in a blood pumping device are described below in conjunction with the accompanying figures. In some embodiments, referring to fig. 2, windings 115 at least partially surround the outer sides of magnetic steel 122, and the gap between windings 115 and rotor assembly 12 forms a second flow chamber 1113.

In some embodiments, the iron core 111, the windings 115 and the magnetic steel 122 may be cylinders, or may be polygonal cylindrical structures such as square cylinders. The present embodiment is exemplified by the iron core 111, the windings 115, and the magnetic steel 122 being cylinders. The accommodating cavity 1111 is formed by surrounding the iron core 111, the accommodating cavity 1111 is used for accommodating components such as the winding 115, the magnetic steel 122, the bearing and the like, and the cavity left after the accommodating cavity 1111 is occupied by the components such as the winding 115, the magnetic steel 122, the bearing and the like is removed is the second flow cavity 1113. It is easily understood that when the core 111 is composed of the inner core 112 and the outer core 113, the accommodation chamber 1111 is formed by surrounding the inner core 111.

In other embodiments, the second flow-through chamber 1113 is also located within the core 111. For example, when the core 111 is integrally formed, the first flow chamber 1112 and the second flow chamber 1113 are each prepared by performing a machining process on the core 111. Or when the iron core 111 is composed of the inner iron core 112 and the outer iron core 113, a gap between the inner iron core 112 and the outer iron core 113 forms a first flow cavity 1112, and a second flow cavity 1113 formed by a processing technology is formed on the inner iron core 112 and/or the outer iron core 113. The specific form of the second flow chamber 1113 located in the core 111 may refer to the form of the first flow chamber 1112 formed by the groove 114, which is not described herein.

In some embodiments, the motor 10 further includes a distal bearing 13 and a proximal bearing 14, where the distal bearing 13 and the proximal bearing 14 are sleeved on the rotating shaft 121. The shaft 121 is rotatably connected to the stator assembly 11 by a distal bearing 13 and a proximal bearing 14, the distal bearing 13 being located on the side of the proximal bearing 14 facing away from the first conduit. The first flow lumen 1112 and the second flow lumen 1113 communicate directly or indirectly through the distal bearing 13, and the second flow lumen 1113 and the second conduit 20 communicate directly or indirectly through the proximal bearing 14.

In some of these embodiments, the distal bearing 13 and the proximal bearing 14 may be sliding bearings or ball bearings. In some implementations, the distal bearing 13 and the proximal bearing 14 are ball bearings, and the distal bearing 13 and the proximal bearing 14 are provided with a gap for allowing the perfusate to pass through, for example, a gap between the balls, and the perfusate on both sides of the bearing in the axial direction can flow through the gap on the bearing. For example, the perfusate flowing from the first flow chamber 1112 to the second flow chamber 1113 flows out of the second pipe 20 after passing through the distal bearing 13 and the proximal bearing 14 in this order, or the perfusate flowing from the second pipe 20 flows out of the first pipe after passing through the proximal bearing 14 and the distal bearing 13 in this order, and then flows out of the first pipe through the first flow chamber 1112. In alternative further implementations, the distal bearing 13 and the proximal bearing 14 are sliding bearings, the distal bearing 13 and other components (e.g., bearing blocks) forming a gap allowing the passage of the perfusate, and the proximal bearing 14 and other components (e.g., bearing blocks) forming a gap allowing the passage of the perfusate. In alternative further implementations, one of the distal bearing 13 and the proximal bearing 14 is a ball bearing, the other is a slide bearing, and the embodiments may be a fusion of the first two implementations.

In the blood pumping device provided by the embodiment, particles generated during bearing rotation can be taken away when perfusion liquid flows through the distal bearing 13 and/or the proximal bearing 14, so that bearing abrasion is reduced, and the service life of the motor 10 is further prolonged.

Fig. 8 shows a schematic structural view of an exemplary proximal end cap, and fig. 9 shows a schematic structural view of an exemplary outer core and distal end cap.

As can be seen in conjunction with fig. 2, 8 and 9, in some of these embodiments, the motor 10 further includes a distal end cover 15 and a proximal end cover 16, the distal end cover 15 being connected to the distal end of the stator assembly 11 and the proximal end cover 16 being connected to the proximal end of the stator assembly 11. The distal end cover 15 is provided with a first through hole 151 penetrating the distal end cover 15 in the first direction x, and at least part of the rotation shaft 121 protrudes from the first through hole 151 out of the accommodation chamber 1111. The proximal cover 16 is provided with a second through hole 161 penetrating the proximal cover 16 in the first direction x, and the second through hole 161 is used for directly or indirectly communicating the second flow cavity 1113 with the second conduit 20. Distal closure 15 is used to seal the distal end of receiving chamber 1111 and proximal closure 16 is used to seal the proximal end of receiving chamber 1111.

In some of these embodiments, the distal end of the distal closure 15 has a conical flow profile that acts as a blood flow surface in the operational state.

In some embodiments, the impeller 42 is disposed in the outflow channel 40 of the blood pumping device, the rotating shaft 121 extends out of the accommodating cavity 1111 from the first through hole 151 and is connected to the impeller 42, when the motor 10 is started, the rotating shaft 121 drives the impeller 42 to rotate, and when the impeller 42 rotates, blood is pumped from the suction window to the outflow window 41 and the blood pumping function is achieved.

In some of these embodiments, the materials of the proximal and distal caps 16, 15 include metals and non-metals, and the materials of the distal and proximal caps 15, 16 may be the same or different. For example, the material of the distal end cover 15 and the proximal end cover 16 are each 316 stainless steel.

Fig. 10 shows a schematic structural view of an exemplary distal bearing housing, and fig. 11 shows a schematic structural view of an inner core and a proximal bearing housing of another example.

As can be seen in conjunction with fig. 2, 10 and 11, in some embodiments, the motor 10 further includes a proximal bearing seat 17 and a distal bearing seat 18, the proximal bearing seat 17 is connected to the proximal end of the stator assembly 11, a first mounting hole 171 penetrating the proximal bearing seat 17 along the axial direction x of the rotation shaft 121 is provided on the proximal bearing seat 17, the proximal bearing 14 and the proximal cover 16 are both embedded in the first mounting hole 171, and the proximal cover 16 is located at an end of the proximal bearing 14 facing away from the distal bearing 13. The distal bearing seat 18 is connected with the distal end of the stator assembly 11, a second mounting hole 181 penetrating through the distal bearing seat 18 along the axial direction x of the rotating shaft 121 is arranged on the distal bearing seat 18, and the distal bearing 13 is sleeved on the rotating shaft 121 and embedded in the second mounting hole 181. The distal bearing seat 18 is connected with the distal end of the stator assembly 11, the distal bearing seat 18 is provided with a second mounting hole 181 penetrating through the distal bearing seat 18 along the first direction x, and the distal bearing 13 is embedded in the second mounting hole 181.

It will be appreciated that the insertion of the proximal bearing 14 into the first mounting hole 171 means that the outer circumferential surface of the proximal bearing 14 is fixedly attached to the circumferential surface of the proximal bearing seat 17 facing the first mounting hole 171. And the inner peripheral surface of the proximal bearing 14 is sleeved on the rotating shaft 121 and fixedly connected with the rotating shaft 121. The distal bearing 13 is the same.

In some of these embodiments, the distal cover 15 and the distal bearing seat 18 form a gap in the first direction x, and the gap between the distal cover 15 and the distal bearing seat 18 forms a third flow chamber 19, the third flow chamber 19 communicating with the first flow chamber 1112 and the second flow chamber 1113 through the distal bearing 13. The two end surfaces of the distal bearing 13 in the first direction x face the second and third flow chambers 1113 and 19, respectively.

The radial dimension of the first through hole 151 is slightly larger than the radial dimension of the rotating shaft 121, so that the perfusate in the third circulation chamber 19 can flow into the outflow channel 40 through the gap between the first through hole 151 and the rotating shaft 121 on the distal end cover 15, and can also flow into the second circulation chamber 1113 through the gap between the balls on the distal end bearing 13. The radial dimension of the first through hole 151 can be used for controlling the flow of most of perfusion liquid to the distal end bearing 13, and the small part of perfusion liquid is used for balancing the pressure difference between the outflow channel 40 and the position of the third flow-through cavity 19, so that the total amount of blood flowing into the motor 10 at the outflow channel 40 is reduced, and the probability of thrombus formation of the blood in the motor 10 is reduced.

In some of these embodiments, the first conduit is a perfusion conduit and the second conduit 20 is a return conduit. The perfusate of the first conduit flows through the first flow chamber 1112, the third flow chamber 19, the distal bearing 13, the second flow chamber 1113, and the proximal bearing 14 in that order and then out of the motor 10 through the second conduit 20.

In the blood pumping device provided by the embodiment, the particles generated during the rotation of the bearings can be taken away when the perfusion fluid flows through the distal bearing 13 and the proximal bearing 14, so that the particles generated during the operation of the motor 10 are effectively reduced and enter the human body, the total amount of the perfusion fluid flowing into the patient is reduced, the total amount of the particles flowing into the patient is further reduced, and the product safety is improved. By making the first pipe be a perfusion pipe and the second pipe 20 be a return pipe, the perfusate will first enter the third flow chamber 19 from the first flow chamber 1112, and then flow out from the second pipe 20 after the bearing is washed, so that the content of particles in the perfusate at the third flow chamber 19 is extremely low, and the total amount of particles flowing into the patient from the first through hole 151 is reduced.

In some of these embodiments, the circumferential surface of the distal bearing housing 18 facing the second mounting hole 181 includes a fifth step surface 182 and a sixth step surface 183, the fifth step surface 182 being located on a side of the sixth step surface 183 facing away from the proximal bearing housing 12. The radial dimension of the fifth step surface 182 is smaller than the radial dimension of the sixth step surface 183, and the distal bearing 13 is fitted in the sixth step surface 183. The perfusate in the third flow chamber 19 flows through the second mounting hole 181 where the fifth step surface 182 is located, and then flows into the second flow chamber 1113 through the distal bearing 13.

In the blood pumping device provided in this embodiment, the radial dimension of the fifth step surface 182 is smaller than the radial dimension of the sixth step surface 183, so that the side wall of the fifth step surface 182 facing the sixth step surface 183 will abut against the distal bearing 13, thereby restricting the movement of the distal bearing 13 along the first direction x, and further improving the connection stability between the distal bearing 13 and the distal bearing seat 18.

Fig. 12 shows a schematic cross-sectional structural view of the inner core and proximal bearing housing of fig. 11 for one example.

As can be seen in connection with fig. 2, 11 and 12, in some of these embodiments, the proximal bearing seat 17 is further provided with a first communication hole 172, and the first communication hole 172 communicates directly or indirectly with the first communication cavity 1112 and the first conduit.

In some embodiments, the connection between the first conduit and the proximal bearing block 17, and the connection between the second conduit 20 and the proximal cap 16 may be welded, glued, or otherwise sealed.

Fig. 13 shows a schematic structural diagram of an exemplary second pipe.

As can be seen in conjunction with fig. 13, in some of these embodiments, the first and second conduits 20 may be straight tubes or other shaped tubes, as the application is not limited in particular. In addition, for the return conduit, a notch 21 is provided at the proximal end of the return conduit, and the number of notches 21 may be at least one. When the number of the notches 21 is two or more, the plurality of notches 21 are symmetrically or asymmetrically arranged along the circumferential direction. The notch 21 is used for being connected with a supporting wire (not shown) at least partially positioned in the return pipeline, and the supporting wire is connected with the return pipeline at an embedded position through laser welding or cementing after being embedded into the notch 21, so that the connection strength of the return pipeline and the motor 10 is improved.

In some of these embodiments, one opening of the first communication hole 172 is located on the end face of the proximal bearing housing 17 facing away from the distal bearing housing 18 and communicates with the first conduit, and the other opening is located on the circumferential face of the proximal bearing housing 17 facing away from the first mounting hole 171 and communicates with the first communication chamber 1112.

In some embodiments, the distal end cover 15 and the outer core 113 may be separately manufactured and then connected by welding, gluing, or the like, and the distal end cover 15 and the outer core 113 may be integrally formed. The proximal bearing seat 17 and the inner core 112 may be separately manufactured and then connected by welding, gluing, etc., and the proximal bearing seat 17 and the inner core 112 may be integrally formed. When the proximal bearing seat 17 and the inner core 112 are connected after being prepared separately, the proximal end of the inner core 112 is abutted against the distal end face of the proximal bearing seat 17, and then the connection positions are connected through welding, cementing and other processes. The distal end cap 15 is identical to the outer core 113.

As can be seen in conjunction with fig. 2 and 3, in some of these embodiments, the circumferential surface of the inner core 112 facing the outer core 113 includes a first step surface 1121 and a second step surface 1122, the first step surface 1121 being located at the distal end of the inner core 112 and the second step surface 1122 being located at the proximal end of the inner core 112, the radial dimension of the first step surface 1121 being smaller than the radial dimension of the second step surface 1122. The circumferential surface of the proximal bearing seat 17 facing away from the first mounting hole 171 includes a third step surface 173 and a fourth step surface 174, the third step surface 173 being located on a side of the fourth step surface 174 adjacent to the inner core 112, the radial dimension of the third step surface 173 being smaller than the radial dimension of the fourth step surface 174, the radial dimension of the third step surface 173 being smaller than the radial dimension of the second step surface 1122, one of the openings of the first communication hole 172 being located on the third step surface 173.

The distal end cover 15 is lapped on the first step surface 1121, the outflow channel 40 is lapped on the circumferential surface of the distal end cover 15 facing away from the first step surface 1121, and the radial dimension of the joint between the distal end cover 15 and the inner iron core 112 and the radial dimension of the joint between the distal end cover 15 and the outflow channel 40 are effectively reduced by making the radial dimension of the first step surface 1121 smaller than the radial dimension of the second step surface 1122, so that the intervention difficulty of the motor 10 and the blood pumping device is further reduced.

Wherein, the plurality of step surfaces on the circumferential surface of the proximal bearing seat 17 facing away from the first mounting hole 171 means that a plurality of bosses with different radial dimensions are provided on the circumferential surface, the outer circumferential surface of the boss is defined as a step surface, and the radial dimensions refer to the diameters of the boss. The inner core 112 faces the stepped surface on the circumferential surface of the outer core 113. In some embodiments, the radial dimension of the third step surface 173 is smaller than the radial dimension of the fourth step surface 174, and the radial dimension of the third step surface 173 is smaller than the radial dimension of the second step surface 1122, such that an annular groove is formed at the third step surface 173 that is concave in the axial direction of the rotary shaft 121 and surrounds the axis, and the annular groove communicates with the third circulation chamber 19. When the groove 114 is provided on the inner core 112, the groove 114 extends from the first step surface 1121 to the second step surface 1122 and communicates with the annular groove formed by the third step surface 173, the groove 114 communicates with the third flow chamber 19 at the first step surface 1121, and the groove 114 communicates with the first pipe at the third step surface 173 through the first communication hole 172. By positioning one of the openings of the first communication hole 172 at the third stepped surface 173, the perfusate in the first pipe can flow into the annular groove formed by the third stepped surface 173 through the first communication hole 172 and continue to flow into the first communication chamber 1112 formed by the groove 114. The annular grooves formed by the third stepped surface 173 can be such that when the number of the first communicating chambers 1112 is plural, the plurality of first communicating holes 172 need not be provided to communicate with the respective first communicating chambers 1112, and only the plurality of first communicating chambers 1112 need to communicate with the annular grooves formed by the third stepped surface 173. The proximal end of the outer core 113 is sleeved outside the fourth step surface 174, and the fourth step surface 174 abuts against the inner peripheral surface of the outer core 113, that is, the fourth step surface 174 is embedded on the outer core 113. By abutting the fourth step surface 174 against the inner peripheral surface of the outer core 113, the outer core 113 seals the annular groove formed at the third step surface 173, and thus the annular groove has only two outlets of the groove 114 and the first communication hole 172.

In some of these embodiments, the inner core 112 is coupled to the proximal bearing housing 17 and the third fourth step surface 174 on the proximal bearing housing 17 is coupled to the outer core 113. It may also be understood that the outer core 113 is connected to the inner core 112 through the proximal bearing seat 17, and the outer core 113 is sleeved outside the inner core 112, and a gap for forming the first flow chamber 1112 is formed between the outer core 113 and the inner core 112.

In some embodiments, the motor 10 further includes a housing (not shown) that is disposed over the core 111, at least a portion of which is in contact with the second step surface 1122.

It will be appreciated that the components of the blood pumping device that contact the human body and blood are all made of biosafety materials, and may be metal or nonmetal. For example, the components may be 316 stainless steel when they are metal. In other embodiments, the iron core 111 may also be used as a housing of the motor 10 to directly contact with the tissue of the patient, so that the motor 10 does not need to be provided with a housing, thereby reducing the diameter of the motor 10 and reducing the intervention difficulty.

It will be appreciated that the various components of the foregoing embodiments are described separately and that in practice the various components may be integrally formed in a single piece. For example, the inner core 112 and the proximal bearing housing 17 are integrally formed, for example, the outer core 113 is integrally formed with the distal end cover 15, for example, the inner core 112 and the outer core 113 are integrally formed, for example, and for example, the inner core 112 is integrally formed with the distal end bearing housing 18. The above is only a part of examples of integral forming, and not all integral forming schemes, as long as the combination schemes of processing requirements and performance requirements can be met, are all within the protection scope of the application.

In some alternative embodiments, the present application further provides a fluid pumping device for delivering a body fluid other than blood, the fluid pumping device including a motor 10, a first conduit and a second conduit 20, the motor 10 including a stator assembly 11, the stator assembly 11 including a core 111, the core 111 enclosing to form a receiving chamber 1111, a first flow chamber 1112 being provided within the core 111, and a second flow chamber 1113 being provided within the core 111 and/or within the receiving chamber 1111 in communication with the first flow chamber 1112. The first conduit communicates with the first flow chamber 1112 and the second conduit 20 communicates with the second flow chamber 1113, one of the first conduit and the second conduit 20 being a perfusion conduit and the other being a return conduit. Wherein the perfusion tube is used for conveying perfusion liquid to the motor 10, and the reflux tube is used for discharging the perfusion liquid in the motor 10.

In some of these embodiments, the bodily fluid includes interstitial fluid, digestive fluid, and the like.

The structure of the liquid pumping device refers to the blood pumping device, and can produce the same technical effect as the blood pumping device, and the description is not repeated here.

In addition, the application also provides a motor which comprises a stator assembly, wherein the stator assembly comprises an iron core, the iron core is enclosed to form a containing cavity, a first circulation cavity is arranged in the iron core, and a second circulation cavity communicated with the first circulation cavity is arranged in the iron core and/or the containing cavity. One of the first flow cavity and the second flow cavity is used for being communicated with a perfusion pipeline, the other is used for being communicated with a backflow pipeline, the perfusion pipeline is used for conveying perfusion liquid into the motor, and the backflow pipeline is used for discharging the perfusion liquid in the motor.

It will be appreciated that the motor provided by the present application may be any motor of the aforementioned blood pumping device and liquid pumping device, and will not be described here again.

In the foregoing, only the specific embodiments of the present application are described, and it will be clearly understood by those skilled in the art that, for convenience and brevity of description, the specific working processes of the systems, modules and units described above may refer to the corresponding processes in the foregoing method embodiments, which are not repeated herein. It should be understood that the scope of the present application is not limited thereto, and any equivalent modifications or substitutions can be easily made by those skilled in the art within the technical scope of the present application, and they should be included in the scope of the present application.

Claims

1. A blood pumping device for delivering blood, comprising:

The motor comprises a stator assembly, wherein the stator assembly comprises an iron core, the iron core is enclosed to form a containing cavity, a first circulation cavity is arranged in the iron core, and a second circulation cavity communicated with the first circulation cavity is arranged in the iron core and/or the containing cavity;

A first conduit in communication with the first flow-through chamber;

and the second pipeline is communicated with the second circulation cavity, one of the first pipeline and the second pipeline is a perfusion pipeline, the other is a reflux pipeline, the perfusion pipeline is used for conveying perfusion liquid to the motor, and the reflux pipeline is used for discharging the perfusion liquid in the motor.

2. The blood pumping device of claim 1, wherein the first flow lumen is a strip lumen extending in a first direction, wherein the first direction is a direction in which a distal end of the motor is directed proximally.

3. The blood pumping device according to claim 2, wherein the iron core includes an inner iron core and an outer iron core that is sleeved outside the inner iron core, and an outer peripheral surface of the inner iron core is attached to an inner peripheral surface of the outer iron core:

A groove is formed in the circumferential surface, facing the outer iron core, of the inner iron core, and a gap between the groove and the outer iron core forms the first flow cavity;

Or, a groove is formed in the circumferential surface, facing the inner iron core, of the outer iron core, and a gap between the groove and the inner iron core forms the first flow cavity;

Or, the circumferential surface of the inner iron core facing the outer iron core and the circumferential surface of the outer iron core facing the inner iron core are respectively provided with a groove, and a first circulation cavity is formed between the grooves on the inner iron core and the grooves on the outer iron core.

4. A blood pumping device according to claim 2 or claim 3, wherein the first flow chamber extends helically within the core in the first direction.

5. The blood pumping device of claim 4, wherein the motor further comprises a rotor assembly, the rotor assembly comprising a shaft and a magnetic steel, the shaft extending in the first direction, at least a portion of the shaft being located within the receiving chamber, the magnetic steel being located within the receiving chamber and over the shaft;

the pole pair number of the magnetic steel is P, the first circulation cavity is spirally wound on the rotating shaft, and the winding circle number T=1/P or T=1/(2P) of the single first circulation cavity.

6. The blood pumping apparatus of claim 5, wherein the stator assembly further comprises a winding positioned within the receiving cavity, the winding being nested outside the magnetic steel, a gap between the winding and the rotor assembly forming the second flow-through cavity;

The length of the winding in the first direction is L, the pitch H=PL of the first circulation cavity when the circle number T=1/P of the first circulation cavity is around, and the pitch H=2PL of the first circulation cavity when the circle number T=1/(2P) of the first circulation cavity is around.

7. The blood pumping device of claim 5, wherein the motor further comprises:

the distal end bearing is sleeved on the rotating shaft and is communicated with the first circulation cavity and the second circulation cavity;

the near-end bearing is sleeved on the rotating shaft, the rotating shaft is rotationally connected with the stator assembly through the far-end bearing and the near-end bearing, and the far-end bearing is positioned at one side of the near-end bearing, which is away from the first pipeline;

The distal end sealing cover is connected with the distal end of the stator assembly, a first through hole penetrating through the distal end sealing cover along the first direction is formed in the distal end sealing cover, at least part of the rotating shaft extends out of the accommodating cavity from the first through hole, and the distal end sealing cover is used for sealing the distal end of the accommodating cavity;

The proximal end sealing cover is connected with the proximal end of the stator assembly and used for sealing the proximal end of the accommodating cavity, a second through hole penetrating through the distal end sealing cover along the first direction is formed in the proximal end sealing cover, and the second through hole is used for communicating the second circulation cavity with the second pipeline.

8. The blood pumping device of claim 7, wherein the motor further comprises:

The proximal bearing seat is connected with the proximal end of the stator assembly, a first mounting hole penetrating through the proximal bearing seat along the first direction is formed in the proximal bearing seat, the proximal bearing and the proximal sealing cover are embedded in the first mounting hole, and the proximal sealing cover is located at one end, away from the distal bearing, of the proximal bearing;

The remote bearing seat is connected with the remote end of the stator assembly, a second mounting hole penetrating through the remote bearing seat along the first direction is formed in the remote bearing seat, and the remote bearing is embedded in the second mounting hole.

9. The blood pumping device of claim 8, wherein the distal cover and the distal bearing housing have a gap in the first direction, and wherein the gap between the distal cover and the distal bearing housing forms a third flow chamber that communicates the first flow chamber and the second flow chamber.

10. The blood pumping device of claim 9, wherein the first conduit is a perfusion conduit and the second conduit is a return conduit.

11. The blood pumping device of claim 8, wherein the proximal housing further comprises a first communication port, the first communication port communicating the first flow lumen with the first conduit.

12. The blood pumping device of claim 11, wherein one opening of the first communication hole is located on an end face of the proximal bearing block on a side facing away from the distal bearing block and communicates with the first conduit, and the other opening is located on a circumferential face of the proximal bearing block facing away from the first mounting hole and communicates with the first communication chamber.

13. The blood pumping device of claim 1, wherein the core comprises an inner core and an outer core sleeved outside the inner core, the outer core is disposed in a gap with the inner core, and a gap between the inner core and the outer core forms the first flow chamber.

14. The utility model provides a motor, its characterized in that includes stator module, stator module includes the iron core, the iron core encloses to close and forms and hold the chamber, be equipped with first circulation chamber in the iron core, in the iron core and/or hold the intracavity be equipped with the second circulation chamber of first circulation chamber intercommunication, first circulation chamber with one of them is used for with filling pipeline intercommunication in the second circulation chamber, another is used for with backflow pipeline intercommunication.