Blood pump

Abstract

The invention discloses a blood pump and relates to the technical field of medical instruments.The blood pump comprises an impeller, a pump shell assembly and a connector, the pump shell assembly comprises a pump shell and a spacing ring body, the pump shell is provided with a containing cavity, a liquid inlet, a first liquid outlet and a second liquid outlet, and the first liquid outlet and the second liquid outlet are located on the two opposite sides of the spacing ring body in the axial direction; the impeller is arranged in the containing cavity and penetrates through the spacer ring body, a channel for blood circulation is formed between the circumferential surface of the impeller and the radial inner surface of the spacer ring body, the first liquid outlet is located in the side wall corresponding to the area between the spacer ring body and the connector, and the end, close to the connector, of the impeller is provided with a first permanent magnet assembly; the connector is provided with a first electromagnetic assembly, and the first electromagnetic assembly is used for generating magnetic moment between the first electromagnetic assembly and the first permanent magnet assembly under the condition that a power source is switched on, so that the impeller rotates under the action of the magnetic moment. The connector does not need to be connected with the impeller through an output shaft, and the risk that thrombus is formed between the connector and the impeller is reduced.

Description

Technical Field

[0001] This application relates to the technical field of medical devices, and particularly to a blood pump. Background Art

[0002] 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. Its main function is to provide power for blood flow and transport blood to various parts of the body. When a patient's heart has problems and cannot provide power, the patient's life is in danger. A blood pump can be implanted into the patient's heart to provide power for the patient's blood.

[0003] In related technologies, the impeller of a blood pump is driven by a motor. The output shaft of the motor rotates and outputs power, driving the impeller fixed to the output shaft to rotate. However, thrombus is likely to form at the connection between the output shaft of the motor and the impeller, increasing the surgical risk. Summary of the Invention

[0004] In view of this, embodiments of this application are expected to provide a blood pump to improve the safety during the use of the blood pump.

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

[0006] An impeller;

[0007] A pump housing assembly, including a pump housing and a spacer ring body. The pump housing has a receiving cavity, a liquid inlet, a first liquid outlet, and a second liquid outlet. The spacer ring body is disposed inside the pump housing. The first liquid outlet and the second liquid outlet are located on the axially opposite sides of the spacer ring body. The impeller is disposed in the receiving cavity and passes through the spacer ring body. There is a channel for blood flow between the circumferential surface of the impeller and the radially inner surface of the spacer ring body;

[0008] A connector, located on one axial side of the impeller and connected to one axial end of the pump housing. The first liquid outlet is located on the side wall corresponding to the area between the spacer ring body and the connector;

[0009] One end of the impeller close to the connector has a first permanent magnet assembly, and the connector has a first electromagnetic assembly. 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 rotates under the action of the magnetic torque.

[0010] In some embodiments, the impeller includes a hub and blades. The blades are disposed on the hub. A first ferromagnetic unit is disposed within the spacer ring body, and a second permanent magnet assembly is disposed at a portion of the hub that passes through the spacer ring body. During the rotation of the impeller, the first ferromagnetic unit can form at least a radial acting force with the second permanent magnet assembly, so that the impeller is suspended in the accommodation cavity.

[0011] In some embodiments, the impeller includes a hub and blades. The blades are disposed on the hub. The blood pump includes a second ferromagnetic unit, and a third permanent magnet assembly is disposed at an end of the hub away from the connector. During the rotation of the impeller, the second ferromagnetic unit can form at least a radial acting force with the third permanent magnet assembly, so that the impeller is suspended in the accommodation cavity.

[0012] In some embodiments, the impeller includes a hub and blades. The blades are disposed on the hub. One side of the hub facing the connector has a first end face, and one side of the connector facing the hub has a second end face. The first end face and the second end face face each other. When the first electromagnetic assembly is powered on, a magnetic floating gap can be formed between the first end face and the second end face under the interaction of the first permanent magnet assembly and the first electromagnetic assembly.

[0013] In some embodiments, when the first electromagnetic assembly is powered off, the first end face and the second end face are in contact with each other under the interaction of the first permanent magnet assembly and the first electromagnetic assembly.

[0014] In some embodiments, the pump housing includes a first housing section and a second housing section. The first housing section is connected to an end of the second housing section close to the connector. The first housing section and the spacer ring body are connected to form a pre-assembled unit, and the pre-assembled unit and the second housing section are of a split structure and are connected.

[0015] In some embodiments, a part of the spacer ring body and the first housing section are of an integrally formed structure.

[0016] In some embodiments, the impeller includes a hub and blades. The blades are disposed on the hub. The hub includes an end seat and an impeller shaft. The end seat is connected to an axially first end of the impeller shaft close to the connector. The blades are disposed on the impeller shaft. Along the axis of the impeller, the end seat extends from the region where the first liquid outlet is located to the region where the second liquid outlet is located. The outer diameter of the end of the end seat close to the connector is larger than the outer diameter of the end of the end seat close to the impeller shaft.

[0017] In some embodiments, the first permanent magnet assembly is encapsulated within the end seat.

[0018] In some embodiments, the circumferential outer surface of one end of the end seat close to the connector has a concave arc surface, which is recessed towards the inside of the end seat, and the concave arc surface extends to the end surface of the end seat facing the connector, for guiding blood to the second liquid outlet.

[0019] In some embodiments, the impeller includes a hub and blades, the blades are arranged on the hub, and the cross-sectional shape of the hub at any part in a plane perpendicular to the axial direction of the impeller is circular.

[0020] In some embodiments, the connector includes a cylindrical part and an end cover, the first electromagnetic assembly is arranged in the cylindrical part, the axial first end of the cylindrical part facing the impeller has an opening, the end cover is arranged at one end of the cylindrical part close to the impeller and closes the opening, and the wire body for connecting with the first electromagnetic assembly is led out from the axial second end of the cylindrical part.

[0021] In some embodiments, the first ferromagnetic unit includes an electromagnetic ring structure, the electromagnetic ring structure surrounds the part of the hub passing through the spacer ring body, and the electromagnetic ring structure is used to form a radial acting force with the second permanent magnet assembly when the power is turned on.

[0022] In some embodiments, the pump housing has a wiring channel that is not communicated with the accommodating cavity, the wire body for connecting with the electromagnetic ring structure is led out from the inside of the connector and passes through the wiring channel.

[0023] The blood pump provided by the embodiment of the present application has the connector located on one axial side of the impeller. When the first electromagnetic assembly of the connector is powered on, a magnetic moment is generated between the first electromagnetic assembly and the first permanent magnet assembly, so that the impeller rotates under the action of the magnetic moment, driving blood to flow from the liquid inlet of the pump housing to the first liquid outlet and the second liquid outlet. Through the driving mode of the magnetic moment, the connector does not need to be connected to the impeller by setting an output shaft, the structure is simple, and the risk of forming thrombus between the connector and the impeller is reduced, improving the surgical safety; secondly, both the first liquid outlet and the second liquid outlet axially spaced in the embodiment of the present application can make blood flow out, providing a greater output pressure for the blood and a greater blood output head; in addition, the connector is arranged on one axial side of the impeller, the structure is simple and compact, reducing the radial size of the blood pump, facilitating the placement of the blood pump into a target position with a small space in the body, such as the ventricle, without occupying a large radial space and reducing the surgical risk. Description of the Drawings

[0024] Figure 1 It is a schematic structural diagram of a blood pump provided by the embodiment of the present application;

[0025] Figure 2 is Figure 1 a schematic structural view from another perspective;

[0026] Figure 3 is a cross-sectional view of a blood pump provided by an embodiment of the present application, wherein the dotted arrow in the figure indicates the blood flow direction;

[0027] Figure 4 is a cross-sectional view of a blood pump provided by another embodiment of the present application.

[0028] Description of reference numerals

[0029] Impeller 1; First permanent magnet assembly 11; Hub 12; End seat 121; First end face 121a; Concave arc face 121b; Impeller shaft 122; Blade 13; Second permanent magnet assembly 14; Third permanent magnet assembly 15; Core shaft 16; Pump housing assembly 2; Pump housing 21; First housing section 211; Support member 2111; Second housing section 212; Spacer ring body 22; Accommodation cavity 2a; Liquid inlet 2b; First liquid outlet 2c; Second liquid outlet 2d; Connector 3; Second end face 3a; First electromagnetic assembly 31; Cylindrical portion 32; Open end 32a; End cover 33; First ferromagnetic unit 4; Second ferromagnetic unit 5; Wire body a. Specific embodiments

[0030] The following further describes the embodiments of the present application in detail with reference to the drawings and embodiments. The following embodiments are used to illustrate the present application, but cannot be used to limit the scope of the present application.

[0031] In the following description, the terms "first / second / ..." only distinguish different objects, and do not indicate that there is any same or related relationship between the objects. It should be understood that the described orientation description "axial direction" represents the axial direction shown in the specific corresponding schematic diagram, which may or may not be the axial direction in the normal use state.

[0032] It should be noted that the term "comprising", "including" or any other variant thereof is intended to cover a non-exclusive inclusion, so that a process, method, article or device including a series of elements not only includes those elements, but also includes other elements not explicitly listed, or further includes elements inherent to such process, method, article or device. Without further limitation, an element defined by the statement "including an..." does not exclude the existence of additional identical elements in the process, method, article or device including the element. "Plurality" means greater than or equal to two.

[0033] Blood pumps are commonly used medical devices that can provide the driving force for blood flow. For example, the heart is the power organ of the human body, and its main function is to provide the driving force for blood flow and transport blood to various parts of the body. When a 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 transient blood flow interruption during percutaneous coronary intervention or the increased cardiac load caused by injecting contrast agents can both trigger circulatory collapse and even sudden death. At this time, a blood pump can be used to provide power for the patient's blood and pump the blood from the ventricle to the arterial blood vessels.

[0034] An embodiment of the present application provides a blood pump. Please refer to Figures 1 to 4 , the blood pump includes an impeller 1, a pump housing assembly 2, and a connector 3.

[0035] The pump housing assembly 2 includes a pump housing 21 and a spacer ring body 22.

[0036] The pump housing 21 has a receiving cavity 2a, a liquid inlet 2b, a first liquid outlet 2c, and a second liquid outlet 2d. The spacer ring body 22 is disposed inside the pump housing 21, and the first liquid outlet 2c and the second liquid outlet 2d are located on the axially opposite sides of the spacer ring body 22. That is to say, along the axis of the pump housing 21, the spacer ring body 22 is disposed between the first liquid outlet 2c and the second liquid outlet 2d.

[0037] The impeller 1 is disposed inside the receiving cavity 2a and passes through the spacer ring body 22. There is a channel for blood flow between the circumferential surface of the impeller 1 and the radially inner surface of the spacer ring body 22. This channel communicates the first liquid outlet 2c and the second liquid outlet 2d.

[0038] That is to say, the receiving cavity 2a communicates with the liquid inlet 2b, the first liquid outlet 2c, and the second liquid outlet 2d. That is, blood enters the blood pump from the liquid inlet 2b and flows out of the blood pump through the receiving cavity 2a from the first liquid outlet 2c and the second liquid outlet 2d.

[0039] The impeller 1 is disposed inside the receiving cavity 2a, and the impeller 1 is used to drive blood to flow from the liquid inlet 2b to the first liquid outlet 2c and the second liquid outlet 2d.

[0040] It can be understood that the liquid inlet 2b is used for blood to enter the blood pump, and the first liquid outlet 2c and the second liquid outlet 2d are used for blood to leave the blood pump. Exemplarily, the liquid inlet 2b can be connected to the ventricle, and the first liquid outlet 2c and the second liquid outlet 2d can be connected to the arterial blood vessels. In this way, under the rotation of the impeller 1, the blood from the ventricle can flow through the liquid inlet 2b and the first liquid outlet 2c to the arterial blood vessels, or flow through the liquid inlet 2b and the second liquid outlet 2d to the arterial blood vessels to achieve blood pumping.

[0041] The first liquid outlet 2c and the second liquid outlet 2d are arranged on the side wall of the pump housing 21. The arrangement positions of the first liquid outlet 2c and the second liquid outlet 2d are not limited. In some examples, the second liquid outlet 2d is located downstream of the first liquid outlet 2c along the blood flow direction; in other examples, the first liquid outlet 2c is located downstream of the second liquid outlet 2d along the blood flow direction.

[0042] In the embodiments of the present application, taking the second liquid outlet 2d being located downstream of the first liquid outlet 2c along the blood flow direction as an example for description, that is, the second liquid outlet 2d is located on the side closer to the connector 3 along the axis of the first liquid outlet 2c.

[0043] It can be understood that the impeller 1 is arranged in the accommodation cavity 2a. It can be that the impeller 1 is located between the liquid inlet 2b and the second liquid outlet 2d, or a part of the structure of the impeller 1 is located between the liquid inlet 2b and the second liquid outlet 2d, and another part of the structure extends into the range where the second liquid outlet 2d is located.

[0044] The connector 3 is located on one axial side of the impeller 1. Specifically, the connector 3 can be located on the side closer to the second liquid outlet 2d along the axis of the impeller 1, and the connector 3 is connected to one end of the pump housing 21 along the axis closer to the second liquid outlet 2d.

[0045] The second liquid outlet 2d is located on the side wall corresponding to the area between the spacer ring body 22 and the connector 3.

[0046] The impeller 1 has a first permanent magnet assembly 11, and the connector 3 has a first electromagnetic assembly 31. The first electromagnetic assembly 31 is used to generate a magnetic torque with the first permanent magnet assembly 11 when the power is turned on, so that the impeller 1 rotates under the action of the magnetic torque.

[0047] Specifically, when the first electromagnetic assembly 31 is powered on, the blood pump can drive the impeller 1 to rotate in the pump housing 21 through the connector 3, forming a negative pressure near the liquid inlet 2b of the blood pump, so that the blood in the ventricle smoothly enters the accommodation cavity 2a of the pump housing 21 from the liquid inlet 2b. Through the work of the impeller 1, the mechanical energy is converted into the kinetic energy and pressure potential energy of the blood. Part of the blood is discharged from the first liquid outlet 2c, and another part of the blood flows through the channel between the circumferential surface of the impeller 1 and the radial inner surface of the spacer ring body 22 and is discharged from the second liquid outlet 2d and enters the arterial blood vessel to achieve the purpose of ventricular assistance.

[0048] In the related art, the impeller of the blood pump is driven by a motor. The output shaft of the motor will rotate and output power to drive the impeller fixed on the output shaft to rotate. However, a thrombus is likely to form at the connection between the output shaft of the motor and the impeller, increasing the surgical risk. In addition, the motor adopts a structure in which the stator and the rotor are arranged radially, making the radial size of the motor larger and not conducive to the miniaturization of the blood pump.

[0049] In the embodiment of the present application, for the blood pump, when the first electromagnetic component 31 of the connector 3 is powered on, a magnetic torque is generated between the first electromagnetic component 31 and the first permanent magnetic component 11, so that the impeller 1 rotates under the action of the magnetic torque, driving the blood to flow from the liquid inlet 2b of the pump housing 21 to the first liquid outlet 2c and the second liquid outlet 2d. Through the driving mode of the magnetic torque, the connector 3 does not need to be connected to the impeller 1 by setting an output shaft, the structure is simple, and the risk of thrombus formation between the connector 3 and the impeller 1 is reduced, improving the surgical safety; secondly, both the first liquid outlet 2c and the second liquid outlet 2d axially spaced in the embodiment of the present application can make the blood flow out, providing a greater output pressure for the blood and a greater blood output head; in addition, the connector 3 is arranged on one axial side of the impeller 1, the structure is simple and compact, reducing the radial size of the blood pump, facilitating the placement of the blood pump into the body, such as a target position with a small space such as the ventricle, without occupying a large radial space and reducing the surgical risk.

[0050] In some embodiments, please refer to Figures 3 to 4 , the impeller 1 includes a hub 12 and blades 13, and the blades 13 are arranged on the hub 12.

[0051] It should be noted that the setting position of the blades 13 is not limited. For example, in some examples, the blades 13 are located between the liquid inlet 2b and the second liquid outlet 2d, and in other examples, a part of the blades 13 is located between the liquid inlet 2b and the second liquid outlet 2d, and the other part extends into the area where the second liquid outlet 2d is located.

[0052] It can be understood that the shape of the blades 13 is not limited. For example, the blades 13 can be spiral blades; or for another example, the blades 13 can be formed by combining multiple independent sub - blades.

[0053] Here, the cross - sectional shape of the blades 13 is not limited. For example, the cross - sectional shape of the blades 13 can be an airfoil shape. At this time, the thicknesses of different parts of the cross - section of the blades 13 are different. Of course, the thicknesses of different parts of the cross - section of the blades 13 can also be the same.

[0054] Here, the number of the blades 13 is not limited. For example, the number of the blades 13 can be one or multiple.

[0055] Here, the form of the blades 13 is not limited. For example, the blades 13 can be in the form of the blades of an axial - flow pump, or in the form of the blades of a centrifugal pump, or in the form of the blades of a mixed - flow pump.

[0056] In some embodiments, the blade 13 is in the form of a blade of an axial flow pump. The blade 13 extends axially along the hub 12. When the impeller 1 rotates, blood passes through the blade 13 along the axial direction of the impeller 1, and due to the inclination angle of the blade 13, a pressure that changes the direction is generated. The inclination angle of the blade 13 gives the blood a relatively high tangential velocity and a relatively low pressure. The blade 13 of the axial flow pump generates restraint and centrifugal force through the tangential velocity, pushing the blood to move along the axial direction of the impeller 1, and the centrifugal force is relatively small.

[0057] In other embodiments, the blade 13 is in the form of a blade of a centrifugal pump. When the impeller 1 rotates, due to the action of centrifugal force and pressure, the blood is pushed towards the outside of the impeller 1, that is, towards the inner wall of the pump casing 21, forming a rotating flow. In this embodiment, the design of the blade 13 causes changes in the tangential and axial velocity components of the blood on the blade 13, that is, the curvature and rotation of the blade 13 generate a strong centrifugal force, forcing the blood to leave the impeller 1 and move to the inner wall of the pump casing 21, increasing the pressure and head.

[0058] In still other embodiments, the blade 13 is in the form of a blade of a mixed pump. It can be understood that the mixed pump combines the characteristics of an axial flow pump and a centrifugal pump. When the impeller 1 rotates, the axial and centrifugal forces act simultaneously. The blood passes through the blade 13 in the axial direction and also moves in the tangential direction due to the curved shape and angle of the blade 13. In this way, the blood can be affected by the centrifugal force and axial force brought by the blade 13.

[0059] In some embodiments, please refer to Figure 1 and Figure 2 , the cross-sectional shape of any part of the hub 12 in a plane perpendicular to the axial direction of the impeller 1 is circular.

[0060] It can be understood that the cross-sectional area shape of any part of the hub 12 in a plane perpendicular to the axial direction of the impeller 1 is circular, and the resistance to the flow of blood on the outer wall of the hub 12 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 hub 12. In addition, compared with other complex shapes, the circular cross-section is easier to achieve a uniform stress distribution under the same material and size conditions. This makes the hub 12 have better durability and compressive capacity, and improves the structural strength of the hub 12.

[0061] In some embodiments, please refer to Figure 3 and Figure 4 , one side of the hub 12 facing the connector 3 has a first end face 121a, and one side of the connector 3 facing the hub 12 has a second end face 3a. The first end face 121a and the second end face 3a face each other. When the first electromagnetic component 31 is connected to the power supply, a magnetic floating gap can be formed between the first end face 121a and the second end face 3a under the interaction of the first permanent magnetic component 11 and the first electromagnetic component 31.

[0062] It is understandable that the magnetic levitation gap means that when the first electromagnetic component 31 is powered on, the first end face 121a and the second end face 3a are arranged at an interval, that is, the first end face 121a and the second end face 3a do not contact each other.

[0063] In this embodiment, a magnetic levitation gap can be formed between the first end face 121a and the second end face 3a under the interaction of the first permanent magnet component 11 and the first electromagnetic component 31. The first end face 121a and the second end face 3a do not contact each other, avoiding the contact between the connector 3 and the impeller 1 during the working process. There is no mechanical wear between the connector 3 and the impeller 1, extending the service lives of the connector 3 and the impeller 1. The structure is simple and highly reliable, facilitating the continuous operation of the blood pump and reducing the frequency of reoperation; in addition, there is almost no noise generated by mechanical friction during the operation of the blood pump, providing a quieter and more comfortable surgical treatment environment.

[0064] The formation method of the magnetic levitation gap is not limited, and the method for maintaining the stable rotation of the impeller 1 under the magnetic levitation gap is not limited.

[0065] Exemplarily, when the first electromagnetic component 31 is just powered on and has not driven the impeller 1 to rotate, there is an interaction between the first electromagnetic component 31 and the first permanent magnet component 11, generating a magnetic moment. The magnetic moment causes the impeller 1 to receive a rotational driving force and a repulsive force along the axial direction that repels the connector 3. Under the action of the repulsive force, the impeller 1 moves in a direction away from the connector 3. In this way, a gap is generated between the first end face 121a and the second end face 3a, thereby forming a magnetic levitation gap; when the impeller 1 rotates, the impeller 1 drives the blood to flow from the liquid inlet 2b towards the first liquid outlet 2c and the second liquid outlet 2d. The impeller 1 is axially subjected to a force exerted by the blood towards the liquid inlet 2b side. By changing the control program to change relevant parameters such as the current of the power supply, etc., the repulsive force that repels the connector 3 along the axial direction of the impeller 1 is converted into an attractive force that attracts the connector 3, that is, an attractive force that moves towards the second end face 3a. This attractive force is opposite to the direction of the force exerted by the blood and can balance each other. In this way, the impeller 1 is axially force-balanced, and the impeller 1 can maintain stable rotation under the magnetic levitation gap.

[0066] In some embodiments, when the first electromagnetic component 31 is powered off, the first end face 121a and the second end face 3a contact each other under the interaction of the first permanent magnet component 11 and the first electromagnetic component 31.

[0067] Exemplarily, the first permanent magnet assembly 11 has a constant magnetic field, and the first electromagnetic assembly 31 has an iron core and a coil wound around the iron core. When an electric current passes through it, a magnetic field will be generated. When there is no current passing through the non-energized first electromagnetic assembly 31, no self-generated magnetic field is produced. When the first electromagnetic assembly 31 is close to the first permanent magnet assembly 11, the magnetic field generated by the first permanent magnet assembly 11 will generate an induced magnetic field on the iron core of the first electromagnetic assembly 31, making the iron core of the first electromagnetic assembly 31 also have magnetism and attracting each other with the first permanent magnet assembly 11.

[0068] In this way, the impeller 1 and the connector 3 can be in contact with each other when the first electromagnetic assembly 31 is powered off. When the blood pump is implanted into the body, the impeller 1 can be fixed to the connector 3, reducing the surgical risk caused by the detachment of the impeller 1.

[0069] It can be understood that in this embodiment, the first electromagnetic assembly 31 is disconnected from the power supply, that is, the first electromagnetic assembly 31 and the first permanent magnet assembly 11 cannot generate a magnetic torque. When the first electromagnetic assembly 31 is powered off, the impeller 1 is only affected by the attractive force that moves towards the first electromagnetic assembly 31 under the interaction between the first permanent magnet assembly 11 and the first electromagnetic assembly 31, that is, the acting force towards the second end face 3a. Under this attractive force, the first end face 121a and the second end face 3a are in contact with each other.

[0070] The following briefly describes the switching process of the acting force on the impeller 1 when the blood pump of this embodiment operates from power-off to power-on.

[0071] When the first electromagnetic assembly 31 is not powered on, no magnetic torque is generated between the first electromagnetic assembly 31 and the first permanent magnetic assembly 11. An attractive force is generated between the first permanent magnetic assembly 11 and the first electromagnetic assembly 31 along the axial direction, driving the impeller 1 to move towards the connector 3 until it contacts the connector 3, that is, the first end face 121a contacts the second end face 3a, facilitating the installation of the impeller 1 and the placement of the blood pump into the human body. When the blood pump is placed into the human body and the first electromagnetic assembly 31 is powered on, at this time, the impeller 1 has not started to rotate. Under the action of the magnetic torque generated between the first electromagnetic assembly 31 and the first permanent magnetic assembly 11, the impeller 1 is subjected to a rotational driving force and a repulsive force that moves away from the connector 3 along the axial direction. Thus, the first end face 121a moves away from the second end face 3a along the axial direction, creating a magnetic floating gap between them. The impeller 1 rotates under the action of the rotational driving force, driving the blood to flow from the liquid inlet 2b towards the first liquid outlet 2c and the second liquid outlet 2d. The blood exerts a force on the impeller 1 along the axial direction towards the side of the liquid inlet 2b. By changing parameters such as the current of the power supply, the repulsive force that causes the impeller 1 to move away from the connector 3 along the axial direction is transformed into an attractive force that moves towards the connector 3 along the axial direction. This attractive force is opposite to the direction of the force exerted by the blood and is balanced with each other. Thus, the impeller 1 is in axial force balance and can rotate stably under the magnetic floating gap.

[0072] In some examples, please refer to Figure 3 , the first end face 121a and the second end face 3a are parallel to each other along the axial direction, which can make the magnetic floating gap between them be set at an equal distance, facilitating the uniform distribution of the magnetic field and the control of the force balance of the impeller 1.

[0073] In some embodiments, please refer to Figure 3 , the hub 12 includes an end seat 121 and an impeller shaft 122. The end seat 121 is connected to the first axial end of the impeller shaft 122 close to the connector 3, and the blades 13 are arranged on the impeller shaft 122.

[0074] Axially along the impeller 1, the end seat 121 extends from the area where the first liquid outlet 2c is located to the area where the second liquid outlet 2d is located. The outer diameter of the end seat 121 at the end close to the connector 3 is larger than the outer diameter of the end seat 121 at the end close to the impeller shaft 122. For example, axially and in the direction away from the connector 3, the cross-sectional area of the end seat 121 in a plane perpendicular to the axial direction of the impeller 1 gradually decreases generally within the length range of the area where the second liquid outlet 2d is located. In this way, after part of the blood is discharged through the first liquid outlet 2c, the end seat 121 can guide the blood flowing axially along the outer wall of the end seat 121 to the second liquid outlet 2d, and the end seat 121 can gently change the flow direction of the blood; in addition, the end seat 121 extends from the area where the first liquid outlet 2c is located to the area where the second liquid outlet 2d is located, which can play a guiding effect and guide the blood to the second liquid outlet 2d, eliminating the need to set up additional guiding structures, improving the blood pumping efficiency of the blood pump, and reducing the design cost.

[0075] Exemplarily, please refer to Figure 3 , the circumferential outer surface of the end of the end seat 121 close to the connector 3 has a concave arc surface 121b, the concave arc surface 121b is recessed towards the inside of the end seat 121, and the concave arc surface 121b extends to the end face of the end seat 121 facing the connector 3, for guiding the blood to the second liquid outlet 2d. In this way, the blood flow direction can be better changed, and the damage to the blood can be reduced.

[0076] The installation position of the first permanent magnet assembly 11 is not limited.

[0077] In some embodiments, please refer to Figure 3 , the first permanent magnet assembly 11 is encapsulated in the end seat 121. In this way, the sealing of the first permanent magnet assembly 11 is realized, the service life of the first permanent magnet assembly 11 is extended, and in addition, the distance between the first permanent magnet assembly 11 and the first electromagnetic assembly 31 is shortened, improving the control accuracy of the first electromagnetic assembly 31.

[0078] The manner of realizing the suspension of the impeller 1 in the accommodation cavity 2a is not limited.

[0079] Exemplarily, in some embodiments, please refer to Figure 3 and Figure 4 , a first ferromagnetic unit 4 is arranged in the spacer ring body 22, and a second permanent magnet assembly 14 is arranged at the part of the hub 12 passing through the spacer ring body 22. Among them, during the rotation of the impeller 1, the first ferromagnetic unit 4 can form at least a radial acting force with the second permanent magnet assembly 14, so that the impeller 1 is suspended in the accommodation cavity 2a.

[0080] It can be understood that the first ferromagnetic unit 4 can form at least a radial acting force with the second permanent magnet assembly 14, which includes at least two cases.

[0081] In the first one, only radial force is formed between the first ferromagnetic unit 4 and the second permanent magnet assembly 14, for example, a radial repulsive force. In this way, the impeller 1 can be stably suspended in the accommodating cavity 2a under this force, achieving radial limitation, so that the impeller 1 can rotate stably.

[0082] The second type is that the force formed between the first ferromagnetic unit 4 and the second permanent magnet component 14 includes two components, one is a radial force, and the other is an axial force. The radial force can be a repulsive force, so that the impeller 1 can be stably suspended in the accommodating chamber 2a to achieve radial limitation. The axial force can be balanced with the attraction generated by the first electromagnetic component 31 and the first permanent magnet component 11 and the force exerted by the blood on the impeller 1. The impeller 1 can maintain a force balance in the axial direction, so that the impeller 1 can rotate stably.

[0083] It can be understood that when only radial force is formed between the first ferromagnetic unit 4 and the second permanent magnet component 14, the impeller 1 is limited in the radial direction. At this time, the impeller 1 is axially subjected to the attraction force of the first electromagnetic component 31 and the force exerted by the blood, and the two are balanced to achieve axial limitation of the impeller 1, so that the impeller 1 can rotate stably; when the action formed between the first ferromagnetic unit 4 and the second permanent magnet component 14 includes radial force and axial force, the radial force enables the impeller 1 to be radially limited, and the axial force can be toward the liquid inlet 2b side or toward the first liquid outlet 2c and the second liquid outlet 2d side. By controlling parameters such as the current of the power supply, this axial force and the attraction force of the first electromagnetic component 31 and the force exerted by the blood on the impeller 1 in the axial direction are balanced to achieve axial limitation of the impeller 1, so that the impeller 1 can rotate stably.

[0084] It should be noted that in the related art, the rotation of the impeller is not stable enough during operation, and the end is prone to radial shaking, which reduces its working efficiency. Mechanical bearings are often used to support the impeller and limit the movement of the impeller. However, the contact surfaces of the mechanical bearings that slide against each other will produce friction, wear and local temperature rise during operation, forming blood retention areas and thrombus attachment points around the bearings, increasing the risk of surgery.

[0085] In this embodiment, by providing the first ferromagnetic unit 4, radial limitation of the impeller 1 can be achieved, so that the impeller 1 can rotate stably, avoiding shaking of the impeller 1 during rotation, reducing the risk of thrombosis, and improving the working efficiency of the blood pump.

[0086] In some other embodiments, please refer to Figure 3 and Figure 4, the blood pump includes a second ferromagnetic unit 5, and a third permanent magnet assembly 15 is provided at one end of the hub 12 away from the connector 3. Among them, during the rotation of the impeller 1, the second ferromagnetic unit 5 can form at least a radial acting force with the third permanent magnet assembly 15, so that the impeller 1 is suspended in the accommodation cavity 2a.

[0087] It should be noted that the second ferromagnetic unit 5 can form at least a radial acting force with the third permanent magnet assembly 15, which includes at least two cases.

[0088] First, only a radial acting force is formed between the second ferromagnetic unit 5 and the third permanent magnet assembly 15. For example, a radial repulsive force. In this way, the impeller 1 can be stably suspended in the accommodation cavity 2a under this acting force, realizing radial limit, so that the impeller 1 rotates stably.

[0089] Second, the acting force formed between the second ferromagnetic unit 5 and the third permanent magnet assembly 15 includes two component forces, one radial acting force and one axial acting force. The radial acting force can be a repulsive force, so that the impeller 1 can be stably suspended in the accommodation cavity 2a, realizing radial limit. The axial acting force can balance the attractive force generated by the first electromagnetic assembly 31 and the first permanent magnet assembly 11 and the acting force exerted by the blood on the impeller 1. The impeller 1 can maintain force balance axially, so that the impeller 1 rotates stably.

[0090] It can be understood that when only a radial acting force is formed between the second ferromagnetic unit 5 and the third permanent magnet assembly 15, the impeller 1 realizes radial limit. At this time, the impeller 1 is axially subjected to the attractive force of the first electromagnetic assembly 31 and the acting force exerted by the blood, and the two balance each other to realize the axial limit of the impeller 1. In this way, the impeller 1 can rotate stably; when the acting force formed between the second ferromagnetic unit 5 and the third permanent magnet assembly 15 includes a radial acting force and an axial acting force, the radial acting force enables the impeller 1 to realize radial limit. The axial acting force can be directed towards the liquid inlet 2b side, or towards the first liquid outlet 2c and the second liquid outlet 2d side. By controlling parameters such as the current of the power supply, this axial acting force can be made to balance the attractive force of the first electromagnetic assembly 31 and the acting force exerted by the blood on the impeller 1 axially, realizing the axial limit of the impeller 1. In this way, the impeller 1 can rotate stably.

[0091] In this embodiment, the setting of the second ferromagnetic unit 5 can realize the radial limit of the impeller 1, enable the impeller 1 to rotate stably, avoid the impeller 1 from shaking during rotation, reduce the risk of thrombus formation, and improve the working efficiency of the blood pump.

[0092] It can be understood that the blood pump can be configured such that only the first ferromagnetic unit 4 and the second permanent magnet assembly 14 interact to achieve the suspension of the impeller 1 in the accommodation cavity 2a; the blood pump can also be configured such that only the second ferromagnetic unit 5 and the third permanent magnet assembly 15 interact to achieve the suspension of the impeller 1 in the accommodation cavity 2a; of course, the blood pump can also be configured with the first ferromagnetic unit 4, the second permanent magnet assembly 14, the second ferromagnetic unit 5, and the third permanent magnet assembly 15 at the same time. In this way, the first ferromagnetic unit 4 interacts with the second permanent magnet assembly 14, and the second ferromagnetic unit 5 interacts with the third permanent magnet assembly 15, resulting in a better radial limiting effect on the impeller 1 and further improving the stability of the rotation of the impeller 1.

[0093] The specific structures of the first ferromagnetic unit 4 and the second ferromagnetic unit 5 are not limited, and they can be permanent magnet structures or electromagnetic structures. The following describes the first ferromagnetic unit 4 as an example.

[0094] In some embodiments, the first ferromagnetic unit 4 includes a permanent magnet ring structure that surrounds the part of the hub 12 passing through the spacer ring body 22. In this way, the permanent magnet ring structure has a simple layout, can be quickly installed on the inner wall of the spacer ring body 22, and the permanent magnet ring structure can continuously form a radially repulsive force with the second permanent magnet assembly 14 to suspend the impeller 1 in the accommodation cavity 2a.

[0095] It should be noted that "ring-shaped" means that the overall contour of the permanent magnet ring structure is cylindrical.

[0096] The part where the permanent magnet ring structure surrounds the hub 12 passing through the spacer ring body 22 means that the permanent magnet ring structure surrounds the outer periphery of the part of the hub 12 passing through the spacer ring body 22, and a certain gap is formed between the inner wall of the permanent magnet ring structure and the outer wall of the hub 12.

[0097] In other embodiments, the first ferromagnetic unit 4 includes an electromagnetic ring structure that surrounds the part of the hub 12 passing through the spacer ring body 22, and the electromagnetic ring structure is used to form a radial force with the second permanent magnet assembly 14 when the power is turned on.

[0098] In this way, the electromagnetic ring structure can form a radial force, such as a repulsive force, with the second permanent magnet assembly 14 when the power is turned on to suspend the impeller 1 in the accommodation cavity 2a.

[0099] It can be understood that in this embodiment, relevant parameters can also be changed through a control program, so that a magnetic torque can be generated between the electromagnetic ring structure and the second permanent magnet component 14 when the power is turned on, so that the impeller 1 rotates under the combined action of the magnetic torques of the first electromagnetic component 31 and the first permanent magnet component 11, and the magnetic torques of the electromagnetic ring structure and the second permanent magnet component 14. In this way, the rotational driving forces generated by the two magnetic torques received by the impeller 1 can be superimposed on each other, so that the work done by the impeller 1 per unit time is greater, the kinetic energy and pressure potential energy of the blood are greater, and thus the blood delivery speed can be increased, the working efficiency of the blood pump can be improved, and the situation where only the first electromagnetic component 31 and the first permanent magnet component 11 consume a large amount of energy during driving can be improved, the heat dissipated when the blood pump works can be reduced, thereby solving the problem of serious overheating of the blood pump and reducing the surgical risk.

[0100] It can be understood that in the embodiment where the blood pump is provided with the first ferromagnetic unit 4 and the second ferromagnetic unit 5 at the same time, both the first ferromagnetic unit 4 and the second ferromagnetic unit 5 are set as electromagnetic ring structures, and then relevant parameters are changed through a control program, so that the impeller 1 can rotate under the combined action of the magnetic torques of the first electromagnetic component 31 and the first permanent magnet component 11, the magnetic torques of the first ferromagnetic unit 4 and the second permanent magnet component 14, and the magnetic torques of the second ferromagnetic unit 5 and the third permanent magnet component 15. At this time, the rotational driving forces generated by the three magnetic torques received by the impeller 1 can be superimposed on each other, thereby further improving the working efficiency of the blood pump.

[0101] The connection method of the electromagnetic ring structure to the external power supply is not limited.

[0102] Exemplarily, the electromagnetic ring structure is arranged in the spacer ring body 22. The pump housing 21 has a wiring channel that is not communicated with the accommodating cavity 2a, and the wire body a for connecting to the electromagnetic ring structure is led from the inside of the spacer ring body 22 to the wiring channel, passes through the wiring channel, and is led out from the inside of the connector 3.

[0103] Exemplarily, the wiring channel can be arranged in the internal space of the wall body of the pump housing 21.

[0104] It can be understood that the pump housing 21 has a wiring channel, and a region for the wire body a to pass through is also provided at the connection between the pump housing 21 and the connector 3, so that the wire body a is led out from the inside of the connector 3. For example, the connector 3 has a lead hole that penetrates the circumferential outer wall of the connector 3. One end of the wire body a for connecting to the electromagnetic ring structure is led out from the inside of the connector 3 through the lead hole, passes through the wiring channel to be connected to the electromagnetic ring structure, and the other end of the wire body a is used to connect to the power supply.

[0105] Exemplarily, one end of the connector 3 axially away from the pump housing 21 is connected to the lead-out member, and the other end of the wire body a is led out through the inside of the connector 3 into the lead-out member, and then led out of the body and connected to the power supply. In this way, the wire body a will not come into contact with the blood in the pump housing 21, and does not need to additionally occupy the space of the accommodation cavity 2a, will not affect the blood pumping efficiency, and improves the safety.

[0106] It can be understood that one end of the power cord connected to the first electromagnetic component 31 is located inside the connector 3 and connected to the first electromagnetic component 31, and the other end and the wire body a connected to the electromagnetic ring structure are led out from the inside of the connector 3 and connected to the lead-out member, and then connected to the power supply. In this way, the power supply can supply power to the first electromagnetic component 31 and the electromagnetic ring structure.

[0107] Exemplarily, the lead-out member can be a catheter.

[0108] The structure of the pump housing 21 is not limited.

[0109] In some embodiments, please refer to Figure 3 , the pump housing 21 includes a first housing section 211 and a second housing section 212. The first housing section 211 is connected to one end of the second housing section 212 close to the connector 3. The first housing section 211 and the spacer ring body 22 are connected to form a pre-assembled unit, and the pre-assembled unit and the second housing section 212 are of a split structure and are connected.

[0110] In this way, after the first housing section 211 and the spacer ring body 22 are connected to form a pre-assembled unit and then installed with the second housing section 212, it is convenient for the overall installation of the blood pump. The spacer ring body 22 does not need to be directly installed into the inside of the pump housing 21, improving the assembly efficiency.

[0111] Exemplarily, the first housing section 211 encloses an installation space for the spacer ring body 22, and the spacer ring body 22 is arranged in the installation space of the first housing section 211.

[0112] Exemplarily, the pre-assembled unit and the second housing section 212 are detachably connected. In this way, when the first ferromagnetic unit 4 arranged in the spacer ring body 22 fails, it is convenient to disassemble for repair or replacement.

[0113] In some embodiments, a part of the spacer ring body 22 and the first housing section 211 are of an integrally formed structure. In this way, the pre-assembled unit can be integrally produced, reducing the assembly process and lowering the production cost.

[0114] In some embodiments, please refer to Figure 1 and Figure 2, the first housing segment 211 includes at least two support members 2111 formed at one end of the first housing segment 211 close to the second liquid outlet 2d. The support members 2111 are connected to the connector 3, and the support members 2111 are arranged at intervals along the circumferential direction of the pump housing 21. The interval between two adjacent support members 2111 forms the first liquid outlet 2d.

[0115] Here, the support member 2111 can be in a strip structure.

[0116] Exemplarily, three support members 2111 are formed at one end of the pump housing 2 close to the second liquid outlet 2d to improve the connection strength between the support member 2111 and the connector 3.

[0117] The connection method between the support member 2111 and the connector 3 is not limited and can be a detachable connection or a non-detachable connection, etc.

[0118] In some embodiments, the support member 2111 is welded to the connector 3, and the connection is reliable.

[0119] In some other embodiments, a clamping groove is formed on the outer circumferential surface of the connector 3, and the support member 2111 is clamped with the clamping groove. In this way, it is convenient for the disassembly, assembly and cleaning of the support member 2111 and the connector 3.

[0120] The specific structure of the connector 3 is not limited.

[0121] In some embodiments, the connector 3 includes a cylindrical portion 32. The first electromagnetic assembly 31 is disposed in the cylindrical portion 32. The axial first end of the cylindrical portion 32 facing the impeller 1 has an opening 32a, and the opening 32a is sealed by potting. In this way, the manufacturing process of the connector 3 is simple, the first electromagnetic assembly 31 will not come into contact with blood, the service life of the first electromagnetic assembly 31 is extended, and the surgical safety is improved.

[0122] In some other embodiments, please refer to Figure 3 and Figure 4 , the connector 3 includes a cylindrical portion 32 and an end cap 33. The first electromagnetic assembly 31 is disposed in the cylindrical portion 32. The axial first end of the cylindrical portion 32 facing the impeller 1 has an opening 32a, and the end cap 33 is disposed at one end of the cylindrical portion 32 close to the impeller 1 and closes the opening 32a. In this way, by disposing the first electromagnetic assembly 31 in the cylindrical portion 32 and closing one end of the opening 32a, it can be effectively isolated and protected, the influence of blood on the first electromagnetic assembly 31 can be reduced, and its stability and service life can be improved; in addition, by providing the end cap 33 to seal the first electromagnetic assembly 31, the structural strength of the connector 3 is increased.

[0123] Exemplarily, the power cord for connecting to the first electromagnetic assembly 31 is led out from the axial second end of the cylindrical portion 32.

[0124] Exemplarily, the second axial end of the cylinder part 32 is connected to the lead-out part, and the power line for connecting to the first electromagnetic component 31 is led out through the cylinder part 32 into the lead-out part, and then led out of the body to be connected to the power supply. In this way, the contact between the power line and the blood is reduced, and the surgical safety is improved.

[0125] In some embodiments, please refer to Figure 4 , the impeller 1 includes a core shaft 16 disposed within the hub 12, and the first permanent magnet assembly 11, the second permanent magnet assembly 14, and the third permanent magnet assembly 15 are disposed on the core shaft 16 so that the first permanent magnet assembly 11, the second permanent magnet assembly 14, and the third permanent magnet assembly 15 are coaxially assembled.

[0126] Exemplarily, the first permanent magnet assembly 11, the second permanent magnet assembly 14, and the third permanent magnet assembly 15 can be respectively bonded to the core shaft 16, and the core shaft 16 is injection-molded inside the hub 12, reducing the assembly difficulty of the impeller 1, thereby improving the assembly efficiency of the blood pump.

[0127] 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, various changes and modifications can be made to the present application. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present application shall be included within the protection scope of the present application.

Claims

1. A blood pump, characterized in that, Comprising: An impeller; A pump housing assembly, including a pump housing and a spacer ring body. The pump housing has a receiving cavity, a liquid inlet, a first liquid outlet, and a second liquid outlet. The spacer ring body is disposed within the pump housing. The first liquid outlet and the second liquid outlet are located on the axially opposite sides of the spacer ring body. The impeller is disposed within the receiving cavity and passes through the spacer ring body. There is a channel for blood flow between the circumferential surface of the impeller and the radially inner surface of the spacer ring body; A connector, located on one axial side of the impeller, connected to one axial end of the pump housing. The first liquid outlet is located on the side wall corresponding to the region between the spacer ring body and the connector; One end of the impeller close to the connector has a first permanent magnet assembly, and the connector has a first electromagnetic assembly. 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 rotates under the action of the magnetic torque.

2. The blood pump according to claim 1, wherein The impeller includes a hub and blades. The blades are disposed on the hub. A first ferromagnetic unit is disposed within the spacer ring body. A second permanent magnet assembly is disposed at the part of the hub passing through the spacer ring body. Wherein, during the rotation of the impeller, the first ferromagnetic unit can form at least a radial acting force with the second permanent magnet assembly, so that the impeller is suspended in the receiving cavity.

3. The blood pump according to claim 1, characterized in that, The impeller includes a hub and blades. The blades are disposed on the hub. The blood pump includes a second ferromagnetic unit. A third permanent magnet assembly is disposed at one end of the hub away from the connector. Wherein, during the rotation of the impeller, the second ferromagnetic unit can form at least a radial acting force with the third permanent magnet assembly, so that the impeller is suspended in the receiving cavity.

4. The blood pump according to claim 1, wherein, The impeller includes a hub and blades. The blades are disposed on the hub. One side of the hub facing the connector has a first end face, and one side of the connector facing the hub has a second end face. The first end face and the second end face face each other. When the first electromagnetic assembly is powered on, a magnetic floating gap can be formed between the first end face and the second end face under the interaction of the first permanent magnet assembly and the first electromagnetic assembly.

5. The blood pump according to claim 4, characterized in that, When the first electromagnetic assembly is powered off, the first end face and the second end face are in contact with each other under the interaction of the first permanent magnet assembly and the first electromagnetic assembly.

6. The blood pump according to claim 1, wherein The pump housing includes a first housing section and a second housing section. The first housing section is connected to one end of the second housing section close to the connector. The first housing section and the spacer ring body are connected to form a pre-assembled whole. The pre-assembled whole and the second housing section are of a split structure and are connected.

7. The blood pump according to claim 6, characterized in that, A part of the spacer ring body is an integrally formed structure with the first housing section.

8. The blood pump according to claim 1, characterized in that, The impeller includes a hub and blades. The blades are arranged on the hub. The hub includes an end seat and an impeller shaft. The end seat is connected to the axial first end of the impeller shaft close to the connector. The blades are arranged on the circumferential side of the impeller shaft. Along the axial direction of the impeller, the end seat extends from the area where the first liquid outlet is located to the area where the second liquid outlet is located. The outer diameter of the end seat at the end close to the connector is greater than the outer diameter of the end seat at the end close to the impeller shaft.

9. The blood pump according to claim 8, wherein The first permanent magnet assembly is encapsulated in the end seat.

10. The blood pump according to claim 8, wherein, The outer circumferential surface of the end seat at the end close to the connector has a concave arc surface. The concave arc surface is recessed towards the inside of the end seat. The concave arc surface extends to the end face of the end seat facing the connector, and is used to guide blood to the second liquid outlet.

11. The blood pump according to claim 1, characterized in that The impeller includes a hub and blades. The blades are arranged on the hub. The cross-sectional shape of the hub at any part in the plane perpendicular to the axial direction of the impeller is circular.

12. The blood pump according to claim 1, wherein The connector includes a cylindrical part and an end cover. The first electromagnetic assembly is arranged in the cylindrical part. The cylindrical part has an opening towards the axial first end of the impeller. The end cover is arranged at the end of the cylindrical part close to the impeller and closes the opening. The wire body for connecting to the first electromagnetic assembly is led out from the axial second end of the cylindrical part.

13. The blood pump according to claim 2, characterized in that, The first ferromagnetic unit includes an electromagnetic ring structure. The electromagnetic ring structure surrounds the part of the hub passing through the spacer ring body, and is used to form a radial acting force with the second permanent magnet assembly when the power is turned on.

14. The blood pump according to claim 13, characterized in that, The pump housing has a wiring channel that is not communicated with the accommodating cavity. The wire body for connecting to the electromagnetic ring structure is led out from the inside of the connector and passes through the wiring channel.

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