Ventricular auxiliary system

Abstract

The ventricular auxiliary system comprises a pump head end assembly and a main machine end assembly, the pump head end assembly comprises a motor, an impeller, a conveying sheathing canal and a cable, the motor is arranged at the far end of the conveying sheathing canal, the impeller is installed on the motor, and the impeller comprises a wheel shaft and at least two blades; the wheel shaft is provided with an inflow end and an outflow end; the blades are connected to the axle and extend in the length direction of the axle. At least one end of each blade is bent in the circumferential direction of the axle. The host end assembly comprises a host, a filling box and a driving mechanism; the perfusion box is detachably installed on the main machine, the driving mechanism is connected to the main machine and used for driving the liquid pumping unit in the perfusion box to work, and the liquid outlet end of the liquid pumping unit is connected with the motor through a cable and used for cooling the motor. More efficient and stable blood flow conveying is achieved through structure reconstruction and function cooperation.

Description

Technical Field

[0001] The present invention relates to the technical field of cardiac disease treatment devices, and particularly to a ventricular assist system. Background Art

[0002] In the treatment of heart diseases in heart failure patients, in recent years, ventricular assist devices have played an increasingly important role during the operation. By using a ventricular assist device to assist the heart in pumping blood into the aorta, the heart load is reduced and myocardial injury is restored. Therefore, the ventricular assist device has become the preferred treatment method for doctors. One of the most important structures of the ventricular assist device is the blood pump impeller. The motor drives the impeller to generate centrifugal force, pumping the blood in the heart to the whole body. The structure of the impeller affects the blood pumping efficiency and hemolysis value. Under the condition of a limited rotational speed, how to improve the blood pumping efficiency, obtain a good and stable blood flow field, and the head of the impeller by improving the structure of the impeller is the main problem in the structural improvement of the current ventricular assist device. Summary of the Invention

[0003] Based on the above description, the present invention provides a ventricular assist system to solve the technical problems in the prior art.

[0004] The technical solution of the present invention to solve the above technical problems is as follows: A ventricular assist system, which includes a pump head end assembly and a host end assembly; The pump head end assembly includes a motor, an impeller, a delivery sheath tube and a cable. The motor is disposed at the distal end of the delivery sheath tube, the impeller is mounted on the motor, and the impeller includes a shaft and at least two blades; the shaft has an inlet end and an outlet end which are opposite to each other; the blades are connected to the shaft and extend along the length direction of the shaft, and at least one end of the blade is bent circumferentially along the shaft. The host end assembly includes a host, a perfusion box and a driving mechanism; the perfusion box is detachably mounted on the host, the driving mechanism is connected to the host and is used to drive the pump liquid unit inside the perfusion box to work, and the liquid outlet end of the pump liquid unit is connected to the motor through the cable for cooling the motor.

[0005] Compared with the prior art, the technical solution of the present application has the following beneficial technical effects: The ventricular assist system provided by this application improves the blood pumping efficiency through the coordinated operation of multiple components: it uses a delivery sheath with a motor at the distal end to transport blood, combines with a spiral flow channel formed by the circumferential bending of the impeller blades, enhances the axial propulsion ability of the blood and reduces the turbulent loss; the cable is internally provided with a cooling channel to ensure the efficient and stable operation of the motor; the bent part of the blade helps the impeller to have a greater head during blood pumping, thereby increasing the aortic perfusion pressure and increasing the blood pumping efficiency; the detachable perfusion box and the lightweight design simplify the clinical operation while enhancing the portability of the system, and the overall realizes more efficient and stable blood flow delivery through structural reconstruction and functional coordination.

[0006] Based on the above technical solutions, the present invention can be further improved as follows.

[0007] Further, one end of the blade close to the inflow end is bent and the bending radius is 2.5 mm to 10 mm, and / or one end of the blade close to the outflow end is bent and the bending radius is 2 mm to 10 mm.

[0008] Further, the included angle range of the projections of both ends of the blade on the cross-section of the axle is 30° - 150°, the length of the blade accounts for 65% - 85% of the total length of the impeller, and the total length of the impeller is 5 mm to 15 mm.

[0009] Further, the outer diameter range of the impeller is 3 mm to 15 mm, and the outer diameter of the impeller is determined by the outer edge of the blade; the thickness of the blade is 0.2 mm to 2 mm, the edges of the blade are smoothly transitioned and the transition fillet radius is between 0.05 mm and 1 mm, and the connection between the blade and the axle is fillet transitioned and the transition fillet radius is between 0.1 mm and 1 mm.

[0010] Further, the axle includes an inflow section close to the inflow end, an outflow section close to the outflow end, and a guiding section located between the inflow section and the outflow section. The axle is a streamlined structure with an outer diameter gradually increasing along the flow direction, and the guiding section is a cylinder; the side walls of the inflow section and the guiding section are fillet transitioned and the transition fillet radius is 40 mm to 80 mm, the outer diameter of the top end of the inflow section ranges from 0.1 mm to 2 mm, and the side walls of the outflow section and the guiding section are fillet transitioned and the transition fillet radius is 3 mm to 10 mm; the transition fillet of the side wall of the inflow section protrudes outward, and the transition fillet of the side wall of the outflow section sinks inward.

[0011] Further, the motor includes a housing, a coil, an inner membrane and a rotor. The coil is bonded inside the housing, the rotor is located inside the coil, and the inner membrane is bonded to the inner side of the coil to isolate the coil and the rotor.

[0012] Further, the delivery sheath is a multi-lumen composite catheter axially provided with a mutually isolated liner rod hole, perfusion tube hole, and motor circuit hole. The cable includes a perfusion tube, motor circuit, and connector. One end of the perfusion tube communicates with the perfusion tube hole, and the other end is connected to the connector. The connector is connected to the liquid outlet end of the perfusion box, and the motor circuit is arranged in the motor circuit hole.

[0013] Further, a card slot for installing the perfusion box is formed on the main body. A pressure detection unit is arranged at the bottom of the card slot for detecting the pressure received. The perfusion box further includes a box body, a liquid inlet tube, and a liquid outlet tube. The box body is detachably hung on the card slot. The lower end of the box body corresponds to the bottom of the card slot. A pressure-receiving part is arranged on the box body. When the perfusion box is installed on the main body, the pressure-receiving part is in close contact with the pressure detection unit. The liquid inlet tube and the liquid outlet tube are connected to the liquid pumping unit, and the side wall of the liquid outlet tube contacts the pressure-receiving part. The driving mechanism is connected to the main body for driving the liquid pumping unit to pump liquid from the liquid inlet tube and pump it out from the liquid outlet tube. Wherein, when liquid flows through the liquid outlet tube, the pressure-receiving part bulges outwards to press the pressure detection unit.

[0014] Further, at least one end of the card slot is formed with a first limiting part, and second limiting parts are formed on both sides of the card slot. The box body is configured to be limited at one end by the first limiting part and at both sides by the second limiting parts.

[0015] Further, the first limiting part is a limiting groove formed at one end of the bottom of the card slot. A limiting protrusion is formed at one end of the box body corresponding to the limiting groove. When the limiting protrusion and the limiting groove cooperate, the other end of the box body can rotate along the limiting groove. The second limiting part includes a bayonet formed on the side wall of the card slot, and a snap is movably arranged on the side wall of the box body. The snap is engaged with the bayonet.

[0016] Further, a pressing part is formed on the strip. When the snap and the bayonet cooperate, pressing the pressing part separates the snap and the bayonet.

[0017] Further, a pressure storage cavity is formed on the lower end surface of the box body. The liquid outlet tube is communicated with the pressure storage cavity. The pressure-receiving part includes a flexible heat-sealing film arranged on the surface of the pressure-receiving cavity. The flexible heat-sealing film is configured to bulge outwards when liquid flows through the inside of the pressure storage cavity.

[0018] Further, the liquid pumping unit includes a liquid pumping cylinder, a piston rod, and a piston driving member. A liquid pumping cavity is formed inside the liquid pumping cylinder. The liquid inlet pipe and the liquid outlet pipe are both communicated with the liquid pumping cavity. One-way valves are provided on both the liquid inlet pipe and the liquid outlet pipe. The piston rod is axially movably arranged inside the box body, and one end of the piston rod is slidably sealed with the liquid pumping cavity. The piston driving member drives the piston rod to reciprocate under the drive of the driving mechanism.

[0019] Further, a rack is formed on the piston rod, and the piston driving member includes a gear meshing with the rack.

[0020] Further, the driving mechanism includes a motor, and the motor is arranged on a side of the main body away from the card slot. Description of the Drawings

[0021] Figure 1 It is a schematic diagram of the overall structure of a ventricular assist system provided by an embodiment of the present invention; Figure 2 It is a schematic cross-sectional structure diagram of the motor in an embodiment of the present invention; Figure 3 It is a schematic cross-sectional view of the delivery sheath in an embodiment of the present invention; Figure 4 It is a schematic side view structure diagram of the impeller in an embodiment of the present invention; Figure 5 It is a schematic three-dimensional structure diagram of the impeller in an embodiment of the present invention; Figure 6 It is a schematic top view structure diagram of the impeller in an embodiment of the present invention; Figure 7 It is a schematic diagram of the projected included angle of the blades in an embodiment of the present invention; Figure 8 It is a schematic structure diagram of the wheel shaft in an embodiment of the present invention; Figure 9 It is a schematic structure diagram of the card slot in an embodiment of the present invention; Figure 10 It is a schematic internal structure diagram of the card slot in an embodiment of the present invention; Figure 11 It is a schematic three-dimensional structure diagram of the perfusion box in an embodiment of the present invention; Figure 12 It is a schematic structure diagram of the side and back of the perfusion box in an embodiment of the present invention; Figure 13 It is a schematic structure diagram of the liquid pumping unit in an embodiment of the present invention; Figure 14 It is a schematic internal structure diagram of the perfusion box in an embodiment of the present invention; Figure 15 It is a schematic installation structure diagram of the main body end assembly in an embodiment of the present invention. Detailed implementation manners

[0022] To facilitate the understanding of the present application, the present application will be described more comprehensively below with reference to the relevant drawings. Embodiments of the present application are shown in the drawings. However, the present application can be implemented in many different forms and is not limited to the embodiments described herein. On the contrary, these embodiments are provided to make the disclosure of the present application more thorough and comprehensive.

[0023] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by those of ordinary skill in the technical field to which this application belongs. The terms used in the specification of this application herein are only for the purpose of describing specific embodiments and are not intended to limit this application.

[0024] It can be understood that spatial relationship terms such as "under", "below", "lower", "beneath", "above", "upper", etc. can be used herein to describe the relationship between an element or feature shown in the figure and other elements or features. It should be understood that in addition to the orientation shown in the figure, spatial relationship terms also include different orientations of the device during use and operation. For example, if the device in the drawing is flipped, the element or feature described as "under other elements" or "beneath it" or "under it" will be oriented "above" other elements or features. Therefore, the exemplary terms "under" and "beneath" can include both the upper and lower orientations. In addition, the device can also include other orientations (such as rotating 90° or other orientations), and the spatial description terms used herein are accordingly interpreted.

[0025] It should be noted that when an element is considered to be "connected" to another element, it can be directly connected to the other element or connected to the other element through an intermediate element. In the following embodiments, "connection", if there is a transmission of electrical signals or data between the connected circuits, modules, units, etc., should be understood as "electrical connection", "communication connection", etc.

[0026] As used herein, the singular forms "a", "an" and "the" may also include the plural forms unless the context clearly indicates otherwise. It should also be understood that the terms "comprise / include" or "have" etc. specify the presence of the stated features, wholes, steps, operations, components, parts or combinations thereof, but do not preclude the presence or addition of one or more other features, wholes, steps, operations, components, parts or combinations thereof.

[0027] As Figure 1 shown, the present application provides a ventricular assist system, which includes a pump head end assembly and a host end assembly B.

[0028] Combined withFigures 2 to 15 As shown, the pump head end assembly A includes a motor 100, an impeller 400, a delivery sheath 200, and a cable 300. The motor 100 is disposed at the distal end of the delivery sheath 200, and the impeller 400 is mounted on the motor 100.

[0029] The host end assembly B includes a host 500, a perfusion cassette 700, and a driving mechanism 610. The perfusion cassette 700 is detachably mounted on the host 500. The driving mechanism 800 is connected to the host 500 and is used to drive the pump liquid unit M inside the perfusion cassette 700 to work. The liquid outlet end of the pump liquid unit M is connected to the motor 100 through the cable 300 and is used for cooling the motor 100.

[0030] The ventricular assist system provided by the present application improves the blood pumping efficiency through the coordinated work of multiple components. It uses a delivery sheath with a motor disposed distally to transport blood, combines with the helical flow path formed by the circumferential bending of the impeller blades to enhance the axial propulsion ability of the blood and reduce the turbulent loss. The cable has an internal cooling channel to ensure the efficient and stable operation of the motor. The bent part of the blade helps the impeller to have a greater head during blood pumping, thereby increasing the aortic perfusion pressure and the blood pumping efficiency. The detachable perfusion cassette and the lightweight design simplify the clinical operation while enhancing the portability of the system. Overall, through the structural reconstruction and functional coordination, it realizes a more efficient and stable blood flow delivery.

[0031] Preferably, the motor 100 includes a housing 110, a coil 120, an inner membrane 130, and a rotor 140. The coil 120 is bonded inside the housing 110. The rotor 140 is located inside the coil 120. The inner membrane 130 is bonded to the inner side of the coil 120 and is used to isolate the coil 120 and the rotor 140.

[0032] Through the isolation of the inner membrane 130, the rotor 140 and the coil 120 will not come into contact during operation, preventing the internal clearance from becoming too small due to the vibration or heat generation of the rotor 140 during motor operation, wearing the coil 120, and further causing the motor to be damaged after the coil 120 is damaged. At the same time, the inner membrane 130 also prevents the glue from entering the motor during the assembly of the motor 100, resulting in the motor 100 being stuck. This greatly improves the service life of the motor 100 and reduces the assembly difficulty.

[0033] The impeller 400 includes a shaft 420 and at least two blades 410. The shaft 420 has opposite inlet ends 42a and outlet ends 42b. The blades 410 are connected to the shaft 420 and extend along the length direction of the shaft 420. At least one end of the blade 410 is bent circumferentially along the shaft 420.

[0034] For the convenience of description, the end of the blade 410 close to the inlet end 42a is called the upper blade end 411, and the end of the blade 410 at the outlet end 42b is called the lower blade end 412.

[0035] Therefore, the circumferential bending of at least one end of the blade 410 along the axle 420 can be in three situations, namely, two single-bending structures in which the blade upper end 411 is bent and the blade lower end 412 is straight or the blade upper end 411 is straight and the blade lower end 412 is bent, and a double-bending structure in which the blade upper end 411 is bent and the blade lower end 412 is bent.

[0036] The upper end 411 of the blade is bent to increase the blood pumping at the inlet end 42a, and the lower end 412 of the blade is bent to increase the blood pumping at the outlet end 42a. The simultaneous bending of the upper end 411 and the lower end 412 of the blade helps the impeller provide a greater lift when pumping blood, increase the aortic perfusion pressure, and increase work efficiency.

[0037] Comparative analysis shows that the double-bend structure is superior to the single-bend structure. The bending radius R3 of the upper end 411 of the blade ranges from 2.5 mm to 10 mm, and the bending radius R4 of the lower end 412 of the blade ranges from 2 mm to 10 mm.

[0038] Preferably, the angle α of the projections of the two ends of the blade 410 on the cross section of the wheel shaft 420 ranges from 30° to 150°. Under this structure, the blood pumping efficiency of the impeller 400 is optimal, the flow rate is larger at the same speed, and the hemolytic index is lower.

[0039] If the length of the blade 410 is too long or too short, the blood pumping efficiency will also be affected. In the present embodiment, the length of the blade 410 accounts for 65%-85% of the total length of the impeller 400. Preferably, the total length of the impeller 400 is 5 mm to 15 mm.

[0040] An outer diameter of the impeller 400 that is too large or too small will have an impact on the entire device. Specifically, an outer diameter of the impeller 400 that is too large will cause the overall outer diameter of the ventricular assist device to be larger, causing greater trauma during the introduction of the device and increasing the risk of blood loss and infection. When the outer diameter of the impeller 400 is too small, the blood pumping efficiency of the device is limited. In the present embodiment, the outer diameter of the impeller 400 ranges from 3 mm to 15 mm, wherein the outer diameter of the impeller 400 is determined by the outer edge of the blade 410.

[0041] In addition, regarding the thickness of the blade 410, if the blade 410 is too thick, the blood pumping efficiency will be affected, and if the blade 410 is too thin, the processing will become more difficult, the strength will be insufficient, and it will be easy to break. In this embodiment, the thickness of the blade 410 is 0.2mm~2mm.

[0042] Preferably, the edge of the blade 410 has a smooth transition and the transition fillet radius is between 0.05mm and 1mm, the connection between the blade 410 and the axle 420 has a rounded transition and the transition fillet radius is between 0.1mm and 0.5mm. The design of these two transition fillets can effectively reduce the shear force during blood transportation and reduce the hemolysis value.

[0043] For the axle 420, the axle 420 includes an inflow section L1 near the inflow end 42a, an outflow section L3 near the outflow end 42b, and a flow guiding section L2 located between the inflow section L1 and the outflow section L3.

[0044] The axle 420 has a streamlined structure with an outer diameter gradually increasing along the flow direction, and the flow guiding section L2 is a cylinder; the side walls of the inflow section L1 and the flow guiding section L2 are transitioned with rounded corners with a transition circle radius of 40 mm to 80 mm, the outer diameter range of the top end 421 of the inflow section L1 is 0.1 mm to 2 mm, and the side walls of the outflow section L3 and the flow guiding section L2 are transitioned with rounded corners with a transition circle radius of 3 mm to 10 mm; among them, the transition circle of the side wall of the inflow section L1 protrudes outward, and the transition circle of the side wall of the outflow section L3 sinks inward.

[0045] The above structural design ensures smoother blood flow during pumping, can provide better blood compatibility, reduce the hemolysis value, provide a greater perfusion pressure for the aorta during pumping, and reduce the direct impact of blood on blood vessels.

[0046] In this application, the delivery sheath 200 is a multi-lumen composite catheter and axially has mutually isolated liner rod holes 210, perfusion tube holes 220, and motor circuit holes 230. It has excellent anti-bending properties, is made of polymer materials such as PEBA, TPU, or PE, and has a smooth surface. In addition to using a liner rod to enhance the anti-bending property, a spring-like structure can also be wrapped inside the material to ensure that it is not easily bent.

[0047] The cable 300 includes a perfusion tube (not shown in the figure), a motor circuit (not shown in the figure), and a connector 301. One end of the perfusion tube is communicated with the perfusion tube hole 220, the other end is connected to the connector 301, the connector is connected to the liquid outlet end of the liquid pumping unit M, and the motor circuit is arranged in the motor circuit hole 230 for supplying power to the motor 100.

[0048] In actual use, it is found that there are many inconveniences in the installation and operation of the existing liquid perfusion system. The process is complex, the operation difficulty is relatively large, and the skill requirements for the instrument operator are relatively high. This not only increases the burden on medical staff but also may reduce the treatment effect due to improper operation. In addition, once the perfusion system is blocked or has other problems, the replacement and maintenance work are also inconvenient. This not only increases the treatment cost of patients but also may affect the safety and treatment effect of patients due to system failures.

[0049] In addition to the above structural improvements, this application also includes the following improvements regarding the host end component B: A card slot 600 for installing the perfusion box 700 is formed on the host 500, and the host 500 has a display screen.

[0050] At the bottom of the card slot 600, a pressure detection unit is provided, that is, a sensor 620 for detecting the applied pressure, which is connected to the host 500. When an external pressure acts, the real-time pressure will be displayed on the display screen.

[0051] The perfusion cassette 700 further includes a cassette body 70a, a liquid inlet pipe 730 and a liquid outlet pipe 740. The cassette body 70a is composed of an upper cover 720 and a lower cover 710. The cassette body 70a is detachably hung on the card slot 600. The lower end of the cassette body 70a corresponds to the bottom of the card slot 600. A pressure-receiving part 750 is provided on the cassette body 70a. When the perfusion cassette 700 is installed on the host 500, the pressure-receiving part 750 is in close contact with the pressure detection unit (i.e., the sensor 620). The liquid inlet pipe 730 and the liquid outlet pipe 740 are connected to the liquid pumping unit M. The side wall of the liquid outlet pipe 740 contacts the pressure-receiving part 750; The driving mechanism 610 is connected to the host 500 and is used to drive the liquid pumping unit M to pump the liquid from the liquid inlet pipe 730 and pump it out from the liquid outlet pipe 740; wherein, when the liquid flows through the liquid outlet pipe 740, the pressure-receiving part 750 protrudes outward to press the sensor 620.

[0052] At least one end of the card slot 600 is formed with a first limiting part, and second limiting parts are formed on both sides of the card slot 600. The cassette body 70a is configured to be limited at one end by the first limiting part and limited at both sides by the second limiting parts.

[0053] The first limiting part is a limiting groove 602 formed at one end of the bottom of the card slot 600. A limiting protrusion 702 is formed at the lower end of the cassette body 70a corresponding to the limiting groove 602. When the limiting protrusion 702 and the limiting groove 602 cooperate, the other end of the cassette body 70a can rotate along the limiting groove 602; The second limiting part includes a bayonet 601 formed on the side wall of the card slot 600. A movably arranged buckle 701 is formed on the side wall of the cassette body 70a. The buckle 701 is engaged with the bayonet 601.

[0054] The perfusion cassette 700 is inserted into the limiting groove 602 by inserting the limiting protrusion 702, and then the perfusion cassette 700 is rotated and pushed until the buckle 701 latches the bayonet 602. At the same time, the pressure-receiving part 750 is in close contact with the sensor 620. This method completes the work of the perfusion system and the monitoring of the perfusion pressure through one step, greatly reducing the operation difficulty of doctors and being simpler and more practical than the traditional method.

[0055] Wherein, a pressing part 703 is formed on the buckle 701. When the buckle 701 and the bayonet 601 cooperate, pressing the pressing part 703 separates the buckle 701 and the bayonet 601. The design of this structure realizes the disassembly of the perfusion cassette 700 simply and efficiently.

[0056] When the perfusion cartridge 700 becomes blocked or malfunctions, it is necessary to replace the perfusion cartridge 700 in a timely manner to prevent the motor 100 from overheating or malfunctioning due to lack of perfusion. This device can directly press the pressing part 703 to retract the two-sided buckles 701, and then gently pull and rotate to directly remove and replace the perfusion cartridge 700, which is simple and convenient, greatly shortening the replacement time and reducing the surgical risk.

[0057] Preferably, a pressure storage cavity 70b is formed on the lower end surface of the cartridge body 70a, and the liquid outlet pipe 740 is communicated with the pressure storage cavity 70b. The pressure receiving part 750 includes a flexible heat-sealing film 751 arranged on the surface of the pressure receiving cavity 70b, and the flexible heat-sealing film 751 is configured to bulge outward when liquid flows through the inside of the pressure storage cavity 70b.

[0058] Among them, the flexible heat-sealing film 751 is made of medical materials such as TPU, Pebax or PVC. When liquid flows in through the liquid inlet pipe 730, the flexible heat-sealing film 751 bulges to apply pressure to the sensor 620, thereby reacting the pressure in the lumen in real time.

[0059] In this embodiment, the liquid pumping unit M includes a liquid pumping cylinder 900, a piston rod 950 and a piston driving member 800. A liquid pumping cavity 910 is formed inside the liquid pumping cylinder 900. Both the liquid inlet pipe 730 and the liquid outlet pipe 740 are communicated with the liquid pumping cavity 910. Check valves are arranged on both the liquid inlet pipe 730 and the liquid outlet pipe 740 to prevent liquid backflow. The piston rod 950 is axially movably arranged inside the cartridge body 70a, and one end of the piston rod 950 is slidably sealed with the liquid pumping cavity. The piston driving member 800 drives the piston rod 950 to reciprocate under the drive of the driving mechanism 610.

[0060] As an optional driving method, a rack is formed on the piston rod 950, and the piston driving member 800 includes a gear meshing with the rack. The above is only an optional driving method for the piston rod 950. In other embodiments, a cam structure can also be used in cooperation with a spring to achieve reciprocating drive, or it can be directly pushed and pulled by a stepping cylinder, which will not be elaborated here.

[0061] The driving mechanism 610 is preferably a motor, and the motor is arranged on the side of the main body 500 away from the card slot 600. Among them, the structure 603 is the assembly position of the motor 610, and the structure 604 is the assembly hole of the sensor 620. This structural design effectively saves installation space and optimizes the layout.

[0062] When it works, the motor drives the gear to rotate reciprocally, pushing the piston rod 950 to realize the functions of liquid suction and pumping. The liquid is sucked into the liquid pumping cylinder 900 through the liquid inlet pipe 730, then pushed into the pressure storage cavity 70b through the piston rod 950, and then transported to the motor 100 through the delivery sheath tube to realize the cooling perfusion of the motor.

[0063] The above are only the preferred embodiments of the present invention and are not intended to limit the present invention. Any modifications, equivalent replacements, improvements, etc. made within the spirit and principles of the present invention shall be included within the protection scope of the present invention.

Claims

1. A ventricular assist system, characterized in that, It includes a pump head end assembly and a main body end assembly; The pump head end assembly includes a motor, an impeller, a delivery sheath tube and a cable. The motor is arranged at the distal end of the delivery sheath tube, the impeller is mounted on the motor, and the impeller includes a shaft and at least two blades; the shaft has an inlet end and an outlet end which are opposite to each other; the blades are connected to the shaft and extend along the length direction of the shaft, and at least one end of the blade is bent along the circumferential direction of the shaft; The main body end assembly includes a main body, a perfusion box and a driving mechanism; the perfusion box is detachably mounted on the main body, the driving mechanism is connected to the main body and is used for driving a liquid pumping unit inside the perfusion box to work, and the liquid outlet end of the liquid pumping unit is connected to the motor through the cable for cooling the motor.

2. The ventricular assist system according to claim 1, characterized in that, One end of the blade close to the inlet end is bent and the bending radius is 2.5 mm to 10 mm; And / or one end of the blade close to the outlet end is bent and the bending radius is 2 mm to 10 mm.

3. The ventricular assist system according to claim 1, characterized in that The included angle range of the projections of the two ends of the blade on the cross-section of the shaft is 30° - 150°, the length of the blade accounts for 65% - 85% of the total length of the impeller, and the total length of the impeller is 5 mm to 15 mm.

4. The ventricular assist system according to claim 1, characterized in that The outer diameter range of the impeller is 3 mm to 15 mm, and the outer diameter of the impeller is determined by the outer edge of the blade; the thickness of the blade is 0.2 mm to 2 mm, the edge of the blade has a smooth transition and the transition fillet radius is between 0.05 mm and 1 mm, and the connection between the blade and the shaft has a fillet transition and the transition fillet radius is between 0.1 mm and 1 mm.

5. The ventricular assist system according to claim 1, wherein The shaft includes an inlet section close to the inlet end, an outlet section close to the outlet end and a guiding section located between the inlet section and the outlet section. The shaft is a streamlined structure with an outer diameter gradually increasing along the flow direction, and the guiding section is a cylinder; the side wall of the inlet section and the side wall of the guiding section have a fillet transition and the transition circle radius is 40 mm to 80 mm, the outer diameter range of the top end of the inlet section is 0.1 mm to 2 mm, and the side wall of the outlet section and the side wall of the guiding section have a fillet transition and the transition circle radius is 3 mm to 10 mm; the transition circle of the side wall of the inlet section protrudes outwards, and the transition circle of the side wall of the outlet section sinks inwards.

6. The ventricular assist system according to claim 1, wherein The motor includes a housing, a coil, an inner membrane and a rotor. The coil is bonded inside the housing, the rotor is located inside the coil, and the inner membrane is bonded to the inner side of the coil for isolating the coil and the rotor.

7. The ventricular assist system according to claim 1, wherein The delivery sheath tube is a multi-cavity composite catheter and axially provided with a mutually isolated liner rod hole, a perfusion tube hole and a motor circuit hole. The cable includes a perfusion tube, a motor circuit and a connector. One end of the perfusion tube is communicated with the perfusion tube hole, the other end is connected to the connector, the connector is connected to the liquid outlet end of the liquid pumping unit, and the motor circuit is arranged in the motor circuit hole.

8. The ventricular assist system according to claim 1, wherein A card slot for installing the perfusion box is formed on the main body, and a pressure detection unit is arranged at the bottom of the card slot for detecting the perfusion pressure; The perfusion box further comprises a box body, a liquid inlet pipe and a liquid outlet pipe, the box body is detachably mounted on the card slot, the lower end of the box body corresponds to the bottom of the card slot, a pressure-bearing portion is arranged on the box body, the pressure-bearing portion is closely fitted with the pressure detection unit when the perfusion box is mounted on the host, the liquid inlet pipe and the liquid outlet pipe are connected to the liquid pump unit, and the side wall of the liquid outlet pipe is in contact with the pressure-bearing portion; The driving mechanism is connected to the host and is used to drive the liquid pumping unit to pump liquid into the liquid inlet pipe and out of the liquid outlet pipe; When liquid flows through the liquid outlet pipe, the pressure receiving portion protrudes outward to press the pressure detection unit.

9. The ventricular assist system according to claim 8, wherein A first limiting portion is formed at at least one end of the card slot, and second limiting portions are formed at both sides of the card slot. The box body is configured to be limited by the first limiting portion at one end and limited by the second limiting portions at both sides.

10. The ventricular assist system according to claim 9, wherein The first limiting portion is a limiting groove formed at one end of the bottom of the card slot, and a limiting protrusion is formed at one end of the box body corresponding to the limiting groove. When the limiting protrusion and the limiting groove cooperate, the other end of the box body can rotate along the limiting groove; the second limiting portion includes a bayonet formed on the side wall of the card slot, and a movable buckle is formed on the side wall of the box body, and the buckle cooperates with the bayonet to be engaged.

11. The ventricular assist system according to claim 10, wherein, A pressing portion is formed on the clamping strip, and when the buckle and the bayonet are matched, the pressing portion is pressed to separate the buckle and the bayonet.

12. The ventricular assist system according to claim 11, characterized in that, A pressure storage chamber is formed on the lower end surface of the box body, the liquid outlet pipe is connected to the pressure storage chamber, the pressure-bearing part includes a flexible hot-melt film arranged on the surface of the pressure-bearing chamber, and the flexible hot-melt film is constructed to bulge outward when liquid flows through the inside of the pressure storage chamber.

13. The ventricular assist system according to claim 11, wherein, The pump fluid unit includes a pump fluid cylinder, a piston rod and a piston driving member. A pump fluid cavity is formed inside the pump fluid cylinder. The liquid inlet pipe and the liquid outlet pipe are both connected to the pump fluid cavity. The liquid inlet pipe and the liquid outlet pipe are both provided with a one-way valve. The piston rod is axially movably arranged inside the box body and one end of the piston rod is slidingly sealed with the pump fluid cavity. The piston driving member drives the piston rod to reciprocate under the drive of the driving mechanism.

14. The ventricular assist system according to claim 11, wherein A rack is formed on the piston rod, and the piston driving member includes a gear matched with the rack.

15. The ventricular assist system according to claim 11, characterized in that, The driving mechanism comprises a motor, and the motor is arranged on a side of the host away from the card slot.

Images