Bearings for blood pumps, blood pumps, and ventricular assist circulation devices

Abstract

The present invention provides a bearing for a blood pump, a blood pump, and a ventricular assist circulation device. The blood pump bearing comprises: a bearing body and an additional component; the bearing body is configured to connect to an output shaft of a driver and follow the output shaft in axial movement; the bearing body has a first limiting portion, and the additional component has a second limiting portion, the first limiting portion and the second limiting portion cooperating to limit the axial displacement of the bearing body. This arrangement enables the additional component to axially limit the bearing body, providing the bearing with an axial limiting function, thereby enhancing the bearing's axial load capacity and wear resistance, thereby ensuring that the output shaft connected to the bearing can operate safely, reliably, and stably at high speed.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to a bearing for a blood pump, a blood pump, and a ventricular assist circulation device. Background Art

[0002] Cardiovascular disease is currently one of the leading causes of death, with lesions in the coronary arteries being the most serious cause of death. Coronary artery lesions can cause chest pain, myocardial ischemia, and sudden cardiac death. Coronary artery lesions typically form plaques within the coronary arteries, a major factor seriously impacting human health. Currently, treatment for these plaques requires percutaneous coronary intervention (PCI). During high-risk PCI procedures, the patient's heart is fragile and its blood supply capacity is insufficient, posing a high risk for surgery. To address this, a percutaneous blood pump is needed to power the heart. Its main operating principle is to pump blood through the aorta, across the aortic valve, with the inlet window positioned in the left ventricle and the outlet window in the aorta. A motor-driven impeller rotates, pumping blood from the left ventricle into the aorta, reducing cardiac workload and maintaining blood circulation, thus ensuring the successful completion of high-risk PCI procedures.

[0003] The main structure of a percutaneous interventional blood pump includes a drive motor and an impeller. The impeller is mounted on the output shaft of the drive motor. The rotation of the motor drives the impeller blades to rotate. Currently used percutaneous interventional blood pumps have the following disadvantages:

[0004] 1) The drive motor's shaft is supported in the motor housing by dual rolling bearings. Since the blood pump's outer diameter is typically 4-6 mm, its small size and complex structure make assembly very difficult. Furthermore, during the machining of the motor housing and bearing housing, the coaxiality of the two bearing housings must be ensured, which requires higher precision and assembly requirements, resulting in high production and processing costs.

[0005] 2) Due to the small size of percutaneous interventional blood pumps, the speed is usually as high as 30,000 rpm or more to ensure the blood flow rate. However, rolling bearings have poor wear resistance at high speeds and can only work for 7-14 days at most, which makes it impossible to achieve continuous rotation for a long time.

[0006] 3) The impeller rotates at high speed, pumping blood out of the outlet window. This pumped blood generates a large reaction force on the impeller. The axial component of this reaction force acts on the rolling bearings, which primarily bear radial loads and cannot withstand large axial loads. This dual-roller bearing structure, when operating at high speeds and subjected to continuous axial loads, can lead to severe bearing wear, increased noise, severe heat generation, and a reduced service life.

[0007] Therefore, developing a bearing with an axial limit function to enhance the axial load capacity of the bearing, improve the wear resistance of the bearing, and thus ensure the high-speed, safe, reliable and stable operation of the output shaft connected to the bearing has become an urgent problem to be solved by bearing or pump body manufacturers. Summary of the Invention

[0008] The purpose of the present invention is to provide a bearing for a blood pump, a blood pump and a ventricular assist circulation device to solve the problems that existing bearings cannot achieve axial limiting function, have weak axial load capacity and low bearing wear resistance.

[0009] To solve the above technical problems, the present invention provides a bearing for a blood pump, comprising: a bearing body and an additional component; the bearing body is used to be connected to the output shaft of a driving member and follow the output shaft in axial movement along the output shaft; the bearing body has a first limiting portion, and the additional component has a second limiting portion, and the first limiting portion and the second limiting portion cooperate to limit the axial displacement of the bearing body.

[0010] Optionally, the additional component is used to be fixed on a pump housing, the first limiting portion is arranged on the outer surface of the bearing body along the circumference of the bearing body, and the second limiting portion is arranged to match the first limiting portion.

[0011] Optionally, one of the first limiting portion and the second limiting portion includes a groove, and the other of the first limiting portion and the second limiting portion includes a protrusion.

[0012] Optionally, there is a gap between the first limiting portion and the second limiting portion for injection of perfusion fluid to form a sliding liquid film.

[0013] Optionally, the longitudinal section of the groove is an annular structure, and the protrusions are continuous protrusion structures or intermittent protrusion structures arranged toward the groove.

[0014] Optionally, the cross section of the groove is a U-groove structure, and / or the cross section of the protrusion is a U-groove structure.

[0015] Optionally, the cross-section of the groove is a semi-U-groove shape, and the semi-U-groove shape has a first end and a second end, the first end is close to the proximal end, and the second end is close to the distal end; the first limiting portion includes the groove, and the protrusion abuts against the first end; or, the second limiting portion includes the groove, and the protrusion abuts against the second end.

[0016] Optionally, the bearing body has an end face, which is used to face a distal end, and the first limiting portion is arranged on the end face; the first limiting portion includes at least one inclined surface and an axial through groove, the inclined surface is inclined downward toward the rotation direction of the bearing body, and the axial through groove is arranged on the bearing through hole of the bearing body along the axial direction of the bearing, for allowing the perfusion fluid to flow from the proximal end to the distal end; the second limiting portion includes a baffle, which faces the inclined surface and is spaced apart from the inclined surface.

[0017] Optionally, the first limiting portion further includes at least two of the inclined surfaces and a drainage groove, wherein the drainage groove is arranged between the two inclined surfaces, and the drainage groove is communicated with the axial through groove.

[0018] Optionally, the inclined surfaces are arranged in a fan-blade shape on the end surface.

[0019] Optionally, the bearing for the blood pump is made of ceramic material.

[0020] In order to solve the above technical problems, the present invention also provides a blood pump, comprising: a driving member, a pump housing and a bearing for a blood pump as described above; the driving member includes an output shaft; the pump housing is arranged outside the driving member, and the pump housing has a first chamber and a second chamber; the bearing body of the bearing for the blood pump is arranged on the output shaft, the additional component of the bearing for the blood pump is arranged on the pump housing, and the bearing for the blood pump is arranged between the first chamber and the second chamber.

[0021] To solve the above technical problems, the present invention further provides a ventricular assist circulation device, comprising: the blood pump as described above and a controller; the controller is connected to the blood pump and is used to control the operation of the blood pump.

[0022] The present invention provides a bearing for a blood pump, a blood pump, and a ventricular assist circulation device. The bearing for the blood pump comprises: a bearing body and an additional component. The bearing body is configured to connect to an output shaft of a driver and follow the output shaft in axial movement. The bearing body has a first limiting portion, and the additional component has a second limiting portion, wherein the first limiting portion and the second limiting portion cooperate to limit the axial displacement of the bearing body. This configuration enables the additional component to axially limit the bearing body, providing the bearing with an axial limiting function, thereby enhancing the bearing's axial load capacity and wear resistance, thereby ensuring that the output shaft connected to the bearing can operate safely, reliably, and stably at high speed. BRIEF DESCRIPTION OF THE DRAWINGS

[0023] Those skilled in the art will appreciate that the accompanying drawings are provided for a better understanding of the present invention and do not constitute any limitation on the scope of the present invention.

[0024] Figure 1 A schematic diagram of a blood pump.

[0025] Figure 2 This is a schematic diagram of a bearing for a blood pump according to a first embodiment of the present invention.

[0026] Figure 3 This is a cross-sectional view of the connection between the bearing and the output shaft for a blood pump according to the first embodiment of the present invention.

[0027] Figure 4 Schematic diagram of a blood pump according to embodiment 1 of the present invention.

[0028] Figure 5 This is a schematic diagram of a bearing for a blood pump according to a second embodiment of the present invention.

[0029] Figure 6 This is a cross-sectional view of a bearing for a blood pump according to a second embodiment of the present invention.

[0030] Figure 7 This is a three-dimensional diagram of a bearing for a blood pump according to a third embodiment of the present invention.

[0031] Figure 8 This is a schematic diagram of a bearing for a blood pump according to a third embodiment of the present invention.

[0032] Figure 9 This is a schematic diagram of a limiting portion of a bearing for a blood pump according to a third embodiment of the present invention.

[0033] Figure 10 This is a schematic diagram of the connection between a bearing and an output shaft for a blood pump according to a third embodiment of the present invention.

[0034] Figure 11 This is a schematic diagram of a blood pump according to embodiment 3 of the present invention.

[0035] In the attached figure:

[0036] F-reaction force, V-hollow arrow;

[0037] 10 - blood pump, 11 - pump housing, 11a - blood inlet port, 11b - outlet window, 12 - driving element, 12a - motor stator core, 12b - motor coil winding, 12c - rotor magnet, 12d - output shaft, 12e - impeller, 13 - bearings, 13a - first bearing, 13b - second bearing;

[0038] A-proximal end, B-distal end, C-first end, D-second end, V1-hollow arrow, V2-flow direction of perfusion fluid, V3-rotation direction of bearing body, F1-axial component of hydraulic pressure, a-high side, b-low side;

[0039] 100-Bearings for blood pumps,

[0040] 110 - bearing body, 111 - bearing through hole, 112 - end face, 113 - first limiting portion, 1131 - groove, 1132 - inclined surface, 1133 - drain groove, 1134 - axial through groove;

[0041] 120 - additional component, 121 - second limiting portion, 1211 - protrusion, 1212 - baffle, 122 - gap;

[0042] 200-blood pump, 210-driving element, 211-output shaft, 212-impeller;

[0043] 220 - pump housing, 221 - first chamber, 222 - second chamber, 223 - blood inlet end, 224 - outlet window. DETAILED DESCRIPTION

[0044] To make the objects, advantages, and features of the present invention more clearly apparent, the present invention is further described below in conjunction with the accompanying drawings and specific embodiments. It should be noted that the drawings are all in a very simplified form and are not drawn to scale. They are only used to conveniently and clearly assist in illustrating the purposes of the embodiments of the present invention. In addition, the structures shown in the drawings are often part of the actual structure. In particular, different drawings may need to illustrate different focuses and sometimes use different scales.

[0045] As used in this specification, the singular forms "a", "an", and "the" include plural objects, and the term "or" is generally used in a sense including "and / or" unless the content clearly indicates otherwise. In addition, in the following description, "distal end" and "proximal end" are used for ease of description. The "proximal end" is the side close to the pump body motor; the "distal end" is the side close to the pump body blades. In addition, in the description below, a large number of specific details are given to provide a more thorough understanding of the present invention. However, it is obvious to those skilled in the art that the present invention can be implemented without one or more of these details. In other examples, in order to avoid confusion with the present invention, some technical features known in the art are not described.

[0046] Please refer to Figure 1 As shown, Figure 1The figure is a schematic diagram of a blood pump. Before introducing the embodiments of the present invention, the blood pump 10 and its main operating principles are described to facilitate understanding of the bearing, blood pump, and ventricular assist circulatory device provided by the present invention. The blood pump 10 primarily comprises a pump housing 11, a driver 12, and a bearing 13. The driving element of the driver 12 is, for example, a motor. The driver 12 includes a motor stator core 12a, motor coil windings 12b, a rotor magnet 12c, an output shaft 12d, and an impeller 12e. The pump housing 11 is, for example, a cylindrical tube and is disposed externally of the driver 12. The pump housing 11 has a blood inlet port 11a and an outlet window 11b. The blood inlet port 11a is located at the distal end of the blood pump 10, and at least one outlet window 11b is disposed circumferentially around the blood pump 10. The bearing 13 comprises a first bearing 13a and a second bearing 13b, forming a support system that supports the high-speed rotation of the rotor magnet 12c. The outlet window 11b and the impeller 12e constitute a fluid component. The blood pump 10 is connected to a cable conduit at the proximal end and to a controller outside the body. The controller controls the driving member 12, thereby controlling the blood pumping operation of the blood pump 10. The main working principle of the blood pump 10 is as follows: the driving member 12 rotates at high speed under the control of the external controller, and the impeller 12e pumps the blood entering from the blood inlet port 11a out of the outlet window 11b. Figure 1 As shown, the direction of blood flow in the blood pump 10 is shown by the hollow arrow V. When the impeller 12e rotates at high speed to pump blood out from the outlet window 11b, the impeller 12e will be subjected to a reaction force F exerted by the blood. The direction of the reaction force F is shown as follows: Figure 1 In the direction of the arrow shown, from the proximal end to the distal end, the reaction force F is transmitted to the bearing 13 through the impeller 12e and the output shaft 12d, and is borne by the first bearing 13a and the second bearing 13b. In practice, for conventional motors, the first bearing 13a and the second bearing 13b typically employ radial ball bearings. While radial ball bearings can withstand large radial loads, they cannot sustain axial loads. When the blood pump 10 is in operation, the bearing 13 is continuously impacted by the reaction force F, accelerating wear of the bearing 13, generating noise and continuous heat generation, reducing the service life of the bearing 13, and reducing the reliability of the blood pump 10 and the blood pump system. Furthermore, during assembly, the two radial ball bearings must maintain coaxiality and other assembly accuracies, which requires high precision and presents assembly difficulties.

[0047] An embodiment of the present invention provides a bearing, a blood pump, and a ventricular assist circulation device, wherein the bearing comprises: a bearing body and an additional component; the bearing body is configured to connect to an output shaft of a driver and follow the output shaft in axial movement; the bearing body has a first limiting portion, and the additional component has a second limiting portion, wherein the first limiting portion and the second limiting portion cooperate to limit the axial displacement of the bearing body. This configuration enables the additional component to axially limit the bearing body, providing the bearing with an axial limiting function, thereby enhancing the bearing's axial load capacity and improving its wear resistance, thereby ensuring that the output shaft connected to the bearing can operate safely, reliably, and stably at high speed. Furthermore, the bearing is disposed on the output shaft of the blood pump, enabling the output shaft to be provided with both an axially limiting bearing and a radially limiting bearing, thereby reducing the difficulty of assembling the entire rotating shaft. Furthermore, the axially limiting bearing prevents wear of the bearing due to axial reaction force, thereby reducing heat generation in the blood pump, improving its operating efficiency, and reducing hemolysis. Furthermore, the first limiting portion and the second limiting portion are spaced apart so that the perfusion fluid generates axial hydraulic pressure between the first limiting portion and the second limiting portion, which can offset the axial reaction force of the output shaft and ensure that the output shaft does not move.

[0048] The following description is given with reference to the accompanying drawings.

[0049] [Example 1]

[0050] Please refer to Figures 2 to 4 ,in, Figure 2 This is a schematic diagram of a bearing for a blood pump according to a first embodiment of the present invention; Figure 3 This is a cross-sectional view of the connection between the bearing and the output shaft of the blood pump according to the first embodiment of the present invention; Figure 4 Schematic diagram of a blood pump according to embodiment 1 of the present invention.

[0051] The bearing 100 for a blood pump of this embodiment is used to limit the axial displacement of an output shaft 211 of a driving member 210. Furthermore, the bearing 100 for a blood pump can be applied to a blood pump 200, and the bearing 100 for a blood pump is connected to the output shaft 211 of the driving member 210. In order to facilitate understanding of the scheme of the bearing 100 for a blood pump, this article first introduces the blood pump 200. Figure 4As shown, the blood pump 200 includes, for example, a drive member 210, a pump housing 220, and a bearing 100 for the blood pump. The drive member 210 includes a motor (not shown), an output shaft 211, and an impeller 212, which are connected in sequence. The pump housing 220 is disposed outside the drive member 210. The pump housing 220 preferably has a first chamber 221, a second chamber 222, a blood inlet port 223, and an outlet window 224. The motor is housed in the first chamber 221, the impeller 212 is housed in the second chamber 222, the output shaft 211 passes through the first and second chambers 221, 222, and the blood inlet port 223 and outlet window 224 are used for pumping blood in and out, respectively. The bearing 100 for the blood pump is located between the first and second chambers 221, 222. The structures and principles of other components of the blood pump 200 can be found in the above description or in the prior art and will not be further described here. It should be understood that the bearing 100 for the blood pump is not limited to being disposed within the blood pump 200, but may also be disposed within other pump components. The bearing 100 for the blood pump may be connected to the output shaft of a drive member of the pump component. The bearing 100 for the blood pump will be described in detail below.

[0052] like Figure 2 As shown, the bearing 100 for a blood pump includes a bearing body 110 and an additional component 120 .

[0053] like Figure 3 As shown, the bearing body 110 is configured to be connected to the output shaft 211 of a driving member 210, such as the output shaft 211 of the blood pump 200, and to follow the output shaft 211 in axial movement. The bearing body 110 is, for example, a rotating body and preferably has a bearing through-hole 111 extending through the output shaft 211. The output shaft 211 serves as the power output shaft of the blood pump 200, transmitting the rotation of the motor rotor. The bearing body 110 is preferably fixedly connected to the output shaft 211 and can also rotate synchronously with the output shaft 211.

[0054] like Figure 3 and Figure 4 As shown, the bearing body 110 has a first limiting portion 113, and the additional component 120 has a second limiting portion 121. The first limiting portion 113 and the second limiting portion 121 cooperate to limit the axial displacement of the bearing body 110. The bearing body 110 is, for example, disposed on the output shaft 211. In this embodiment, as Figure 2 and Figure 3As shown, the first limiting portion 113 is preferably provided on the outer surface of the bearing body 110 along the circumference of the bearing body 110. The additional component 120 is used to be fixed on a pump housing. Preferably, the additional component 120 is used to be fixed on the pump housing of a blood pump 200. Those skilled in the art know that when the bearing body 110 rotates, the pump housing does not rotate with the bearing body 110, that is, when the bearing body 110 rotates, the bearing body 110 remains stationary. When the bearing body 110 undergoes axial displacement, the additional component 120 fixed on the pump housing 220 does not undergo axial displacement. Therefore, the second limiting portion 121 on the additional component 120 is provided to match the first limiting portion 113 and is used to limit the axial displacement of the first limiting portion 113. Specifically, the position of the second limiting portion 121 can match the circumferential position of the first limiting portion 113 that has not started to move on the bearing body 110. When the bearing body 110 undergoes circumferential rotation and axial displacement, the first limiting portion 113 also undergoes circumferential rotation and axial displacement. The first limiting portion 113 undergoes axial displacement, while the second limiting portion 121 does not move axially, thereby limiting the axial movement of the first limiting portion 113, thereby achieving axial limitation of the bearing body 110. Preferably, the first limiting portion 113 may include one of a groove 1131 and a protrusion 1211, and the second limiting portion 121 includes the other of the groove 1131 and the protrusion 1211, thereby enabling the first limiting portion 113 and the second limiting portion 121 to be locked in place via a concave-convex structure. Furthermore, the first limiting portion 113 preferably includes a groove 1131, and the second limiting portion 121 preferably includes a protrusion 1211. The groove 1131 is provided on the outer surface of the bearing body 110 , and the protrusion 1211 is preferably provided on the pump housing 220 , so that the groove 1131 on the bearing body 110 is limited by the protrusion 1211 .During the movement of the output shaft 211, the impeller 212 rotates with the output shaft 211, pumping blood in through the blood inlet end 223 and out through the outlet window 224. During the blood pumping process, the output shaft 211 displaces due to the reaction force of the blood, and the bearing body 110 also axially displaces along with the output shaft 211. The provision of the additional component 120 allows the additional component 120 to limit the axial displacement of the bearing body 110, and thereby the axial displacement of the bearing body 110 and the output shaft 211, thereby enhancing the axial load capacity of the bearing. Furthermore, the improved axial load capacity of the blood pump bearing 100 prevents continuous impact from the reaction force of blood, reduces wear on the blood pump bearing 100, and prevents noise and continuous heat generation from the blood pump bearing 100. This ensures the safety, reliability, and stability of the high-speed operation of the output shaft 211 connected to the blood pump bearing 100, thereby enabling long-term continuous rotation of the blood pump 200 and increasing the service life of the blood pump 200. At the same time, the bearing 100 for the blood pump with an axial limiting function cooperates with the bearing with a radial limiting function to jointly limit the axial and radial displacement of the output shaft 211 or the motor rotor connected to the output shaft. During the assembly process of the two bearings, the coaxial accuracy requirements are low, thereby reducing the assembly difficulty of the bearing 100 for the blood pump and reducing the production and processing costs of the blood pump 200. In other embodiments, the first limiting portion 113 can also be a protrusion, and the second limiting portion 121 can also be a groove. Of course, the arrangement of the first limiting portion 113 and the second limiting portion 121 is not limited to the arrangement of a concave-convex structure. For example, the interaction of the magnetic force of a magnet can also be used to limit the axial displacement of the first limiting portion 113, or other structures that can limit the axial displacement of the bearing body 110.

[0055] More preferably, Figure 3 and Figure 4 As shown, the longitudinal section of the groove 1131 is an annular structure. For example, the first limiting portion 113 includes a groove 1131, and the groove 1131 is arranged in the circumference of the bearing body 110, so that when the bearing body 10 rotates, the groove 1131 of the annular structure can be limited in axial displacement by the protrusion 1211. The protrusion 1211 is a continuous protrusion structure arranged toward the groove 1131, or a spaced protrusion structure. For example, the second limiting portion 121 includes the protrusion 1211, and the protrusion 1211 is a circular protrusion. The circular protrusion is tightly matched with the pump housing 220 and remains relatively fixed. The protrusion 1211 is arranged toward the groove 1131 on the bearing body 110. In another embodiment, the protrusion 1211 can be an intermittent annular structure, that is, the protrusion 1211 is arranged at intervals in the circular space.

[0056] Furthermore, Figure 3 As shown, to ensure that the bearing 100 for a blood pump has good processing performance and good rotation performance, the cross-section of the groove 1131 and / or the protrusion 1211 is a U-groove structure. In other embodiments, the groove and the protrusion can also have other shapes, for example, the cross-section of the groove and the protrusion is square or triangular.

[0057] Furthermore, since the motor of the blood pump 200 is not sealed, and the bearing 100 for the blood pump is located between the first chamber 221 and the second chamber 222, in order to prevent the blood in the first chamber 221 where the impeller 212 is located from entering the second chamber 222 where the motor is located, and to prevent dry friction between the first limiting portion 113 and the second limiting portion 121, a gap 122 is provided between the first limiting portion 113 and the second limiting portion 121. When the blood pump 200 is working, the operator continuously injects a perfusion liquid from the proximal end A to the distal end B of the blood pump 200, as shown in FIG. Figure 4 The perfusate shown flows in direction V2. The perfusate is injected into the gap 122 between the first limiting portion 113 and the second limiting portion 121 to form a sliding liquid film. When the output end 211 is subjected to the axial reaction force of blood, the output shaft 211 and the rotating shaft body 110 are axially limited by the additional component 120. This further prevents wear of the blood pump bearing 100 under the axial reaction force, reduces heat generation in the blood pump 200, improves the operating efficiency of the blood pump 200, and reduces hemolysis, thereby ensuring the safety, reliability, and stability of the blood pump 200 during high-speed operation. It should be understood that the perfusate should be a blood-safe solution, such as saline or glucose solution. Furthermore, the perfusate should have sufficient perfusion pressure, for example, greater than the blood pressure at the impeller 212, to ensure that blood cannot enter the second chamber 222. Furthermore, the perfusate can dissipate heat generated by the motor, ensuring the safe operation of the blood pump 200.

[0058] Furthermore, the bearing 100 for the blood pump is made of ceramic material, specifically, ceramic powder is molded and sintered, thereby improving the wear resistance of the bearing 100 for the blood pump.

[0059] This embodiment provides a blood pump 200, comprising a drive member, a pump housing, and the aforementioned bearing 100 for a blood pump; the drive member 210 includes an output shaft 211; the pump housing 220 is disposed on the exterior of the drive member 210; the bearing body 110 of the bearing 100 for a blood pump is disposed on the output shaft 211, the first limiting portion 113 of the bearing 100 for a blood pump is disposed on the bearing body 110, and the second limiting portion 121 of the bearing 100 for a blood pump is disposed on the pump housing 220. Specifically, the blood pump 100 may be an invasive blood pump. The blood pump 200 possesses the beneficial effects of the bearing 100 for a blood pump, which will not be further described herein.

[0060] This embodiment also provides a ventricular assist circulatory device, including the blood pump 200 described above. The ventricular assist circulatory device provides the beneficial effects of the blood pump 200, which will not be described in detail here. The structures and principles of the other components of the ventricular assist circulatory device can be referenced in the prior art and will not be further described here.

[0061] [Example 2]

[0062] Please refer to Figures 5 and 6 ,in, Figure 5 is a schematic diagram of a bearing according to a second embodiment of the present invention; Figure 6 This is a cross-sectional view of a bearing according to a second embodiment of the present invention.

[0063] The same parts of the bearing in the second embodiment as those in the first embodiment will not be described again, and only the differences will be described below.

[0064] During operation of the blood pump 200, the operator continuously injects perfusion fluid into the first chamber 221. However, due to the continuous flushing of the perfusion fluid and the reaction force of the blood when the impeller 212 rotates, the driving member 210 is always subjected to an axial force directed from the proximal end A to the distal end B, i.e., a force that drags the impeller 212 toward the distal end B. Therefore, the U-groove in the first embodiment only limits the axial displacement of the bearing 100 used for the blood pump from the proximal end A to the distal end B when the blood pump 200 is in operation. Figures 5 and 6As shown, in order to facilitate the processing of the bearing body 110, simplify the structure of the bearing body 110 and reduce the processing cost of the bearing body 110, in the second embodiment, the cross-section of the groove 1131 is a semi-U-groove shape. The semi-U-groove has a first end C and a second end D, the first end C is used to be close to the proximal end A, and the second end D is used to be away from the proximal end A, that is, the second end D is used to be close to a distal end B. Specifically, the "proximal end" is the side close to the motor; the "distal end" is the side close to the impeller 212. Preferably, the first limiting portion 113 includes a semi-U-groove groove, and the second limiting portion 121 includes a protrusion 1211. The protrusion 1211 is preferably a U-groove shape. When the bearing body 110 moves toward the distal end B, the protrusion 1211 can abut against the first end C, thereby limiting the movement of the bearing body 110 toward the distal end B. In another preferred embodiment, the second limiting portion 121 includes a groove with a semi-U-groove structure and is arranged on a pump housing 220. The first limiting portion 113 includes a protrusion and is arranged on the bearing body 110. When the bearing body 110 moves toward the distal end B, the protrusion on the bearing body 110 can abut against the second end D of the groove, thereby limiting the movement of the bearing body 110 toward the distal end B.

[0065] It should be understood that the limiting principle between the groove 1131 and the protrusion 1211 is the same as in the first embodiment, employing a physical structure to axially limit the bearing body 110. A gap is provided between the groove 1131 and the protrusion 1211 for injecting the perfusion fluid to form a sliding fluid film. The protrusions 1211 can be a continuous annular structure or a spaced annular arrangement. The cross-section of the protrusion 1211 can also be configured according to actual circumstances and is not limited to a U-groove shape, etc., and will not be further described in this second embodiment.

[0066] [Example 3]

[0067] Please refer to Figures 7 to 11 ,in, Figure 7 This is a three-dimensional diagram of a bearing for a blood pump according to a third embodiment of the present invention; Figure 8 This is a schematic diagram of a bearing for a blood pump according to a third embodiment of the present invention; Figure 9 This is a schematic diagram of a limiting portion of a bearing for a blood pump according to a third embodiment of the present invention; Figure 10 This is a schematic diagram of the connection between the bearing and the output shaft of a blood pump according to the third embodiment of the present invention; Figure 11 This is a schematic diagram of a blood pump according to embodiment 3 of the present invention.

[0068] The same parts of the bearing for the blood pump in the third embodiment as those in the first and second embodiments will not be described again, and only the differences will be described below.

[0069] like Figures 7 to 11As shown, the bearing body 110 has an end face 112, which is used to face a distal end. The first limiting portion 113 is provided on the end face 112. The first limiting portion 113 includes at least one inclined surface 1132 and an axial through groove 1134. The inclined surface 1132 is inclined downward toward the rotation direction V3 of the bearing body. Specifically, as shown in FIG. Figure 9 Taking the schematic direction shown in as an example, the rotation direction V3 of the bearing body is toward Figure 9 The inclined surface 1132 is tilted downward toward the rotation direction V3 of the bearing body due to the upward movement. This causes the inclined surface 1132 to form a high side a and a low side b. The second limiting portion 121 includes a baffle 1212. The baffle 1212 is, for example, a plate-shaped structure. The baffle 1212 is disposed opposite to the inclined surface 1132 and spaced apart from the inclined surface 1132, thereby forming a gap 122 between the first limiting portion 113 and the second limiting portion 121. In this embodiment, the downward tilt of the inclined surface 1132 toward the rotation direction V3 of the bearing body means that the axial distance of the low side b of the inclined surface 1132 relative to the baffle 1212 is farther than the axial distance of the high side a relative to the baffle. Therefore, the inclined surface 1132 presents a downward tilt toward the rotation direction V3 of the bearing body. When the bearing 100 for the blood pump rotates, the inclined surface 1132 is inclined downward along the rotation direction V3 of the bearing body, as shown in FIG. Figure 9 The perfusion fluid shown flows toward V2, and the perfusion fluid flows along the inclined surface 1132 from the low side b to the high side a, as shown in FIG. Figure 10 and Figure 11As shown, during flow, the perfusate is squeezed in the gap 122, generating an axial component of hydraulic pressure F1. At this point, the axial component of hydraulic pressure F1 at the inclined surface 1132, which faces the distal end B, is directed toward the proximal end A. This axial component of hydraulic pressure F1 counteracts the reaction force of the blood, thereby achieving axial restraint of the first stopper 113 and, consequently, the bearing body 110. Furthermore, in this embodiment, the axial component of hydraulic pressure F1 is equal to the sum of the reaction force of the blood and the impact force of the perfusate on the bearing body 110, thereby maintaining the bearing body 110 in a balanced state. The bearing 100 for a blood pump is disposed on an output shaft 211, and the baffle 1212 is similarly disposed on the output shaft 211, enabling the baffle 1212 to be positioned opposite the first stopper 113. It should be noted that the gap 122 can be understood as a hydraulic gap, and the bearing 100 for a blood pump utilizes hydraulic axial force to axially restrain the output end 211. Specifically, the bearing body 110 drives the end surface 112 to rotate. The rotation of the end surface, including the inclined surface 1132, drives the perfusate toward the gap 122 and flows from the lower side b to the higher side a of the inclined surface 1132. This squeeze generates hydraulic pressure, which in turn generates a force (i.e., the axial component of the hydraulic pressure F1) that counteracts the axial reaction force of the blood and the impact force of the perfusate on the bearing body 110. This prevents distal movement of the output shaft 211, further preventing wear and heat generation of the blood pump bearing 100 under the axial reaction force, and improving the safe, reliable, and stable high-speed operation of the blood pump 200. In actual operation, the perfusate flows from the outer periphery of the bearing body 110 toward the end surface 112, thereby providing the majority of the axial component of the perfusate-generated force. Furthermore, the axial through-groove 1134 is provided on the bearing through-hole 111 of the bearing body 110 along the axial direction of the bearing 100 for a blood pump, and is configured to allow perfusion fluid to flow from the proximal end A to the distal end B. The axial through-groove 1134 extends axially through the bearing body 110, providing a flow path for the perfusion fluid to flow from the proximal end A to the distal end B. This allows the perfusion fluid to flow from the axial through-hole 111 at the center of the axial body 110 to the end face 112, thereby ensuring sufficient fluid perfusion in the gap 122. This further increases the axial component F1 of the hydraulic pressure, making the bearing operating more stable and preventing the gap 122 from being unable to be filled with perfusion fluid.

[0070] Further, such as Figure 7 and Figure 8As shown, the first limiting portion 113 includes at least two inclined surfaces 1132 and a drainage groove 1133. The drainage groove 1133 is located between the height differences between two inclined surfaces 1213. The drainage groove 1133 communicates with the axial through-groove 1134, allowing the perfusion fluid in the axial through-groove 1134 to flow through the drainage groove 1133 into the gap 122, thereby increasing the flow rate of the perfusion fluid, ensuring that the gap 122 is fully filled with the perfusion fluid and increasing the axial component F1 of the hydraulic pressure. The drainage groove 1133 and the axial through-groove 1134 together form a flow channel, allowing the perfusion fluid to flow from the center to the end surface 112. In this third embodiment, there are six inclined surfaces 1132, each of which is arranged downwardly inclined toward the rotation direction V3 of the bearing body. More preferably, the inclined surface 1132 is preferably designed using fluid mechanics, and each of the inclined surfaces 1132 is arranged in a fan-shaped manner on the end surface 112, so that when the bearing body 110 rotates, the perfusion liquid can generate a larger axial component of force in the gap 122 and ensure uniform force. Preferably, the shape of each inclined surface 1132 is the same, thereby ensuring that when the perfusion liquid flows, the same axial component of force can be generated between each inclined surface 1132 and the gap 122. More preferably, the drainage groove 1133 can be a groove structure. Specifically, the drainage groove 1133 has a groove structure at the position where two of the inclined surfaces 1132 meet. It should be understood that the heights of the two inclined surfaces 1132 connected by the drainage groove 1133 along the groove width direction are inconsistent. In other embodiments, the number of the inclined surfaces 1132 is not limited to six, and those skilled in the art can set the number of inclined surfaces 1132 according to actual conditions.

[0071] It should be understood that in the above-mentioned embodiments 1 to 3, the configurations of the bearing body 110 and the additional component 120 may be combined. For example, the first limiting portion 113 may include a groove 1131, an inclined surface 1132, a drain groove 1133, and an axial through-groove 1134; or, the first limiting portion 113 may include a protrusion 1211, an inclined surface 1132, a drain groove 1133, and an axial through-groove 1134. The second limiting portion 121 may include a protrusion 1211 or a baffle 1212; or, the second limiting portion 121 may include a groove 1131 or a baffle 1212. The groove 1131 may be either a U-groove-shaped groove or a semi-U-groove-shaped groove.

[0072] In summary, the present invention provides a bearing for a blood pump, a blood pump, and a ventricular assist circulation device. The bearing for the blood pump comprises: a bearing body and an additional component; the bearing body is configured to connect to an output shaft of a driver and follow the output shaft in axial movement; the bearing body has a first limiting portion, and the additional component has a second limiting portion, wherein the first limiting portion and the second limiting portion cooperate to limit the axial displacement of the bearing body. This configuration enables the additional component to axially limit the bearing body, providing the bearing with an axial limiting function, thereby enhancing the bearing's axial load capacity and wear resistance, thereby ensuring that the output shaft connected to the bearing can operate safely, reliably, and stably at high speed.

[0073] The above description is only a description of the preferred embodiments of the present invention and does not limit the scope of the present invention. Any changes and modifications made by ordinary technicians in the field of the present invention based on the above disclosure shall fall within the scope of protection of the claims.

Claims

1. A bearing for a blood pump, characterized in that: include: Bearing body and additional components; The bearing body is used to be connected to an output shaft of a driving member and move along the axial direction of the output shaft following the output shaft; The bearing body has a first limiting portion, and the additional component has a second limiting portion, wherein the first limiting portion and the second limiting portion cooperate to limit the axial displacement of the bearing body; The bearing body has an end face, which is used to face a distal end, and the first limiting portion is arranged on the end face; the first limiting portion includes at least one inclined surface, which is inclined downward toward the rotation direction of the bearing body, and the second limiting portion includes a baffle, which faces the inclined surface and is spaced apart from the inclined surface.

2. The bearing for a blood pump according to claim 1, characterized in that: The additional component is used to be fixed on a pump housing. The first limiting portion is arranged on the outer surface of the bearing body along the circumference of the bearing body, and the second limiting portion is arranged to match the first limiting portion.

3. The bearing for a blood pump according to claim 1, characterized in that: One of the first limiting portion and the second limiting portion includes a groove, and the other of the first limiting portion and the second limiting portion includes a protrusion.

4. The bearing for a blood pump according to claim 3, characterized in that: There is a gap between the first limiting portion and the second limiting portion for injection of perfusion liquid to form a sliding liquid film.

5. The bearing for a blood pump according to claim 3, characterized in that: The longitudinal section of the groove is an annular structure, and the protrusions are continuous protrusion structures or intermittent protrusion structures arranged toward the groove.

6. The bearing for a blood pump according to claim 3, characterized in that: The cross section of the groove and / or the cross section of the protrusion is a U-groove structure.

7. The bearing for a blood pump according to claim 3, characterized in that: The cross-section of the groove is a semi-U-groove shape, and the semi-U-groove shape has a first end and a second end, the first end is close to the proximal end, and the second end is close to the distal end; the first limiting portion includes the groove, and the protrusion abuts against the first end; or, the second limiting portion includes the groove, and the protrusion abuts against the second end.

8. The bearing for a blood pump according to claim 1, characterized in that: The bearing body has an end face, which is used to face a distal end, and the first limiting portion is arranged on the end face; the first limiting portion also includes an axial through-groove, which is arranged on the bearing through-hole of the bearing body along the axial direction of the bearing, and is used to allow the perfusion fluid to flow from the proximal end to the distal end.

9. The bearing for a blood pump according to claim 8, characterized in that: The first limiting portion further includes at least two inclined surfaces and a drain groove, wherein the drain groove is provided between the two inclined surfaces and is communicated with the axial through groove.

10. The bearing for a blood pump according to claim 8, characterized in that: The inclined surfaces are arranged on the end surface in a fan-shaped manner.

11. The bearing for a blood pump according to claim 1, characterized in that: The bearing for the blood pump is made of ceramic material.

12. A blood pump, characterized in that: include: A drive member, a pump housing, and a bearing for a blood pump according to any one of claims 1 to 11; The driving member includes an output shaft; The pump housing is arranged outside the driving member, and the pump housing has a first chamber and a second chamber; The bearing body of the bearing for the blood pump is arranged on the output shaft, the additional component of the bearing for the blood pump is arranged on the pump housing, and the bearing for the blood pump is arranged between the first chamber and the second chamber.

13. A ventricular assist circulation device, characterized in that: include: The blood pump and controller according to claim 12; the controller is connected to the blood pump and is used to control the operation of the blood pump.

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