Blood pumps and ventricular assist systems

Abstract

The blood pump (10) and ventricular assist system include a pump case (11) having a housing cavity (112), a conduit assembly (13), and an impeller (15). The conduit assembly (13) includes a liquid discharge tube (133) communicating with the housing cavity (112) and having a liquid outlet (1332), and further includes a liquid inlet (1312) communicating with the housing cavity (112). The conduit assembly (13) is capable of being drilled into the ventricular wall to position the liquid inlet (1312) within the ventricle, and the liquid discharge tube (133) has a certain length so that, when the conduit assembly (13) is drilled into the ventricle wall, the liquid discharge tube (133) can be extended through the ventricle until it drills through the aortic valve to position the liquid outlet (1332) in the aorta. The impeller (15) is rotatably housed in the housing cavity (112).

Description

[Technical Field]

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS This application claims priority from a Chinese patent application bearing application number 202211580636.9, filed with the State Intellectual Property Office of China on December 9, 2022, the entire contents of which are incorporated herein by reference.

[0002] This application relates to the field of medical devices, and more particularly to blood pumps and ventricular assist systems. [Background technology]

[0003] A blood pump is a device connected between the ventricle and blood vessels to assist patients with severe ventricular dysfunction or heart failure by providing a constant blood flow and blood pressure. Conventional blood pumps require an artificial blood vessel outside the heart to connect to the aorta, so a hole must be opened in the aorta to transport blood from the ventricle to the aorta via the blood pump and artificial blood vessel. However, opening a hole in the aorta is likely to cause aortic diseases such as dissection and hematoma, and the surgery is difficult, so improvements are needed. Summary of the Invention [Problem to be solved by the invention]

[0004] Based on this, the present application provides a blood pump and a ventricular assist system that avoids aortic diseases caused by aortic perforation and reduces the difficulty of surgery.

[0005] An embodiment of a first aspect of the present application provides a blood pump, the blood pump comprising: a pump case having a storage cavity; a conduit assembly including a liquid discharge tube communicating with the storage cavity and having a liquid outlet, and a liquid inlet communicating with the storage cavity, the liquid inlet being capable of being drilled into a ventricular wall so that the liquid inlet is located within the ventricle, the liquid discharge tube having a certain length such that when the conduit assembly is drilled into the ventricular wall, the liquid discharge tube can be extended through the ventricle until it drills through the aortic valve so that the liquid outlet is located in the aorta; An impeller is rotatably accommodated within the accommodation cavity, thereby causing liquid that has entered the accommodation cavity through the liquid inlet to flow through the liquid discharge pipe and out of the liquid outlet.

[0006] An embodiment of a second aspect of the present application provides a ventricular assist system including a blood pump, the blood pump comprising: a pump case having a storage cavity; a conduit assembly including a liquid discharge tube communicating with the storage cavity and having a liquid outlet, and a liquid inlet communicating with the storage cavity, the liquid inlet being capable of being drilled into a ventricular wall so that the liquid inlet is located within the ventricle, the liquid discharge tube having a certain length such that when the conduit assembly is drilled into the ventricular wall, the liquid discharge tube can be extended through the ventricle until it drills through the aortic valve so that the liquid outlet is located in the aorta; An impeller is rotatably accommodated within the accommodation cavity, thereby causing liquid that has entered the accommodation cavity through the liquid inlet to flow through the liquid discharge pipe and out of the liquid outlet.

[0007] The details of one or more embodiments of the invention are set forth in the accompanying drawings and the description below. Other features, objects, and advantages of the invention will become apparent from the description, accompanying drawings, and claims.

[0008] In order to more clearly explain the technical aspects of the embodiments of the present application, the following briefly introduces drawings that may be used in the description of the embodiments or prior art. The accompanying drawings in the following description are merely some embodiments of the present application, and those skilled in the art may obtain other accompanying drawings from these accompanying drawings without any creative effort. [Brief explanation of the drawings]

[0009] [Figure 1] 1 is a schematic diagram illustrating the configuration of a blood pump provided in a first embodiment of the present invention. [Figure 2] FIG. 2 is a plan view of the blood pump shown in FIG. [Figure 3] FIG. 3 is a cross-sectional view taken along the direction AA in FIG. 2. [Figure 4] FIG. 3 is a cross-sectional view taken along the direction BB in FIG. 2. [Figure 5] FIG. 2 is an exploded view of the blood pump shown in FIG. 1, observed from one angle. [Figure 6] FIG. 2 is an exploded view of the blood pump shown in FIG. 1, observed from another angle. [Figure 7] FIG. 2 is a side view of the blood pump shown in FIG. [Figure 8] FIG. 8 is a cross-sectional view taken along the CC direction in FIG. [Figure 9] FIG. 2 is an exploded view of the bottom shell and impeller of the blood pump shown in FIG. 1. [Figure 10] FIG. 2 is an assembly view of the bottom shell and impeller of the blood pump shown in FIG. 1. [Figure 11] FIG. 11 is a cross-sectional view taken along the DD direction in FIG. [Figure 12] FIG. 2 is a diagram showing the configuration of the blood pump shown in FIG. 1 after the drive motor is assembled. [Figure 13] FIG. 8 is a cross-sectional view taken along the EE direction in FIG. 7. [Figure 14] FIG. 10 is a structural diagram of a blood pump provided in a second embodiment of the present invention. [Figure 15] FIG. 15 is a cross-sectional view taken along the FF direction in FIG. [Figure 16] FIG. 15 is a partial exploded view of the blood pump shown in FIG. 14. DETAILED DESCRIPTION OF THE INVENTION

[0010] In order to make the object, technical features and advantages of the present application clearer and easier to understand, the present application will be described in more detail below with reference to the accompanying drawings, i.e., examples. It should be understood that the specific examples described herein are merely for the purpose of illustrating the present application and are not intended to limit the present application.

[0011] It should be noted that when an element is referred to as being "fixed" or "mounted" to another element, it may be mounted directly or indirectly to the other element. When an element is referred to as being "connected" to another element, it may be connected directly or indirectly to the other element.

[0012] Additionally, the terms "first" and "second" are for descriptive purposes only and should not be understood as expressing or suggesting relative importance and implicitly indicating the number of technical features shown. Therefore, a feature identified by "first" or "second" expresses or suggests that one or more of the feature is included. In the description of this application, "plurality" means two or more, unless otherwise specified.

[0013] In order to explain the technical aspects of the present application, the following description will be given with reference to the accompanying drawings and examples.

[0014] As used herein, the end closest to the healthcare professional is defined as the "proximal end" and the end farther from the healthcare professional is defined as the "distal end."

[0015] 1 to 3, the present invention provides a blood pump 10, which includes a pump case 11 having a storage cavity 112, a conduit assembly 13, and an impeller 15. The conduit assembly 13 has a first liquid flow path 136 and a second liquid flow path 138, both of which communicate with the storage cavity 112. The first liquid flow path 136 has a first opening remote from the storage cavity 112, and the second liquid flow path 138 has a second opening remote from the storage cavity 112. The conduit assembly 13 is capable of passing through a first organ, and when the conduit assembly 13 is inserted through the first organ, the first opening is located within the first organ and communicates with the first organ. The conduit assembly 13 has a certain length (specifically, the length here means the length in the extension direction of the conduit assembly 13), and due to this length of the conduit assembly 13, when the conduit assembly 13 is inserted through a first organ, the conduit assembly 13 can extend through the inside of the first organ to a second organ that is in communication with the first organ, and the second opening can be in communication with the second organ. The impeller 15 is rotatably housed in the storage cavity 112, and causes liquid that enters the storage cavity 112 from one of the first opening and the second opening to flow out through the other of the first opening and the second opening.

[0016] When the conduit assembly 13 of the blood pump 10 of the present invention is inserted into a first organ, the first opening is located within the first organ and communicates with the first organ. The conduit assembly 13 has a certain length L1, allowing it to extend through the interior of the first organ and into a second organ connected to the first organ, thereby connecting the second opening to the second organ. As the impeller 15 rotates, liquid flows into the housing cavity 112 through one of the first and second openings and out through the other of the first and second openings. This allows for pumping of liquid from the first organ to the second organ or vice versa without the need for external artificial tubing. In other words, the blood pump 10 described above can fulfill the auxiliary pumping function for blood without requiring a hole in the second organ, while avoiding diseases caused by holes in the second organ. Furthermore, according to the blood pump 10 described above, there is no need for external artificial piping, and therefore there is no need to prepare a route for arranging the artificial piping, thereby reducing the difficulty of the surgery.

[0017] A first embodiment of the present invention will be described with reference to FIGS. 1 to 3, with the left ventricle of the heart being the first organ and the aorta being the second organ.

[0018] The blood pump 10 of the first embodiment of the present invention includes a pump case 11 having a storage cavity 112, a conduit assembly 13, and an impeller 15. The conduit assembly 13 includes a liquid discharge tube 133 communicating with the storage cavity 112 and having a liquid outlet 1332. Specifically, the liquid outlet 1332 is a second opening for liquid to flow out, and a second liquid flow path 138 is a passage for liquid to flow out. The conduit assembly 13 further includes a liquid inlet 1312 communicating with the storage cavity 112. Specifically, the liquid inlet 1312 is a first opening for liquid to enter. The first liquid flow path 136 is an inlet passage for liquid to flow in. The conduit assembly 13 can be drilled into a ventricular wall. When the conduit assembly 13 is drilled into the ventricular wall, the liquid inlet 1312 is located within the ventricle and communicates with the ventricle. The liquid discharge pipe 133 has a certain length L1, and due to the length L1 of the liquid discharge pipe 133, when the conduit assembly 13 is drilled into the ventricular wall, the liquid discharge pipe 133 can be extended through the ventricle until it drills through the aortic valve so that the liquid outlet 1332 is positioned in the aorta and communicates with the aorta. The impeller 15 is rotatably housed in the housing cavity 112, so that the liquid that enters the housing cavity 112 from the liquid inlet 1312 passes through the liquid discharge pipe 133 and flows out from the liquid outlet 1332.

[0019] Here, the length L1 means the length of the liquid discharge pipe 133 in the extension direction.

[0020] The liquid discharge pipe 133 of the blood pump 10 provided by the present invention has a certain length L1. Due to the length L1 of the liquid discharge pipe 133, when the blood pump 10 is attached to the left ventricle, the pump case 11 is located outside the heart, the conduit assembly 13 is drilled into the ventricular wall, the liquid inlet 1312 is located inside the left ventricle, and the liquid discharge pipe 133 extends through the ventricle until it drills through the aortic valve, so that the liquid outlet 1332 is located in the aorta. Therefore, as the impeller 15 rotates, blood in the ventricle is sucked into the receiving cavity 112 through the liquid inlet 1312 and flows into the aorta through the liquid outlet 1332, thereby realizing the blood in the ventricle being pumped into the aorta. That is, the blood in the left ventricle can be pumped to the aorta without the need for external artificial tubing. That is, the above-described blood pump 10 satisfies the auxiliary pumping function of blood without requiring a hole in the aorta, and can avoid aortic diseases such as dissection and hematoma caused by surgical hole in the aorta. Furthermore, the above-described blood pump 10 does not require an external artificial tubing, so there is no need to prepare a route for the artificial tubing, reducing the difficulty of surgery and eliminating the problem of blood leakage due to the connection of an artificial blood vessel. Furthermore, because the heart and other organs in the thoracic cavity are in close contact with each other, the blood pump 10 provided by the present invention allows the conduit assembly 13 to extend directly from the ventricle to the aorta, eliminating the need to connect a circumscribed artificial blood vessel, significantly reducing the space occupied in the thoracic cavity and avoiding other diseases caused by contact between the artificial blood vessel and other organs.

[0021] The storage cavity 112 has a first cavity surface 1121 and a second cavity surface 1122 opposite to the first cavity surface 1121, and the impeller 15 is provided between the first cavity surface 1121 and the second cavity surface 1122. That is, the first cavity surface 1121 and the second cavity surface 1122 are provided on opposite sides of the impeller 15 and are installed facing two surfaces of the impeller 15, respectively.

[0022] In this embodiment, the pump case 11 is further provided with a drain cavity 114 that communicates with the liquid discharge pipe 133 and the storage cavity 112, and the liquid that enters the storage cavity 112 from the liquid inlet 1312 can flow through the drain cavity 114 into the liquid discharge pipe 133. Specifically, the storage cavity 112 and the drain cavity 114 are arranged along the axial direction of the impeller 15, and the drain cavity 114 is closer to the first cavity surface 1121 than to the second cavity surface 1122.

[0023] 4 to 6, the pump case 11 includes a bottom shell 118 having a storage cavity 112. The pump case 11 further includes a top shell 116, and the top shell 116 and the bottom shell 118 are connected to each other to collectively enclose a liquid discharge cavity 114. The top shell 116 is connected to a liquid discharge pipe 133.

[0024] The top shell 116 includes a body 1162 and a flange 1164. The body 1162 is fitted over the bottom shell 118, and the outer circumferential surface of the body 1162 is flush with the outer circumferential surface of the bottom shell 118. The body 1162 is provided with an outflow hole 1166 that communicates with the drainage cavity 114, and the flange 1164 protrudes from the body 1162 and surrounds the outflow hole 1166. The flange 1164 is an annular wall and is coaxial with the outflow hole 1166. The flange 1164 is connected to the liquid drain pipe 133, and the outflow hole 1166 communicates with the liquid drain pipe 133. Here, liquid that flows out of the drainage cavity 114 flows through the outflow hole 1166 to the liquid drain pipe 133 and finally flows out from the liquid outlet 1332.

[0025] 7 to 9, the bottom shell 118 is generally worm-shell shaped. The bottom shell 118 includes a first shell wall 1181 and a second shell wall 1182 facing the first shell wall 1181, and the storage cavity 112 is located between the first shell wall 1181 and the second shell wall 1182. Here, the first cavity surface 1121 is provided on the first shell wall 1181, and the second cavity surface 1122 is provided on the second shell wall 1182. That is, the impeller 15 is located between the first shell wall 1181 and the second shell wall 1182. The first shell wall 1181 is connected to the top shell 116 and, together with the top shell 116, encloses the drainage cavity 114.

[0026] The bottom shell 118 further has a peripheral wall that is connected to both the first shell wall 1181 and the second shell wall 1182 and that, together with the first shell wall 1181 and the second shell wall 1182, encloses the storage cavity 112. The peripheral wall has an inner periphery 1184.

[0027] In one embodiment, the inner peripheral surface 1184 is an involute surface. Here, an involute surface means a surface that extends according to an involute curve. In a plan view direction (i.e., the axial direction of the impeller 15), the plan view of the inner peripheral surface 1184 is approximately in the shape of an involute curve.

[0028] A guide protrusion 1186 is provided within the drainage cavity 114. The position of the guide protrusion 1186 corresponds to the position of the opening of the liquid discharge pipe 133 at one end side remote from the liquid outlet 1332, so that the liquid within the drainage cavity 114 is guided to the liquid discharge pipe 133 and flows out through the liquid outlet 1332. Specifically, the guide protrusion 1186 protrudes from the shell wall of the bottom shell 118, more specifically, from the first shell wall 1181. A guide surface 1185, which is a tapered surface, is provided on the outer periphery of the guide protrusion 1186 so that the liquid within the drainage cavity 114 can be guided out. The guide surface 1185 may be the entire outer periphery of the guide protrusion 1186, or may be a part of the outer periphery of the guide protrusion 1186. In this embodiment, the position of the guide protrusion 1186 corresponds approximately to the position of the impeller 15, so that the position where the liquid flows in through the conduit assembly 13 and the position where the liquid flows out through the conduit assembly 13 can be relatively concentrated. Since both the liquid inlet 1312 and the liquid outlet 1332 are installed on the conduit assembly 13, the position of the guide protrusion 1186 corresponds approximately to the position of the impeller 15, which contributes to the miniaturization of the conduit assembly 13 and facilitates attachment of the conduit assembly 13 to the aortic valve. In this embodiment, the guide protrusion 1186 has a substantially dish-shaped configuration. In other embodiments, the guide protrusion 1186 may have a truncated cone or bicone shape, etc., as long as it can discharge the liquid from the drainage cavity 114.

[0029] The bottom shell 118 further includes a connecting pipe portion 1187, which is disposed within the drainage cavity 114 and communicates with the first liquid flow path 136. Specifically, the connecting pipe portion 1187 protrudes from the guide protrusion 1186. The position of the connecting pipe portion 1187 corresponds to the position of the opening of the liquid discharge pipe 133 at one end away from the liquid outlet 1332, allowing the liquid in the drainage cavity 114 to flow through the guide protrusion 1186 and the connecting pipe portion 1187 to the liquid outlet 1332. More specifically, the connecting pipe portion 1187 protrudes from the center of the guide protrusion 1186. In this embodiment, the connecting pipe portion 1187 has a generally hollow cylindrical shape. In other embodiments, the connecting pipe portion 1187 may have other shapes, such as a generally hollow rectangular parallelepiped shape, and the specific configuration may be determined according to actual circumstances.

[0030] The bottom shell 118 is further provided with a liquid circulation hole 1188, which communicates with the connecting pipe portion 1187 and penetrates the shell wall of the bottom shell 118 and the guide protrusion 1186. In this embodiment, the liquid circulation hole 1188 may be a circular hole that penetrates the center of the guide protrusion 1186. In other embodiments, the liquid circulation hole 1188 may penetrate other positions on the guide protrusion 1186, and the liquid circulation hole 1188 may also be a square hole, a triangular hole, an elliptical hole, or other type of hole, and specific configurations may be determined according to actual circumstances.

[0031] The bottom shell 118 includes a first shell 1189 and a second shell 1180, which are joined together to form the storage cavity 112. The first shell 1189 is connected to the top shell 116. The placement of the first shell 1189 and the second shell 1180 facilitates loading of the impeller 15 into the storage cavity 112.

[0032] Referring to FIG. 5 , a communication passage 119 that connects the storage cavity 112 and the drainage cavity 114 is provided in the pump case 11, and liquid in the storage cavity 112 can flow through the connecting passage 119 to flow out of the drainage cavity 114. Specifically, the communication passage 119 is disposed in the bottom shell 118. The communication passage 119 has a connecting surface that connects the second cavity surface 1122 and the drainage cavity 114, and at least a portion of the connecting surface is a guide slope 1191. The guide slope 1191 is used to guide the liquid in the storage cavity 112 to the drainage cavity 114. The guide slope 1191 can guide the liquid to flow from the storage cavity 112 to the drainage cavity 114. In this embodiment, the distance from the guide slope 1191 to the second cavity surface 1122 gradually increases from the end closest to the storage cavity 112 to the end remote from the storage cavity 112. Specifically, the guide slope 1191 connects the surface of the second shell wall 1182 facing the first shell wall 1181 with the surface of the first shell wall 1181 facing the drainage cavity 114.

[0033] Specifically, the second cavity surface 1122 is provided on the side of the second shell wall 1182 facing the first shell wall 1181. Here, the second cavity surface 1122 may be the entire surface of the second shell wall 1182 facing the first shell wall 1181, or may be a part of the surface of the second shell wall 1182 facing the first shell wall 1181. The surface of the first shell wall 1181 facing the drainage cavity 114 is the surface opposite the first cavity surface 1121 of the first shell wall 1181.

[0034] Note that the guide slope 1191 may be the entire connecting surface connecting the second cavity surface 1122 and the drainage cavity 114, or may be a part of the connecting surface. For example, in some embodiments, the guide slope 1191 is a portion of the connecting surface adjacent to the drainage cavity 114, in some embodiments, the guide slope 1191 is a portion of the connecting surface adjacent to the storage cavity 112, and in some embodiments, the guide slope 1191 is an intermediate portion of the connecting surface in the extension direction of the communication flow path 119.

[0035] 9 to 11, the angle θ between the guide slope 1191 and the surface of the second shell wall 1182 facing the first shell wall 1181 is 135° to 155°. In this embodiment, θ decreases once along the direction of liquid flow, then increases, and remains constant between 135° and 155°, thereby improving the stability of the liquid flow. In another embodiment, θ is a constant value between 135° and 155° along the direction of liquid flow, thereby improving the stability of the liquid flowing from the storage cavity 112 to the drainage cavity 114, enabling the blood pump 10 to be made smaller, and reducing the burden on the heart. If θ exceeds 155° under the condition that the distance between the surface of the second shell wall 1182 facing the first shell wall 1181 and the first cavity surface 1121 is constant, the length of the guide slope 1191 must be increased to connect the surface of the second shell wall 1182 facing the first shell wall 1181 and the first cavity surface 1121, thereby increasing the volume of the bottom shell 118 and the volume of the blood pump 10. If θ is less than 135°, the flow rate of the liquid into the drain cavity 114 will be slow, which is unfavorable for a stable flow of the liquid.

[0036] In this embodiment, the width of the communicating channel 119 gradually decreases along the direction of liquid flow. In the illustrated embodiment, the direction of liquid flow refers to the direction in which the liquid flows from the storage cavity 112 through the connecting passage 119 to the drainage cavity 114. By gradually decreasing the width of the communicating channel 119 along the direction of liquid flow, the liquid is gradually constricted along the direction of liquid flow, increasing the flow rate of the liquid to the drainage cavity 114, reducing the adverse effects of gravity on the liquid, and improving the flow rate and speed of blood pumping. In one embodiment, the width of the communicating channel 119 decreases linearly, but in another embodiment, the width of the communicating channel 119 decreases nonlinearly, for example, exponentially.

[0037] In this embodiment, as shown in Figure 11, the communicating channels 119 extend along quadratic and higher-order Bezier curves to improve the stability of the liquid flow and achieve a more stable blood pumping flow field. In one embodiment, the communicating channels 119 may extend along a circular arc. In another embodiment, the communicating channels 119 may extend along a diagonal line, which may accelerate the flow rate of the liquid into the drainage cavity 114 and thereby improve the flow rate and speed of the blood pumping.

[0038] In this embodiment, the width of communicating channel 119 gradually decreases along the direction of liquid flow, and the angle θ between guide slope 1191 and the surface of second shell wall 1182 facing first shell wall 1181 is between 135° and 155°. In one embodiment, the width of communicating channel 119 gradually decreases along the direction of liquid flow, and the angle θ between guide slope 1191 and the surface of second shell wall 1182 facing first shell wall 1181 is not limited. In another embodiment, the width of communicating channel 119 is not limited along the direction of liquid flow, and the angle θ between guide slope 1191 and the surface of second shell wall 1182 facing first shell wall 1181 is between 135° and 155°.

[0039] Communication channel 119 further has first side surface 1195 and second side surface 1197, both of which are connected to guide slope 1191. A rounded corner α is provided at the connection between first side surface 1195 and guide slope 1191, and a rounded corner β (shown in FIG. 9 ) is provided at the connection between second side surface 1197 and guide slope 1191. The provision of the rounded corners reduces sharp edges at the connection and can reduce hemolysis. The radii of rounded corners α and β may be 0.1 mm to 0.5 mm. However, if the radii of rounded corners α and β are less than 0.1 mm, the improvement in hemolysis is insignificant. If the radii of rounded corners α and β are more than 0.5 mm, the outflow of blood is hindered, and the pumped blood flow rate is likely to be too low. In other embodiments, the connection between the first side surface 1195 and the guide slope 1191 and the connection between the second side surface 1197 and the guide slope 1191 do not need to have rounded corners, but may be set specifically according to the actual situation.

[0040] First side surface 1195 is connected to one end of inner circumferential surface 1184, and second side surface 1197 is connected to the other end of inner circumferential surface 1184, where a rounded corner γ (shown in FIG. 8) is formed at the connection between first side surface 1195 and inner circumferential surface 1184. The radius of rounded corner γ is 0.2 mm to 0.5 mm. If the radius of rounded corner γ is less than 0.2 mm, a sharp corner will be formed at the connection between inner circumferential surface 1184 and first side surface 1195, making hemolysis more likely to occur. If the radius of rounded corner γ is more than 0.5 mm, blood outflow will be hindered and the pumped blood flow rate will be reduced.

[0041] In this embodiment, the second side surface 1197 is also an involute surface, that is, the second side surface 1197 has a substantially involute curved shape in plan view. In other embodiments, the second side surface 1197 may be an arcuate surface.

[0042] 1, 4, and 5, the conduit assembly 13 is connected to the pump case 11, the liquid inlet 1312 is located at a proximal end of the conduit assembly 13 relative to the liquid outlet 1332 and is used for the entry of liquid (e.g., blood), and the liquid outlet 1332 is located at a distal end of the conduit assembly 13 and is used for the exit of liquid. The liquid outlet 1332 communicates with the drainage cavity 114, allowing the conduit assembly 13 to have both the functions of liquid inflow and liquid discharge, i.e., liquid can enter the pump case 11 through the conduit assembly 13 and can also exit through the conduit assembly 13.

[0043] The liquid discharge pipe 133 is connected to the pump case 11 and communicates with the storage cavity 112. For example, the liquid discharge pipe 133 is connected to the flange 1164 of the top shell 116, and the liquid in the discharge cavity 114 flows along the inner circumferential surfaces of the flange 1164 and the liquid discharge pipe 133 to the liquid discharge pipe 133 and then out through the liquid outlet 1332. In this embodiment, the inner circumferential surface of the liquid discharge pipe 133 may be flush with the inner circumferential surface of the flange 1164 so that the liquid can more stably and smoothly flow out of the discharge cavity 114. The liquid inlet 1312 is exposed to the outer circumferential surface of the liquid discharge pipe 133, and the liquid outlet 1332 is installed in the liquid discharge pipe 133.

[0044] The liquid discharge tube 133 can be drilled into the ventricular wall and can extend from the pump case 11 to the aortic valve so that the liquid outlet 1332 is positioned in the aorta, thereby allowing blood in the storage cavity 112 to enter the aorta through the liquid outlet 1332 and transporting blood in the ventricle from inside the heart to the aorta.

[0045] The liquid discharge pipe 133 has a liquid discharge pipe chamber 1334 which communicates with the liquid outlet 1332 and the storage cavity 112 , specifically, the drain cavity 114 communicates with the liquid outlet 1332 through the liquid discharge pipe chamber 1334 .

[0046] 3 and 12, in this embodiment, the conduit assembly 13 includes a first tube section 137 and a second tube section 139, both of which are installed in the liquid discharge tube 133. The first tube section 137 is connected between the second tube section 139 and the pump case 11, the liquid inlet 1312 is installed in the first tube section 137, and the liquid outlet 1332 is installed in the second tube section 139. In this embodiment, the outer diameter of the first tube section 137 is larger than the outer diameter of the second tube section 139, i.e., the outer diameter of the distal end of the liquid discharge tube 133 is smaller than the outer diameter of the proximal end of the conduit assembly 13, thereby reducing damage to the aorta caused by the liquid discharge tube 133. In this embodiment, the second tubular section 139 is provided with a transition section 1391 connected to the first tubular section 137, and the outer diameter of the transition section 1391 gradually decreases along the direction from the first tubular section 137 to the second tubular section 139, thereby avoiding the generation of sharp edges and facilitating safe insertion of the conduit assembly 13 into the ventricle. In this embodiment, the generating line of the transition section 1391 may be a circular arc line or a quadratic Bezier curve, and in other embodiments, the generating line of the transition section 1391 may be a diagonal line.

[0047] In this embodiment, the conduit assembly 13 further includes a liquid inlet pipe 131, the liquid inlet 1312 is connected to the liquid inlet pipe 131, at least a portion of the liquid inlet pipe 131 is disposed within the liquid outlet pipe 133, and the length of the liquid inlet pipe 131 is shorter than the length of the liquid outlet pipe 133. Specifically, at least a portion of the liquid inlet pipe 131 is disposed within the first pipe section 137, and in one embodiment, the entire liquid inlet pipe 131 is located within the liquid outlet pipe 133. In another embodiment, a portion of the liquid inlet pipe 131 is located within the liquid outlet pipe 133, and the remaining portion protrudes from the liquid outlet pipe 133.

[0048] A liquid flow path 134 is formed between the liquid inlet pipe 131 and the liquid outlet pipe 133, and at least a portion of the liquid flow path 134 is located between the liquid inlet pipe 131 and the first pipe portion 137. In this embodiment, the inner circumferential surface of the liquid inlet pipe 131 surrounds the first liquid flow path 136, and the liquid flow path 134 becomes a second liquid flow path 138, which communicates with both the liquid outlet 1332 and the storage cavity 112. Liquid can flow from the liquid inlet 1312 into the liquid inlet pipe 131, then pass through the storage cavity 112 and the liquid flow path 134 in order, and flow out from the liquid outlet 1332.

[0049] 3, 6 and 9, the liquid inlet tube 131 is connected to the pump case 11, specifically to the first shell wall 1181 of the bottom shell 118, and is connected to the receiving cavity 112, with the liquid inlet 1312 communicating with the liquid inlet tube 131. In this embodiment, the liquid inlet tube 131 is connected to the connecting tube portion 1187 in the drainage cavity 114, thereby separating the first liquid flow path 136 and the second liquid flow path 138 so that the liquid flow in the first liquid flow path 136 and the liquid flow in the second liquid flow path 138 do not affect each other, thereby improving the smoothness and stability of liquid inflow and discharge and increasing the flow rate and speed of blood pumping. The liquid inlet pipe 131 is connected to the connecting pipe portion 1187 in the drainage cavity 114 and communicates with the liquid flow hole 1188, so that the liquid in the drainage cavity 114 flows along the outer peripheral surface of the connecting pipe portion 1187 and the outer peripheral surface of the liquid inlet pipe 131 to the liquid discharge pipe 133 and flows out from the liquid outlet 1332. In this embodiment, the outer peripheral surface of the liquid inlet pipe 131 may be flush with the outer peripheral surface of the connecting pipe portion 1187 so that the liquid flows out of the drainage cavity 114 more stably and smoothly. In other embodiments, the bottom shell 118 may not include the connecting pipe portion 1187, and the end of the liquid inlet pipe 131 close to the pump case 11 may protrude from the liquid outlet pipe 133 and be connected to the guide protrusion 1186, or the liquid inlet pipe 131 may be inserted directly into the storage cavity 112 without being connected to the guide protrusion 1186, but either way will allow the liquid to enter the storage cavity 112 through the liquid inlet pipe 131.

[0050] The liquid inlet pipe 131 is connected to the liquid circulation hole 1188, and the liquid circulation hole 1188 passes through the center of the guide protrusion 1186, so that the position where the liquid flows in through the pipe assembly 13 and the position where the liquid flows out through the pipe assembly 13 can be relatively concentrated, which contributes to the miniaturization of the pipe assembly 13.

[0051] In this embodiment, the liquid inlet 1312 is connected to the liquid inlet tube 131 but not to the liquid outlet tube chamber 1334, and the liquid outlet tube chamber 1334 is connected to the liquid outlet 1332. Therefore, the flow of liquid entering the liquid inlet tube 131 from the liquid inlet 1312 and the flow of liquid flowing out from the liquid outlet tube chamber 1334 to the liquid outlet 1332 do not affect each other, improving the smoothness and stability of liquid inflow and discharge, and improving the flow rate and speed of blood pumping.

[0052] In this embodiment, there are multiple liquid inlets 1312, which are arranged circumferentially perpendicular to the axis of the liquid discharge pipe 133 and are all exposed to the outer surface of the liquid discharge pipe 133. All of the multiple liquid inlets 1312 are connected to the liquid inlet pipe 131, so that liquid that enters through any of the multiple liquid inlets 1312 can also flow into the storage cavity 112. Even if one liquid inlet 1312 is blocked by the ventricular wall when blood enters, blood can enter the ventricle through the remaining liquid inlets 1312, thereby realizing normal inflow and outflow of blood.

[0053] In this embodiment, there are two liquid inlets 1312, and the two liquid inlets 1312 are arranged opposite each other. This allows the forces acting on the blood pump 10 to be relatively balanced while the liquid enters the blood pump 10 through the two liquid inlets 1312, thereby preventing tilting due to an imbalance of forces. In one embodiment, the positions of the two liquid inlets 1312 do not need to correspond to each other. In another embodiment, there may be only one liquid inlet 1312, which can be specifically determined according to the actual situation.

[0054] Referring to FIG. 13, in this embodiment, the inner diameter of the liquid inlet pipe 131 at one end adjacent to the receiving cavity 112 is d, and the total cross-sectional area S of the liquid flow passage 134 at one end adjacent to the receiving cavity 112 is S=πd 2 / 4, i.e., the sum of the areas of the two annular sectors shown in FIG. 13 is equal to the area of ​​the inner cross section of the liquid inlet pipe 131. In this way, the cross-sectional area of ​​the liquid inlet region is equal to the cross-sectional area of ​​the liquid outlet region, and the flow rate of the liquid entering the blood pump 10 and the flow rate of the liquid outflowing from the blood pump 10 are approximately the same, improving the stability of the flow rate of the pumped blood.

[0055] The conduit assembly 13 further includes a connecting member 135, which is connected between the liquid inlet pipe 131 and the liquid outlet pipe 133 and is used to fix the liquid inlet pipe 131 inside the liquid outlet pipe 133. In this embodiment, there are two connecting members 135, which are installed along the circumferential direction of the liquid inlet pipe 131 and located at both radial ends of the liquid inlet pipe 131. In other embodiments, the number of connecting members 135 may be one or three or more, as long as the purpose of fixing the liquid inlet pipe 131 inside the liquid outlet pipe 133 is met.

[0056] Continuing to refer to FIG. 6 , the connecting member 135 includes a connecting bottom surface 1352 and a connecting side surface 1354 that are connected to each other. The connecting bottom surface 1352 faces the drainage cavity 114, allowing liquid flowing out of the drainage cavity 114 to contact the connecting bottom surface 1352. The connecting side surface 1354 faces the inner wall of the liquid discharge pipe 133, allowing liquid flowing out of the drainage cavity 114 to contact the connecting side surface 1354. In this embodiment, a rounded corner δ (shown in FIG. 6 ) is provided at the connection between the connecting bottom surface 1352 and the connecting side surface 1354 to reduce hemolysis. For example, the radius of the rounded corner δ may be 0.1 mm to 0.5 mm. In other embodiments, the radius of the rounded corner δ may be other values ​​and is not limited thereto.

[0057] In other embodiments, the conduit assembly 13 may not include the liquid inlet pipe 131, i.e., the conduit assembly 13 may include only the liquid outlet pipe 133. The liquid outlet pipe 133 includes a first liquid flow path 136 and a second liquid flow path 138 separated by a partition plate, and the partition plate is connected to the inner wall of the liquid outlet pipe 133, where the first liquid flow path 136 communicates with the liquid inlet 1312 and the second liquid flow path 138 communicates with the liquid outlet 1332. This also makes it possible for the liquid that enters the storage cavity 112 from the liquid inlet 1312 to pass through the liquid outlet pipe 133 and flow out from the liquid outlet 1332 when the impeller 15 rotates.

[0058] The impeller 15 is rotatably housed within the storage cavity 112, so that liquid entering the storage cavity 112 from the liquid inlet 1312 is transported to the liquid outlet 1332 through the liquid discharge cavity 114. A rotor (not shown) is provided within the impeller 15, and the rotor can be linked to a stator of a drive motor. When the stator drives the rotor to rotate within the storage cavity 112, the impeller 15 also follows the rotor and rotates synchronously within the storage cavity 112. For the specific configuration of the impeller 15, please refer to the prior art.

[0059] The blood pump 10 further includes a drive motor 17 connected to the pump case 11 on the side remote from the conduit assembly 13, and the drive motor 17 is in transmission communication with the impeller 15 to rotate the impeller 15. For example, the drive motor 17 includes a stator that is magnetically coupled to a rotor in the impeller 15 and rotates the rotor, thereby rotating the impeller 15.

[0060] Next, a second embodiment of the present invention will be described, with the left ventricle of the heart being the first organ and the aorta being the second organ.

[0061] 14 to 16, a blood pump 20 according to a second embodiment of the present invention includes a pump case 21, a conduit assembly 23, and an impeller 25. The pump case 21 is provided with a storage cavity 212. The conduit assembly 23 includes a liquid discharge pipe 233 communicating with the storage cavity 212. The liquid discharge pipe 233 is connected to the pump case 21 and is provided with a liquid outlet 2332. Specifically, the liquid outlet 2332 serves as a second opening for liquid to flow out. The conduit assembly 23 further includes a liquid inlet 2312 communicating with the storage cavity 212. Specifically, the liquid inlet 2312 serves as a first opening for liquid to flow in. The conduit assembly 23 can be drilled into a ventricle wall. When the conduit assembly 23 is drilled into the ventricle wall, the liquid inlet 2312 is located within the ventricle and communicates with the ventricle. The liquid discharge pipe 233 has a certain length L2, and due to the length L2 of the liquid discharge pipe 233, when the conduit assembly 23 is drilled into the ventricular wall, the liquid discharge pipe 233 can be extended through the ventricle until it drills through the aortic valve so that the liquid outlet 2332 is positioned in the aorta and communicates with the aorta. The impeller 25 is rotatably housed in the housing cavity 212, and causes the liquid that has entered the housing cavity 212 from the liquid inlet 2312 to flow out through the liquid outlet 2332.

[0062] Unlike the blood pump 10, the pump case 21 of the blood pump 20 includes at least a portion of an arc-shaped outer circumferential surface, and the liquid discharge pipe 233 extends from the pump case 21 along a tangential direction of the arc-shaped outer circumferential surface. This allows the blood pump 20 to discharge liquid along a tangential direction of the arc-shaped outer circumferential surface of the pump case 21 by rotation of the impeller 25. Furthermore, the blood pump 20 does not include a top shell 116 (FIG. 5). The liquid discharge pipe 233 is connected to the bottom shell 218, which does not include a guide slope 1191 (FIG. 13). Therefore, blood that enters the storage cavity 212 through the liquid inlet 2312 is transported directly to the liquid outlet 2332 of the liquid discharge pipe 233 by rotation of the impeller 25, and flows to the aorta without passing through other components such as the drain cavity 114 (FIG. 3). This allows for smoother blood transport and an increased blood pumping flow rate.

[0063] The blood pump 20 includes a liquid inlet tube 231 connected to the pump case 21 and installed outside the liquid outlet tube 233, the liquid inlet tube 231 communicating with the housing cavity 212, and a liquid inlet 2312 communicating with the liquid inlet tube 231. The liquid inlet tube 231 extends from the pump case 21 in a curved manner in a direction approaching the liquid outlet tube 233, so that when the liquid outlet tube 233 is drilled into the ventricular wall, the liquid inlet tube 231 can also be drilled into the ventricular wall so that the liquid inlet 2312 is located within the ventricle. This eliminates the need to drill a separate hole in the heart to insert the liquid inlet tube 231, and also makes it possible to pump blood from the ventricle to the aorta without an artificial blood vessel, thereby avoiding the need for a hole in the aorta.

[0064] The liquid inlet 2312 is provided on the liquid inlet tube 231 and communicates with the receiving cavity 212 through the lumen of the liquid inlet tube 231, the liquid outlet tube 233 is provided outside the liquid inlet tube 231, and the liquid outlet 2332 communicates with the receiving cavity 212 through the lumen of the liquid outlet tube 233. That is, the liquid inlet tube 231 and the liquid outlet tube 233 of the blood pump 20 are independent of each other, and their lumen do not communicate with each other. The inner wall of the liquid inlet tube 231 surrounds the first liquid flow path, and the inner wall of the liquid outlet tube 233 surrounds the second liquid flow path.

[0065] In this embodiment, the liquid inlet pipe 231 extends from the pump case 21 to the liquid outlet pipe 233 so that the direction of the liquid inlet pipe 231 matches the direction of the liquid outlet pipe 233, thereby facilitating a fixed connection between the subsequent liquid inlet pipe 231 and the liquid outlet pipe 233, so that when the liquid outlet pipe 233 pierces the aortic valve, the liquid inlet pipe 231 can pierce the ventricular wall.

[0066] The conduit assembly 23 further includes a connection sleeve 234 that can be drilled into the ventricular wall, and the connection sleeve 23 has a first connection hole 2341 and a second connection hole 2342 that are spaced apart, and the liquid discharge pipe 233 is drilled into the first connection hole 2341, for example, the liquid discharge pipe 233 passes through the first connection hole 2341 and extends in a direction away from the pump case 21. The liquid inlet pipe 231 is connected to the connection sleeve 234 and communicates with the second connection hole 2342, and the liquid inlet 2312 is one opening of the second connection hole 2342, i.e., the liquid inlet 2312 may be provided in the connection sleeve 234. Alternatively, the liquid inlet tube 231 may be drilled through the second connecting hole 2342, the liquid inlet 2312 may be provided on the liquid inlet tube 231, and the end of the liquid inlet tube 231 remote from the pump case 21 may be flush with the end face of the connecting sleeve 234 or may protrude from the end face of the connecting sleeve 234. The connecting sleeve 234 is used to secure the liquid inlet tube 231 and the liquid outlet tube 233, and when installing the blood pump 20, simply inserting the connecting sleeve 234 into the ventricular wall allows both the liquid inlet tube 231 and the liquid outlet tube 233 to be inserted therein, eliminating the need to insert the liquid inlet tube 231 separately into the heart wall, thereby reducing the difficulty of the surgery.

[0067] The blood pump 20 further includes a drive motor 27 connected to the pump case 21, and the drive motor 27 is rotatably joined to the impeller 25 to rotate the impeller 25.

[0068] In one embodiment, both blood pump 10 and blood pump 20 can be used for the right ventricle, i.e., the right ventricle of the heart is the first organ and the pulmonary artery is the second organ. The first opening is a liquid inlet 1312 for liquid to enter, the second opening is a liquid outlet 1332 for liquid to exit, the first liquid flow path 136 is surrounded by the inner circumferential surface of the liquid inlet tube 131 (or liquid inlet tube 231), and the second liquid flow path 138 is surrounded by the outer circumferential surface of the liquid inlet tube 131 and the inner circumferential surface of the liquid outlet tube 133, or is surrounded only by the inner circumferential surface of the liquid outlet tube 233. That is, when the blood pump 10 is attached to the right ventricle of the heart, the conduit assembly 13 can be drilled into the pulmonary valve so that the first opening is located in the right ventricle and the second opening is located in the pulmonary artery. This allows blood in the pulmonary artery to be pumped to the right ventricle without the need for a circumscribed artificial blood vessel. This avoids the need for a hole in the pulmonary artery, satisfies the need for auxiliary blood pumping, and prevents pulmonary artery disease caused by surgical hole in the pulmonary artery. In addition, there is no need to prepare a path for the artificial blood vessel, which reduces the difficulty of the surgery and also eliminates the problem of blood leakage caused by clamping and transferring the artificial blood vessel.

[0069] In other embodiments, blood pump 10 and blood pump 20 may be applied to other tissues similar to the heart, as long as they satisfy the objective of pumping fluid from a first organ to a second organ, or from a second organ to a first organ.

[0070] In view of the above, the present invention provides a blood pump 10 and a blood pump 20. The blood pump 10 includes a pump case 11 having a storage cavity 112, a conduit assembly 13, and an impeller 15. The conduit assembly 13 includes a liquid discharge tube 133 communicating with the storage cavity 112 and having a liquid outlet 1332, and further includes a liquid inlet 1312 communicating with the storage cavity 112. The conduit assembly 13 can be drilled into the ventricular wall to position the liquid inlet 1312 within the ventricle, and the liquid discharge tube 133 has a certain length L1 so that, when the conduit assembly 13 is drilled into the ventricular wall, the liquid discharge tube 133 can extend through the ventricle until it drills the aortic valve to position the liquid outlet 1332 in the aorta. The impeller 15 is rotatably housed within the housing cavity 112, and allows liquid that has entered the housing cavity 112 through the liquid inlet 1312 to flow through the liquid outlet 1332 and exit the liquid outlet 1332. The conduit assembly 13 is drilled into the ventricular wall so that the liquid inlet 1312 is located within the ventricle, and the liquid outlet 133 has a fixed length L1. Therefore, when the conduit assembly 13 is drilled into the ventricular wall, the liquid outlet 133 can be extended through the ventricle until it penetrates the aortic valve so that the liquid outlet 1332 is located in the aorta. This allows blood in the ventricle to be pumped to the aorta without the need for a circumscribed artificial blood vessel. In other words, the above-described blood pump 10 can fulfill the role of auxiliary blood pumping without requiring a hole in the aorta, and can avoid aortic diseases such as dissection and hematoma caused by a surgical hole in the aorta. Furthermore, the above-described blood pump 10 does not require an artificial blood vessel to be circumscribed, which eliminates the need to prepare a path for the artificial blood vessel, reducing the difficulty of the surgery and eliminating the problem of blood leakage due to the connection of the artificial blood vessel. Furthermore, since the heart and other organs in the thoracic cavity are in close contact with each other, the blood pump 10 provided by the present invention allows the conduit assembly 13 to extend directly from the ventricle to the aorta, eliminating the need for an artificial blood vessel to be circumscribed, significantly reducing the space occupied by the thoracic cavity and avoiding other diseases caused by contact between the artificial blood vessel and other organs.

[0071] The blood pumps 10 and 20 can also be used in the right ventricle, and can pump blood in the pulmonary artery to the right ventricle without the need for a circumscribed artificial blood vessel, thereby avoiding the need for pulmonary artery perforation, satisfying auxiliary blood pumping, avoiding pulmonary artery disease due to surgical perforation of the pulmonary artery, eliminating the need to prepare a path for the artificial blood vessel, reducing the difficulty of surgery, and eliminating the problem of blood leakage due to clamping and switching of the artificial blood vessel.The blood pump 20 can also be applied to other tissues similar to the heart, as long as it can pump fluid from a first organ to a second organ, or from a second organ to the first organ.

[0072] The present invention further provides a ventricular assist system (not shown) including the blood pump 10 (or blood pump 20). The ventricular assist system may further include a ventricular connection assembly (not shown) and a console (not shown), etc. The ventricular connection assembly is used to attach the blood pump 10 to the heart, and the console is electrically connected to the blood pump 10 to control the operation of the blood pump 10. The configurations or devices of the ventricular connection assembly and the console may be referred to in the prior art and are not specifically limited herein.

[0073] The ventricular assist system provided by the present invention includes a blood pump 10, which can prevent aortic diseases such as dissection and hematoma caused by perforation of the aorta during surgery, reduce the difficulty of surgery, and prevent the occurrence of other diseases caused by contact between the artificial blood vessel and other organs. Therefore, the ventricular assist system provided by the present invention can also reduce the difficulty of surgery and prevent the occurrence of other diseases caused by contact between the artificial blood vessel and other organs.

[0074] The above examples are merely for the purpose of explaining the technical aspects of the present invention and are not intended to limit the present invention. Although the present invention has been described in detail with reference to the above-mentioned embodiments, it should be understood by those skilled in the art that modifications may still be made to the technical aspects described in the above-mentioned embodiments, or equivalent replacements may be made to some of the technical features therein. Such modifications or replacements do not deviate from the essence of the corresponding technical aspects from the spirit and scope of the technical aspects in each embodiment of the present invention, and are all intended to be included in the protection scope of the present invention.

Claims

1. 1. A blood pump comprising: a pump case having a storage cavity; a conduit assembly including a liquid discharge tube communicating with the storage cavity and having a liquid outlet, and a liquid inlet communicating with the storage cavity, the liquid inlet being capable of being drilled into a ventricular wall so that the liquid inlet is located within the ventricle, the liquid discharge tube having a certain length so that when the conduit assembly is drilled into the ventricular wall, the liquid discharge tube can be extended through the ventricle until it drills through the aortic valve so that the liquid outlet is located in the aorta; an impeller that is rotatably housed within the housing cavity, thereby causing liquid that has entered the housing cavity from the liquid inlet to flow through the liquid discharge pipe and out of the liquid outlet.

2. 2. The blood pump according to claim 1, wherein the conduit assembly further comprises a liquid inlet pipe at least a portion of which is disposed within the liquid outlet pipe and communicates with the storage cavity, a liquid flow path is formed between the liquid inlet pipe and the liquid outlet pipe, the liquid flow path communicating with the storage cavity, and the liquid inlet is exposed to an outer circumferential surface of the liquid outlet pipe and communicates with the liquid inlet pipe.

3. 3. The blood pump according to claim 2, wherein the conduit assembly further comprises a connecting member connected between the liquid inlet pipe and the liquid outlet pipe, the connecting member having a connecting bottom surface and a connecting side surface connected to each other, the connecting bottom surface facing the receiving cavity, the connecting side surface connected to the inner surface of the liquid outlet pipe, and a rounded corner at the connecting portion between the connecting bottom surface and the connecting side surface.

4. The inner diameter of the liquid inlet pipe at one end adjacent to the storage cavity is d, and the total cross-sectional area S of the liquid flow passage at one end adjacent to the storage cavity is S = πd ２ 3. The blood pump according to claim 2, wherein the ratio of the rotational speed of the pump to the rotational speed of the blood is 1 / 4.

5. 3. The blood pump according to claim 2, wherein the liquid inlet is a plurality of liquid inlets, the plurality of liquid inlets are arranged along a circumferential direction perpendicular to the axis of the liquid outlet pipe, and all of the liquid inlets are exposed to the outer circumferential surface of the liquid outlet pipe, and all of the plurality of liquid inlets are connected to the liquid inlet pipe.

6. 6. The blood pump according to claim 5, wherein there are two liquid inlets, and the two liquid inlets are disposed opposite each other.

7. 3. The blood pump of claim 2, wherein the conduit assembly includes a first tube section and a second tube section, the first tube section is connected between the second tube section and the pump case, the liquid inlet is located in the first tube section, the liquid outlet is located in the second tube section, and the outer diameter of the first tube section is larger than the outer diameter of the second tube section.

8. 2. The blood pump according to claim 1, wherein the pump case further includes a drain cavity that connects the liquid discharge pipe to the storage cavity, and the liquid that has entered the storage cavity from the liquid inlet can flow into the liquid discharge pipe through the drain cavity.

9. 9. The blood pump according to claim 8, wherein the storage cavity has a first cavity surface and a second cavity surface opposite to the first cavity surface, the impeller is located between the first cavity surface and the second cavity surface, the drainage cavity is adjacent to the first cavity surface, a communication flow path is further provided in the pump case to communicate the storage cavity and the drainage cavity, the communication flow path has a connection surface connecting the second cavity surface and the drainage cavity, and at least a portion of the connection surface is a guide slope.

10. 9. The blood pump according to claim 8, wherein the pump case comprises a bottom shell and a top shell, the receiving cavity is disposed in the bottom shell, the top shell and the bottom shell are connected to each other to jointly enclose the drainage cavity, and the liquid drainage pipe is connected to the top shell.

11. 11. The blood pump of claim 10, wherein the bottom shell includes a first shell wall and a second shell wall opposite to the first shell wall, the storage cavity is located between the first shell wall and the second shell wall, the top shell and the first shell wall collectively surround the drainage cavity, and the bottom shell further includes a communicating passage communicating the storage cavity with the drainage cavity, the communicating passage having a guide slope connecting a surface of the second shell wall facing the first shell wall and a surface of the first shell wall facing the drainage cavity.

12. the communicating flow path further has a first side surface and a second side surface, both of which are connected to the guide slope, and a rounded corner is provided at a connection portion between the first side surface and the guide slope and at a connection portion between the second side surface and the guide slope; and / or a guide protrusion is further provided in the liquid discharge cavity, and the position of the guide protrusion corresponds to the position of an opening at one end of the liquid discharge tube away from the liquid outlet.

13. the communicating passage further includes a first side surface and a second side surface, both of which are connected to the guide slope; the bottom shell further includes a peripheral wall, which is connected to both the first shell wall and the second shell wall, thereby jointly enclosing the storage cavity; the peripheral wall includes an inner peripheral surface, one end of which is connected to the first side surface and the other end of which is connected to the second side surface; 12. The blood pump according to claim 11, wherein a rounded corner is formed at a connection between the inner circumferential surface and the first side surface, the radius of the rounded corner being 0.2 mm to 0.5 mm, and / or the inner circumferential surface and the second side surface are both involute surfaces.

14. 11. The blood pump according to claim 10, wherein the conduit assembly further comprises a liquid inlet pipe communicating with both the liquid inlet and the storage cavity, the bottom shell comprises a guide protrusion and a connecting pipe portion, the guide protrusion protruding from a shell wall of the bottom shell, the connecting pipe portion protruding from the guide protrusion and communicating with the liquid inlet pipe, the bottom shell further comprises a liquid communication hole communicating with the connecting pipe portion, the liquid communication hole penetrating the shell wall of the bottom shell and the guide protrusion so as to communicate the liquid inlet pipe with the storage cavity.

15. 12. The blood pump according to claim 11, wherein a width of the communicating flow path gradually narrows along the direction of flow of the liquid, and / or an angle θ between the guide inclined surface and a surface of the second shell wall facing the first shell wall is 135° to 155°.

16. 2. The blood pump according to claim 1, wherein the conduit assembly further comprises a liquid inlet pipe provided outside the liquid outlet pipe, the liquid inlet pipe communicating with the receiving cavity and the liquid inlet, and the liquid outlet pipe being provided outside the liquid inlet pipe.

17. 17. The blood pump of claim 16, wherein the liquid discharge pipe and the liquid inlet pipe are both connected to the pump case, the pump case having an outer peripheral surface that is at least partially arcuate, the liquid discharge pipe extending from the pump case along a tangent direction of the arcuate outer peripheral surface, and the liquid inlet pipe extending from the pump case in a curved manner in a direction approaching the liquid discharge pipe.

18. the conduit assembly further includes a connection sleeve that can be drilled into the ventricular wall, the connection sleeve having a first connection hole and a second connection hole that are spaced apart, and the liquid discharge tube is drilled into the first connection hole; 17. The blood pump according to claim 16, wherein the liquid inlet pipe is connected to the connecting sleeve and communicates with the second connecting hole, and the liquid inlet is one opening of the second connecting hole, or the liquid inlet pipe is drilled into the second connecting hole and the liquid inlet is provided in the liquid inlet pipe.

19. 1. A blood pump comprising: a pump case having a storage cavity; a conduit assembly having a first liquid flow path with a first opening away from the storage cavity and a second liquid flow path with a second opening away from the storage cavity, both of the first liquid flow path and the second liquid flow path communicating with the storage cavity, wherein the conduit assembly is insertable into a first organ, and when the conduit assembly is inserted into the first organ, the first opening is located within the first organ and communicates with the first organ, and the conduit assembly has a certain length so that when the conduit assembly is inserted into the first organ, the conduit assembly can extend through the inside of the first organ to a second organ communicating with the first organ, so that the second opening communicates with the second organ; an impeller that is rotatably housed within the housing cavity, thereby causing liquid that enters the housing cavity through one of the first opening and the second opening to flow out through the other of the first opening and the second opening.

20. 1. A ventricular assist system comprising: including a blood pump, The blood pump comprises: a pump case having a storage cavity; a conduit assembly including a liquid discharge tube communicating with the storage cavity and having a liquid outlet, and a liquid inlet communicating with the storage cavity, the liquid inlet being capable of being drilled into a ventricular wall so that the liquid inlet is located within the ventricle, the liquid discharge tube having a certain length such that when the conduit assembly is drilled into the ventricular wall, the liquid discharge tube can be extended through the ventricle until it drills through the aortic valve so that the liquid outlet is located in the aorta; an impeller rotatably housed within the housing cavity, causing liquid entering the housing cavity through the liquid inlet to flow through the liquid discharge tube and out of the liquid outlet.

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