Blood pump

Abstract

The application provides a blood pump, which comprises a pump shell, a pipeline assembly and an impeller, the pump shell is provided with a receiving cavity; the pipeline assembly comprises a liquid outlet pipe communicated with the receiving cavity, the liquid outlet pipe is provided with a liquid outlet, the pipeline assembly is further provided with a liquid inlet, the liquid inlet is communicated with the receiving cavity, the pipeline assembly can be arranged on the ventricular wall so that the liquid inlet is located in the ventricle, the liquid outlet pipe has a certain length, so that when the pipeline assembly is arranged on the ventricular wall, the liquid outlet pipe can extend to the aortic valve through the ventricle, and the liquid outlet is located in the aorta; the impeller is rotatably arranged in the receiving cavity, so that the liquid in the receiving cavity from the liquid inlet can flow out from the liquid outlet through the liquid outlet pipe. The blood pump provided by the application can pump the blood in the ventricle to the aorta without setting an artificial blood vessel, avoids the aortic diseases such as dissection and hematoma caused by the hole on the aorta, and reduces the operation difficulty. The application further provides a ventricular assist system.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and more specifically, to a blood pump and ventricular assist system. Background Technology

[0002] A blood pump is a device that connects the ventricles to blood vessels to assist patients with severe ventricular insufficiency or heart failure by providing a certain blood flow and blood pressure. Traditional blood pumps involve connecting an artificial blood vessel outside the heart to the aorta, requiring a hole to be made in the aorta to pump blood from the ventricles through the pump and the artificial blood vessel to the aorta. However, making a hole in the aorta can easily lead to aortic diseases such as aortic dissection and hematoma, and the surgery is also difficult, necessitating improvements. Summary of the Invention

[0003] The purpose of this invention is to provide a blood pump and ventricular assist system that avoids aortic disease caused by opening a hole in the aorta and reduces the difficulty of surgery. This invention achieves the above objective through the following technical solutions.

[0004] In a first aspect, the present invention provides a blood pump, comprising a pump housing, a conduit assembly, and an impeller. The pump housing has a receiving cavity. The conduit assembly includes a liquid outlet pipe communicating with the receiving cavity, the liquid outlet pipe having a liquid outlet. The conduit assembly also has a liquid inlet, the liquid inlet communicating with the receiving cavity. The conduit assembly can penetrate the ventricular wall so that the liquid inlet is located within the ventricle. The liquid outlet pipe has a certain length so that when the conduit assembly penetrates the ventricular wall, the liquid outlet pipe can extend through the ventricle to penetrate the aortic valve, so that the liquid outlet is located within the aorta. The impeller is rotatably received within the receiving cavity to allow liquid entering the receiving cavity from the liquid inlet to flow out from the liquid outlet via the liquid outlet pipe.

[0005] In one embodiment, the piping assembly further includes an inlet pipe, which is at least partially disposed within the outlet pipe. The inlet pipe communicates with the receiving cavity, and a liquid flow channel is formed between the inlet pipe and the outlet pipe. The liquid flow channel communicates the outlet and the receiving cavity. The inlet is exposed on the outer peripheral surface of the outlet pipe and communicates with the inlet pipe.

[0006] In one embodiment, the piping assembly further includes a connector connected between the inlet pipe and the outlet pipe. The connector includes a connected bottom surface and a connected side surface, the bottom surface facing the receiving cavity, and the side surface connected to the inner surface of the outlet pipe. The connection between the bottom surface and the side surface has a rounded corner.

[0007] In one embodiment, the inner diameter of the inlet pipe near the receiving cavity is d, and the total cross-sectional area of ​​the liquid flow channel near the receiving cavity is S = πd. 2 / 4.

[0008] In one embodiment, there are multiple liquid inlets, which are arranged circumferentially along the axis perpendicular to the liquid outlet pipe and are all exposed on the outer peripheral surface of the liquid outlet pipe. All of the multiple liquid inlets are in communication with the liquid inlet pipe.

[0009] In one embodiment, there are two liquid inlets, which are arranged opposite to each other.

[0010] In one embodiment, the pipeline assembly includes a first pipe section and a second pipe section, the first pipe section being connected between the second pipe section and the pump housing, the liquid inlet being disposed in the first pipe section, the liquid outlet being disposed in the second pipe section, and the outer diameter of the first pipe section being larger than the outer diameter of the second pipe section.

[0011] In one embodiment, the pump housing further has a liquid outlet chamber that connects the liquid outlet pipe and the receiving chamber, allowing liquid entering the receiving chamber from the liquid inlet to flow into the liquid outlet pipe via the liquid outlet chamber.

[0012] In one embodiment, the receiving 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 liquid outlet cavity is close to the first cavity surface, and the pump casing is further provided with a connecting channel connecting the receiving cavity and the liquid outlet cavity, the connecting channel having a connecting surface connecting the second cavity surface and the liquid outlet cavity, at least a portion of the connecting surface being the guide slope.

[0013] In one embodiment, the pump housing includes a bottom shell and a top shell, the receiving cavity is disposed in the bottom shell, the top shell is connected to the bottom shell to jointly enclose the liquid outlet cavity, and the liquid outlet pipe is connected to the top shell.

[0014] In one embodiment, the bottom shell includes a first shell wall and a second shell wall opposite to the first shell wall, the receiving cavity is located between the first shell wall and the second shell wall, the top shell and the first shell wall together enclose the liquid outlet cavity, and the bottom shell is also provided with a communicating channel connecting the receiving cavity and the liquid outlet cavity, the communicating channel having a guiding slope, the guiding slope connecting the surface of the second shell wall facing the first shell wall and the surface of the first shell wall facing the liquid outlet cavity.

[0015] In one embodiment, the connecting channel further has a first side and a second side, both of which are connected to the guide slope. The connection between the first side and the guide slope has a rounded corner, and the connection between the second side and the guide slope also has a rounded corner.

[0016] And / or, the outlet cavity is further provided with a drainage protrusion, the position of which corresponds to the position of the opening at the end of the outlet tube furthest from the outlet.

[0017] In one embodiment, the communicating channel further has a first side and a second side, both of which are connected to the guide slope. The bottom shell also has a peripheral wall, which is connected to both the first shell wall and the second shell wall to jointly form the receiving cavity. The peripheral wall has an inner peripheral surface, one end of which is connected to the first side and the other end of which is connected to the second side, wherein:

[0018] The connection between the inner circumferential surface and the first side surface is formed with a rounded corner, the radius of which is 0.2mm-0.5mm; and / or, both the inner circumferential surface and the second side surface are involute surfaces.

[0019] In one embodiment, the piping assembly further includes a liquid inlet pipe that communicates with both the liquid inlet and the receiving cavity. The bottom shell further includes a drainage protrusion and a connecting pipe portion. The drainage protrusion protrudes from the shell wall of the bottom shell, and the connecting pipe portion protrudes from the drainage protrusion and communicates with the liquid inlet pipe. The bottom shell also has a liquid flow hole that communicates with the connecting pipe portion. The liquid flow hole penetrates the shell wall of the bottom shell and the drainage protrusion to connect the liquid inlet pipe and the receiving cavity.

[0020] In one embodiment, the width of the connecting channel gradually decreases along the flow direction of the liquid; and / or, the angle θ between the guide slope and the surface of the second shell wall facing the first shell wall is 135°-155°.

[0021] In one embodiment, the piping assembly further includes an inlet pipe disposed outside the outlet pipe, the inlet pipe communicating with the receiving cavity and the inlet port, and the outlet pipe disposed outside the inlet pipe.

[0022] In one embodiment, both the outlet pipe and the inlet pipe are connected to the pump housing, the pump housing including at least a partially arc-shaped outer peripheral surface, the outlet pipe extending from the pump housing along the tangent direction of the arc-shaped outer peripheral surface, and the inlet pipe extending from the pump housing in a bent direction toward the outlet pipe.

[0023] In one embodiment, the conduit assembly further includes a connecting sleeve capable of penetrating the ventricular wall. The connecting sleeve has a first connecting hole and a second connecting hole spaced apart, and the outlet tube passes through the first connecting hole, wherein:

[0024] The liquid inlet tube is connected to the connecting sleeve, and the liquid inlet tube communicates with the second connecting hole, and the liquid inlet is an opening of the second connecting hole; or, the liquid inlet tube passes through the second connecting hole, and the liquid inlet is located on the liquid inlet tube.

[0025] Secondly, the present invention also provides a blood pump, including a pump housing, a conduit assembly, and an impeller. The pump housing is provided with a receiving cavity. The conduit assembly has a first liquid flow channel and a second liquid flow channel, both of which are in communication with the receiving cavity. The first liquid flow channel has a first opening away from the receiving cavity, and the second liquid flow channel has a second opening away from the receiving cavity. The conduit assembly is capable of penetrating a first organ. When the conduit assembly is penetrating the first organ, the first opening is located inside the first organ and is in communication with the first organ. The conduit assembly has a certain length so that when the conduit assembly is penetrating the first organ, it can extend through the interior of the first organ to a second organ in communication with the first organ, and the second opening is in communication with the second organ. The impeller is rotatably housed within the receiving cavity to allow liquid entering the receiving cavity from one of the first opening and the second opening to flow out through the other of the first opening and the second opening.

[0026] Thirdly, the present invention also provides a ventricular assist system, including the blood pump of any of the above embodiments.

[0027] Compared to existing technologies, the blood pump and ventricular assist system provided by this invention includes a pump housing, a tubing assembly, and an impeller. The tubing assembly can penetrate the ventricular wall, placing the inlet within the ventricle. The outlet tube has a certain length so that when the tubing assembly penetrates the ventricular wall, the outlet tube can extend through the ventricle to the aortic valve, placing the outlet within the aorta. This eliminates the need for external artificial blood vessels to pump blood from the ventricle to the aorta. In other words, this blood pump eliminates the need for openings in the aorta, thus avoiding aortic diseases such as dissection and hematoma caused by surgical openings while still providing auxiliary blood pumping. Furthermore, since the blood pump does not require external artificial blood vessels, there is no need to manage the placement of artificial blood vessels, reducing surgical difficulty and preventing leakage problems caused by connecting artificial blood vessels. Additionally, because the heart and other organs are closely adjacent within the thoracic cavity, the blood pump and ventricular assist system provided by this invention can extend the tubing assembly directly from the ventricle to the aorta without external artificial blood vessel connections, significantly reducing the space occupied in the thoracic cavity and avoiding other diseases caused by contact between artificial blood vessels and other organs.

[0028] These or other aspects of the invention will become more apparent from the following description of the embodiments. Attached Figure Description

[0029] To more clearly illustrate the technical solutions in the embodiments of this application, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0030] Figure 1 This is a schematic diagram of the blood pump provided in the first embodiment of the present invention.

[0031] Figure 2 yes Figure 1 The top view of the blood pump shown.

[0032] Figure 3 yes Figure 2 Cross-sectional view along the AA direction.

[0033] Figure 4 yes Figure 2 Cross-sectional view along the BB direction.

[0034] Figure 5 yes Figure 1 The image shown is an exploded view of the blood pump from one perspective.

[0035] Figure 6 yes Figure 1 The image shows an exploded view of the blood pump from another perspective.

[0036] Figure 7yes Figure 1 The side view of the blood pump shown.

[0037] Figure 8 yes Figure 7 Cross-sectional view along the CC direction.

[0038] Figure 9 yes Figure 1 The diagram shows an exploded view of the bottom casing and impeller of the blood pump.

[0039] Figure 10 yes Figure 1 The diagram shows the assembly of the blood pump's base and impeller.

[0040] Figure 11 yes Figure 10 Cross-sectional view along the DD direction.

[0041] Figure 12 yes Figure 1 The diagram shows the structure of the blood pump after it is equipped with a drive motor.

[0042] Figure 13 yes Figure 7 Cross-sectional view along the EE direction.

[0043] Figure 14 This is a schematic diagram of the blood pump provided in the second embodiment of the present invention.

[0044] Figure 15 yes Figure 14 Cross-sectional view along the FF direction.

[0045] Figure 16 yes Figure 14 The image shows a partially exploded view of the blood pump. Detailed Implementation

[0046] To facilitate understanding of the embodiments of the present invention, a more complete description of the embodiments will be given below with reference to the accompanying drawings. Preferred embodiments of the present invention are shown in the drawings. However, the present invention can be implemented in many different forms and is not limited to the embodiments described herein. Rather, these embodiments are provided to provide a thorough and complete understanding of the disclosure of the present invention.

[0047] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains. The terminology used herein in the embodiments of the invention is for the purpose of describing particular implementations only and is not intended to limit the invention.

[0048] In this article, "proximal" is defined as the end closer to the medical staff, and "distal" is defined as the end farther away from the medical staff.

[0049] Please see Figures 1 to 3 The present invention provides a blood pump 10, including a pump housing 11, a conduit assembly 13, and an impeller 15. The pump housing 11 is provided with a receiving cavity 112. The conduit assembly 13 has a first fluid flow channel 136 and a second fluid flow channel 138, both of which are connected to the receiving cavity 112. The first fluid flow channel 136 has a first opening away from the receiving cavity 112, and the second fluid flow channel 138 has a second opening away from the receiving cavity 112. The conduit assembly 13 can penetrate into a first organ. When the conduit assembly 13 penetrates into the first organ, the first opening is located in the first organ. The second opening is connected to the first organ and communicates with the first organ. The conduit assembly 13 has a certain length (specifically, the length in the direction of extension of the conduit assembly 13) such that when the conduit assembly 13 is inserted into the first organ, it can extend through the interior of the first organ to the second organ that communicates with the first organ and communicate with the second organ. The impeller 15 is rotatably housed in the receiving cavity 112 to allow liquid entering the receiving 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.

[0050] When the tubing assembly 13 of the blood pump 10 provided by the present invention is inserted into the first organ, the first opening is located inside the first organ and communicates with the first organ. Since the tubing assembly 13 has a certain length L1, this length L1 allows the tubing assembly 13 to extend through the interior of the first organ to the second organ, which communicates with the first organ, and the second opening communicates with the second organ. Therefore, under the action of the impeller 15 rotating, the liquid enters the receiving cavity 112 through one of the first opening and the second opening, and flows out through the other of the first opening and the second opening. It can pump the liquid in the first organ to the second organ or pump the liquid in the second organ to the first organ without the need for external artificial tubing. That is, the blood pump 10 does not require drilling a hole in the second organ, which can meet the needs of auxiliary blood pumping and avoid diseases caused by drilling a hole in the second organ. Furthermore, since the blood pump 10 does not require external artificial tubing, there is no need to sort out the layout path of artificial tubing, which reduces the difficulty of surgery.

[0051] Please see Figures 1 to 3 In the first embodiment of the present invention, the left ventricle of the heart is used as the first organ and the aorta is used as the second organ.

[0052] The blood pump 10 of the first embodiment of the present invention includes a pump housing 11, a conduit assembly 13, and an impeller 15. The pump housing 11 has a receiving cavity 112. The conduit assembly 13 includes a liquid outlet pipe 133 communicating with the receiving cavity 112, and the liquid outlet pipe 133 has a liquid outlet 1332. Specifically, the liquid outlet 1332 is a second opening for liquid outflow; a second liquid flow channel 138 is a liquid outflow channel. The conduit assembly 13 also has a liquid inlet 1312 communicating with the receiving cavity 112. Specifically, the liquid inlet 1312 is a first opening for liquid inflow. A first liquid flow channel 136 is a liquid inflow channel. The conduit assembly 13 can penetrate the ventricular wall. When the conduit assembly 13 penetrates the ventricular wall, the liquid inlet 1312 is located within the ventricle and communicates with the ventricle. The outlet tube 133 has a certain length L1, which allows the outlet tube 133 to extend through the ventricle to the aortic valve when the tubing assembly 13 passes through the ventricular wall, so that the outlet 1332 is located in the aorta and communicates with the aorta; the impeller 15 is rotatably housed in the receiving cavity 112 so that the liquid entering the receiving cavity 112 from the inlet 1312 flows out from the outlet 1332 through the outlet tube 133.

[0053] Here, length L1 refers to the length of the outlet pipe 133 in the extension direction.

[0054] Because the outlet pipe 133 of the blood pump 10 provided by the present invention has a certain length L1, this length L1 ensures that when the blood pump 10 is installed in the left ventricle, the pump housing 11 is located outside the heart, the tubing assembly 13 passes through the ventricular wall, the inlet 1312 is located in the left ventricle, and the outlet pipe 133 extends through the ventricle to pass through the aortic valve, so that the outlet 1332 is located in the aorta. Therefore, under the action of the impeller 15 rotating, the blood in the ventricle is drawn into the receiving cavity 112 from the inlet 1312 and flows through the outlet 133. 2. The blood flows to the aorta, thereby pumping blood from the ventricles into the aorta without the need for external artificial blood vessels. This means the blood pump 10 eliminates the need for openings in the aorta, allowing for auxiliary blood pumping while avoiding aortic diseases such as dissection and hematoma caused by surgical openings. Furthermore, since the blood pump 10 does not require external artificial blood vessels, there is no need to manage the placement of artificial blood vessels, reducing surgical difficulty and eliminating leakage problems caused by connecting artificial blood vessels. Additionally, because the heart and other organs are closely adjacent within the chest cavity, the blood pump 10 provided by this invention can extend the tubing assembly 13 directly from the ventricle to the aorta without external artificial blood vessel connections, significantly reducing the space occupied in the chest cavity and avoiding other diseases caused by contact between artificial blood vessels and other organs.

[0055] The receiving cavity 112 has a first cavity surface 1121 and a second cavity surface 1122 opposite to the first cavity surface 1121, and an 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 located on opposite sides of the impeller 15 and are respectively arranged opposite to the two surfaces of the impeller 15.

[0056] In this embodiment, the pump housing 11 is further provided with a liquid outlet chamber 114, which connects the liquid outlet pipe 133 and the receiving chamber 112. Liquid entering the receiving chamber 112 from the liquid inlet 1312 can flow into the liquid outlet pipe 133 through the liquid outlet chamber 114. Specifically, the receiving chamber 112 and the liquid outlet chamber 114 are arranged along the axial direction of the impeller 15; the liquid outlet chamber 114 is closer to the first cavity surface 1121 than the second cavity surface 1122.

[0057] Please see Figures 4 to 6 The pump housing 11 includes a bottom housing 118, which has a receiving cavity 112. The pump housing 11 also includes a top housing 116, which is connected to the bottom housing 118 to jointly enclose a liquid outlet cavity 114. The top housing 116 is connected to the liquid outlet pipe 133.

[0058] The top shell 116 includes a body 1162 and a flange 1164. The body 1162 covers the bottom shell 118, and the outer peripheral surface of the body 1162 is coplanar with the outer peripheral surface of the bottom shell 118. The body 1162 is provided with an outflow through hole 1166, which communicates with the liquid outlet chamber 114. The flange 1164 protrudes from the body 1162 and surrounds the outflow through hole 1166. The flange 1164 is annular and coaxial with the outflow through hole 116. The flange 1164 is connected to the liquid outlet pipe 133, and the outflow through hole 1166 communicates with the liquid outlet pipe 133. The liquid flowing out of the liquid outlet chamber 114 flows through the outflow through hole 1166 to the liquid outlet pipe 133 and finally flows out from the liquid outlet 1332.

[0059] Please see Figures 7 to 9 The bottom shell 118 is generally volute-shaped. The bottom shell 118 includes a first shell wall 1181 and a second shell wall 1182 opposite to the first shell wall 1181. A receiving cavity 112 is located between the first shell wall 1181 and the second shell wall 1182. A first cavity surface 1121 is disposed on the first shell wall 1181, and a second cavity surface 1122 is disposed 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 the first shell wall 1181 and the top shell 116 together enclose the liquid outlet cavity 114.

[0060] The bottom shell 118 also has a peripheral wall that is connected to both the first shell wall 1181 and the second shell wall 1182, so as to form a receiving cavity 112 together with the first shell wall 1181 and the second shell wall 1182. The peripheral wall has an inner peripheral surface 1184.

[0061] In one embodiment, the inner circumferential surface 1184 is an involute surface. An involute surface means that the surface extends in an involute pattern. In a top view (i.e., along the axis of the impeller 15), the inner circumferential surface 1184 is approximately involute in shape.

[0062] A drainage protrusion 1186 is provided inside the liquid outlet chamber 114. The position of the drainage protrusion 1186 corresponds to the position of the opening at the end of the liquid outlet pipe 133 away from the liquid outlet 1332, so as to guide the liquid in the liquid outlet chamber 114 to the liquid outlet pipe 133 and flow out through the liquid outlet 1332. Specifically, the drainage protrusion 1186 protrudes from the shell wall of the bottom shell 118, and more specifically, the drainage protrusion 1186 protrudes from the first shell wall 1181. A drainage surface 1185 is provided on the outer periphery of the drainage protrusion 1186. The drainage surface 1185 is a conical surface to drain the liquid in the liquid outlet chamber 114. The drainage surface 1185 can be the entire outer periphery of the drainage protrusion 1186, or it can be part of the outer periphery of the drainage protrusion 1186. In this embodiment, the position of the drainage protrusion 1186 roughly corresponds to the position of the impeller 15, allowing the inflow and outflow of liquid through the pipe assembly 13 to be relatively concentrated. Since both the inlet 1312 and the outlet 1332 are located on the pipe assembly 13, the approximate correspondence between the drainage protrusion 1186 and the impeller 15 facilitates the miniaturization of the pipe assembly 13, thereby making it easier to install the pipe assembly 13 on the aortic valve. In this embodiment, the drainage protrusion 1186 is generally disc-shaped. In other embodiments, the drainage protrusion 1186 can also be frustum-shaped or biconical, as long as it can guide the liquid out of the outlet chamber 114.

[0063] The bottom shell 118 also includes a connecting pipe portion 1187, which is disposed within the liquid outlet chamber 114 and communicates with the first liquid flow channel 136. Specifically, the connecting pipe portion 1187 protrudes from the drainage protrusion 1186, and its position corresponds to the opening at the end of the liquid outlet pipe 133 furthest from the liquid outlet 1332. Liquid in the liquid outlet chamber 114 can flow sequentially to the liquid outlet 1332 via the drainage protrusion 1186 and the connecting pipe portion 1187. More specifically, the connecting pipe portion 1187 protrudes from the middle of the drainage protrusion 1186. In this embodiment, the connecting pipe portion 1187 is generally a hollow cylindrical structure. In other embodiments, the connecting pipe portion 1187 can also be generally a hollow cuboid or other structures, which can be set according to the actual situation.

[0064] The bottom shell 118 is also provided with a liquid flow hole 1188, which communicates with the connecting pipe portion 1187 and penetrates the shell wall of the bottom shell 118 and the drainage protrusion 1186. In this embodiment, the liquid flow hole 1188 penetrates the middle of the drainage protrusion 1186, and the liquid flow hole 1188 can be a circular hole. In other embodiments, the liquid flow hole 1188 can also penetrate other positions of the drainage protrusion 1186, and the liquid flow hole 1188 can also be a square hole, a triangular hole, an elliptical hole, or other types of holes, which can be set according to the actual situation.

[0065] The bottom shell 118 also includes a first shell 1189 and a second shell 1180, which cooperate to form a receiving cavity 112. The first shell 1189 is connected to the top shell 116. By providing the first shell 1189 and the second shell 1180, it is convenient to install the impeller 15 into the receiving cavity 112.

[0066] Combination Figure 5 The pump casing 11 also has a connecting channel 119 that connects the receiving cavity 112 and the outlet cavity 114, allowing liquid in the receiving cavity 112 to flow into the outlet cavity 114 through the connecting channel 119. Specifically, the connecting channel 119 is located in the bottom shell 118. The connecting channel 119 has a connecting surface that connects the second cavity surface 1122 and the outlet cavity 114, at least a portion of which is a guide slope 1191. The guide slope 1191 guides the liquid in the receiving cavity 112 to the outlet cavity 114. The guide slope 1191 guides the liquid from the receiving cavity 112 into the outlet cavity 114. In this embodiment, the distance from the guide slope 1191 to the second cavity surface 1122 gradually increases from the end closer to the receiving cavity 112 to the end farther from the receiving cavity 112. Specifically, the guide slope 1191 connects the surface of the second shell wall 1182 facing the first shell wall 1181 and the surface of the first shell wall 1181 facing the liquid outlet cavity 114.

[0067] Specifically, the second cavity surface 1122 is located on the side of the second shell wall 1182 facing the first shell wall 1181. The second cavity surface 1122 can be the entire surface of the second shell wall 1182 facing the first shell wall 1181, or it can be a portion 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 liquid outlet cavity 114 is the surface of the first shell wall 1181 that is opposite to the first cavity surface 1121.

[0068] It should be noted that the flow guiding slope 1191 can be the entire connecting surface; or, the flow guiding slope 1191 can be a part of the connecting surface connecting the second cavity surface 1122 and the liquid outlet cavity 114. For example, in some embodiments, the flow guiding slope 1191 is a section of the connecting surface near the liquid outlet cavity 114; in some embodiments, the flow guiding slope 1191 is a section of the connecting surface near the receiving cavity 112; in some embodiments, the flow guiding slope 1191 is the middle section of the connecting surface in the extension direction of the connecting channel 119.

[0069] Please see Figures 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°-155°. In this embodiment, along the direction of liquid flow, θ first decreases and then increases, and remains between 135° and 155°, thus improving the smoothness of liquid flow. In other embodiments, θ is a fixed value along the direction of liquid flow, and its value is between 135° and 155°. This improves the stability of liquid flow from the receiving cavity 112 to the outlet cavity 114 while also enabling miniaturization of the blood pump 10 and reducing the burden on the heart. With the distance between the surface of the second shell wall 1182 facing the first shell wall 1181 and the first cavity surface 1121 remaining constant, when θ is greater than 155°, the length of the guide slope 1191 needs to be increased to connect the guide slope 1191 with the surface of the second shell wall 1182 facing the first shell wall 1181 and the first cavity surface 1121. This results in an increase in the volume of the bottom shell 118, thereby increasing the volume of the blood pump 10. When θ is less than 135°, it slows down the flow velocity of the liquid towards the outlet cavity 114, which is not conducive to the smooth flow of the liquid.

[0070] In this embodiment, the width of the connecting channel 119 gradually decreases along the liquid flow direction. In the illustrated embodiment, the liquid flow direction refers to the direction in which the liquid flows from the receiving cavity 112 through the connecting channel 119 towards the outlet cavity 114. The gradual decrease in the width of the connecting channel 119 along the liquid flow direction causes the liquid to gradually tighten along the flow direction, thereby accelerating the liquid flow velocity towards the outlet cavity 114, weakening the adverse effects caused by liquid gravity, and improving the pumping flow rate and speed. In one embodiment, the reduction in the width of the connecting channel 119 is linear; in another embodiment, the reduction in the width of the connecting channel 119 can also be non-linear, for example, exponential.

[0071] In this embodiment, as Figure 11As shown, the connecting channel 119 extends along a second-order or higher Bézier curve, improving the smoothness of the liquid flow and thus achieving a more stable pumping flow field. In one embodiment, the connecting channel 119 can also extend along an arc. In another embodiment, the connecting channel 119 can also extend along an oblique line, satisfying the purpose of accelerating the flow velocity of the liquid towards the outlet chamber 114 and increasing the pumping flow rate and speed.

[0072] In this embodiment, the width of the connecting channel 119 gradually decreases along the liquid flow direction, and 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°-155°. In one embodiment, the width of the connecting channel 119 gradually decreases along the liquid flow direction, and the angle θ between the guide slope 1191 and the surface of the second shell wall 1182 facing the first shell wall 1181 is not limited. In another embodiment, the width of the connecting channel 119 is not limited along the liquid flow direction, and 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°-155°.

[0073] The connecting channel 119 also has a first side surface 1195 and a second side surface 1197, both of which are connected to the guide slope 1191. The connection between the first side surface 1195 and the guide slope 1191 has a rounded corner α, and the connection between the second side surface 1197 and the guide slope 1191 has a rounded corner β (e.g., ...). Figure 9 As shown, rounded corners can reduce sharp edges at the connection points, thus reducing hemolysis. The radii of rounded corners α and β can be 0.1mm-0.5mm. When the rounded corner radius is less than 0.1mm, the improvement in hemolysis is not significant; when the rounded corner radius is greater than 0.5mm, it will obstruct blood flow and easily cause insufficient pumping flow. 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, may not have rounded corners, which can be set according to the actual situation.

[0074] The first side surface 1195 is connected to one end of the inner circumferential surface 1184, and the second side surface 1197 is connected to the other end of the inner circumferential surface 1184. A fillet γ is formed at the junction of the first side surface 1195 and the inner circumferential surface 1184 (e.g., a rounded corner γ). Figure 8 As shown, the radius of the fillet γ is 0.2mm-0.5mm. A fillet radius less than 0.2mm will create a sharp corner at the connection between the inner circumferential surface 1184 and the first side surface 1195, which can easily lead to hemolysis. A fillet radius greater than 0.5mm will obstruct blood flow, thereby reducing the pumping blood flow rate.

[0075] In this embodiment, the second side surface 1197 is also an involute surface, that is, the top view of the second side surface 1197 is approximately involute. In other embodiments, the second side surface 1197 may also be an arc surface.

[0076] Please continue reading. Figure 1 , Figure 4 and Figure 5 The pipe assembly 13 is connected to the pump housing 11. The inlet 1312 is closer to the proximal end of the pipe assembly 13 than the outlet 1332. The inlet 1312 is used for the entry of liquid (such as blood). The outlet 1332 is located at the distal end of the pipe assembly 13. The outlet 1332 is used for the outflow of liquid. The outlet 1332 is connected to the outlet chamber 114, so that the pipe assembly 13 has both inlet and outlet functions. That is, liquid can enter the pump housing 11 through the pipe assembly 13 and can also flow out through the pipe assembly 13.

[0077] The outlet pipe 133 is connected to the pump housing 11 and communicates with the receiving cavity 112. For example, the outlet pipe 133 is connected to the flange 1164 of the top housing 116. Liquid in the outlet cavity 114 can also flow along the inner circumferential surface of the flange 1164 and the inner circumferential surface of the outlet pipe 133 to the outlet pipe 133 and flow out from the outlet port 1332. In this embodiment, the inner circumferential surface of the outlet pipe 133 can be coplanar with the inner circumferential surface of the flange 1164, making the liquid flow out of the outlet cavity 114 more stable and smooth. The inlet port 1312 is exposed on the outer circumferential surface of the outlet pipe 133, and the outlet port 1332 is disposed on the outlet pipe 133.

[0078] The outlet tube 133 can penetrate the ventricular wall and extend from the pump housing 11 to penetrate the aortic valve, so that the outlet 1332 is located in the aorta, allowing blood in the receiving cavity 112 to enter the aorta through the outlet 1332, thereby realizing the transportation of blood from inside the heart to the aorta.

[0079] The liquid outlet tube 133 has a liquid outlet cavity 1334, which is connected to the liquid outlet 1332 and the receiving cavity 112. Specifically, the liquid outlet cavity 114 is connected to the liquid outlet 1332 via the liquid outlet cavity 1334.

[0080] Please see Figure 3 and Figure 12In this embodiment, the conduit assembly 13 includes a first pipe section 137 and a second pipe section 139. Both the first pipe section 137 and the second pipe section 139 are disposed within the outlet pipe 133. The first pipe section 137 is connected between the second pipe section 139 and the pump housing 11. The inlet 1312 is disposed within the first pipe section 137, and the outlet 1332 is disposed within the second pipe section 139. In this embodiment, the outer diameter of the first pipe section 137 is larger than the outer diameter of the second pipe section 139, that is, the outer diameter of the distal end of the outlet pipe 133 is smaller than the outer diameter of the proximal end of the conduit assembly 13, which can reduce the damage of the outlet pipe 133 to the aorta. In this embodiment, the second pipe section 139 is provided with a transition section 1391, which is connected to the first pipe section 137. Along the direction from the first pipe section 137 to the second pipe section 139, the outer diameter of the transition section 1391 gradually decreases to avoid the formation of sharp edges, facilitating the safe insertion of the conduit assembly 13 into the ventricle. In this embodiment, the generatrix of the transition segment 1391 can be a circular arc or a second-order Bézier curve. In other embodiments, the generatrix of the transition segment 1391 can also be a diagonal line.

[0081] In this embodiment, the pipe assembly 13 further includes an inlet pipe 131, with an inlet port 1312 communicating with it. The inlet pipe 131 is at least partially disposed within the outlet pipe 133, and its length is less than the length of the outlet pipe 133. Specifically, at least a portion of the inlet pipe 131 is disposed within the first pipe segment 137. In one embodiment, the inlet pipe 131 may be entirely located within the outlet pipe 133. In another embodiment, a portion of the inlet pipe 131 is located within the outlet pipe 133, with the remaining portion extending out of the outlet pipe 133.

[0082] A liquid flow channel 134 is formed between the inlet pipe 131 and the outlet pipe 133. The liquid flow channel 134 is at least partially located between the inlet pipe 131 and the first pipe segment 137. In this embodiment, the inner circumferential surface of the inlet pipe 131 forms a first liquid flow channel 136, and the liquid flow channel 134 is a second liquid flow channel 138. The liquid flow channel 134 is connected to both the outlet port 1332 and the receiving cavity 112. Liquid can flow into the inlet pipe 131 from the inlet port 1312, and then flow out from the outlet port 1332 sequentially through the receiving cavity 112 and the liquid flow channel 134.

[0083] Please see Figure 3 , Figure 6 and Figure 9The inlet pipe 131 is connected to the pump housing 11. Specifically, the inlet pipe 131 is connected to the first shell wall 1181 of the bottom shell 118, and the inlet pipe 131 communicates with the receiving cavity 112. The inlet port 1312 communicates with the inlet pipe 131. In this embodiment, the inlet pipe 131 is connected to the connecting pipe portion 1187 in the outlet cavity 114, thereby separating the first liquid flow channel 136 and the second liquid flow channel 138, avoiding mutual interference between the liquid flow in the first liquid flow channel 136 and the liquid flow in the second liquid flow channel 138, improving the smoothness and stability of liquid inlet and outlet, thereby increasing the flow rate and speed of blood pumping. The inlet pipe 131 is connected to the connecting pipe portion 1187 in the outlet chamber 114 and communicates with the liquid flow hole 1188. This allows the liquid in the outlet chamber 114 to flow along the outer circumferential surface of the connecting pipe portion 1187 and the outer circumferential surface of the inlet pipe 131 to the outlet pipe 133, and then out through the outlet port 1332. In this embodiment, the outer circumferential surface of the inlet pipe 131 can be coplanar with the outer circumferential surface of the connecting pipe portion 1187, making the liquid flow from the outlet chamber 114 more stable and smooth. In other embodiments, the bottom shell 118 may not include the connecting pipe portion 1187. One end of the inlet pipe 131 near the pump housing 11 may protrude from the outlet pipe 133 and connect to the drainage protrusion 1186. Alternatively, the inlet pipe 131 may not connect to the drainage protrusion 1186 but extend directly into the receiving cavity 112. Both methods satisfy the requirement that liquid enter the receiving cavity 112 via the inlet pipe 131.

[0084] The inlet pipe 131 is connected to the liquid flow hole 1188, and the liquid flow hole 1188 passes through the middle of the drainage protrusion 1186, so that the position of liquid flowing in and out of the pipe assembly 13 can be relatively concentrated, which is conducive to the miniaturization of the pipe assembly 13.

[0085] In this embodiment, the inlet 1312 is connected to the inlet pipe 131, the inlet 1312 is not connected to the outlet pipe cavity 1334, and the outlet pipe cavity 1334 is connected to the outlet 1332. Therefore, the liquid flow entering from the inlet 1312 into the inlet pipe 131 and the liquid flow flowing out from the outlet pipe cavity 1334 into the outlet 1332 will not affect each other, thus improving the smoothness and stability of liquid inlet and outlet, thereby increasing the flow rate and speed of blood pumping.

[0086] In this embodiment, there are multiple inlet ports 1312, which are arranged circumferentially along the axis perpendicular to the outlet pipe 133 and are all exposed on the outer peripheral surface of the outlet pipe 133. All multiple inlet ports 1312 are connected to the inlet pipe 131, so that liquid entering through any of the multiple inlet ports 1312 can flow into the receiving cavity 112. Even if a certain inlet port 1312 is blocked by the ventricular wall when blood enters, blood can still enter the ventricle through other inlet ports 1312 to achieve normal blood inflow and outflow.

[0087] In this embodiment, there are two inlets 1312, which are arranged opposite to each other. This ensures that the force on the blood pump 10 is relatively balanced as the liquid enters the blood pump 10 through the two inlets 1312, preventing tilting caused by unbalanced forces. In one embodiment, the positions of the two inlets 1312 may not correspond. In another embodiment, there may be only one inlet 1312, which can be set according to the actual situation.

[0088] Please see Figure 13 In this embodiment, the inner diameter of the liquid inlet pipe 131 near the receiving cavity 112 is d, and the total cross-sectional area of ​​the liquid flow channel 134 near the receiving cavity 112 is S=πd. 2 / 4, that is, Figure 13 The sum of the areas of the two fan-shaped annular sections shown is equal to the area of ​​the inner cross section of the inlet pipe 131. This makes the cross-sectional area of ​​the liquid inflow zone equal to the cross-sectional area of ​​the liquid outflow zone, so that the flow rate of the liquid entering the blood pump 10 is approximately equal to the flow rate of the liquid flowing out of the blood pump 10, thereby improving the stability of the blood pump flow rate.

[0089] The piping assembly 13 also includes connectors 135, which connect the inlet pipe 131 and the outlet pipe 133 to secure the inlet pipe 131 inside the outlet pipe 133. In this embodiment, there are two connectors 135, which are arranged circumferentially along the inlet pipe 131 and located at both radial ends of the inlet pipe 131. In other embodiments, the number of connectors 135 may be one, three, or more, as long as the purpose of securing the inlet pipe 131 inside the outlet pipe 133 is met.

[0090] Please continue reading. Figure 6 The connector 135 includes a connected bottom surface 1352 and a connected side surface 1354. The bottom surface 1352 faces the outlet chamber 114, allowing the liquid flowing out of the outlet chamber 114 to contact the bottom surface 1352. The side surface 1354 is opposite to the inner wall of the outlet pipe 133, allowing the liquid flowing out of the outlet chamber 114 to also contact the side surface 1354. In this embodiment, the connection between the bottom surface 1352 and the side surface 1354 has a rounded corner δ (e.g., ...). Figure 6 (As shown), to reduce hemolysis. As an example, the radius of the fillet δ can be 0.1mm-0.5mm. In other embodiments, the radius of the fillet can also be other values, which are not limited here.

[0091] It should be noted that in other embodiments, the pipe assembly 13 may not include the inlet pipe 131, that is, the pipe assembly 13 may only include the outlet pipe 133. The outlet pipe 133 may include a first liquid flow channel 136 and a second liquid flow channel 138. The first liquid flow channel 136 and the second liquid flow channel 138 are separated by a partition, and the partition is connected to the inner wall of the outlet pipe 133. The first liquid flow channel 136 is connected to the inlet 1312, and the second liquid flow channel 138 is connected to the outlet 1332. Similarly, when the impeller 15 is in operation, the liquid that enters the receiving cavity 112 from the inlet 1312 can flow out from the outlet 1332 through the outlet pipe 133.

[0092] The impeller 15 is rotatably housed within the receiving cavity 112 to transport liquid entering the receiving cavity 112 from the inlet 1312 to the outlet 1332 via the outlet cavity 114. The impeller 15 may contain a rotor (not shown), which can cooperate with the stator of a motor. When the stator drives the rotor to rotate within the receiving cavity 112, the impeller 15 also rotates synchronously with the rotor within the receiving cavity 112. The specific structure of the impeller 15 can be found in existing technology.

[0093] The blood pump 10 also includes a drive motor 17, which is connected to the side of the pump housing 11 away from the pipeline assembly 13. The drive motor 17 is driven by the impeller 15 to drive the impeller 15 to rotate. For example, the drive motor 17 includes a stator inside, which is magnetically engaged with the rotor inside the impeller 15, causing the rotor to rotate, thereby driving the impeller 15 to rotate.

[0094] The second embodiment of the present invention is described using the left ventricle of the heart as the first organ and the aorta as the second organ.

[0095] Please see Figures 14 to 16The blood pump 20 of the second embodiment of the present invention includes a pump housing 21, a conduit assembly 23, and an impeller 25. The pump housing 21 has a receiving cavity 212. The conduit assembly 23 includes a liquid outlet pipe 233 communicating with the receiving cavity 212. The liquid outlet pipe 233 is connected to the pump housing 21 and has a liquid outlet 2332. Specifically, the liquid outlet 2332 is a second opening for liquid outflow. The conduit assembly 23 also has a liquid inlet 2312 communicating with the receiving cavity 212. Specifically, the liquid inlet 2312 is a first opening for liquid inflow. The conduit assembly 23 can penetrate the ventricular wall. When the conduit assembly 23 penetrates the ventricular wall, the liquid inlet 2312 is located within the ventricle and communicates with the ventricle. The outlet tube 233 has a certain length L2, which allows the outlet tube 233 to extend through the ventricle to the aortic valve when the tubing assembly 23 passes through the ventricular wall, so that the outlet 2332 is located in the aorta and communicates with the aorta; the impeller 25 is rotatably housed in the receiving cavity 212 so that the liquid entering the receiving cavity 212 from the inlet 2312 flows out through the outlet 2332.

[0096] Unlike blood pump 10, blood pump 20 has a pump housing 21 that includes at least a partially arc-shaped outer peripheral surface. An outlet pipe 233 extends from the pump housing 21 along the tangential direction of the arc-shaped outer peripheral surface, allowing the blood pump 20 to flow out along the tangential direction of the arc-shaped outer peripheral surface of the pump housing 21 under the action of the rotating impeller 25. Additionally, blood pump 20 does not include a top shell 116. Figure 5 The outlet pipe 233 is connected to the bottom shell 218, which does not include the guide slope 1191. Figure 13 The blood entering the receiving cavity 212 through the inlet 2312 is directly transported to the outlet 2332 of the outlet pipe 233 under the rotation of the impeller 25, and flows towards the aorta, without passing through the outlet cavity 114. Figure 3 Other structures, such as the pump, make blood delivery smoother and increase blood flow.

[0097] The blood pump 20 also includes an inlet tube 231, which is connected to the pump housing 21 and located outside the outlet tube 233. The inlet tube 231 communicates with the receiving cavity 212, and the inlet port 2312 communicates with the inlet tube 231. The inlet tube 231 bends and extends from the pump housing 21 toward the outlet tube 233, so that the inlet tube 231 can also be inserted into the ventricular wall while the outlet tube 233 is inserted into the ventricular wall, and the inlet port 2312 is located in the ventricle. This eliminates the need to drill a hole in the heart to insert the inlet tube 231, and also eliminates the need for artificial blood vessels to pump blood from the ventricle to the aorta, thus avoiding the need to drill a hole in the aorta.

[0098] The inlet 2312 is located in the inlet pipe 231 and communicates with the receiving cavity 212 through the lumen of the inlet pipe 231. The outlet pipe 233 is located outside the inlet pipe 231, and the outlet 2332 communicates with the receiving cavity 212 through the lumen of the outlet pipe 233. That is, the inlet pipe 231 and the outlet pipe 233 of the blood pump 20 are independent of each other, and the lumen of the inlet pipe 231 and the lumen of the outlet pipe 233 are not connected. The inner peripheral wall of the inlet pipe 231 forms a first fluid flow channel, and the inner peripheral wall of the outlet pipe 233 forms a second fluid flow channel.

[0099] In this embodiment, the inlet pipe 231 extends from the pump housing 21 toward the outlet pipe 233, so that the inlet pipe 231 and the outlet pipe 233 have the same orientation, which facilitates the subsequent fixed connection of the inlet pipe 231 and the outlet pipe 233. Thus, while the outlet pipe 233 passes through the aortic valve, the inlet pipe 231 can pass through the ventricular wall.

[0100] The piping assembly 23 also includes a connecting sleeve 234, which can pass through the ventricular wall. The connecting sleeve 234 has a first connecting hole 2341 and a second connecting hole 2342 spaced apart. The outlet pipe 233 passes through the first connecting hole 2341. For example, the outlet pipe 233 passes through the first connecting hole 2341 and extends in a direction away from the pump housing 21. The inlet pipe 231 is connected to the connecting sleeve 234 and communicates with the second connecting hole 2342. The inlet port 2312 is an opening of the second connecting hole 2342. That is, the inlet port 2312 can be provided on the connecting sleeve 234; or, the inlet pipe 231 passes through the second connecting hole 2342, and the inlet port 2312 is provided on the inlet pipe 231. The end of the inlet pipe 231 away from the pump housing 21 can be flush with or protrude from the end face of the connecting sleeve 234. The connecting sleeve 234 is used to fix the inlet tube 231 and the outlet tube 233. When installing the blood pump 20, the inlet tube 231 and the outlet tube 233 can be inserted into the ventricular wall by inserting the connecting sleeve 234 into the ventricular wall. It is not necessary to insert the inlet tube 231 into the heart wall separately, which reduces the difficulty of the operation.

[0101] The blood pump 20 also includes a drive motor 27, which is connected to the pump housing 21. The drive motor 27 is in transmission cooperation with the impeller 25 to drive the impeller 25 to rotate.

[0102] In one embodiment, both blood pump 10 and blood pump 20 can be used in the right ventricle, that is, 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 entry, and the second opening is a liquid outlet 1332 for liquid outflow. The first liquid flow channel 136 is formed by the inner circumferential surface of the liquid inlet pipe 131 (or liquid inlet pipe 231), and the second liquid flow channel 138 is formed by the outer circumferential surface of the liquid inlet pipe 131 and the inner circumferential surface of the liquid outlet pipe 133, or only by the inner circumferential surface of the liquid outlet pipe 233. That is, when the blood pump 10 is installed in the right ventricle of the heart, the conduit assembly 13 can be inserted through the pulmonary valve, so that the first opening is located in the right ventricle and the second opening is located in the pulmonary artery. Thus, blood in the pulmonary artery can be pumped to the right ventricle without the need for an external artificial blood vessel, avoiding the need to make a hole in the pulmonary artery. While meeting the needs of assisting blood pumping, it avoids pulmonary artery disease caused by surgical opening of the pulmonary artery. Furthermore, it eliminates the need to sort out the layout path of the artificial blood vessel, reducing the difficulty of the operation and also eliminating the problem of blood leakage caused by clamping and connecting the artificial blood vessel.

[0103] In other embodiments, blood pump 10 and blood pump 20 can also be applied to other tissues similar to the heart, to achieve the purpose of pumping fluid from the first organ to the second organ, or pumping fluid from the second organ to the first organ.

[0104] In summary, the blood pump 10 and blood pump 20 provided by the present invention include a pump housing 11, a pipe assembly 13, and an impeller 15. The pump housing 11 is provided with a receiving cavity 112. The pipe assembly 13 includes an outlet pipe 133 communicating with the receiving cavity 112. The outlet pipe 133 is provided with an outlet port 1332. The pipe assembly 13 also has an inlet port 1312 communicating with the receiving cavity 112. The pipe assembly 13 can penetrate the ventricular wall so that the inlet port 1312 is located in the ventricle. The outlet pipe 133 has a certain length L1 so that when the pipe assembly 13 penetrates the ventricular wall, the outlet pipe 133 can extend through the ventricle to penetrate the aortic valve so that the outlet port 1332 is located in the aorta. The impeller 15 is rotatably received in the receiving cavity 112 so that the liquid entering the receiving cavity 112 from the inlet port 1312 flows out from the outlet port 1332 through the outlet pipe 133. The conduit assembly 13 is inserted through the ventricular wall, with the inlet 1312 located within the ventricle. The outlet 133 has a certain length L1, allowing it to extend through the ventricle to the aortic valve, with the outlet 1332 located in the aorta. This eliminates the need for external artificial blood vessels, allowing blood to be pumped from the ventricle to the aorta without the need for an external artificial blood vessel. The blood pump 10 eliminates the need for an opening in the aorta, providing auxiliary blood pumping while avoiding aortic diseases such as dissection and hematoma caused by surgical openings. Furthermore, since the blood pump 10 does not require an external artificial blood vessel, it eliminates the need to manage the placement of artificial blood vessels, reducing surgical difficulty and preventing leakage problems caused by connecting artificial blood vessels. Additionally, because the heart and other organs are closely adjacent within the thoracic cavity, the blood pump 10 provided by this invention can extend the conduit assembly 13 directly from the ventricle to the aorta without external artificial blood vessel connections, significantly reducing the space occupied in the thoracic cavity and preventing other diseases caused by contact between artificial blood vessels and other organs.

[0105] It should be noted that blood pumps 10 and 20 can also be used in the right ventricle, and can pump blood from the pulmonary artery to the right ventricle without the need for external artificial blood vessels. This avoids the need for openings in the pulmonary artery, thus preventing pulmonary artery disease caused by surgical openings while still providing auxiliary blood pumping. Furthermore, it eliminates the need to manage the placement of artificial blood vessels, reducing surgical difficulty and preventing leakage problems caused by clamping and transferring artificial blood vessels. In addition, blood pump 10 can also be applied to other tissues similar to the heart, fulfilling the purpose of pumping fluid from one organ to another, or vice versa.

[0106] The present invention also provides a ventricular assist system (not shown), including a blood pump 10 (or blood pump 20). The ventricular assist system may further include a ventricular connection assembly (not shown) and a control console (not shown), etc. The ventricular connection assembly can be used to install the blood pump 10 in the heart, and the control console can be electrically connected to the blood pump 10 to control the operation of the blood pump 10. The structures or devices such as the ventricular connection assembly and the control console can refer to the prior art, and are not specifically limited here.

[0107] The ventricular assist system provided by the present invention includes a blood pump 10. Since the blood pump 10 can avoid aortic diseases such as dissection and hematoma caused by surgical opening of the aorta, the difficulty of the operation is reduced, and other diseases caused by contact between the artificial blood vessel and other organs are avoided. Therefore, the ventricular assist system provided by the present invention can also reduce the difficulty of the operation and avoid other diseases caused by contact between the artificial blood vessel and other organs.

[0108] In this invention, the terms "first," "second," etc., are used only for distinguishing descriptions and should not be construed as referring to specific or particular structures. The term "some embodiments" refers to specific features, structures, materials, or characteristics described in connection with that embodiment or example that are included in at least one embodiment or example of the invention. In this invention, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described can be combined in any suitable manner in one or more embodiments or examples. Moreover, without contradiction, those skilled in the art can combine and integrate different embodiments or examples described in this invention, as well as the features of different embodiments or examples.

[0109] The above embodiments are only used to illustrate the technical solutions of the present invention, and are not intended to limit them. Although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of the present invention, and should all be included within the protection scope of the present invention.

Claims

1. A blood pump, characterized in that, include: Pump housing, wherein the pump housing is provided with a receiving cavity; A conduit assembly having a first fluid flow channel and a second fluid flow channel, both of which are in communication with a receiving cavity. The first fluid flow channel has a first opening away from the receiving cavity, and the second fluid flow channel has a second opening away from the receiving cavity. The conduit assembly is capable of penetrating a first organ. When the conduit assembly is penetrating the first organ, the first opening is located inside the first organ and is in communication with the first organ. The conduit assembly has a certain length so that when the conduit assembly is penetrating the first organ, it can extend through the interior of the first organ to a second organ in communication with the first organ, and the second opening is in communication with the second organ. and An impeller is rotatably housed within the receiving cavity to allow liquid entering the receiving cavity from one of the first opening and the second opening to flow out through the other of the first opening and the second opening. The pipe assembly includes an outlet pipe communicating with the receiving cavity, the outlet pipe having an outlet port, which is the second opening. The pipe assembly also has an inlet port, which is the first opening. The pump housing also has an outlet chamber communicating with the outlet pipe and the receiving cavity, allowing liquid entering the receiving cavity from the inlet port to flow into the outlet pipe via the outlet chamber. The pump housing includes a bottom shell and a top shell, the receiving cavity being disposed in the bottom shell, the top shell being connected to the bottom shell to jointly enclose the outlet chamber, and the outlet pipe being connected to the top shell.

2. The blood pump according to claim 1, characterized in that, The tubing assembly can penetrate the ventricular wall so that the inlet is located within the ventricle. The outlet tube has a certain length so that when the tubing assembly penetrates the ventricular wall, the outlet tube can extend through the ventricle to penetrate the aortic valve or pulmonary valve so that the outlet is located in the aorta or pulmonary artery. When the impeller rotates, it can draw the liquid that enters the receiving cavity from the inlet through the outlet tube and flow out from the outlet.

3. The blood pump according to claim 2, characterized in that, The outlet pipe is connected to the pump housing. The pipeline assembly also includes an inlet pipe, which is connected to the pump housing and communicates with both the inlet and the receiving cavity. The inlet pipe is at least partially disposed inside the outlet pipe, or the inlet pipe is disposed outside the outlet pipe.

4. The blood pump according to claim 2, characterized in that, The pipeline assembly further includes an inlet pipe, which is connected to both the inlet port and the receiving cavity. The inlet pipe is at least partially disposed within the outlet pipe. The inner circumferential surface of the inlet pipe forms the first liquid flow channel. At least a portion of the second liquid flow channel is formed between the inlet pipe and the outlet pipe. The inlet port is exposed on the outer circumferential surface of the outlet pipe.

5. The blood pump according to claim 4, characterized in that, The inner diameter of the inlet pipe near the receiving cavity is d, and the total cross-sectional area of ​​the first liquid flow channel near the receiving cavity is S=πd. 2 / 4.

6. The blood pump according to claim 4, characterized in that, The pipeline assembly includes a first pipe section and a second pipe section. The first pipe section is connected between the second pipe section and the pump housing. The liquid inlet is located in the first pipe section, and the liquid outlet is located in the second pipe section. The outer diameter of the first pipe section is larger than the outer diameter of the second pipe section. At least a portion of the liquid inlet pipe is located within the first pipe section.

7. The blood pump according to claim 1, characterized in that, The receiving cavity and the liquid outlet cavity are arranged along the axial direction of the impeller.

8. The blood pump according to claim 1, characterized in that, The receiving 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 liquid outlet cavity is closer to the first cavity surface than the second cavity surface. The pump casing is also provided with a connecting channel connecting the receiving cavity and the liquid outlet cavity. The connecting channel has a connecting surface connecting the second cavity surface and the liquid outlet cavity. At least a portion of the connecting surface is a guide slope, wherein: the guide slope is used to guide the liquid in the receiving cavity to the liquid outlet cavity, or, from the end near the second cavity surface to the end away from the second cavity surface, the distance from the guide slope to the second cavity surface gradually increases.

9. The blood pump according to claim 1, characterized in that, The receiving 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 liquid outlet cavity is closer to the first cavity surface than the second cavity surface. The bottom shell includes a first shell wall and a second shell wall opposite to the first shell wall. The receiving cavity is located between the first shell wall and the second shell wall. The first cavity surface is disposed on the first shell wall, and the second cavity surface is disposed on the second shell wall. The top shell and the first shell wall together enclose the liquid outlet cavity. The bottom shell also has a connecting flow channel connecting the receiving cavity and the liquid outlet cavity. The connecting flow channel has a guide slope. The guide slope is used to guide the liquid in the receiving cavity to the liquid outlet cavity, or, from the end near the second cavity surface to the end away from the second cavity surface, the distance from the guide slope to the second cavity surface gradually increases.

10. The blood pump according to claim 8 or 9, characterized in that, The connecting channel also has a first side and a second side, both of which are connected to the guide slope. The connection between the first side and the guide slope has a rounded corner, and the connection between the second side and the guide slope also has a rounded corner. And / or, the width of the connecting channel gradually decreases along the flow direction of the liquid; And / or, the angle θ between the guide slope and the second cavity surface is 135°-155°.

11. The blood pump according to claim 9, characterized in that, The connecting channel also has a first side and a second side, both of which are connected to the guide slope. The bottom shell also has a peripheral wall, which is connected to both the first shell wall and the second shell wall to jointly form the receiving cavity. The peripheral wall has an inner peripheral surface, one end of which is connected to the first side and the other end of which is connected to the second side, wherein: The connection between the inner circumferential surface and the first side surface is formed with a rounded corner, the radius of which is 0.2mm-0.5mm; and / or, both the inner circumferential surface and the second side surface are involute surfaces.

12. The blood pump according to claim 1 or 8, characterized in that, The liquid outlet chamber is also provided with a drainage protrusion. The position of the drainage protrusion corresponds to the position of the opening at the end of the liquid outlet pipe away from the liquid outlet, so that the drainage protrusion can guide the liquid in the liquid outlet chamber to the liquid outlet pipe and flow out through the liquid outlet. Alternatively, the pump housing includes a bottom shell and a top shell, the receiving cavity is disposed in the bottom shell, the top shell is connected to the bottom shell to jointly enclose the liquid outlet cavity, and the liquid outlet pipe is connected to the top shell; the pipeline assembly also includes an inlet pipe, the inlet pipe is connected to both the liquid inlet and the receiving cavity, the inlet pipe is at least partially disposed within the liquid outlet pipe, and the inlet pipe is connected to the bottom shell; the bottom shell includes a drainage protrusion and a connecting pipe portion, the drainage protrusion protrudes from the shell wall of the bottom shell, the position of the drainage protrusion corresponds to the position of the opening at the end of the liquid outlet pipe away from the liquid outlet, so that the drainage protrusion can guide the liquid in the liquid outlet cavity to the liquid outlet pipe and flow out through the liquid outlet; the connecting pipe portion protrudes from the drainage protrusion and is connected to the liquid inlet pipe, the bottom shell also has a liquid flow hole connected to the connecting pipe portion, the liquid flow hole penetrates the shell wall of the bottom shell and the drainage protrusion, so that the liquid inlet pipe and the receiving cavity are connected.

13. The blood pump according to claim 1, characterized in that, The piping assembly further includes an inlet pipe, which is connected to both the inlet port and the receiving cavity, and the inlet pipe is at least partially disposed within the outlet pipe; the piping assembly further includes a connector, which is connected between the inlet pipe and the outlet pipe, and the connector includes a connected bottom surface and a connected side surface, the bottom surface facing the outlet cavity, the side surface being connected to the inner surface of the outlet pipe, and the connection between the bottom surface and the side surface having a rounded corner.

14. The blood pump according to any one of claims 3-6 and 13, characterized in that, The length of the inlet pipe is less than the length of the outlet pipe.

15. The blood pump according to any one of claims 3-6 and 13, characterized in that, There are multiple liquid inlets, which are arranged circumferentially along the axis perpendicular to the liquid outlet pipe and are all exposed on the outer circumferential surface of the liquid outlet pipe. All of the multiple liquid inlets are connected to the liquid inlet pipe.

16. The blood pump according to claim 15, characterized in that, There are two liquid inlets, which are arranged opposite to each other.

17. The blood pump according to claim 3, characterized in that, The inlet pipe is disposed outside the outlet pipe. The pump housing includes at least a partially arc-shaped outer peripheral surface. The outlet pipe extends from the pump housing along the tangent direction of the arc-shaped outer peripheral surface. The inlet pipe bends and extends from the pump housing toward the outlet pipe.

18. The blood pump according to claim 3, characterized in that, The inlet pipe is disposed outside the outlet pipe, the inner peripheral wall of the inlet pipe forms the first fluid flow channel, and the inner peripheral wall of the outlet pipe forms the second fluid flow channel; the pipeline assembly further includes a connecting sleeve, the connecting sleeve being able to pass through the ventricular wall, the connecting sleeve having a first connecting hole and a second connecting hole spaced apart, the outlet pipe passing through the first connecting hole, wherein: The liquid inlet tube is connected to the connecting sleeve, and the liquid inlet tube communicates with the second connecting hole, and the liquid inlet is an opening of the second connecting hole; or, the liquid inlet tube passes through the second connecting hole, and the liquid inlet is located on the liquid inlet tube.

19. The blood pump according to any one of claims 1-9, characterized in that, The blood pump also has a drive motor connected to the pump housing, and the drive motor is driven to rotate the impeller. Alternatively, the impeller may have a rotor inside, and the blood pump may also have a drive motor connected to the pump housing. The drive motor may have a stator inside, which magnetically engages with the rotor to make the rotor rotate, thereby driving the impeller to rotate.

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