Ventricular assist device

Abstract

The invention provides a ventricular assist device. The ventricular assist device comprises a pump shell and an impeller. The pump shell is provided with a liquid inlet, a flow guide cone is fixedly arranged in the pump shell, the flow guide cone is opposite to the liquid inlet, and the flow guide cone is provided with a flow guide face opposite to the liquid inlet. The impeller is arranged in the pump shell and provided with a main runner and a branch runner communicated with the main runner, the main runner is opposite to the liquid inlet, the branch runner extends in the radial direction of the main runner, the impeller is provided with an inner wall face, and the inner wall face is provided with a drainage face portion which is provided with a first end and a second end. The distance from the first end to the central axis of the main runner is greater than that from the second end to the central axis of the main runner; when the impeller rotates in a suspended mode, a gap is formed between the flow guide cone and the inner wall face, the flow guide face is close to the second end of the flow guide face part, and the position of the flow guide face corresponds to the position of the branch flow channel, so that liquid flowing into the main flow channel is guided to the flow guide face through the flow guide face part and guided to the branch flow channel from the flow guide face. Therefore, thrombus entering a gap between the impeller and the flow guide cone can be reduced.

Description

Technical Field

[0001] The present application relates to the field of medical device technology, and in particular to a ventricular assist device. Background Art

[0002] As a medical device that assists or replaces the heart's pumping of blood, the ventricular assist device has very high operating requirements. However, some current ventricular assist devices do not fully consider the possibility that blood may carry blood clots into the device during design, which may get stuck in the internal structure of the ventricular assist device, thereby affecting its normal operation. Summary of the Invention

[0003] To this end, the present application provides a ventricular assist device to solve the problem of thrombus being stuck in the ventricular assist device and affecting its normal operation.

[0004] The first aspect of the present application provides a ventricular assist device comprising: a pump casing and an impeller; the pump casing has a liquid inlet, a guide cone is fixedly provided in the pump casing, the guide cone is opposite to the liquid inlet, and the guide cone has a guide surface opposite to the liquid inlet; the impeller is rotatably arranged in the pump casing, the impeller has a first surface and a second surface opposite to each other, the first surface is closer to the liquid inlet than the second surface, the impeller also has a main channel running through the first surface and the second surface, and a branch channel connected to the main channel, the main channel is opposite to the liquid inlet, the branch channel extends radially along the main channel, the impeller also has an inner wall surface defining the main channel, the inner wall surface is connected to the main channel The first surface and the second surface, the inner wall surface has a drainage surface portion, the drainage surface portion has a first end close to the first surface and a second end close to the second surface, the distance from the first end to the central axis of the main channel is greater than the distance from the second end to the central axis of the main channel; wherein, the guide cone is located in the main channel, and when the impeller rotates in suspension, there is a gap between the guide cone and the inner wall surface, the guide surface is close to the second end of the drainage surface portion, and the position of the guide surface corresponds to the position of the branch channel, so that the liquid flowing into the main channel can be drained to the guide surface through the drainage surface portion, and then diverted from the guide surface to the branch channel.

[0005] In a possible implementation manner, along the central axis of the main flow channel and in a direction approaching the second surface of the impeller, the distance from the guide surface portion to the central axis of the main flow channel gradually decreases.

[0006] In one possible embodiment, when the impeller is suspended and rotating, the second end of the drainage surface portion is closer to the liquid inlet than the edge of the guide surface, wherein the central axis of the main flow channel coincides with the central axis of the guide cone:

[0007] The virtual extension surface of the drainage surface intersects with the guide surface;

[0008] Alternatively, the intersection of the virtual extended surface of the drainage surface portion and the virtual extended surface of the guide surface is located in the gap between the inner wall surface of the impeller and the guide cone.

[0009] In one possible embodiment, the inner wall surface of the impeller further has a first straight annular surface portion, the first straight annular surface portion and the drainage surface portion are arranged along the central axis of the main channel, the first straight annular surface portion is closer to the second surface than the drainage surface portion, the diameter of the first straight annular surface portion is constant along the central axis of the main channel, and the first straight annular surface portion surrounds the guide cone.

[0010] In a possible implementation, the drainage surface portion is arranged around the central axis of the main channel, the second end of the drainage surface portion is connected to the first straight annular surface portion, and a rounded corner is provided at the connection between the drainage surface portion and the first straight annular surface portion.

[0011] In one possible embodiment, the inner wall surface of the impeller further includes a second straight annular surface portion, wherein the diameter of the second straight annular surface portion is constant along the central axis of the main flow channel and is larger than the diameter of the first straight annular surface portion; the flow guide surface portion connects the first straight annular surface portion and the second straight annular surface portion; the impeller includes a first annular disk, a second annular disk, and a support plate, wherein the first annular disk and the second annular disk are coaxial and spaced apart; the support plates are multiple, and the multiple support plates are spaced apart along the circumference of the first annular disk and evenly arranged between the first annular disk and the second annular disk to form a plurality of the branch flow channels; the first annular disk and the second annular disk each include an accommodating cavity for accommodating magnetic material; the inner annular surface of the first annular disk, the inner side surfaces of the multiple support plates, and the inner annular surface of the second annular disk jointly define the main flow channel; the first surface is the surface of the first annular disk facing away from the second annular disk, and the second surface is the surface of the second annular disk facing away from the first annular disk; the first straight annular surface portion is the inner annular surface of the second annular disk, the second straight annular surface portion is the inner annular surface of the first annular disk, and the flow guide surface portion is the inner side surfaces of the multiple support plates.

[0012] In one possible embodiment, the guide cone has a cylindrical body and a conical head fixed to one end of the cylindrical body, the end of the cylindrical body away from the conical head is fixed to the pump casing, the central axis of the cylindrical body coincides with the central axis of the liquid inlet, the conical head is coaxial with the cylindrical body, the top of the conical head faces the liquid inlet, the guide surface is the conical surface of the conical head, and the first straight annular surface surrounds the cylindrical body; the main channel has a first opening located on the first surface, the diameter of the first opening is defined as D1, the diameter of the liquid inlet is defined as D2, the difference between the diameter of the first straight annular surface and the diameter of the cylindrical body is defined as △d, and the maximum movement distance of the impeller relative to the cylindrical body in the radial direction is defined as L, wherein L≤△d / n, n is a number greater than or equal to 1.5, and D2+L≤D1.

[0013] In one possible implementation, D1≤D2+Δd.

[0014] In one possible embodiment, the ventricular assist device further has at least one of the following features:

[0015] The impeller further has an outer wall surface, and the branch channel runs through the outer wall surface and the inner wall surface;

[0016] The branch channel is located between the first surface and the second surface of the impeller;

[0017] The ventricular assist device further includes a drive assembly capable of driving the impeller to rotate in suspension;

[0018] The guide surface is a conical surface or an arc-shaped conical surface, and the guide surface has a cone top, which faces the liquid inlet.

[0019] In one possible embodiment, the pump casing has a boosting chamber, the impeller is arranged in the boosting chamber in a suspended and rotatable manner, the boosting chamber is connected to the liquid inlet, the boosting chamber has a first chamber wall opposite to the liquid inlet, the guide cone is arranged on the first chamber wall, the guide surface is a conical surface or an arc-shaped conical surface, the guide surface has a cone top and an edge away from the cone top, the cone top faces the liquid inlet, the diverter has a bottom surface close to the second surface and a top surface opposite to the bottom surface, when the impeller is suspended and rotated, the distance from the edge of the guide surface to the first chamber wall is greater than the distance from the bottom surface of the diverter to the first chamber wall, and is less than the distance from the top surface of the diverter to the first chamber wall.

[0020] In a possible implementation manner, the virtual extended surface at the edge of the guide surface is perpendicular to the central axis of the guide surface.

[0021] In one possible embodiment, the ventricular assist device further includes an inlet pipe, an outlet pipe and a connecting elbow; the inlet pipe is fixedly connected to the outlet pipe, and the axes of the inlet pipe and the outlet pipe are parallel; the pump housing also has a liquid outlet, the outlet pipe is connected to the pump housing, and the outlet pipe is communicated with the liquid outlet; the connecting elbow is connected between the pump housing and the inlet pipe, and the connecting elbow communicates the inlet pipe and the liquid inlet; the inner diameter of the inlet pipe is equal to the inner diameter of the outlet pipe; the inner diameter of the part of the connecting elbow away from the inlet pipe is larger than the inner diameter of the inlet pipe.

[0022] In one possible embodiment, the ventricular assist device further includes a liquid inlet pipe and a liquid outlet pipe; the liquid outlet pipe includes a tube body and a connecting shell, the connecting shell is connected to the tube body and forms a channel with the tube body, the channel is parallel to the axis of the tube body, the pump housing also has a liquid outlet, the tube body is connected to the pump housing, and the tube body is communicated with the liquid outlet; the liquid inlet pipe is connected to the pump housing, and the liquid inlet pipe is communicated with the liquid inlet, and the liquid inlet pipe is arranged in the channel; wherein the hardness of the liquid inlet pipe is less than the hardness of the liquid outlet pipe.

[0023] In one possible embodiment, the liquid inlet pipe includes a first connecting section and a first extension section connected to the first connecting section, the first connecting section is fixedly connected to the pump casing and connected to the liquid inlet, the first connecting section is made of metal or alloy, the first extension section includes a polymer material, and the first connecting section and the first extension section are an integrally formed structure.

[0024] In one possible embodiment, the ventricular assist device further includes an extension hose; the extension hose is connected to an end of the liquid outlet tube away from the liquid outlet, and the extension hose is communicated with the liquid outlet tube, wherein the material of the extension hose is softer than that of the liquid outlet tube; when the liquid inlet tube and the liquid outlet tube are passed through and fixed to the heart wall, the liquid inlet tube is located in the ventricular cavity, and the extension hose can extend into the artery.

[0025] In one possible embodiment, the extension hose includes a second connecting section and a second extension section, the second connecting section is made of metal or alloy material, the second extension section is made of a polymer material, the second connecting section and the second extension section are an integrally formed structure, and the second connecting section is connected to the liquid outlet pipe.

[0026] In a possible implementation manner, the second extension section includes a soft rubber layer and a metal wire layer, and the metal wire layer is disposed in the soft rubber layer.

[0027] In a possible embodiment, the metal wire layer includes at least two metal wires, and the at least two metal wires extend in a wavy shape along the axial direction of the extension hose; and / or, the at least two metal wires extend in a wavy shape along the circumferential direction of the extension hose, and adjacent metal wires are fixedly connected.

[0028] In one possible embodiment, the pump casing further has a boosting chamber and a liquid outlet connected to the boosting chamber, the boosting chamber is connected to the liquid inlet, the boosting chamber has a first chamber wall, a second chamber wall and an annular wall, the first chamber wall and the second chamber wall are spaced apart and opposite to each other, the annular wall connects the first chamber wall and the second chamber wall, the liquid inlet is located in the second chamber wall, the guide cone is provided in the first chamber wall, the liquid outlet is located in the annular wall, and the impeller can be suspended and rotatably provided in the boosting chamber; the boosting chamber further has a guide wall, the guide wall extends from the first chamber wall to the liquid outlet, and the distance from the guide wall to the first chamber wall gradually increases in the direction away from the first chamber wall.

[0029] In one possible embodiment, the guide cone has a cylindrical body and a conical head fixed to one end of the cylindrical body, the end of the cylindrical body away from the conical head is fixed to the pump casing, the central axis of the cylindrical body coincides with the central axis of the liquid inlet, the conical head is coaxial with the cylindrical body, the top of the conical head faces the liquid inlet, and the guide surface is the conical surface of the conical head; the inner wall surface of the impeller further has a first straight annular surface, the first straight annular surface and the drainage surface are arranged along the central axis of the main flow channel, the first straight annular surface is closer to the second surface than the drainage surface, and is arranged along the center of the main flow channel. The central axis, the diameter of the first straight annular surface is constant, and the first straight annular surface surrounds the guide cone; the impeller has an outer wall surface, and the branch channel runs through the outer wall surface and the inner wall surface; the difference between the diameter of the first straight annular surface and the diameter of the cylindrical body is defined as △d, the maximum radial movement distance of the impeller is defined as L, 0<L≤△d, and when the central axis of the main channel coincides with the central axis of the cylindrical body, the minimum distance between the orthographic projection of the outer wall surface on the first cavity wall and the guide wall is defined as T, wherein, when the central axis of the main channel coincides with the central axis of the cylindrical body, L / 2<T.

[0030] In a ventricular assist device, when the impeller rotates in the boost chamber, blood containing thrombus enters the main channel of the impeller through the liquid inlet, and part of the blood containing thrombus enters the shunt channel and flows out of the shunt channel, while the other part of the blood containing thrombus flows into the gap between the impeller and the guide cone; and because the pressure at the periphery of the impeller is greater than the pressure in the main channel of the impeller, part of the blood at the periphery of the impeller will flow from the periphery of the impeller through the gap between the impeller and the pump casing to the gap between the impeller and the guide cone under the action of the pressure difference, causing the thrombus to be difficult to discharge in the gap between the impeller and the guide cone and continue to accumulate, making it easy for the thrombus to adhere to the inner wall surface of the impeller and / or the guide cone, thereby affecting the rotation of the impeller. In the present application, the inner wall surface of the impeller has a drainage surface, the first end of the drainage surface is closer to the liquid inlet than the second end, and the distance from the first end of the drainage surface to the central axis of the main channel is greater than the distance from the second end to the central axis of the main channel, so that there is an inclined surface from the first end to the second end of the drainage surface, and the distance relative to the central axis of the main channel gradually decreases; and because when the impeller is suspended and rotated, the guide surface is close to the second end of the drainage surface, and the position of the guide surface corresponds to the position of the diversion channel, so that the blood containing thrombus entering the main channel from the liquid inlet will be guided to the guide surface under the guidance of the drainage surface and diverted to the diversion channel through the guide surface, thereby reducing the thrombus entering the gap between the impeller and the guide cone, so as to reduce the thrombus attached to the inner wall surface of the impeller and / or the guide cone, and thereby reducing the impact on the rotation of the impeller. BRIEF DESCRIPTION OF THE DRAWINGS

[0031] In order to more clearly illustrate the technical solution of the present application, the following is a brief introduction to the drawings required for use in the implementation. Obviously, the drawings described below are some implementation methods of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without any creative work.

[0032] Figure 1 A schematic structural diagram of a ventricular assist device provided in some embodiments of the present application;

[0033] Figure 2 for Figure 1 Schematic diagram of the structural explosion;

[0034] Figure 3 for Figure 2 A magnified view of the middle part of the structure;

[0035] Figure 4 for Figure 3 Schematic diagram of the structural explosion;

[0036] Figure 5 for Figure 3 sectional view of

[0037] Figure 6 for Figure 5 A partial enlarged view of the middle M part;

[0038] Figure 7 is a cross-sectional view of the impeller and the magnetic material inside it;

[0039] Figure 8 for Figure 1 Cross-sectional view along AA;

[0040] Figure 9 for Figure 2 The enlarged diagram of the structure of the extension hose, where Figure 9 The figure shows the structure of the extended hose after removing one soft rubber layer;

[0041] Figure 10 A schematic structural diagram of a ventricular assist device provided in a third embodiment of the present application;

[0042] Figure 11 for Figure 10 Structural explosion diagram;

[0043] Figure 12 Schematic diagram of the flow direction of liquid from the periphery of the impeller to the main flow channel of the impeller.

[0044] Reference numerals: ventricular assist device 1, pump housing 10, guide cone 20, impeller 30, liquid inlet 11, liquid outlet 12, boosting chamber 13, first chamber wall 131, second chamber wall 132, annular wall 133, guide wall 134, cylindrical body 21, cone head 22, guide surface 220, cone top 221, edge 222, drive assembly 40, rotor 41, stator 42, mounting housing 401, first fixed magnetic ring 51, second fixed magnetic ring 52, first surface 301, first opening 3011, second surface 302, inner wall surface 303, outer wall surface 304, main channel 31, central axis OO' of main channel, diverter channel 32, drainage surface 3031, first end 303a, second end 303b, drainage The virtual extended surface 303c of the face, the virtual extended surface 2201 of the guide surface, the gap H, the first straight annular surface 3032, the second straight annular surface 3033, the first annular disk 33, the second annular disk 34, the support plate 35, the cutting plane T, the first liquid inlet pipe 51, the first liquid outlet pipe 52, the connecting elbow 53, the first tube shell 531, the second tube shell 532, the adapter 54, the first connecting part 530, the second connecting part 100, the opening 540, the extension hose 55, the first connecting section 551, the first extension section 552, the soft rubber layer 5521, the metal wire layer 5522, the second liquid inlet pipe 56, the second connecting section 561, the second extension section 562, the second liquid outlet pipe 57, the tube body 571, and the connecting shell 572. DETAILED DESCRIPTION

[0045] The following will be combined with the drawings in the embodiments of this application to clearly and completely describe the technical solutions in the embodiments of this application. Obviously, the embodiments described are only part of the embodiments of this application, not all of the embodiments. Based on the embodiments in this application, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of this application.

[0046] In the description of this application, unless otherwise specified or limited, the term "connection" should be understood in a broad sense. For example, it can mean a fixed connection, a detachable connection, or an integral connection; it can mean a direct connection, an indirect connection through an intermediate medium, or internal communication between two components; it can mean a communication connection; or it can mean an electrical connection. Those skilled in the art will understand the specific meanings of the above terms in this application based on the specific circumstances.

[0047] In the description of this application, the terms "first", "second", "third", etc. are used to distinguish different objects rather than to describe a specific order. In addition, the terms "upper", "lower", "inner", "outer", etc. indicate directions or positional relationships based on the directions or positional relationships shown in the accompanying drawings. They are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific direction, be constructed and operated in a specific direction. Therefore, they cannot be understood as limitations on this application.

[0048] The ventricular assist device 1 is used to assist or replace the heart in pumping blood. Specifically, the ventricular assist device 1 can be a left ventricular assist device or a right ventricular assist device. Figures 1-4 As shown, in the first embodiment of the present application, the ventricular assist device 1 includes a pump housing 10 , a guide cone 20 and an impeller 30 .

[0049] like Figure 3 As shown, the pump housing 10 is generally volute-shaped. In other embodiments, the pump housing 10 can also be in other shapes, such as a hollow cylinder. The pump housing 10 has a liquid inlet 11. The liquid inlet 11 is circular. In other embodiments, the liquid inlet 11 can also be in other shapes such as an ellipse.

[0050] The pump housing 10 also has a liquid outlet 12. In the illustrated embodiment, the outline of the liquid outlet 12 is composed of an arcuate side and three straight sides connected in sequence with rounded corners. In other embodiments, the liquid outlet 12 can also be a circular, elliptical or other shape.

[0051] like Figure 5 and Figure 6As shown, the pump housing 10 further comprises a boost chamber 13. The boost chamber 13 comprises a first chamber wall 131, a second chamber wall 132, and an annular wall 133. The first chamber wall 131 and the second chamber wall 132 are spaced apart and opposed to each other, and the annular wall 133 connects the first and second chamber walls 131, 132. In the illustrated embodiment, the first and second chamber walls 131, 132 are parallel. The boost chamber 13 is in communication with the liquid inlet 11 and the liquid outlet 12. The liquid inlet 11 is opposite the first chamber wall 131 and is located on the second chamber wall 132. The liquid outlet 12 is located on the annular wall 133.

[0052] A guide cone 20 is fixedly mounted within the pump housing 10. Specifically, the guide cone 20 is located on the first cavity wall 131. The guide cone 20 faces the liquid inlet 11. The guide cone 20 can be integrally formed and fixed within the pump housing 10, which helps reduce the number of parts. In other embodiments, the guide cone 20 can also be fixed by screws, welding, or adhesive bonding.

[0053] like Figure 4 As shown, the guide cone 20 has a cylindrical body 21 and a conical head 22 fixed to one end of the cylindrical body 21. The end of the cylindrical body 21 away from the conical head 22 is fixed to the pump housing 10. Specifically, the end of the cylindrical body 21 away from the conical head 22 is fixed to the first cavity wall 131. The central axis of the cylindrical body 21 coincides with the central axis of the liquid inlet 11; the central axis of the conical head 22 coincides with the central axis of the cylindrical body 21. The guide cone 20 has a guide surface 220 opposite to the liquid inlet 11. The guide surface 220 is the conical surface of the conical head 22. Specifically, the guide surface 220 is a circular conical surface or an arc-shaped conical surface. The guide surface 220 has a cone top 221 and an edge 222 away from the cone top 221. The cone top 221 faces the liquid inlet 11. The cone top 221 is smooth, rather than a spike, which helps to prevent blood from being punctured and causing hemolysis.

[0054] like Figure 8As shown, the impeller 30 is disposed in the pump housing 10 in a manner capable of suspended rotation. That is, the impeller 30 is disposed in the pump housing 10 and is capable of rotating without contact with the pump housing 10. Furthermore, the impeller 30 is disposed in the boost chamber 13 in a manner capable of suspended rotation. The ventricular assist device 1 further includes a drive assembly 40, which is capable of driving the impeller 30 to suspend and rotate. The drive assembly 40 includes a rotor 41 and a stator 42. The rotor 41 is disposed in the impeller 30, and the stator 42 is located outside the pump housing 10. Specifically, the stator 42 can be located inside a mounting housing 401 connected to the pump housing 10. The ventricular assist device 1 further includes a first fixed magnetic ring 51 and a second fixed magnetic ring 52. The first fixed magnetic ring 51 is disposed in the impeller 30, and the rotor 41 is located between the first fixed magnetic ring 51 and the stator 42. The second fixed magnetic ring 52 is disposed in the pump housing 10, and the first fixed magnetic ring 51 is located between the rotor 41 and the second fixed magnetic ring 52. Specifically, the second fixed magnetic ring 52 is disposed on the side of the pump housing 10 facing away from the second cavity wall 132 and is located near the liquid inlet 11; alternatively, the second fixed magnetic ring 52 is disposed within the pump housing wall near the second cavity wall 132. A first magnetic force is generated between the first fixed magnetic ring 51 and the second fixed magnetic ring 52, and a second magnetic force is generated between the stator 42 and the rotor 41. The second magnetic force is in the opposite direction to the first magnetic force. When power is supplied to the stator 42, the stator 42 generates a magnetic field and drives the rotor 41 to rotate, thereby driving the impeller 30 to rotate. The second magnetic force is in the opposite direction to the first magnetic force, and when the impeller is in a preset position, the second magnetic force and the first magnetic force are equal or approximately equal in magnitude, thereby causing the impeller 30 to rotate in suspension within the pump housing 10. That is, the impeller 30 rotates within the pump housing 10 without contacting the pump housing 10.

[0055] like Figure 4-Figure 7 As shown, the impeller 30 is generally annular in shape. It has a first surface 301 and a second surface 302 that oppose each other. The first surface 301 is closer to the liquid inlet 11 than the second surface 302. Specifically, the first surface 301 opposes the second cavity wall 132, while the second surface 302 opposes the first cavity wall 131. The impeller 30 also has a main flow channel 31 that runs through the first and second surfaces 301, 302. The main flow channel 31 opposes the liquid inlet 11. The guide cone 20 is located within the main flow channel 31.

[0056] The impeller 30 further includes an inner wall surface 303 defining the main flow channel 31. The inner wall surface 303 connects the first surface 301 and the second surface 302. The inner wall surface 303 includes a flow guide surface 3031. The flow guide surface 3031 has a first end 303a proximate to the first surface 301 and a second end 303b proximate to the second surface 302. The distance L1 between the first end 303a and the central axis OO' of the main flow channel 31 is greater than the distance L2 between the second end 303b and the central axis OO' of the main flow channel 31.

[0057] The impeller 30 further includes a branch channel 32 communicating with the main channel 31. The branch channel 32 extends radially relative to the main channel 31. Furthermore, the branch channel 32 is located between the first surface 301 and the second surface 302 of the impeller 30. The impeller 30 further includes an outer wall 304 connecting the first surface 301 and the second surface 302. The branch channel 32 extends through the outer wall 304 and the inner wall 303.

[0058] When the impeller 30 is suspended and rotating, a gap H is formed between the guide cone 20 and the inner wall surface 303 of the impeller 30. The guide surface 220 of the guide cone 20 is close to the second end 303b of the flow-guiding surface portion 3031 of the impeller 30. The position of the guide surface 220 of the guide cone 20 corresponds to the position of the diverter channel 32. This allows liquid flowing into the main channel 31 to be guided through the flow-guiding surface portion 3031 of the impeller 30 to the guide surface 220 of the guide cone 20, and then to the diverter channel 32 from the guide surface 220 of the guide cone 20. The following description uses blood as an example.

[0059] In the ventricular assist device, when the impeller 30 rotates in the boost chamber, the blood containing thrombus enters the main channel 31 of the impeller 30 through the liquid inlet 11, and a part of the blood containing thrombus enters the shunt channel 32 and flows out of the shunt channel 32, and the other part of the blood containing thrombus flows into the gap between the impeller 30 and the guide cone 20; and because the pressure at the periphery of the impeller 30 is greater than the pressure in the main channel 31 of the impeller 30, a part of the blood at the periphery of the impeller 30 will flow from the periphery of the impeller 30 through the gap between the impeller 30 and the pump housing 10 to the gap between the impeller 30 and the guide cone 20 under the action of the pressure difference, that is, along the Figure 12The thrombus flows in the direction P, which makes it difficult for the thrombus to be discharged in the gap H between the impeller 30 and the guide cone 20 and continues to accumulate, making it easy for the thrombus to adhere to the inner wall surface 303 of the impeller 30 and / or the guide cone 20, thereby affecting the rotation of the impeller 30. In the present application, the inner wall surface 303 of the impeller 30 has a drainage surface 3031, the first end 303a of the drainage surface 3031 is closer to the liquid inlet 11 than the second end 303b, and the distance L1 from the first end 303a of the drainage surface 3031 to the central axis OO' of the main channel 31 is greater than the distance L2 from the second end 303b to the central axis OO' of the main channel 31, so that there is an inclined surface from the first end 303a to the second end 303b of the drainage surface 3031, the distance from the central axis OO' of the main channel 31 gradually decreasing; and because the impeller 30 rotates in a suspended manner When the guide surface 220 is close to the second end 303b of the drainage surface 3031, and the position of the guide surface 220 corresponds to the position of the bypass channel 32, so that the blood containing thrombus entering the main channel 31 from the liquid inlet 11 will be guided by the drainage surface 3031. More blood containing thrombus will be guided to the guide surface 220 and diverted to the bypass channel 32 through the guide surface 220, thereby reducing the thrombus entering the gap H between the impeller 30 and the guide cone 20, thereby reducing the thrombus attached to the inner wall surface 303 of the impeller 30 and / or the guide cone 20, and thereby reducing the impact on the rotation of the impeller 30.

[0060] like Figure 6 and Figure 7 As shown, further, along the central axis OO' of the main channel 31 and toward the second surface 302 of the impeller 30, the distance between the drainage surface 3031 and the central axis OO' of the main channel 31 gradually decreases. The drainage surface 3031 can be an inclined plane or an inclined curved surface. Compared to a method in which the distance between the drainage surface 3031 and the central axis OO' of the main channel 31 alternates between increasing and decreasing, this embodiment facilitates smoother blood flow through the drainage surface 3031, reduces the occurrence of vortices, and reduces the likelihood of thrombosis.

[0061] In one embodiment, when the impeller 30 is suspended and rotating, the second end 303b of the drainage surface portion 3031 is closer to the liquid inlet 11 than the edge 222 of the guide surface 220, and the central axis OO' of the main channel 31 coincides with the central axis of the guide cone 20, and the intersection of the virtual extended surface 303c of the drainage surface portion 3031 and the virtual extended surface 2201 of the guide surface 220 is located in the gap H between the inner wall surface 303 of the impeller 30 and the guide cone 20.

[0062] The virtual extended surface 303c of the drainage surface portion 3031 refers to a virtual extended surface 303c of the inclined surface of the drainage surface portion 3031, the distance from the central axis OO' of the main channel 31 gradually decreasing. When the drainage surface portion 3031 is an inclined plane, there is one virtual extended surface 303c of the drainage surface portion 3031; when the drainage surface portion 3031 is an inclined curved surface, there are multiple virtual extended surfaces 303c of the drainage surface portion 3031.

[0063] In one embodiment, when the impeller 30 is suspended and rotating, the second end 303b of the drainage surface portion 3031 is closer to the liquid inlet 11 than the edge 222 of the guide surface 220. When the central axis OO' of the main channel 31 of the impeller 30 coincides with the central axis of the guide cone 20, the intersection of the virtual extended surface 303c of the drainage surface portion 3031 and the virtual extended surface 2201 of the guide surface 220 is located in the gap H between the inner wall surface 303 of the impeller 30 and the guide cone 20. Under the action of inertia, the blood containing thrombus flows along the extension direction of the virtual extended surface 303c of the drainage surface 3031, and the intersection of the virtual extended surface 303c of the drainage surface 3031 and the virtual extended surface 2201 of the guide surface 220 is located in the gap H between the inner wall surface 303 of the impeller 30 and the guide cone 20, which can further increase the blood containing thrombus guided from the drainage surface 3031 to the guide surface 220, and reduce the blood containing thrombus entering between the inner wall surface 303 of the impeller 30 and the guide cone 20, that is, the amount of thrombus entering between the inner wall surface 303 of the impeller 30 and the guide cone 20 is further reduced.

[0064] In another embodiment, when the impeller 30 is suspended and rotated, the second end 303b of the drainage surface portion 3031 is closer to the liquid inlet 11 than the edge 222 of the guide surface 220. When the central axis OO' of the main channel 31 of the impeller 30 coincides with the central axis of the guide cone 20, the virtual extended surface 303c of the drainage surface portion 3031 intersects with the guide surface 220. Due to the action of inertia, the blood passing through the drainage surface 3031 will flow along the virtual extended surface 303c of the drainage surface 3031. Therefore, when the central axis OO' of the main channel 31 of the impeller 30 coincides with the central axis of the guide cone 20, and the virtual extended surface 303c of the drainage surface 3031 intersects with the guide surface 220, the blood passes through the drainage surface 3031 and flows along the virtual extended surface 303c of the drainage surface 3031 to the guide surface 220. Therefore, the entry of thrombus between the inner wall surface 303 of the impeller 30 and the guide cone 20 can be further reduced or even avoided, and the accumulation of thrombus in the gap H between the impeller 30 and the guide cone 20 can be further reduced.

[0065] It should be noted that when the impeller 30 is suspended and rotated, the central axis OO' of the main channel 31 of the impeller 30 may be offset relative to the central axis of the guide cone 20. Therefore, a complete description is given here of the relationship between the virtual extended surface 303c of the drainage surface portion 3031 and the guide surface 220 when the impeller 30 is suspended and rotated.

[0066] Specifically, when the offset distance of the central axis OO' of the main flow channel 31 of the impeller 30 relative to the central axis of the guide cone 20 is less than or equal to the preset value, the virtual extended surface 303c of the drainage surface 3031 intersects with the guide surface 220, or the intersection of the virtual extended surface 303c of the drainage surface 3031 and the virtual extended surface 2201 of the guide surface 220 is located in the gap H between the inner wall surface 303 of the impeller 30 and the guide cone 20; the central axis OO' of the main flow channel 31 of the impeller 30 is offset relative to the guide cone 20. When the offset distance of the central axis is greater than a preset value, the virtual extended surface 303c of a portion of the drainage surface portion 3031 intersects with the guide surface 220, and the intersection of the virtual extended surface 303c of the other portion of the drainage surface portion 3031 and the virtual extended surface 2201 of the guide surface 220 is located in the gap H between the inner wall surface 303 of the impeller 30 and the guide cone 20; wherein, the difference between the minimum diameter of the inner wall surface 303 of the impeller 30 and the maximum diameter of the guide cone 20 is defined as △d, 0≤preset value≤0.48△d, △d>0.

[0067] like Figure 4-Figure 7 As shown, the shunt channel 32 further comprises a bottom surface 3021 close to the second surface 302 and a top surface 3022 opposite to the bottom surface 3021. When the impeller 30 is suspended and rotating, the distance between the edge 222 of the guide surface 220 and the first cavity wall 131 is greater than the distance between the bottom surface 3021 of the shunt channel 32 and the first cavity wall 131, and is smaller than the distance between the top surface 3022 of the shunt channel 32 and the first cavity wall 131. This facilitates blood passing through the guide surface 220 into the shunt channel 32.

[0068] Furthermore, the virtual extended surface 2201 at the edge 222 of the guide surface 220 is perpendicular to the central axis of the guide surface 220. The guide surface 220 is an arc-shaped conical surface. The central axis of the guide surface 220 coincides with the central axis of the cylindrical body 21.

[0069] Since the guide surface 220 has a cone top 221 and an edge 222 away from the cone top 221, the cone top 221 faces the liquid inlet 11, the guide surface 220 is an arc-shaped surface, and the virtual extended surface 2201 at the edge 222 of the guide surface 220 is perpendicular to the central axis of the guide surface 220. Therefore, when blood flows out along the guide surface 220, the blood flows out along the virtual extended surface 2201. The distance from the edge 222 of the guide surface 220 to the first cavity wall 131 is greater than the distance from the bottom surface 3021 of the shunt channel 32 to the first cavity wall 131, and is smaller than the distance from the top surface 3022 of the shunt channel 32 to the first cavity wall 131, which is conducive to allowing more blood flowing out along the virtual extended surface 2201 to enter the shunt channel 32, thereby further reducing or even avoiding thrombus entering the inner wall surface 303 of the impeller 30.

[0070] In one embodiment, when the impeller 30 operates smoothly, the bottom surface 3021 and the top surface 3022 of the diverter channel 32 are both perpendicular to the central axis of the guide surface 220, that is, the bottom surface 3021 and the top surface 3022 of the diverter channel 32 are both parallel to the virtual extended surface 2201 at the edge 222 of the guide surface 220.

[0071] Furthermore, the curvature of the guide surface 220 gradually decreases from the cone top 221 to the edge 222 , so that the flow direction of the liquid gradually changes when flowing through the guide surface 220 , and this gradual direction change helps to reduce turbulence and energy loss.

[0072] Optionally, the inner wall surface 303 of the impeller 30 further includes a first straight annular surface portion 3032. The first straight annular surface portion 3032 and the flow guide surface portion 3031 are arranged along the central axis OO' of the main channel 31. The first straight annular surface portion 3032 is closer to the second surface 302 than the flow guide surface portion 3031. The diameter of the first straight annular surface portion 3032 is constant along the central axis OO' of the main channel 31. The first straight annular surface portion 3032 surrounds the guide cone 20. Specifically, the first straight annular surface portion 3032 surrounds the cylindrical body 21. The gap H between the inner wall surface 303 of the impeller 30 and the flow guide cone 20 is the gap between the first straight annular surface portion 3032 and the cylindrical body 21.

[0073] Among them, the intersection of the virtual extended surface 303c of the drainage surface 3031 and the virtual extended surface 2201 of the guide surface 220 is located in the gap H between the inner wall surface 303 of the impeller 30 and the guide cone 20. Specifically, the intersection of the virtual extended surface 303c of the drainage surface 3031 and the virtual extended surface 2201 of the guide surface 220 is located in the gap H between the first straight annular surface 3032 of the impeller 30 and the cylindrical body 21 of the guide cone 20.

[0074] Since the diameter of the first straight annular surface portion 3032 is constant, the virtual extended surface 303 c of the drainage surface portion 3031 and the first straight annular surface portion 3032 are not located in the same plane.

[0075] Furthermore, since the impeller 30 requires a certain clearance from the guide cone 20 during rotation to avoid squeezing blood and causing hemolysis, and to prevent the impeller 30 from contacting the guide cone 20 and affecting the stability of the impeller 30's rotation, compared to a solution in which the diameter of the first straight annular surface portion 3032 is not constant, in this embodiment, the first straight annular surface portion 3032 has a constant diameter and surrounds the guide cone 20, resulting in a constant diameter of the cylindrical body 21 of the guide cone 30. This helps reduce the radial width of the pump body 10, thereby reducing the volume of the pump body 10. Due to the pressure differential, blood on the periphery of the impeller 30 flows through the gap between the wall of the boost chamber 13 and the impeller 30, toward the main flow channel 31 of the impeller 30, and then into the branch channel 32. The blood flow rate in this blood flow path is relatively slow, while the blood flow rate in the gap between the guide cone 20 and the first straight annular surface 3032 through the liquid inlet 11 is relatively fast. If the distance from the first straight annular surface 3032 to the central axis OO' of the main flow channel 31 gradually decreases along the central axis OO' of the main flow channel 31 and toward the second surface 302 of the impeller 30, a recirculation zone is likely to form at the first straight annular surface 3032, thereby easily causing blood vortexes to form in the area near the first straight annular surface 3032. In this embodiment, however, since the diameter of the first straight annular surface 3032 is constant, the formation of the recirculation zone can be reduced or even eliminated, and blood vortexes are less likely to form in the area near the first straight annular surface 3032.

[0076] In other embodiments, the diameter of the first straight annular surface portion 3032 may not be constant, and the slope of the first straight annular surface portion 3032 relative to the first cavity wall 131 may be smaller than the slope of the drainage surface portion 3031, so that the intersection of the virtual extended surface 303c of the drainage surface portion 3031 and the virtual extended surface 2201 of the guide surface 220 is located in the gap H between the first straight annular surface portion 3032 of the impeller 30 and the guide cone 20.

[0077] Optionally, the drainage surface portion 3031 is disposed around the central axis OO' of the main channel 31, and the second end 303b of the drainage surface portion 3031 is connected to the first straight annular surface portion 3032. The connection between the drainage surface portion 3031 and the first straight annular surface portion 3032 is rounded. Compared to a configuration where the connection between the drainage surface portion 3031 and the first straight annular surface portion 3032 is a bent angle, the solution in this embodiment helps reduce the probability of hemolysis when blood passes through the drainage surface portion 3031 and the first straight annular surface portion 3032.

[0078] Optionally, the inner wall surface 303 of the impeller 30 also has a second straight annular surface portion 3033. Along the central axis OO' of the main channel 31, the diameter of the second straight annular surface portion 3033 is constant, and the diameter of the second straight annular surface portion 3033 is larger than the diameter of the first straight annular surface portion 3032; the drainage surface portion 3031 connects the first straight annular surface portion 3032 and the second straight annular surface portion 3033, so that the blood entering from the liquid inlet 11 must pass through the drainage surface portion 3031.

[0079] Among them, Figure 4 、 Figure 7 and Figure 8 As shown, the impeller 30 includes a first annular disk 33, a second annular disk 34, and support plates 35. The first annular disk 33 and the second annular disk 34 are coaxially spaced and spaced apart. There are multiple support plates 35, spaced axially and evenly spaced between the first annular disk 33 and the second annular disk 34, forming multiple flow channels 32. Each of the first and second annular disks 33 and 34 has a receiving cavity 330 and 340 for accommodating magnetic material. The inner annular surface of the first annular disk 33, the inner side surfaces of the multiple support plates 35, and the inner annular surface of the second annular disk 34 collectively define the main flow channel 31. The first surface 301 is the surface of the first annular disk 33 facing away from the second annular disk 34, the second surface 302 is the surface of the second annular disk 34 facing away from the first annular disk 33, the first straight annular surface 3032 is the inner annular surface of the second annular disk 34, the second straight annular surface 3033 is the inner annular surface of the first annular disk 33, and the flow diversion surface 3031 is the inner side surfaces of the multiple support plates 35.

[0080] Because the first annular disk 33 includes a cavity 330 for accommodating magnetic material, the inner diameter of the first annular disk 33 is constant, or in other words, the diameter of the second straight annular surface 3033 is constant. This increases the capacity of the cavity 330 in the first annular disk 33 compared to a solution where the second straight annular surface 3033 is not constant, thereby facilitating the installation of magnetic material. Similarly, because the second annular disk 34 includes a cavity 340 for accommodating magnetic material, the inner diameter of the second annular disk 34 is constant, or in other words, the diameter of the first straight annular surface 3032 is constant. This increases the capacity of the cavity 340 in the second annular disk 34 compared to a solution where the diameter of the first straight annular surface 3032 is not constant, thereby facilitating the installation of magnetic material.

[0081] Specifically, in this embodiment, the magnetic material in the first annular disk 33 is the first fixed magnetic ring 51 , and the magnetic material in the second annular disk 33 is the rotor 41 .

[0082] Optionally, the connection between the second straight ring surface 3033 and the drainage surface 3031 is provided with a rounded corner, which can reduce the chance of hemolysis when blood flows through the connection between the second straight ring surface 3033 and the drainage surface 3031 compared to the angled connection between the second straight ring surface 3033 and the drainage surface 3031.

[0083] Optionally, the main channel 31 has a first opening 3011 located on the first surface 301. The diameter of the first opening 3011 is defined as D1, the diameter of the liquid inlet 11 is defined as D2, the difference between the diameter of the first straight annular surface portion 3032 and the diameter of the cylindrical body 21 is defined as Δd, and the maximum radial movement distance of the impeller 30 relative to the cylindrical body 21 is defined as L, where L ≤ Δd / n, where n is a number greater than or equal to 1.5, such as 2; and D2 + L ≤ D1. This can reduce or even prevent blood entering from the liquid inlet 11 from impacting the first surface 301 of the impeller 30, causing the impeller 30 to significantly tilt.

[0084] Among them, the maximum movement distance L of the impeller 30 relative to the cylindrical body 21 in the radial direction can be specifically the gap between the first straight annular surface portion 3032 and the cylindrical body 21 when the central axis OO' of the main channel 31 coincides with the central axis of the cylindrical body 21, or it can be twice the gap between the first straight annular surface portion 3032 and the cylindrical body 21, or it can be other values.

[0085] The difference between the minimum diameter of the inner wall surface 303 of the impeller 30 and the maximum diameter of the guide cone 20 is the difference between the diameter of the first straight annular surface portion 3032 and the diameter of the cylindrical body 21 .

[0086] Optionally, D1 ≤ D2 + Δd. If the diameter of the first opening 3011 of the impeller 30 is significantly larger than the diameter of the liquid inlet 11, blood entering through the liquid inlet 13 is likely to flow along the second cavity wall 132 and become stagnant, increasing the likelihood of thrombosis and hemolysis, while also reducing the operating efficiency of the ventricular assist device 1. Therefore, ensuring D1 ≤ D2 + Δd can help alleviate the problem of blood stagnation on the inner wall of the pump housing 10 near the liquid inlet 11.

[0087] like Figure 1 and Figure 2As shown, optionally, the ventricular assist device 1 further includes a first liquid inlet pipe 51, a first liquid outlet pipe 52, and a connecting elbow 53. The first liquid inlet pipe 51 is fixedly connected to the first liquid outlet pipe 52, and the axes of the first liquid inlet pipe 51 and the first liquid outlet pipe 52 are parallel. The first liquid outlet pipe 52 is connected to the pump housing 10, and the first liquid outlet pipe 52 is connected to the liquid outlet 12. The connecting elbow 53 is connected between the pump housing 10 and the first liquid inlet pipe 51, and the connecting elbow 53 connects the first liquid inlet pipe 63 and the liquid inlet 11. The inner diameter of the first liquid inlet pipe 51 is equal to the inner diameter of the first liquid outlet pipe 52; the inner diameter of the portion of the connecting elbow 53 away from the first liquid inlet pipe 51 is larger than the inner diameter of the first liquid inlet pipe 51.

[0088] The inner diameter of one end of the connecting elbow 53 connected to the first liquid inlet pipe 51 may be equal to the inner diameter of the first liquid inlet pipe 51 , which facilitates the connection between the connecting elbow 53 and the first liquid inlet pipe 51 .

[0089] The first liquid inlet pipe 51 and the first liquid outlet pipe 52 can be connected in parallel. The axis of the first liquid outlet pipe 52 can be the same as the axis of the liquid outlet 12. In other embodiments, the first liquid inlet pipe 51 and the first liquid outlet pipe 52 can also be connected in a sleeve manner, for example, the first liquid outlet pipe 52 is sleeved on the outer periphery of the first liquid inlet pipe 51.

[0090] Compared with the first liquid inlet pipe 51 and the first liquid outlet pipe 52 being arranged along different axes, or the first liquid inlet pipe 51 and the first liquid outlet pipe 52 being arranged independently, in the present application, the first liquid inlet pipe 51 and the first liquid outlet pipe 52 are fixedly connected, and the axes of the first liquid inlet pipe 51 and the first liquid outlet pipe 52 are parallel, which is conducive to the first liquid inlet pipe 51 and the first liquid outlet pipe 52 entering the patient's heart through an opening, the first liquid inlet pipe 51 entering the ventricular cavity, and the first liquid outlet pipe 52 entering the corresponding arterial blood vessel. Therefore, there is no need to open the arterial blood vessel, nor is there a need to connect the first liquid outlet pipe 52 and the arterial blood vessel through an artificial blood vessel, which is conducive to reducing damage to the arterial blood vessel.

[0091] At the same time, when the flow rate of the ventricular assist device 1 is mainly limited by the inner diameters of the first liquid inlet pipe 51, the first liquid outlet pipe 52 and the connecting elbow 53, since the curved part of the connecting elbow 53 will produce flow loss, the inner diameter of the part of the connecting elbow 53 away from the first liquid inlet pipe 51 is larger than the inner diameter of the first liquid inlet pipe 51 to compensate for the flow loss caused by the curved part; at the same time, the inner diameters of the first liquid inlet pipe 51 and the first liquid outlet pipe 52 are equal, which can make the flow rates in the first liquid inlet pipe 51, the first liquid outlet pipe 52 and the connecting elbow 53 basically equal, thereby ensuring the stability of the blood flow rate, reducing the flow resistance, and thus helping to improve the pumping efficiency of the ventricular assist system.

[0092] Optionally, the first liquid inlet pipe 51 , the first liquid outlet pipe 52 and the connecting elbow 53 may all be made of metal or alloy materials, for example, biocompatible stainless steel or biocompatible nickel-titanium alloy.

[0093] Optionally, the end of the connecting elbow 53 away from the liquid inlet 11 has a first connecting portion 530. The pump housing 10 has a second connecting portion 100, and the liquid outlet 12 is opened in the second connecting portion 100.

[0094] The outer contours of the first connecting portion 530 and the second connecting portion 100 are roughly the same. The first connecting portion 530 is connected to the second connecting portion 100 and forms the outer contour of a symmetrical double-arch rectangle, wherein the double-arch rectangle refers to a rectangle in which two opposite sides are arc sides and the other two opposite sides are straight sides.

[0095] The ventricular assist device 1 also includes an adapter 54 having a double-arched rectangular opening 540 and sealingly extending between the first connecting portion 530 and the second connecting portion 100. The inlet tube 51 is sealedly connected to the adapter 54 and the first connecting portion 530, while the outlet tube 52 is sealedly connected to the adapter 54 and the second connecting portion 100.

[0096] Specifically, the connecting elbow 53 is welded to the pump housing 10; the adapter 54 is welded and sleeved on the first connecting portion 530 of the connecting elbow 53 and the second connecting portion 100 of the pump housing 10; the liquid inlet pipe 51 and the liquid outlet pipe 52 are integrally formed, the liquid inlet pipe 51 is welded to the adapter 54 and the first connecting portion 530, and the liquid outlet pipe 52 is welded to the adapter 54 and the second connecting portion 100. This connection method is conducive to preventing leakage of the ventricular assist device 1. At the same time, the addition of the adapter 54 can enhance the connection stability of the liquid inlet pipe 51 and the liquid outlet pipe 52 to the first connecting portion 530 and the second connecting portion 100. The first connecting portion 530 is connected to the second connecting portion 100 and forms a symmetrical double-arch rectangular outer contour. The adapter 54 correspondingly has a double-arch rectangular opening 540, making the structure of the adapter 54 simpler and easier to process.

[0097] Optionally, the connecting elbow 53 includes a first tube shell 531 and a second tube shell 532, and the first tube shell 531 and the second tube shell 532 are sealed together. Specifically, the sealing connection can be achieved by welding, bonding, etc. The first tube shell 531 is covered on the outside of the pump housing 10. Specifically, the first tube shell 531 is covered on the outside of the pump housing 10. The second fixed magnetic ring 52 is located between the first tube shell 531 and the pump housing 10, and the first tube shell 531 and the pump housing 10 are sealed together. This is conducive to protecting the second fixed magnetic ring 52. At the same time, compared with protecting the second fixed magnetic ring 52 by cooperating with other components and the pump housing 10, in this application, protecting the second fixed magnetic ring 52 by cooperating with the pump housing 10 of the first tube shell 531 of the connecting elbow 53 is conducive to reducing parts and thus reducing the weight of the ventricular assist device 1.

[0098] Optionally, ventricular assist device 1 further includes an extension hose 55, which is connected to the end of outlet tube 52 away from outlet port 12. The internal flow channel of extension hose 55 communicates with the internal flow channel of outlet tube 52. Extension hose 55 is made of a softer material than outlet tube 52. When inlet tube 51 and outlet tube 52 are inserted through and fixed to the heart wall, inlet tube 51 is located within the ventricular cavity, and extension hose 55 can extend into the artery.

[0099] Alternatively, as Figure 9 As shown, the extension hose 55 includes a first connecting section 551 and a first extension section 552. The first connecting section 551 is made of metal or alloy, such as biocompatible stainless steel or biocompatible nickel-titanium alloy; the first extension section 552 is made of a polymer material, such as PTFE (polytetrafluoroethylene); the first connecting section 551 and the first extension section 552 are integrally formed, and the first connecting section 551 is connected to the liquid outlet pipe 52. The first connecting section 551 and the liquid outlet pipe 52 can be fixedly connected by, but not limited to, welding. Optionally, the extension hose 55 is a round tube, and the end of the liquid outlet pipe 52 near the extension hose 55 is also a round tube for easier connection.

[0100] Since the aorta or pulmonary artery usually has a certain physiological curvature, the hard outlet tube 52 directly extending into the aorta or pulmonary artery can easily cause damage to the aorta or pulmonary artery. Therefore, by adding an extension hose 55, when the inlet tube 51 and the outlet tube 52 are passed through and fixed to the heart wall, the inlet tube 51 is located in the ventricular cavity, and the extension hose 55 can be extended into the aorta or pulmonary artery, thereby avoiding scratches on the aorta or pulmonary artery.

[0101] Optionally, the first extension section 552 includes a soft rubber layer 5521 and a metal wire layer 5522, with the metal wire layer 5522 disposed within the soft rubber layer 5521. This facilitates bending of the extension hose 55, and the metal wire layer 5522 provides a certain degree of support, thereby reducing or even preventing the extension hose 55 from collapsing inward and affecting normal bleeding. Furthermore, the metal wire layer 5522 does not directly contact the aorta or pulmonary artery, thereby preventing the metal wire layer 5522 from scratching the aorta or pulmonary artery.

[0102] The metal wire layer 5522 can be a biocompatible nickel-titanium wire. In other embodiments, the metal wire layer 5522 can also be other metal wires.

[0103] Optionally, the metal wire layer 5522 includes at least two metal wires, each of which extends in a wavy pattern along the axial direction of the extension hose 55; and / or, each of which extends in a wavy pattern along the circumference of the extension hose 55, with adjacent metal wires affixed to each other. Adjacent metal wires may be affixed via connectors or welding, or the entire metal wire layer 5522 may be integrally formed. Compared to a method where the metal wires are not connected, in this embodiment, affixing adjacent metal wires further strengthens the support for the extension hose 55, preventing the extension hose 55 from collapsing inward and affecting normal bleeding.

[0104] The second embodiment is similar to the first embodiment, but differs in that the inlet pipe 51 and the connecting elbow 53 are integrally formed, and the connecting elbow 53 and the liquid outlet pipe 52 are both welded to the pump housing 10, and the inlet pipe 51 and the liquid outlet pipe 52 are connected by welding. Since welding the connecting elbow 53 and the inlet pipe 51 will result in a protrusion or depression at the connection, which can easily cause thrombosis, hemolysis, etc., the inlet pipe 51 and the connecting elbow 53 are integrally formed, reducing the protrusion or depression formed by the connection between the connecting elbow 53 and the inlet pipe 51. Therefore, the probability of blood entering the pump housing 10 through the inlet pipe 51 and the connecting elbow 53 and causing thrombosis or hemolysis can be reduced. In other embodiments, the connecting elbow 53 and the liquid outlet pipe 52 can also be connected by welding.

[0105] like Figure 10 and Figure 11As shown, the third embodiment is similar to the first embodiment, but differs in that the ventricular assist device 1 does not have a connecting elbow 53. Instead, the ventricular assist device 1 includes a second liquid inlet pipe 56 and a second liquid outlet pipe 57. The second liquid outlet pipe 57 includes a pipe body 571 and a connecting shell 572. The connecting shell 572 is connected to the pipe body 571 and forms a channel 573 therebetween. The channel 573 is parallel to the axis of the pipe body 571. The pipe body 571 is connected to the pump housing 10 and communicates with the liquid outlet 12. The second liquid inlet pipe 56 is connected to the pump housing 10 and communicates with the liquid inlet 11. The second liquid inlet pipe 56 extends through the channel 573. The hardness of the second liquid inlet pipe 56 is less than that of the second liquid outlet pipe 57.

[0106] Among them, compared with the aforementioned embodiment, blood needs to pass through the first liquid inlet pipe 51 and the connecting elbow 53 in sequence to enter the pump housing 10. When the first liquid inlet pipe 51 and the connecting elbow 53 are connected by welding, the connection between the connecting elbow 53 and the first liquid inlet pipe 51 is not very smooth, which can easily cause thrombosis, hemolysis and the like. In this embodiment, the second liquid inlet pipe 56 is an integrated structure, which reduces the protrusions or depressions formed by the connection between the connecting elbow 53 and the liquid inlet pipe 51, thereby reducing the probability of thrombosis, hemolysis and the like.

[0107] Among them, since the second liquid inlet pipe 56 is at least partially in a bent state, the hardness of the second liquid inlet pipe 56 is less than the hardness of the liquid inlet pipe 51, which is conducive to the second liquid inlet pipe 56 being in a bent state and not easily cracked.

[0108] Among them, since the hardness of the second liquid inlet pipe 56 is less than that of the second liquid outlet pipe 57, the second liquid outlet pipe 57 is penetrated into the heart wall, has better guidance, and is more convenient to be fixed to the heart wall. Therefore, the second liquid inlet pipe 56 is penetrated into the channel 573 of the second liquid outlet pipe 57.

[0109] Optionally, the second liquid inlet tube 56 includes a second connecting section 561 and a second extension section 562 in communication with the second connecting section 561. The second connecting section 561 is fixedly connected to the pump housing 10 and communicates with the liquid inlet 11. The second connecting section 561 and the pump housing 10 may be fixedly connected by, but not limited to, welding. The second connecting section 561 is made of metal or an alloy, such as biocompatible stainless steel or biocompatible nickel-titanium alloy; the second extension section 562 is made of a polymer material, such as PTFE (polytetrafluoroethylene); and the second connecting section 561 and the second extension section 562 are integrally formed.

[0110] Optionally, the second liquid outlet tube 57 is made of metal or alloy material, for example, biocompatible stainless steel or biocompatible nickel-titanium alloy.

[0111] Optionally, the pump housing 10 is made of metal or alloy, for example, biocompatible stainless steel, nickel-titanium alloy, or the like.

[0112] It should be noted that the second liquid inlet pipe 56 has a certain degree of support. The second liquid inlet pipe 56 may have a support member inside, or the material of the second liquid inlet pipe 56 itself may have support after being processed under preset processing conditions, so that the second liquid inlet pipe 56 is not easy to collapse into the inside of the pipe and affect the cross-sectional area of ​​its internal flow channel.

[0113] In some embodiments, since the liquid outlet pipe 52 and the liquid outlet port 12 have the same axis, at least the portion of the liquid inlet pipe 51 away from the liquid inlet port 11 is fixedly connected to the liquid outlet pipe 52, and the axis of at least the portion of the liquid inlet pipe 51 away from the liquid inlet port 11 is parallel to the axis of the liquid outlet pipe 52, when the diameters of the liquid inlet pipe 51 and the liquid outlet pipe 52 are small, it is necessary to set the liquid outlet port 12 in the area of ​​the annular wall 133 close to the second cavity wall 132. Therefore, if Figure 4 and Figure 6 As shown, the pressurizing chamber 13 further has a guide wall 134 , which extends from the first chamber wall 131 to the liquid outlet 12 , and the distance from the guide wall 134 to the first chamber wall 131 gradually increases in a direction away from the first chamber wall 131 .

[0114] The connection between the guide wall 134 and the first cavity wall 131 is rounded, that is, there is a smooth transition between the guide wall 134 and the first cavity wall 131. Compared with a stepped transition or an angled transition between the guide wall 134 and the first cavity wall 131, the rounded connection between the guide wall 134 and the first cavity wall 131 ensures smoother blood flow through the guide wall 134 and the first cavity wall 131, and reduces the risk of hemolysis and thrombosis.

[0115] Furthermore, the difference between the diameter of the first straight annular surface portion 3032 and the diameter of the cylindrical body 21 is defined as Δd; the maximum radial movement distance of the impeller 30 is defined as L, where 0 < L ≤ Δd; and when the central axis OO' of the main flow channel 31 coincides with the central axis of the cylindrical body 21, as shown in FIG. Figure 4 As shown, the minimum distance between the orthographic projection 304a of the outer wall 304 on the first cavity wall 131 and the guide wall 134 is T. When the central axis OO' of the main channel coincides with the central axis of the cylindrical body 21, L / 2 < T. Therefore, during the impeller 30's suspended rotation, the impeller 30 will not contact the guide wall 134, thereby preventing the impeller 30 from rolling due to contact with the guide wall 134. L can be Δd / 3, Δd / 2, or Δd, etc.

[0116] In the above embodiments, the description of each embodiment has its own focus. For parts that are not described in detail in a certain embodiment, reference can be made to the relevant descriptions of other embodiments.

[0117] The above is an implementation method of the embodiment of the present application. It should be pointed out that for ordinary technicians in this technical field, several improvements and modifications can be made without departing from the principles of the embodiment of the present application. These improvements and modifications are also considered to be within the scope of protection of the present application.

Claims

1. A ventricular assist device, characterized in that: include: A pump housing having a liquid inlet, wherein a guide cone is fixedly provided in the pump housing, the guide cone being opposite to the liquid inlet, and the guide cone having a guide surface opposite to the liquid inlet; An impeller is disposed in the pump housing so as to be suspended and rotatable, the impeller having a first surface and a second surface opposite to each other, the first surface being closer to the liquid inlet than the second surface, the impeller further having a main channel running through the first surface and the second surface, and a branch channel communicating with the main channel, the main channel being opposite to the liquid inlet, the branch channel extending in a radial direction of the main channel, the impeller further having an inner wall surface defining the main channel, the inner wall surface connecting the first surface and the second surface, the inner wall surface having a drainage surface portion, the drainage surface portion having a first end close to the first surface and a second end close to the second surface, the distance from the first end to the central axis of the main channel being greater than the distance from the second end to the central axis of the main channel; In which, the guide cone is located in the main channel, and when the impeller is suspended and rotated, there is a gap between the guide cone and the inner wall surface, the guide surface is close to the second end of the drainage surface portion, and the position of the guide surface corresponds to the position of the branch channel, so that the liquid flowing into the main channel can be drained to the guide surface through the drainage surface portion, and then diverted from the guide surface to the branch channel.

2. The ventricular assist device according to claim 1, wherein Along the central axis of the main flow channel and in a direction approaching the second surface of the impeller, a distance from the guide surface portion to the central axis of the main flow channel gradually decreases.

3. The ventricular assist device according to claim 1, wherein When the impeller rotates in suspension, the second end of the drainage surface portion is closer to the liquid inlet than the edge of the guide surface, wherein the central axis of the main flow channel coincides with the central axis of the guide cone: The virtual extension surface of the drainage surface intersects with the guide surface; Alternatively, the intersection of the virtual extended surface of the drainage surface portion and the virtual extended surface of the guide surface is located in the gap between the inner wall surface of the impeller and the guide cone.

4. The ventricular assist device according to claim 1, wherein The inner wall surface of the impeller also has a first straight annular surface portion, which is arranged along the central axis of the main channel with the drainage surface portion. The first straight annular surface portion is closer to the second surface than the drainage surface portion. Along the central axis of the main channel, the diameter of the first straight annular surface portion is constant, and the first straight annular surface portion surrounds the guide cone.

5. The ventricular assist device according to claim 4, wherein: The drainage surface portion is arranged around the central axis of the main flow channel, the second end of the drainage surface portion is connected to the first straight annular surface portion, and a fillet is provided at the connection between the drainage surface portion and the first straight annular surface portion.

6. The ventricular assist device according to claim 4, wherein: The inner wall surface of the impeller further comprises a second straight annular surface portion, the diameter of the second straight annular surface portion being constant along the central axis of the main flow channel and being larger than the diameter of the first straight annular surface portion; the drainage surface portion connects the first straight annular surface portion and the second straight annular surface portion; The impeller includes a first annular disk, a second annular disk and a support plate, the first annular disk and the second annular disk are coaxial and spaced apart, there are multiple support plates, and the multiple support plates are spaced apart along the circumference of the first annular disk and evenly arranged between the first annular disk and the second annular disk to form multiple branch channels, the first annular disk and the second annular disk are both provided with a accommodating cavity for accommodating magnetic material, the inner annular surface of the first annular disk, the inner side surfaces of the multiple support plates and the inner annular surface of the second annular disk jointly define the main flow channel, the first surface is the surface of the first annular disk facing away from the second annular disk, the second surface is the surface of the second annular disk facing away from the first annular disk, the first straight annular surface is the inner annular surface of the second annular disk, the second straight annular surface is the inner annular surface of the first annular disk, and the diversion surface is the inner side surfaces of the multiple support plates.

7. The ventricular assist device according to claim 4, wherein: The guide cone comprises a cylindrical body and a conical head fixed to one end of the cylindrical body, an end of the cylindrical body away from the conical head being fixed to the pump housing, a central axis of the cylindrical body coinciding with a central axis of the liquid inlet, the conical head being coaxial with the cylindrical body, a cone top of the conical head facing the liquid inlet, the guide surface being the conical surface of the conical head, and the first straight annular surface surrounding the cylindrical body; The main channel has a first opening located on the first surface, the diameter of the first opening is defined as D1, the diameter of the liquid inlet is defined as D2, the difference between the diameter of the first straight annular surface portion and the diameter of the cylindrical body is defined as △d, and the maximum radial movement distance of the impeller relative to the cylindrical body is defined as L, wherein L≤△d / n, n is a number greater than or equal to 1.5, and D2+L≤D1.

8. The ventricular assist device according to claim 7, wherein: D1≤D2+△d.

9. The ventricular assist device according to claim 1, wherein: The ventricular assist device further has at least one of the following features: The impeller further has an outer wall surface, and the branch channel runs through the outer wall surface and the inner wall surface; The branch channel is located between the first surface and the second surface of the impeller; The ventricular assist device further includes a drive assembly capable of driving the impeller to rotate in suspension; The guide surface is a conical surface or an arc-shaped conical surface, and the guide surface has a cone top, which faces the liquid inlet.

10. The ventricular assist device according to claim 1, wherein The pump casing has a boosting chamber, and the impeller is arranged in the boosting chamber so as to be suspended and rotatable. The boosting chamber is connected to the liquid inlet, and the boosting chamber has a first chamber wall opposite to the liquid inlet. The guide cone is arranged on the first chamber wall, and the guide surface is a conical surface or an arc-shaped conical surface. The guide surface has a cone top and an edge away from the cone top, and the cone top faces the liquid inlet. The diverter has a bottom surface close to the second surface and a top surface opposite to the bottom surface. When the impeller is suspended and rotated, the distance from the edge of the guide surface to the first chamber wall is greater than the distance from the bottom surface of the diverter to the first chamber wall, and is less than the distance from the top surface of the diverter to the first chamber wall.

11. The ventricular assist device according to claim 10, wherein: The virtual extended surface at the edge of the guide surface is perpendicular to the central axis of the guide surface.

12. The ventricular assist device according to claim 1, wherein The ventricular assist device further includes a liquid inlet tube, a liquid outlet tube and a connecting elbow; The liquid inlet pipe is fixedly connected to the liquid outlet pipe, and the axes of the liquid inlet pipe and the liquid outlet pipe are parallel; The pump housing further has a liquid outlet, the liquid outlet pipe is connected to the pump housing, and the liquid outlet pipe is in communication with the liquid outlet; The connecting elbow is connected between the pump housing and the liquid inlet pipe, and the connecting elbow communicates with the liquid inlet pipe and the liquid inlet; The inner diameter of the liquid inlet pipe is equal to the inner diameter of the liquid outlet pipe; the inner diameter of the portion of the connecting elbow away from the liquid inlet pipe is larger than the inner diameter of the liquid inlet pipe.

13. The ventricular assist device according to claim 1, wherein The ventricular assist device further includes a fluid inlet tube and a fluid outlet tube; The liquid outlet pipe includes a pipe body and a connecting shell, the connecting shell is connected to the pipe body and forms a channel with the pipe body, the channel is parallel to the axis of the pipe body, the pump housing further has a liquid outlet, the pipe body is connected to the pump housing, and the pipe body is in communication with the liquid outlet; The liquid inlet pipe is connected to the pump housing and communicates with the liquid inlet, and the liquid inlet pipe is arranged in the channel; Wherein, the hardness of the liquid inlet pipe is smaller than the hardness of the liquid outlet pipe.

14. The ventricular assist device according to claim 13, wherein: The liquid inlet pipe includes a first connecting section and a first extension section connected to the first connecting section. The first connecting section is fixed to the pump housing and connected to the liquid inlet. The first connecting section is made of metal or alloy, and the first extension section includes a high molecular polymer material. The first connecting section and the first extension section are an integrally formed structure.

15. The ventricular assist device according to any one of claims 12 to 14, characterized in that: The ventricular assist device further includes an extension hose; The extension hose is connected to one end of the liquid outlet tube away from the liquid outlet, and the extension hose is communicated with the liquid outlet tube, wherein the material of the extension hose is softer than that of the liquid outlet tube; when the liquid inlet tube and the liquid outlet tube are passed through and fixed to the heart wall, the liquid inlet tube is located in the ventricular cavity, and the extension hose can be extended into the artery.

16. The ventricular assist device according to claim 15, wherein: The extension hose includes a second connecting section and a second extending section. The second connecting section is made of metal or alloy, the second extending section is made of a polymer material, the second connecting section and the second extending section are an integrally formed structure, and the second connecting section is connected to the liquid outlet pipe.

17. The ventricular assist device according to claim 16, wherein: The second extension section includes a soft rubber layer and a metal wire layer, and the metal wire layer is arranged in the soft rubber layer.

18. The ventricular assist device according to claim 17, wherein: The metal wire layer includes at least two metal wires, and the at least two metal wires extend in a wave shape along the axial direction of the extension hose; and / or the at least two metal wires extend in a wave shape along the circumferential direction of the extension hose, and adjacent metal wires are fixedly connected.

19. The ventricular assist device according to claim 1, wherein The pump housing further comprises a boost chamber and a liquid outlet communicating with the boost chamber, the boost chamber being communicated with the liquid inlet, the boost chamber comprising a first chamber wall, a second chamber wall, and an annular wall, the first chamber wall and the second chamber wall being spaced apart and opposed to each other, the annular wall connecting the first chamber wall and the second chamber wall, the liquid inlet being located in the second chamber wall, the guide cone being located in the first chamber wall, the liquid outlet being located in the annular wall, and the impeller being rotatably and suspendably disposed in the boost chamber; The pressurizing chamber further comprises a guide wall, which extends from the first chamber wall to the liquid outlet, and the distance between the guide wall and the first chamber wall gradually increases in a direction away from the first chamber wall.

20. The ventricular assist device according to claim 19, wherein The guide cone comprises a cylindrical body and a conical head fixed to one end of the cylindrical body, an end of the cylindrical body away from the conical head being fixed to the pump housing, a central axis of the cylindrical body coincides with a central axis of the liquid inlet, the conical head is coaxial with the cylindrical body, the top of the conical head faces the liquid inlet, and the guide surface is the conical surface of the conical head; The inner wall surface of the impeller further comprises a first straight annular surface portion, the first straight annular surface portion and the flow guide surface portion being arranged along the central axis of the main flow channel, the first straight annular surface portion being closer to the second surface than the flow guide surface portion, the diameter of the first straight annular surface portion being constant along the central axis of the main flow channel, and the first straight annular surface portion surrounding the guide cone; The impeller has an outer wall surface, and the branch channel runs through the outer wall surface and the inner wall surface; The difference between the diameter of the first straight annular surface portion and the diameter of the cylindrical body is defined as △d, the maximum radial movement distance of the impeller is defined as L, 0<L≤△d, and the minimum distance between the orthographic projection of the outer wall surface on the first cavity wall and the guide wall when the central axis of the main channel coincides with the central axis of the cylindrical body is defined as T; wherein, when the central axis of the main channel coincides with the central axis of the cylindrical body, L / 2<T.

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