Blood pump

Abstract

The invention discloses a blood pump and relates to the technical field of medical instruments.The blood pump comprises an impeller device, at least one first electromagnetic assembly and a pump shell, the impeller device comprises a cylinder, blades and first permanent magnet assemblies, the radial outer edges of the blades are fixed to the inner wall of the cylinder, and the first permanent magnet assemblies are arranged at at least one end, in the axial direction, of the cylinder; the at least one first electromagnetic assembly is arranged on at least one axial side of the impeller device, the first electromagnetic assembly is used for generating magnetic torque with the first permanent magnet assembly under the condition that a power supply is switched on, so that the impeller device rotates under the action of the magnetic torque, the pump shell is provided with a liquid inlet and a liquid outlet, and the impeller device and the first electromagnetic assembly are arranged in the pump shell; the impeller device is used for driving blood to flow from the liquid inlet to the liquid outlet. According to the blood pump, blood pumping is achieved in a magnetic suspension mode, a motor shaft does not need to be arranged, the structure of the blood pump is simpler, the working stability is high, and the thrombus risk is effectively reduced.

Description

Technical Field

[0001] The present application relates to the technical field of medical devices, and in particular to a blood pump. Background Art

[0002] For high-risk and complex coronary heart disease patients, myocardial ischemia caused by transient blood flow interruption during percutaneous coronary intervention or increased cardiac load caused by injection of contrast agent can both trigger circulatory collapse and even sudden death.

[0003] In related technologies, blood is pumped by a blood pump. The blood pump includes a pump housing, a motor, and an impeller. The pump housing has a liquid inlet and a liquid outlet. The motor enters the human body together with a catheter. The motor has a motor shaft and a motor bearing. The motor shaft is connected to the impeller. The motor drives the impeller to rotate through the motor shaft to drive the blood in the pump housing to flow from the liquid inlet to the liquid outlet, thereby realizing blood pumping. However, since the motor is located in the blood vessel, blood is likely to deposit between the motor shaft and the motor bearing to form thrombus, resulting in motor failure and increasing the risk of stroke. When the motor shaft drives the blade to rotate, the linear velocity of the radial outer edge of the blade is relatively large, and a high shear force will be generated in the gap between the radial outer edge of the blade and the inner wall of the pump housing. The high shear force will cause red blood cells to be damaged and hemolysis will occur. Summary of the Invention

[0004] In view of this, the embodiments of the present application are expected to provide a blood pump that realizes blood pumping through a magnetic levitation method, does not require a motor shaft, has high working stability of the blood pump, and effectively reduces the thrombus risk.

[0005] To achieve the above object, the embodiments of the present application provide a blood pump, including:

[0006] An impeller device, including a cylinder body, blades, and a first permanent magnet assembly. The radial outer edge of the blade is fixed to the inner wall of the cylinder body, and the first permanent magnet assembly is provided at at least one end of the cylinder body along the axial direction;

[0007] At least one first electromagnetic assembly, disposed on at least one side of the impeller device in the axial direction. The first electromagnetic assembly is used to generate a magnetic torque with the first permanent magnet assembly when the power is turned on, so that the impeller device rotates under the action of the magnetic torque;

[0008] A pump housing, having a liquid inlet and a liquid outlet. The impeller device and the first electromagnetic assembly are disposed in the pump housing, and the impeller device is used to drive blood to flow from the liquid inlet to the liquid outlet.

[0009] In some embodiments, the first permanent magnet assemblies are respectively disposed at opposite ends of the cylinder body in the axial direction, and the first electromagnetic assemblies are respectively disposed on opposite sides of the impeller device in the axial direction.

[0010] In some embodiments, the first permanent magnet assemblies are respectively disposed at two axially opposite ends of the cylinder body. The blood pump includes a limiting device, and the limiting device includes a second permanent magnet assembly. The limiting device is disposed at an end of the impeller device axially away from the first electromagnetic assembly. Wherein, an axial acting force is formed between the second permanent magnet assembly and the first permanent magnet assembly facing the second permanent magnet assembly.

[0011] In some embodiments, one end of the blade facing radially outwards is fixed to the inner wall of the cylinder body, and one end of the blade facing radially inwards is a free end.

[0012] In some embodiments, the first electromagnetic assembly surrounds the inner wall of the pump housing. The first electromagnetic assembly has a hollow region axially, and the hollow region is for blood to flow through.

[0013] In some embodiments, the first axial end of the pump housing is open and forms the liquid inlet. The blood pump includes a first flow guiding member, and the first flow guiding member is disposed at the first axial end of the pump housing for guiding blood to the liquid inlet.

[0014] In some embodiments, the blood pump includes a second flow guiding member. The pump housing includes at least two supporting members, and the supporting members are formed at the end of the second end of the pump housing. The supporting members are connected to the second flow guiding member, and the supporting members are arranged at intervals along the circumferential direction of the pump housing. The interval between two adjacent supporting members forms the liquid outlet.

[0015] In some embodiments, along the direction axially approaching the pump housing, the second flow guiding member gradually contracts, and the end of the second flow guiding member extends into the pump housing.

[0016] In some embodiments, the cross-sectional shape of any part of the second flow guiding member in a plane perpendicular to the axial direction of the pump housing is circular.

[0017] In some embodiments, the second flow guiding member has a lead hole, and the lead hole penetrates the circumferential outer wall of the second flow guiding member. The power cord for connecting to the first electromagnetic assembly is led out from the inside of the second flow guiding member through the lead hole and extends along the inner wall of the supporting member towards the first end of the pump housing to be connected to the first electromagnetic assembly.

[0018] In some embodiments, the number of the impeller devices is at least two, and the impeller devices and the first electromagnetic assembly are arranged alternately axially.

[0019] In some embodiments, the impeller device includes a third permanent magnet assembly arranged circumferentially along the cylinder body. The blood pump includes a second electromagnetic assembly disposed on the pump housing and surrounding the outer circumference of the third permanent magnet assembly. The second electromagnetic assembly is configured to generate a magnetic torque with the third permanent magnet assembly when power is turned on, so that the impeller device rotates under the action of the magnetic torque.

[0020] In some embodiments, the blood pump includes at least two magnetic levitation bearings arranged axially at intervals. The magnetic levitation bearing includes a first magnetic ring and a second magnetic ring arranged concentrically. The first magnetic ring is fixedly connected to the cylinder body, and the second magnetic ring is arranged around the inner wall of the pump housing.

[0021] The blood pump according to the embodiment of the present application realizes the pumping of blood by the cooperation of the first electromagnetic assembly and the first permanent magnet assembly to generate a magnetic torque to drive the impeller device to rotate. On the one hand, the pumping of blood is realized by magnetic levitation, and there is no need to set a motor shaft, so the structure of the blood pump is simpler and the working stability is high, effectively reducing the risk of thrombosis. On the other hand, the rotation of the first permanent magnet assembly drives the rotation of the cylinder body and then drives the rotation of the blades, thereby realizing the overall rotation of the impeller device. The cylinder body can reduce the effect of the large circumferential velocity at the outer edge of the blade during rotation on the blood, reduce the probability of red blood cells in the blood being damaged, and thus reduce the risk of hemolysis and improve the working reliability of the blood pump. Description of the Drawings

[0022] Figure 1 is a schematic structural diagram of a blood pump provided by an embodiment of the present application;

[0023] Figure 2 is a cross-sectional view of the blood pump provided by the first embodiment of the present application, wherein the dotted arrow in the figure indicates the flow direction of the blood;

[0024] Figure 3 is a cross-sectional view of the blood pump provided by the second embodiment of the present application, wherein the dotted arrow in the figure indicates the flow direction of the blood;

[0025] Figure 4 is a cross-sectional view of the blood pump provided by the third embodiment of the present application, wherein the dotted arrow in the figure indicates the flow direction of the blood;

[0026] Figure 5 is a cross-sectional view of the blood pump provided by the fourth embodiment of the present application, wherein the dotted arrow in the figure indicates the flow direction of the blood;

[0027] Figure 6 is a cross-sectional view of the blood pump provided by the fifth embodiment of the present application, wherein the dotted arrow in the figure indicates the flow direction of the blood.

[0028] Description of Reference Numerals

[0029] Impeller device 1; cylinder 11; blades 12; first permanent magnet assembly 13; third permanent magnet assembly 14; first electromagnetic assembly 2; hollow area 2a; pump housing 3; liquid inlet 3a; liquid outlet 3b; support member 31; limit device 4; second permanent magnet assembly 41; first flow guide member 5; second flow guide member 6; second electromagnetic assembly 7; magnetic bearing 8; first magnetic ring 81; second magnetic ring 82; power cord a. DETAILED DESCRIPTION

[0030] The following is a further detailed description of the implementation of the present application in conjunction with the accompanying drawings and examples. The following examples are used to illustrate the present application but cannot be used to limit the scope of the present application.

[0031] In the description of the embodiments of the present application, the terms “first”, “second” and “third” are used for descriptive purposes only and are not to be understood as indicating or implying relative importance.

[0032] In the description of the embodiments of the present application, the terms "first end" and "second end" are directions shown in the drawings, and the arrows in the drawings indicate the flow direction of the fluid.

[0033] Blood pumps are commonly used medical devices that can provide power for blood flow. For example, the heart is the power organ of the human body. The main function of the heart is to provide power for blood flow and transport blood to various parts of the body. When the patient's heart has problems and cannot provide power, the patient's life is in danger. For high-risk and complex coronary heart disease patients, myocardial ischemia caused by short-term blood flow blockage during percutaneous coronary intervention or increased cardiac load due to contrast agent injection can cause circulatory collapse or even sudden death. At this time, a blood pump can provide power for the patient's blood and pump blood from the ventricle to the artery.

[0034] Please refer to Figures 1 to 6 An embodiment of the present application provides a blood pump, comprising an impeller device 1, at least one first electromagnetic component 2 and a pump housing 3.

[0035] The impeller device 1 comprises a cylinder 11, blades 12 and a first permanent magnet assembly 13. The radial outer edge of the blade 12 is fixed to the inner wall of the cylinder 11. The first permanent magnet assembly 13 is provided at least at one end of the cylinder 11 in the axial direction.

[0036] At least one first electromagnetic component 2 is arranged on at least one axial side of the impeller device 1. The first electromagnetic component 2 is used to generate a magnetic torque between it and the first permanent magnet component 13 when the power is turned on, so that the impeller device 1 rotates under the action of the magnetic torque.

[0037] The pump housing 3 has a liquid inlet 3a and a liquid outlet 3b. The impeller device 1 and the first electromagnetic assembly 2 are arranged inside the pump housing 3. The impeller device 1 is used to drive blood to flow from the liquid inlet 3a to the liquid outlet 3b.

[0038] It should be noted that the first permanent magnet assembly 13 is fixed to the cylinder 11, that is, the first permanent magnet assembly 13 and the cylinder 11 are relatively stationary. The first electromagnetic assembly 2 is used to generate a magnetic torque with the first permanent magnet assembly 13 when the power is turned on. Under the action of the magnetic torque, the first permanent magnet assembly 13 rotates to drive the cylinder 11 to rotate, and then drives the blade 12 to rotate. In this way, the overall rotation of the impeller device 1 is realized.

[0039] It can be understood that the liquid inlet 3a and the liquid outlet 3b of the pump housing 3 are located on the opposite sides of the impeller device 1 along the axial direction. The liquid inlet 3a is used for blood to enter the blood pump, and the liquid outlet 3b is used for blood to leave the blood pump. Exemplarily, the liquid inlet 3a can be communicated with the ventricle, and the liquid outlet 3b can be communicated with the arterial blood vessel. In this way, under the rotation of the impeller device 1, the blood from the ventricle can flow through the liquid inlet 3a and the liquid outlet 3b to the arterial blood vessel to realize the pumping of blood.

[0040] Specifically, when the first electromagnetic assembly 2 is powered on, the blood pump can drive the impeller device 1 to rotate inside the pump housing 3 through the first electromagnetic assembly 2, form a negative pressure near the liquid inlet 3a of the blood pump, so that the blood in the ventricle can smoothly enter the pump housing 3 from the liquid inlet 3a, do work through the impeller device 1, convert mechanical energy into the kinetic energy and pressure potential energy of the blood, and discharge it from the liquid outlet 3b into the arterial blood vessel to achieve the purpose of ventricular assistance.

[0041] In the related art, the blood pump includes a pump housing, a motor and an impeller. The motor enters the human body together with the catheter. The motor has a motor shaft and a motor bearing. The motor shaft is connected to the impeller. The motor drives the impeller to rotate through the motor shaft to realize the pumping of blood. However, the motor is located in the blood vessel, and blood is likely to deposit between the motor shaft and the motor bearing to form thrombus, resulting in motor failure and increasing the risk of stroke; moreover, when the motor shaft drives the blade to rotate, the linear velocity of the outer edge of the blade in the radial direction is relatively large, and a relatively high shear force will be generated in the gap between the outer edge of the blade in the radial direction and the inner wall of the pump housing. The relatively high shear force will cause red blood cells to be damaged and hemolysis will occur.

[0042] The blood pump according to the embodiment of the present application realizes the pumping of blood by the cooperation of the first electromagnetic component 2 and the first permanent magnet component 13 to generate a magnetic torque to drive the impeller device 1 to rotate. On the one hand, the pumping of blood is realized in a magnetic levitation manner, and there is no need to set a motor shaft. The structure of the blood pump is simpler and the working stability is high, effectively reducing the thrombus risk. On the other hand, the rotation of the first permanent magnet component 13 drives the cylinder 11 to rotate, and then drives the blade 12 to rotate, so as to realize the overall rotation of the impeller device 1. The cylinder 11 can reduce the effect of the large circumferential velocity at the outer edge of the blade 12 during rotation on the blood, reduce the probability of red blood cells in the blood being damaged, thereby reducing the hemolysis risk and improving the working reliability of the blood pump.

[0043] It should be noted that at least one first electromagnetic component 2 is arranged on at least one side of the axial direction of the impeller device 1, including various situations.

[0044] For example, in some examples, the number of the first electromagnetic components 2 is one. At this time, the first electromagnetic component 2 can be arranged at one end of the impeller device 1 along the axial direction and close to the liquid inlet 3a, or the first electromagnetic component 2 can be arranged at one end of the impeller device 1 along the axial direction and close to the liquid outlet 3b. Exemplarily, please refer to Figure 2 , the first electromagnetic component 2 is arranged at one end of the impeller device 1 close to the liquid outlet 3b.

[0045] In other examples, the number of the first electromagnetic components 2 is two, and they are arranged on the opposite sides of the axial direction of the impeller device 1.

[0046] Of course, the number of the first electromagnetic components 2 can also be three or more, and they are arranged on the same side or different sides of the axial direction of the impeller device, which is not limited here.

[0047] It can be understood that in some embodiments, the first electromagnetic component 2 can be fixedly connected to the inner wall of the pump housing 3 by an adhesive method. Specifically, a coating or glue can be applied to the surface of the first electromagnetic component 2 to achieve insulation, and then it can be adhesively fixed to the inner wall of the pump housing 3.

[0048] Of course, in other embodiments, the blood pump includes a first support frame, and the first electromagnetic component 2 is fixed to the inner wall of the pump housing 3 through the first support frame. The first support frame not only connects the first electromagnetic component 2 and the pump housing 3, but also can support and protect the first electromagnetic component 2.

[0049] The specific arrangement manner of the first electromagnetic component 2 and the impeller device 1 is not limited.

[0050] In some embodiments, a first permanent magnet component 13 is arranged at one end of the cylinder 11 along the axial direction close to the first electromagnetic component 2, and the inner wall of the pump housing 3 has an inwardly protruding step surface, and the step surface is located at one end of the cylinder 11 along the axial direction away from the first electromagnetic component 2 for axially limiting the cylinder 11.

[0051] It can be understood that after the first electromagnetic component 2 is powered on, a magnetic torque is generated between the first electromagnetic component 2 and the first permanent magnetic component 13. Under the action of the magnetic torque, the impeller device 1 is subjected to a driving force for driving the cylinder 11 to rotate and an attractive force for driving the cylinder 11 to axially move towards the side close to the first electromagnetic component 2. By providing a stepped surface to axially limit the cylinder 11, the influence of the attractive force generated by the magnetic torque on the cylinder 11 moving towards the side close to the first electromagnetic component 2 on the cylinder 11 can be reduced. Under the action of the magnetic torque, the cylinder 11 can be prevented from axially moving under the action of the stepped surface, thereby realizing the stability of the axial position of the impeller device 1, so that the impeller device 1 only rotates, and the rotation drives the blood to flow from the liquid inlet 3a to the liquid outlet 3b.

[0052] The method of axially limiting the cylinder 11 by the stepped surface is not limited. For example, in some examples, the cylinder 11 is directly axially limited by the stepped surface abutting against the cylinder 11; in another example, in some other examples, the cylinder 11 is axially limited by providing a limiting structure on the stepped surface.

[0053] Of course, the axial limitation of the cylinder 11 can also be achieved by other means.

[0054] In some embodiments, first permanent magnetic components 13 are respectively provided at the opposite axial ends of the cylinder 11, and first electromagnetic components 2 are respectively provided at the opposite axial sides of the impeller device 1; that is, in this embodiment, the number of the first electromagnetic components 2 is two and they are provided at the opposite axial sides of the impeller device 1.

[0055] Please refer to Figure 2 and Figure 4 , it can be understood that an impeller device 1 is provided between the two first electromagnetic components 2, and a magnetic torque is generated between each first electromagnetic component 2 and its adjacent first permanent magnetic component 13. Under the action of the magnetic torque, the impeller device 1 is subjected to a driving force for driving the cylinder 11 to rotate and an attractive force for driving the cylinder 11 to axially move towards the side close to the adjacent first electromagnetic component 2. It can be understood that the impeller device 1 is provided between the two first electromagnetic components 2, and the attractive force of the cylinder 11 moving towards the two first electromagnetic components 2 has one attractive force towards the axial first end and the other attractive force towards the axial second end. When the impeller device 1 rotates under the action of the magnetic torque, the impeller device 1 itself will also be subjected to a reverse force applied by the fluid towards the axial first end. The two attractive forces and the force applied by the fluid received by the impeller device 1 are balanced with each other. In this way, the axial position of the impeller device 1 is stable, and it only rotates under the action of the driving force, driving the blood to flow from the liquid inlet 3a to the liquid outlet 3b.

[0056] It can be understood that in this embodiment, the axial force exerted by the two first electromagnetic assemblies 2 on the impeller device 1 can be balanced with the axial force exerted by the fluid on the impeller device 1 by adjusting parameters such as the current of the power supply.

[0057] In this embodiment, by arranging two first electromagnetic assemblies 2 to cooperate with the impeller device 1, on the one hand, the axial forces received by the impeller device 1 can be balanced with each other, and the axial position of the impeller device 1 is stable. There is no need to provide a limiting structure on the pump housing 3 to limit the impeller device 1, reducing the contact between the impeller device 1 and the pump housing 3, thereby reducing the wear of the impeller device 1 and increasing the structural stability of the blood pump. On the other hand, the rotational driving forces generated by the two magnetic torques received by the impeller device 1 can be superimposed on each other, so that the work done by the impeller device 1 per unit time is greater, making the kinetic energy and pressure potential energy of the blood greater, and thus increasing the blood delivery speed and improving the working efficiency of the blood pump.

[0058] In some other embodiments, please refer to Figure 3 and Figure 5 , the blood pump includes a limiting device 4. The limiting device 4 includes a second permanent magnet assembly 41. The limiting device 4 is arranged at one end of the impeller device 1 axially away from the first electromagnetic assembly 2. Among them, an axial force is formed between the second permanent magnet assembly 41 and the first permanent magnet assembly 13 facing the second permanent magnet assembly 41.

[0059] It can be understood that the installation positions of the limiting device 4 and the first electromagnetic assembly 2 are not limited. For example, in some examples, please refer to Figure 3 , the number of the first electromagnetic assemblies 2 is one, and it is arranged at one end of the impeller device 1 axially close to the liquid outlet 3b. The second permanent magnet assembly 41 is arranged at one end of the impeller device 1 axially close to the liquid inlet 3a. In this way, it is convenient to connect the first electromagnetic assembly 2 to the power supply and shorten the wiring distance. Of course, in some other embodiments, the limiting device 4 can be arranged at one end of the impeller device 1 axially close to the liquid outlet 3b, and the first electromagnetic assembly 2 is arranged at one end of the impeller device 1 axially close to the liquid inlet 3a.

[0060] It can be understood that after the first electromagnetic assembly 2 is powered on, a magnetic torque is generated between the first electromagnetic assembly 2 and the first permanent magnetic assembly 13. Under the action of the magnetic torque, the impeller device 1 is subjected to a driving force for driving the cylinder 11 to rotate and an attractive force for driving the cylinder 11 to axially move toward the side close to the first electromagnetic assembly 2, that is, an attractive force toward the second end. And an axially repulsive force is formed between the second permanent magnetic assembly 41 and the first permanent magnetic assembly 13, that is, a force toward the second end. When the impeller device 1 rotates under the action of the magnetic torque, the impeller device 1 itself is also subjected to a reverse force applied by the fluid toward the first end in the axial direction. Thus, the attractive force received by the impeller device 1, the repulsive force of the second permanent magnetic assembly 41, and the force applied by the fluid can be balanced with each other. In this way, the position of the impeller device 1 in the axial direction is stable, and it only rotates under the action of the driving force, driving the blood to flow from the liquid inlet 3a to the liquid outlet 3b.

[0061] It can be understood that in this embodiment, the parameters of the power supply and the like can be adjusted so that the axial force of the first electromagnetic assembly 2 on the impeller device 1, the axial force applied by the fluid on the impeller device 1, and the axial force applied by the limiting device 4 on the impeller device 1 are balanced with each other.

[0062] In this embodiment, by arranging the limiting device 4 to cooperate with the impeller device 1, the mutual balance of the axial forces received by the impeller device 1 can be realized, and the axial position of the impeller device 1 is stable. There is no need to provide a limiting structure on the pump housing 3 to limit the impeller device 1, reducing the contact between the impeller device 1 and the pump housing 3, and thus reducing the wear of the impeller device 1, thereby increasing the structural stability of the blood pump.

[0063] It can be understood that in some embodiments, the second permanent magnetic assembly 41 can be fixedly connected to the inner wall of the pump housing 3 by bonding. Specifically, a coating or glue can be applied to the surface of the second permanent magnetic assembly 41 to achieve insulation, and then it can be adhesively fixed to the inner wall of the pump housing 3.

[0064] Of course, in other embodiments, the blood pump includes a second support frame, and the second permanent magnetic assembly 41 is fixed to the inner wall of the pump housing 3 through the second support frame. The second support frame not only connects the second permanent magnetic assembly 41 and the pump housing 3, but also can support and protect the second permanent magnetic assembly 41.

[0065] In some embodiments, the impeller device 1 has a rotating shaft, and one end of the blade 12 far from the inner wall of the cylinder 11 is fixed to the rotating shaft. In this way, the structural strength of the blade 12 is increased.

[0066] In other embodiments, please refer to Figures 2 to 5, one end of the blade 12 facing radially outwards is fixed to the inner wall of the cylinder 11, and one end of the blade 12 facing radially inwards is a free end. In this way, the impeller device 1 does not have a rotating shaft, reducing the manufacturing cost, increasing the blood flow space in the cylinder 11, improving the blood flow rate, and thus improving the blood pumping efficiency. In addition, since one end of the blade 12 facing radially inwards does not have a rotating shaft, the phenomenon of blood deposition in the low-speed area at the connection between the blade 12 and the rotating shaft is avoided, reducing the probability of thrombus formation.

[0067] Here, the shape of the blade 12 is not limited. For example, the blade 12 can be a helical blade; for another example, the blade 12 can be multiple independent blades.

[0068] Here, the cross-sectional shape of the blade 12 is not limited. For example, the cross-sectional shape of the blade 12 can be an airfoil shape, in which case the thicknesses of various parts of the cross-section of the blade 12 are different. Of course, the thicknesses of various parts of the cross-section of the blade 12 can also be the same.

[0069] Here, the number of the blades 12 is not limited. For example, the number of the blades 12 can be one or multiple.

[0070] The specific shape of the first electromagnetic component 2 is not limited.

[0071] Exemplarily, the first electromagnetic component 2 surrounds the inner wall of the pump housing 3. The first electromagnetic component 2 has a hollow region 2a in the axial direction, and the hollow region 2a is used for blood to flow through. In this way, the coil winding of the first electromagnetic component 2 can be more convenient, facilitating better support for the pump housing 3. In addition, the hollow region 2a can also provide sufficient flow space for blood, improving the blood delivery efficiency of the blood pump.

[0072] The first electromagnetic component 2 is generally arranged in a cylindrical shape.

[0073] The specific position of the liquid inlet 3a of the pump housing 3 is not limited.

[0074] Exemplarily, the first axial end of the pump housing 3 is open and forms the liquid inlet 3a.

[0075] In some embodiments, please refer to Figures 2 to 5 , the blood pump includes a first flow guiding member 5, and the first flow guiding member 5 is arranged at the first axial end of the pump housing 3 for guiding blood to the liquid inlet 3a.

[0076] The specific shape of the first flow guiding member 5 is not limited. Exemplarily, the first flow guiding member 5 is annular to provide a larger blood flow rate in the same space.

[0077] Exemplarily, the circumferential side wall of the first flow guide member 5 is fixedly connected to the inner wall of the pump housing 3. The inner diameter of the first end of the first flow guide member 5 is greater than the inner diameter of the second end of the first flow guide member 5, and the second end of the first flow guide member 5 is communicated with the liquid inlet 3a. The surface formed between the first end and the second end of the first flow guide member 5 is an arc surface. In this way, while increasing the blood flow rate of the first flow guide member 5, the inner wall of the first flow guide member 5 is streamlined, reducing the blood flow loss. In addition, the flow-through surface of the first flow guide member 5 gradually narrows, increasing the blood flow velocity, which has a good scouring effect on the connection between the first flow guide member 5 and the liquid inlet 3a of the pump housing 3, reducing the probability of thrombus formation.

[0078] The specific position of the liquid outlet 3b of the pump housing 3 is not limited.

[0079] In some embodiments, the second end of the pump housing 3 is open to form the liquid outlet 3b.

[0080] In other embodiments, please refer to Figures 2 to 5 , the blood pump includes a second flow guide member 6. The pump housing 3 includes at least two support members 31 formed at the end of the second end of the pump housing 3. The support members 31 are connected to the second flow guide member 6, and the support members 31 are arranged at intervals along the circumferential direction of the pump housing 3. The interval between two adjacent support members 31 forms the liquid outlet 3b.

[0081] Here, the support member 31 can be in a strip structure.

[0082] Exemplarily, three support members 31 are formed at the end of the second end of the pump housing 3 to improve the connection strength between the support members 31 and the second flow guide member 6.

[0083] The connection manner between the support member 31 and the second flow guide member 6 is not limited, and can be a detachable connection or a non-detachable connection, etc.

[0084] In some embodiments, the support member 31 is welded to the second flow guide member 6, and the connection is reliable.

[0085] In other embodiments, a clamping groove is formed on the circumferential outer surface of the second flow guide member 6, and the support member 31 is clamped with the clamping groove. In this way, it is convenient for the disassembly, assembly and cleaning of the second flow guide member 6 and the support member 31.

[0086] Exemplarily, along the direction approaching the pump housing 3 axially, the second flow guide member 6 gradually contracts, and the end of the second flow guide member 6 extends into the pump housing 3.

[0087] That is to say, along the direction approaching the pump housing 3 axially, the cross-sectional area of the second flow guide member 6 in the plane perpendicular to the axial direction of the pump housing 3 gradually decreases. In this way, the second flow guide member 6 can guide the blood flowing axially along the outer wall of the second flow guide member 6 to the liquid outlet 3b, and the second flow guide member 6 can gently change the blood flow direction.

[0088] Exemplarily, the surface formed between the first end of the second flow guide member 6 and the connection between the second flow guide member 6 and the support member 31 is an arc surface, which can better change the blood flow direction and reduce the damage to the blood.

[0089] Exemplarily, the cross-sectional area shape of the second flow guide member 6 at any part in the plane perpendicular to the axial direction of the pump housing 3 is circular.

[0090] It can be understood that the cross-sectional area shape of the second flow guide member 6 at any part in the plane perpendicular to the axial direction of the pump housing 3 is circular, and the resistance of the blood flowing on the outer wall of the second flow guide member 6 is relatively small. The curvature of the circular boundary is relatively small, and the blood can flow more freely along the cross-section, reducing the flow resistance of the blood on the surface of the second flow guide member 6. In addition, compared with other complex shapes, the circular cross-section is easier to achieve uniform stress distribution under the same material and size conditions. This enables the second flow guide member 6 to have better durability and compressive resistance, and improves the structural strength of the second flow guide member 6.

[0091] The arrangement method of the power line a used to connect with the first electromagnetic component 2 is not limited.

[0092] Exemplarily, the first electromagnetic component 2 is bonded to the inner wall of the pump housing 3. It can be understood that when not bonded, a first gap is formed between the first electromagnetic component 2 and the inner wall of the pump housing 3, and the power line a passes through the first gap to the inside of the pump housing 3 and is then led out of the body through the lead-out member and connected to the power supply. Exemplarily, the lead-out member can be a catheter. In this way, the first gap can achieve the sealing of the power line a through bonding, and the power line a is led out through the inside of the pump housing 3, reducing the contact with the blood and improving the safety.

[0093] In some embodiments, the second flow guide member 6 has a lead hole, the lead hole penetrates the circumferential outer wall of the second flow guide member 6, and the power line a used to connect with the first electromagnetic component 2 is led out from the inside of the second flow guide member 6 through the lead hole and extends along the inner wall of the support member 31 towards the first end of the pump housing 3 to be connected with the first electromagnetic component 2.

[0094] It can be understood that a cavity for the power line a to pass through is formed inside the support member 31, the lead hole is arranged at the connection between the second flow guide member 6 and the support member 31, and one end of the power line a passes through the lead hole inside the second flow guide member 6 and then passes through the cavity inside the support member 31 and extends towards the first end of the pump housing 3 to be connected with the first electromagnetic component 2. It should be noted that the second flow guide member 6 is connected to the lead-out member, and the other end of the power line a is led out to the inside of the lead-out member through the inside of the second flow guide member 6 and then led out of the body and connected to the power supply. In this way, the power line a does not contact the blood, does not occupy the space of the blood circulation area additionally, does not affect the blood pumping efficiency, and improves the safety.

[0095] In some embodiments, please refer to Figure 4 , the number of the impeller devices 1 is at least two, and the impeller devices 1 and the first electromagnetic assemblies 2 are arranged alternately along the axial direction.

[0096] It should be noted that the multiple impeller devices 1 rotate at a high speed in the pump housing 3, which improves the suction intensity of the blood pump. In this way, by arranging the multiple impeller devices 1, the blood pumping efficiency of the blood pump is improved.

[0097] It can be understood that, please refer to Figure 5 , one of the adjacent two first electromagnetic assemblies 2 can be replaced by a limiting device 4. After the first electromagnetic assembly 2 is powered on, a magnetic torque is generated between the first electromagnetic assembly 2 and the first permanent magnetic assembly 13. Under the action of the magnetic torque, the impeller device 1 is subjected to a driving force for driving the cylinder body 11 to rotate and an attractive force for driving the cylinder body 11 to axially move towards the side close to the first electromagnetic assembly 2, and an axially repulsive force is formed between the second permanent magnetic assembly 41 and the first permanent magnetic assembly 13. The force exerted by the fluid on the impeller device 1 along the axial direction towards the axial first end, the attractive force of the first electromagnetic assembly 2, and the repulsive force of the first permanent magnetic assembly 13 are balanced with each other, thereby realizing the axial limit of the impeller device 1.

[0098] In some embodiments, please refer to Figure 6 , the impeller device 1 includes a third permanent magnetic assembly 14 which is arranged along the circumferential direction of the cylinder body 11. The blood pump includes a second electromagnetic assembly 7 which is arranged on the pump housing 3 and surrounds the circumferential outer side of the third permanent magnetic assembly 14. The second electromagnetic assembly 7 is used to generate a magnetic torque between the second electromagnetic assembly 7 and the third permanent magnetic assembly 14 when powered on, so that the impeller device 1 rotates under the action of the magnetic torque.

[0099] It should be noted that the third permanent magnetic assembly 14 is fixed on the cylinder body 11, that is, the third permanent magnetic assembly 14 and the cylinder body 11 are relatively stationary. When the second electromagnetic assembly 7 is powered on, a magnetic torque is generated between the second electromagnetic assembly 7 and the third permanent magnetic assembly 14. Under the action of the magnetic torque, the third permanent magnetic assembly 14 rotates to drive the cylinder body 11 to rotate, and then drives the blade 12 to rotate. In this way, the overall rotation of the impeller device 1 is realized, so as to drive the blood to flow from the liquid inlet 3a towards the liquid outlet 3b.

[0100] It can be understood that in this embodiment, the first electromagnetic assembly 2 and the first permanent magnet assembly 13 generate a magnetic torque to drive the impeller device 1 to rotate, and the second electromagnetic assembly 7 and the third permanent magnet assembly 14 generate a magnetic torque to drive the impeller device 1 to rotate. The work done by the impeller device 1 per unit time is greater, so that the kinetic energy and pressure potential energy of the blood are greater, and thus the blood delivery speed can be increased. In addition, the first electromagnetic assembly 2 and the first permanent magnet assembly 13 are arranged axially, and the second electromagnetic assembly 7 and the third permanent magnet assembly 14 are arranged radially. While driving the impeller device 1 to rotate, they can also not interfere with each other, and the rotational driving force received by the impeller device 1 is relatively large without increasing the axial dimension of the blood pump, improving the working efficiency of the blood pump.

[0101] It can be understood that the second electromagnetic assembly 7 can be fixedly connected to the inner wall of the pump housing 3 by bonding. Specifically, a coating or glue can be applied to the surface of the second electromagnetic assembly 7 to achieve insulation, and then it can be adhesively fixed to the inner wall of the pump housing 3.

[0102] Of course, the second electromagnetic assembly 7 can also be fixedly connected to the inner wall of the pump housing 3 by other means, which is not limited here.

[0103] In some embodiments, please refer to Figure 6 , the blood pump includes at least two magnetic levitation bearings 8 arranged at intervals along the axis. The magnetic levitation bearing 8 includes a first magnetic ring 81 and a second magnetic ring 82 arranged concentrically. The first magnetic ring 81 is fixedly connected to the cylinder body 12, and the second magnetic ring 82 is arranged around the inner wall of the pump housing 3.

[0104] In this way, the first magnetic ring 81 and the second magnetic ring 82 cooperate with each other to support the impeller device 1 without affecting the rotation of the impeller device 1, so that the impeller device 1 can rotate smoothly under the action of the magnetic torques of the first electromagnetic assembly 1 and the first permanent magnet assembly 13 and the magnetic torques of the second electromagnetic assembly 7 and the third permanent magnet assembly 14, increasing the rotational stability of the impeller device 1.

[0105] The above are only the preferred embodiments of the present application and are not used to limit the present application. For those skilled in the art, the present application can have various changes and modifications. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present application shall be included in the protection scope of the present application.

Claims

1. A blood pump, characterized in that, Comprising: An impeller device, including a cylinder, blades and a first permanent magnet assembly, wherein the radially outer edge of the blade is fixed to the inner wall of the cylinder, and the first permanent magnet assembly is provided at at least one end of the cylinder in the axial direction; At least one first electromagnetic assembly, arranged on at least one side in the axial direction of the impeller device, and the first electromagnetic assembly is used to generate a magnetic torque with the first permanent magnet assembly when the power is turned on, so that the impeller device rotates under the action of the magnetic torque; A pump housing, having a liquid inlet and a liquid outlet, wherein the impeller device and the first electromagnetic assembly are arranged in the pump housing, and the impeller device is used to drive blood to flow from the liquid inlet to the liquid outlet.

2. The blood pump according to claim 1, characterized in that, The first permanent magnet assemblies are respectively arranged at the opposite ends of the cylinder in the axial direction, and the first electromagnetic assemblies are respectively arranged at the opposite sides of the impeller device in the axial direction.

3. The blood pump according to claim 1, wherein The first permanent magnet assemblies are respectively arranged at the opposite ends of the cylinder in the axial direction, and the blood pump includes a limiting device, the limiting device includes a second permanent magnet assembly, the limiting device is arranged at one end of the impeller device away from the first electromagnetic assembly in the axial direction, wherein, an axial acting force is formed between the second permanent magnet assembly and the first permanent magnet assembly facing the second permanent magnet assembly.

4. The blood pump according to claim 1, characterized in that, One end of the blade in the radially outward direction is fixed to the inner wall of the cylinder, and one end of the blade in the radially inward direction is a free end.

5. The blood pump according to claim 1, wherein, The first electromagnetic assembly surrounds the inner wall of the pump housing, and the first electromagnetic assembly has a hollow area in the axial direction, and the hollow area is used for blood to flow through.

6. The blood pump according to claim 1, characterized in that, The first end of the pump housing in the axial direction is open and forms the liquid inlet, and the blood pump includes a first flow guide member, and the first flow guide member is arranged at the first end of the pump housing in the axial direction for guiding blood to the liquid inlet.

7. The blood pump according to claim 1, characterized in that, The blood pump includes a second flow guide member, the pump housing includes at least two support members, the support members are formed at the end of the second end of the pump housing, the support members are connected to the second flow guide member, and the support members are arranged at intervals in the circumferential direction of the pump housing, and the interval between two adjacent support members forms the liquid outlet.

8. The blood pump according to claim 7, characterized in that, In the direction of approaching the pump housing along the axial direction, the second flow guide member gradually contracts, and the end of the second flow guide member extends into the pump housing.

9. The blood pump according to claim 7, characterized in that, The cross-sectional shape of any part of the second flow guide member in a plane perpendicular to the axial direction of the pump housing is circular.

10. The blood pump according to claim 7, characterized in that, The second flow guide member has a lead hole, the lead hole penetrates the circumferential side wall of the second flow guide member, and the power line for connecting with the first electromagnetic assembly is led out from the inside of the second flow guide member through the lead hole and extends along the inner wall of the support member towards the first end of the pump housing to be connected with the first electromagnetic assembly.

11. The blood pump according to claim 1, characterized in that, The number of the impeller devices is at least two, and the impeller devices and the first electromagnetic assemblies are arranged alternately in the axial direction.

12. The blood pump according to claim 1, wherein, The impeller device includes a third permanent magnet assembly, which is arranged circumferentially along the cylinder body. The blood pump includes a second electromagnetic assembly, which is disposed on the pump housing and surrounds the circumferential outer side of the third permanent magnet assembly. The second electromagnetic assembly is configured to generate a magnetic torque with the third permanent magnet assembly when the power is turned on, so that the impeller device rotates under the action of the magnetic torque.

13. The blood pump according to claim 12, characterized in that, The blood pump includes at least two magnetic levitation bearings arranged at intervals along the axial direction. The magnetic levitation bearing includes a first magnetic ring and a second magnetic ring arranged concentrically. The first magnetic ring is fixedly connected to the cylinder body, and the second magnetic ring surrounds the inner wall of the pump housing.

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