CN116650828A - blood pump - Google Patents

Abstract

The application relates to a blood pump, which comprises a main-stage pumping device, a first conduit, a secondary-stage pumping device and a second conduit which are sequentially connected; the secondary pumping device comprises a secondary sleeve, a secondary impeller and a support; wherein the secondary impeller is arranged in the secondary sleeve; one end of the support is fixed to a proximal end of the secondary pumping device, and the other end is fixed to a distal end of the secondary pumping device through the secondary impeller in an axial direction of the secondary impeller, the secondary impeller being configured to be rotatable about the support. According to the blood pump, the support piece is used for supporting the secondary impeller, so that the secondary impeller can stably rotate, and the stability of the secondary pumping device in operation is enhanced. Even if the second guide tube and the first guide tube are washed and swung by blood flow, the secondary impeller is supported by the supporting piece and cannot easily generate radial deflection, so that the blood pump can stably run, and the stability of the blood pump during working is effectively improved.

Description

Blood pump

Technical Field

The application relates to the technical field of interventional medical instruments, in particular to a blood pump.

Background

Blood pumps, which are heart assist devices, are commonly used to partially or fully replace the heart to assist the patient's blood circulation. However, some pumping devices of conventional blood pumps are located in the aorta, and the two ends of the pumping device are connected to hoses (such as tubes), which are generally flexible, and when the blood flow rate in the aorta is high, the tubes may not be sufficient to stably support the pumping device in the aorta, so that the secondary impeller in the pumping device is easily deflected radially, and the stability of the blood pump is poor during operation.

Disclosure of Invention

Based on the above, the application provides a blood pump, which aims to solve the problem of poor working stability of the traditional blood pump.

In one embodiment, the blood pump comprises a primary pumping device, a first conduit, a secondary pumping device and a second conduit connected in sequence; wherein the secondary pumping device comprises a secondary sleeve, a support and an impeller arranged in the secondary sleeve; one end of the support is fixed to the proximal end of the secondary pumping device and the other end passes through the secondary impeller to be fixed to the distal end of the secondary pumping device, the secondary impeller being rotatable about the support.

In one embodiment, the secondary pumping device further comprises a secondary motor connecting the secondary sleeve and the second conduit; the secondary motor comprises a rotating shaft, and the rotating shaft extends out from the far end of the secondary motor and is fixedly connected with the secondary impeller; the rotating shaft is arranged as a hollow tube and is rotatably sleeved on the periphery of the supporting piece.

In one embodiment, the proximal end of the secondary motor is configured with a stationary pin and a proximal bearing; wherein the fixing pin is fixedly connected with the second conduit; the near-end bearing is arranged on the fixed pin so as to be connected with the near end of the rotating shaft in a penetrating way; the proximal end of the supporting piece passes through the rotating shaft and the proximal end bearing to be fixedly connected with the fixing pin.

In one embodiment, the distal end of the secondary cannula is provided with a connecting end for connecting and fixing the first catheter; the distal end of the support piece passes through the rotating shaft and the secondary impeller to be fixedly connected with the connecting end.

In one embodiment, a first flushing pipe is arranged inside the first conduit to supply flushing liquid to the primary pumping device; a second flushing pipe is arranged in the second conduit to supply flushing liquid to the secondary stage pumping device; the support member is hollow to form an intermediate passage and communicates the first flush tube with the second flush tube.

In one embodiment, the support member includes a first middle section penetrating through the rotating shaft, a first gap is formed between an outer peripheral surface of the first middle section and an inner peripheral surface of the rotating shaft at intervals, and two ends of the first gap are respectively communicated with the second flushing pipe and the lumen of the secondary sleeve.

In one embodiment, the secondary impeller is provided with a penetrating hole penetrating along the axial direction of the secondary impeller, the proximal end part of the penetrating hole is used for inserting and fixing the distal end of the rotating shaft, and the distal end part of the penetrating hole is used for the supporting piece to penetrate through; the support piece further comprises a second middle section penetrating through the penetrating hole; a second gap is arranged between the outer peripheral surface of the second middle section and the inner peripheral surface of the penetrating hole, and the second gap communicates the first gap with the lumen of the secondary sleeve.

In one embodiment, a first drain hole is formed through the side wall of the first middle section, and the first drain hole is communicated with the first gap; and/or a second drain hole is penetrated through the side wall of the second middle section, and the second drain hole is communicated with the second gap.

In one embodiment, the number of the first drain holes is a plurality, and at least part of the first drain holes are distributed along the axial direction or the circumferential direction of the first middle section;

and/or the number of the second drain holes is a plurality, at least part of the second drain holes are distributed along the axial direction or the circumferential direction of the second middle section.

In one embodiment, at least one of the first and second drain holes is spirally wound around a peripheral wall of the support member and extends in an axial direction of the support member.

In one embodiment, the support has an outer diameter smaller than the outer diameter of the first conduit; the outer diameter of the first conduit is smaller than the outer diameter of the second conduit.

In one embodiment, the support member is made of metal or ceramic

The blood pump of the application is characterized in that the support piece is arranged in the secondary stage pumping device, one end of the support piece is fixed at the proximal end of the secondary stage pumping device, the other end of the support piece penetrates through the secondary impeller to be fixed at the distal end of the secondary stage pumping device, and the secondary impeller can rotate around the support piece, so that the support piece can support the secondary impeller, the secondary impeller can stably rotate, and the stability of the secondary stage pumping device in operation is enhanced. Even if the second guide tube and the first guide tube are washed and swung by blood flow, the secondary impeller is supported by the supporting piece and cannot easily generate radial deflection, so that the blood pump can stably run, and the stability of the blood pump during working is effectively improved.

Drawings

Fig. 1 is a schematic diagram of a blood pump according to an embodiment of the present application.

Fig. 2 is a schematic view of a blood pump according to an embodiment of the present application penetrating a portion of the aorta.

Fig. 3 is a cross-sectional view of the blood pump of fig. 2 disposed through a portion of the aorta.

Fig. 4 is a schematic illustration of the secondary stage pumping device of fig. 1 coupled to a first conduit and a second conduit.

Fig. 5 is an exploded view of a portion of the secondary stage pumping device of fig. 4.

Fig. 6 is a schematic diagram of a secondary stage pumping device in an embodiment of the application.

Fig. 7 is a cross-sectional view of the secondary stage pumping device of fig. 6 taken along A-A.

FIG. 8 is P in FIG. 7 ₁ A schematic diagram is enlarged.

FIG. 9 is P in FIG. 7 ₂ A schematic diagram is enlarged.

Fig. 10 is a cross-sectional view of the secondary stage pumping device of fig. 6 taken along line B-B.

Fig. 11 is a schematic diagram illustrating the assembly of the shaft, the support and the secondary impeller of fig. 7.

Fig. 12 is an axial cross-sectional view of the shaft and support member of fig. 11, after assembly with a secondary impeller.

Fig. 13 is an enlarged view of a portion of the shaft of fig. 12 assembled with a support and a secondary impeller.

Fig. 14 is a schematic view of the shaft and the support member of fig. 7 after being disassembled.

Fig. 15 is a schematic view of another embodiment of the support of fig. 14.

Fig. 16 is a schematic view of the assembled anchor pin and proximal bearing of fig. 7.

Fig. 17 is a schematic view of the internal structure of the fixing pin of fig. 16.

Reference numerals illustrate:

Detailed Description

In order that the above objects, features and advantages of the application will be readily understood, a more particular description of the application will be rendered by reference to the appended drawings. In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present application. The present application may be embodied in many other forms than described herein and similarly modified by those skilled in the art without departing from the spirit of the application, whereby the application is not limited to the specific embodiments disclosed below.

In the description of the present application, it should be understood that, if any, these terms "center", "longitudinal", "transverse", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential", etc., are used herein with respect to the orientation or positional relationship shown in the drawings, these terms refer to the orientation or positional relationship for convenience of description and simplicity of description only, and do not indicate or imply that the apparatus or element referred to must have a particular orientation, be constructed and operated in a particular orientation, and therefore should not be construed as limiting the application.

Furthermore, the terms "first," "second," and the like, if any, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include at least one such feature. In the description of the present application, the terms "plurality" and "a plurality" if any, mean at least two, such as two, three, etc., unless specifically defined otherwise.

In the present application, unless explicitly stated and limited otherwise, the terms "mounted," "connected," "secured," and the like are to be construed broadly. For example, the two parts can be fixedly connected, detachably connected or integrated; can be mechanically or electrically connected; either directly or indirectly, through intermediaries, or both, may be in communication with each other or in interaction with each other, unless expressly defined otherwise. The specific meaning of the above terms in the present application can be understood by those of ordinary skill in the art according to the specific circumstances.

In the present application, unless expressly stated or limited otherwise, the meaning of a first feature being "on" or "off" a second feature, and the like, is that the first and second features are either in direct contact or in indirect contact through an intervening medium. Moreover, a first feature being "above," "over" and "on" a second feature may be a first feature being directly above or obliquely above the second feature, or simply indicating that the first feature is level higher than the second feature. The first feature being "under", "below" and "beneath" the second feature may be the first feature being directly under or obliquely below the second feature, or simply indicating that the first feature is less level than the second feature.

It will be understood that if an element is referred to as being "fixed" or "disposed" on another element, it can be directly on the other element or intervening elements may also be present. If an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present. The terms "vertical," "horizontal," "upper," "lower," "left," "right," and the like as used herein, if any, are for descriptive purposes only and do not represent a unique embodiment.

The present application provides an embodiment of a blood pump that may be used to assist in the flow of blood in the right ventricle or may be incorporated into assist in the flow of blood in the left ventricle, without limitation. In order to avoid redundancy, the following description will take the example that the blood pump is applied to assist the blood flow of the right ventricle. For ease of description, the term "proximal" is defined herein as the end of the interventional medical device that is closer to the operator, and the term "distal" is defined herein as the end of the interventional medical device that is farther from the operator, but is not intended to be limiting.

Referring to fig. 1 to 4, the blood pump 10 includes a primary pumping device 100, a first conduit 200, a secondary pumping device 300, and a second conduit 400, which are sequentially connected. Wherein the primary pumping device 100 is provided with a first inlet 101 and a first outlet 102; the secondary stage pumping device 300 is provided with a second inlet 301 and a second outlet 302. Optionally, the second inlet 301 is provided on the outer circumferential surface of the secondary stage pumping device 300.

Specifically, a pigtail (not shown) may be attached to the distal end of the primary pumping device 100, and positioned on the inner wall of the heart by a pigtail support. The proximal end of the primary pumping means 100 is connected to the distal end of the first catheter 200, the proximal end of the first catheter 200 being connected to the distal end of the secondary pumping means 300; the proximal end of the secondary stage pumping device 300 is then connected to the distal end of the second catheter 400.

After the blood pump 10 is inserted into the patient, the primary pumping device 100 extends from the aorta 20 through the valve and partially into the ventricle such that the first inlet 101 of the primary pumping device 100 is located in the ventricle and the first outlet 102 of the primary pumping device 100 is located in the aorta 20; while the secondary pumping device 300 and the first catheter 200 are in the aorta 20; a second conduit 400 extends from the secondary stage pumping device 300 to outside the patient. When the blood pump 10 is started to operate, blood in the ventricle flows into the main stage pumping device 100 from the first inlet 101, flows out to the ascending portion 22 of the aorta 20 from the first outlet 102 after being accelerated by the main stage pumping device 100, and flows along the ascending portion 22 of the aorta 20 in the direction of the aortic arch 22; subsequently, the blood meets the secondary pumping device 300 and is sucked therein by the second inlet 301 of the secondary pumping device 300, and after the secondary pumping device 300 accelerates again the sucked blood, the blood is discharged from the second outlet 302 into the descending portion 23 of the aorta 20, so that the blood flow can be accelerated, the blood can smoothly flow through the aortic arch 22, and the blood circulation can be accelerated.

As can be seen from the above, the blood pump 10 according to the present application has a two-stage driving function by arranging the primary pumping device 100, the first conduit 200, the secondary pumping device 300, and the second conduit 400 and sequentially connecting the primary pumping device 100, the first conduit 200, the secondary pumping device 300, and the second conduit 400, and accelerating blood at least twice by using the primary pumping device 100 and the secondary pumping device 300, so that the driving force of the blood pump 10 can be effectively enhanced, and the blood flow pumped by the blood pump 10 can be increased. Due to the presence of the secondary pumping device 300, the secondary pumping device 300 creates a negative pressure at the aortic arch 22, which accelerates the blood flow in the ascending portion 22 of the aorta 20 towards the descending portion 23 of the aorta 20, thereby increasing the blood flow.

It will be appreciated that since the blood pump 10 of the present application has a primary pumping means 100 and a secondary pumping means 300, the pumping power of a single pumping means (e.g., the primary pumping means 100 or the secondary pumping means 300) can be appropriately reduced to reduce the axial size reduction of the single pumping means, i.e., the length of the primary pumping means 100, so as to facilitate implantation into a patient, while ensuring that the total pumping power of the blood pump 10 is not less than the pumping power of a conventional blood pump 10. In particular, if the length of the main stage pumping device 100 is reduced, the difficulty of the main stage pumping device 100 traversing the aortic arch 22 may be greatly reduced.

It is contemplated herein that the distal end of the primary pumping device 100 is positioned in the ventricle through the pigtail, and the middle of the primary pumping device 100 may be held in place by the valve. Whereas for the secondary pumping device 300, the secondary pumping device 300 is entirely located in the aorta 20, the second conduit 400 and the first conduit 200 are generally flexible, and the second conduit 400 and the first conduit 200 may not be sufficiently stable to support the secondary pumping device 300 or the secondary impeller 320 of the secondary pumping device 300 may be prone to radial runout when the blood flow rate in the aorta 20 is relatively high.

Referring to fig. 5-7, in view of the above, in some embodiments, the secondary pumping device 300 includes a secondary sleeve 320, a secondary impeller 330, and a support 340; wherein the secondary impeller 330 is disposed within the secondary sleeve 320; one end of the support 340 is fixed to the proximal end of the secondary stage pumping device 300, and the other end is fixed to the distal end of the secondary stage pumping device 300 through the secondary stage impeller 330 in the axial direction of the secondary stage impeller 330. The secondary impeller 330 is configured to be rotatable about a support 340.

Specifically, the second inlet 301 and the second outlet 302 are both provided on the secondary sleeve 320. A secondary impeller 330 is disposed within the secondary sleeve 320 and adjacent the second outlet 302. The support 340 may be provided as a hollow tube or a solid rod. If the supporting member 340 is provided as a solid rod, the supporting member 340 has a relatively high strength, so that the diameter of the supporting member 340 is properly reduced while ensuring that the supporting member 340 has a sufficient strength, thereby reducing the radial space occupied by the supporting member 340 by the secondary stage pumping device 300 and further reducing the radial dimension of the secondary stage pumping device 300.

In the blood pump of the present application, the support 340 is disposed inside the secondary pumping device 300, so that the secondary impeller 330 of the secondary pumping device 300 can be supported by the support 340, and the secondary impeller 330 can be stably rotated, thereby enhancing the stability of the secondary pumping device 300 during operation. Even when the blood flow velocity in the aorta 20 is fast, the second catheter 400 and the first catheter 200 are swung by the blood flow scouring, and the secondary impeller 330 is supported by the support 340, the radial runout does not easily occur.

Optionally, the supporting member 340 is made of a metal material or a ceramic material, so that the supporting member 340 has better strength, is not easy to bend, and can stably support the secondary pumping device 300.

Referring to fig. 7, in some embodiments, the secondary pumping device 300 further includes a secondary motor 310, a secondary sleeve 320 is partially sleeved on the periphery of the secondary motor 310, and the secondary motor 310 connects the secondary sleeve 320 and the second conduit 400; the secondary motor 310 comprises a rotating shaft 314, and the rotating shaft 314 extends out from the distal end of the secondary motor 310 and is fixedly connected with the secondary impeller 330; the rotating shaft 314 is provided as a hollow tube and rotatably sleeved on the outer circumference of the supporting member 340.

Specifically, the proximal end of the secondary motor 310 is fixedly connected with the second catheter 400; the distal end of the secondary motor 310 is fixedly connected with the proximal end of the secondary sleeve 320; the distal end of secondary cannula 320 is fixedly coupled to first catheter 200. As shown in fig. 7, 9 and 11, the supporting member 340 has a first end 341 and a second end 342, and the second end 342 is far from the first end 341; wherein, the first end 341 is penetrating into the secondary motor 310 and is fixed to the proximal end of the secondary motor 310; the second end 342 extends from the distal end of the secondary motor 310 and is secured to the distal end of the secondary cannula 320 through the lumen of the secondary cannula 320 through the secondary impeller 330.

Referring to fig. 7, 9 and 16, further, the proximal end of the secondary motor 310 is provided with a fixing pin 315 and a proximal bearing 316; wherein, the fixing pin 315 is fixedly connected with the second conduit 400; the proximal bearing 316 is mounted on the fixing pin 315 for the proximal end of the rotating shaft 314 to be connected; the proximal end of the support 340 is fixedly coupled to the fixing pin 315 through the rotation shaft 314 and the proximal bearing 316.

Specifically, a first positioning hole 315b (as shown in fig. 16 and 17) is provided at one end of the fixing pin 315 near the second conduit 400, and the first positioning hole 315b is used for inserting and fixing the second conduit 400; the other end of the fixing pin 315 (i.e., the end facing the rotating shaft 314) is provided with a mounting hole 315a and a second positioning hole 315c; the second positioning hole 315c is located at a side of the mounting hole 315a away from the rotation shaft 314. The proximal bearing 316 is embedded in the mounting hole 315a of the fixing pin 315, and the proximal bearing 316 is connected to the proximal end of the rotating shaft 314 in a penetrating manner, so that the rotating shaft 314 can rotate. The proximal end (i.e., first end 341) of the support 340 extends outwardly from the proximal end of the shaft 314 and through the proximal bearing 316 for insertion into the second positioning hole 315c such that the first end 341 of the support 340 is secured within the second positioning hole 315 c.

Referring to fig. 5 and 11, further, a distal end of the secondary sleeve 320 is provided with a connection end 324 for connection and fixation of the first catheter 200; the distal end of the support 340 is fixedly connected with the connecting end 324 through the rotating shaft 314 and the secondary impeller 330. That is, the distal end of the support 340 (i.e., the second end 342) is inserted into and secured to the connection end 324.

Specifically, the connecting end 324 includes a tapered portion 3241 and a spherical portion 3242; the spherical portion 3242 is for guiding flow to the second inlet 301; the tapered portion 3241 has a conical or truncated cone-shaped structure, and the tapered portion 3241 is fixedly connected to the first catheter 200. The connection end 324 is provided with a communication hole that penetrates the tapered portion 3241 and the spherical portion 3242 in the axial direction of the secondary sleeve 320. The second end 342 of the support 340 is inserted and fixed in the communication hole.

In some embodiments, a first flushing flow channel is provided in the primary pumping device 100 to inject flushing fluid (e.g. physiological saline) to prevent thrombus from entering the primary pumping device 100, and to dissipate heat from the primary pumping device 100. The secondary pumping device 300 is provided with a second flushing flow channel for injecting flushing liquid (such as physiological saline) to prevent blood from entering the secondary pumping device 300 to generate thrombus, and can also dissipate heat of the secondary pumping device 300. In view of this, the first conduit 200 is internally perforated with a first flushing pipe (not shown in the figures) for supplying the main stage pumping device 100 with flushing liquid; the second conduit 400 is provided internally with a second flushing pipe 420 for supplying the flushing liquid to the secondary stage pumping means 300.

In this embodiment, in order to prevent the first flushing pipe from passing through the secondary stage pumping device 300, the supporting member 340 is provided in a hollow shape such that an intermediate passage 303 is formed inside the supporting member 340, and the intermediate passage 303 communicates the first flushing pipe with the second flushing pipe 420. That is, the distal end of the second flush tube 420 communicates with both the second flush flow passage, intermediate passage 303 of the secondary stage pumping device 300. So configured, a portion of the rinse solution supplied by the second rinse tube 420 may enter the second rinse flow channel to be supplied to the secondary pumping apparatus 300; another portion is fed via the intermediate channel 303 to the first flushing pipe and then via the first flushing pipe to the main stage pumping device 100.

As shown in fig. 8, of course, the manner of forming the intermediate passage 303 is not limited thereto. In other embodiments, the length of the rotation shaft 314 may be extended such that the distal end of the rotation shaft 314 is rotatably mounted to the connection end 324, and a first gap 304 is formed between the outer circumferential surface of the rotation shaft 314 and the inner circumferential surface of the support 340 at intervals, and the first gap 304 may serve as the intermediate passage 303. By such a design, not only the portion of the flushing fluid supplied from the second flushing pipe 420 can be supplied to the first flushing pipe, but also the distal end of the first gap 304 is not exposed to the distal end of the secondary impeller 330, and the blood in the secondary sleeve 320 is not likely to enter the secondary motor 310 from the first gap 304.

It is worth mentioning that if the first conduit 200 is run through the secondary stage pumping device 300, there may be a plurality of drawbacks: (1) the diameter of the first catheter 200 needs to be reduced, the lumen of the first catheter 200 is difficult to accommodate the wires and first flush tube of the primary pumping device 100, and the strength of the first catheter 200 may be too small to maneuver the guide secondary pumping device 300 through the blood vessel and into the heart; (2) if the diameter of the first conduit 200 is not reduced, the diameter of the secondary pumping device 300 needs to be increased, which causes the secondary pumping device 300 to be increased in volume, thereby increasing the difficulty of implantation into the human body; (3) the first guide tube 200 is easily interfered with the internal components of the secondary stage pumping device 300 during the passage of the secondary stage pumping device 300, and a gap between the outer circumference of the first guide tube 200 and the secondary stage pumping device 300 is difficult to seal, and blood is easily permeated to cause a thrombus accident, etc.

With respect to the foregoing manner of threading the first catheter 200, the proximal end of the first catheter 200 of the present application is only connected to the distal end of the secondary stage pumping device 300 and is used to deliver irrigation fluid or electrical wires through the intermediate channel 303 within the secondary stage pumping device 300, thereby overcoming at least one of the above-mentioned three drawbacks, without reducing the diameter of the first catheter 200 or increasing the diameter of the secondary stage pumping device 300, so that the secondary stage pumping device 300 has a smaller volume, and thus reduces the implantation difficulty.

Referring to fig. 7, 8 and 11, in some embodiments, since the supporting member 340 penetrates the rotating shaft 314, the supporting member 340 includes a first middle section 343 penetrating the rotating shaft 314. Alternatively, a first gap 304 is formed between the outer circumferential surface of the first intermediate section 343 and the inner circumferential surface of the rotating shaft 314 at intervals, and two ends of the first gap 304 are respectively communicated with the first flushing pipe and the lumen of the secondary sleeve 320. This may allow a portion of the irrigant supplied by the second irrigation tube 420 to be diverted to the first gap 304 and discharged along the first gap 304 to the lumen of the secondary cannula 320.

As shown in fig. 7, 12 and 13, based on the above arrangement, on one hand, the inner peripheral surface of the rotating shaft 314 and the outer peripheral surface of the supporting member 340 can be lubricated, the friction coefficient between the rotating shaft 314 and the supporting member 340 can be reduced, and the friction force during the relative rotation of the rotating shaft 314 and the supporting member 340 can be reduced; on the other hand, heat generated by friction can be taken away, and the rotating shaft 314 and the supporting piece 340 can be radiated; and prevents blood within the lumen of the secondary cannula 320 from entering the secondary motor 310 from the exit aperture 331 of the secondary impeller 330. Of course, the shaft 314 can be suspended relative to the support 340, thereby reducing friction between the shaft 314 and the support 340.

Specifically, as shown in fig. 7, 16 and 17, a first positioning hole 315b is formed at one end of the fixing pin 315 near the second conduit 400, the second flushing pipe 420 is inserted into the first positioning hole 315b, the flushing fluid supplied by the second flushing pipe 420 enters the first positioning hole 315b, and then is split into three branches through the first positioning hole 315b, the splitting channel on the fixing pin 315, and the like, and the fluids of the three branches enter the second flushing flow channel, the middle channel 303 and the first gap 304 respectively.

Referring to fig. 7, 8 and 13, further, the secondary impeller 330 is further provided with a through hole 331, and the through hole 331 penetrates the secondary impeller 330 along the axial direction thereof; the proximal portion 331a of the through hole 331 is configured to be inserted and fixed at the distal end of the rotating shaft 314, and the distal portion 331b of the through hole 331 is configured to be penetrated by the supporting member 340. The supporting member 340 further includes a second middle section 344 penetrating into the penetrating hole 331; a second gap 305 is provided between the outer peripheral surface of the second intermediate section 344 and the inner peripheral surface of the through hole 331, and the second gap 305 communicates the first gap 304 with the lumen of the secondary sleeve 320. In this way, flushing fluid from the second flushing pipe 420 can partially enter the first gap 304 and be discharged through the second gap 305 into the lumen of the secondary cannula 320, whereby the distal end of the second gap 305 can be prevented from entering the impeller, the secondary motor 310, and the risk of thrombus formation is reduced.

Referring to fig. 7, 13 and 14, in some embodiments, the side wall of the support 340 may further be provided with a drain hole, which is used to communicate the middle channel 303 with the first gap 304 or the second gap 305, so that the fluid in the middle channel 303 can be partially drained to the first gap 304 or the second gap 305, so as to increase the flow and the flow velocity in the first gap 304 or the second gap 305, so that the resistance of the blood in the lumen of the secondary sleeve 320 entering the secondary impeller 330 and the secondary motor 310 from the second gap 305 is increased, and further, the thrombus is more effectively prevented.

Optionally, a first drain hole 34a is formed through a side wall of the first middle section 343, and the first drain hole 34a is communicated with the first gap 304; and/or, a second drain hole 34b is formed through a sidewall of the second intermediate section 344, and the second drain hole 34b is in communication with the second gap 305. That is, the support 340 may be provided with only one of the first and second drain holes 34a and 34b, or may be provided with both the first and second drain holes 34a and 34b. The number of first drain holes 34a may be one or more; the number of the second drain holes 34b may be one or more.

In this embodiment, a plurality of first drain holes 34a are formed through the sidewall of the first intermediate section 343; at least a portion of the first drain hole 34a is arranged in the axial direction of the first intermediate section 343. This arrangement may allow the fluid in the first intermediate section 343 to gradually drain in the direction of flow thereof, helping to push the fluid in the first gap 304 to flow in the direction of the second gap 305 and accelerating the fluid discharge.

Of course, in other embodiments, at least a portion of the first drain holes 34a may also be circumferentially arranged along the first intermediate section 343. By arranging the first intermediate section 343, when the fluid in the first intermediate section 343 flows out from the part of the drainage hole, the fluid is discharged along the outer circumference of the first intermediate section 343 in a radial manner, so that the flow rate of the flushing fluid at each position of the circumferential surface of the first gap 304 can be more uniform, and the backflow of the blood to the secondary motor 310 through the first gap 304 can be more favorably prevented.

Referring to fig. 7, 13 and 14, in some embodiments, a plurality of second drain holes 34b are formed through a sidewall of the second middle section 344; at least a portion of the second drain hole 34b is axially aligned with the second intermediate section 344. This arrangement may allow the fluid within the second intermediate section 344 to gradually drain in its direction of flow, helping to push the fluid within the second gap 305 out of the lumen of the secondary cannula 320 and accelerating the fluid discharge.

Of course, in other embodiments, at least a portion of the second drain holes 34b may also be circumferentially aligned with the second intermediate section 344. By arranging the two parts, when the fluid in the second middle section 344 flows out from the part of the drainage holes, the fluid is discharged along the outer circumference of the second middle section 344 in a radial drainage way, so that the flow speed of the flushing fluid at each position of the circumferential surface of the second gap 305 can be more uniform, and the backflow of the blood to the first gap 304 through the second gap 305 can be more favorably prevented.

In some embodiments, at least one of the first and second drain holes 34a, 34b is spirally wound around the circumferential wall of the support 340 and extends in the axial direction of the support 340. As shown in fig. 15, taking the first drain hole 34a as an example of spirally surrounding the circumferential wall of the support 340, when the rotating shaft 314 rotates, a driving force in a spiral direction is generated for the fluid discharged from the first drain hole 34a, and because the fluid discharged from the first drain hole 34a also has a tendency to spirally surround, the fluid discharged from the first drain hole 34a to the first gap 304 will be spirally flowed to the second gap 305 (in a direction indicated by a dotted arrow in fig. 15) under the driving force generated by the rotation of the rotating shaft 314, so as to increase the flow rate and the flow velocity in the first gap 304, so that the resistance of the blood in the lumen of the secondary sleeve 320 from the second gap 305 to the impeller and the secondary motor 310 is greater, and further, the thrombus is more effectively prevented.

In some embodiments, a first electrical wire (not shown) is also provided inside the first conduit 200, the distal end of which connects to the drive portion of the primary pumping device 100 to provide electrical power to the primary pumping device 100. Preferably, the first wire and the first flush tube are disposed within the first catheter 200 without interfering with each other. In this embodiment, the first electrical wire is connected to the primary pumping device 100 from the proximal end to the distal end through the second conduit 400, the intermediate channel 303 of the secondary pumping device 300 and the first conduit 200 in this order. The second conduit 400 is also internally sleeved with a second electrical wire (not shown) having a distal end connected to the secondary stage pumping device 300 to provide electrical power to the secondary stage pumping device 300. Preferably, the second wire and the second flush tube 420 are disposed within the first catheter 200 without interfering with each other. Since the first wire, the second wire and the second flush tube 420 are all required to pass through the second catheter 400, only the first wire and the first flush tube need pass through the first catheter 200.

Optionally, the diameter D of the support 340 ₃ Smaller than the outer diameter D of the first conduit 200 ₁ The radial dimension of the support 340 may be made smaller, thereby occupying less radial space of the secondary stage pumping device 300, making the radial dimension of the secondary stage pumping device 300 smaller, and reducing implantation difficulty. Since the first wire, the second wire and the second flush tube 420 all need to pass through the second catheter 400, and only the first wire and the first flush tube need to pass through the first catheter 200, the outer diameter D of the first catheter 200 is also optionally, in view of this ₁ Smaller than the outer diameter D of the second conduit 400 ₂ . This design allows the radial dimension of the first catheter 200 to be kept small, while the first catheter 200 is able to accommodate the wires and the first flush tube of the primary pumping device 100, and the first catheter 200 is flexible to facilitate guiding the two pumping devices for intravascular movement.

Referring to fig. 4, further, the outer diameter D of the second conduit 400 ₂ Less than or equal to the outer diameter D of the first conduit 200 ₁ To avoid the outer diameter D of the second conduit 400 in case the second conduit 400 is able to accommodate the wires of the two pumping means and the second flushing pipe 420 ₂ Too large for itThe implantation into the human body causes an effect. If the second conduit 400 is greater than the outer diameter D of the first conduit 200 ₁ Is excessive in the radial dimension of the second catheter 400, the second catheter 400 is too hard, the second catheter 400 is difficult to adapt to the shape of the blood vessel to bend, and a great implantation difficulty may exist.

In some embodiments, the inner circumferential surface of the rotating shaft 314 is provided with a first ceramic material layer, and the outer circumferential surface of the supporting member 340 is provided with a second ceramic material layer to reduce the friction coefficient between the rotating shaft 314 and the supporting member 340, and reduce the friction force when the rotating shaft 314 and the supporting member 340 relatively rotate.

Referring to fig. 5 and 7, in some embodiments, the secondary pumping device 300 includes a secondary motor 310, and the first flushing flow path is formed within the secondary motor 310. The secondary motor 310 includes a housing 311, a stator 312, a rotor 313 and a rotating shaft 314 mounted in the housing 311; the rotating shaft 314 is sleeved on the outer periphery of the supporting member 340, the distal end of the rotating shaft 314 penetrates out of the housing 311 to be fixedly connected with the secondary impeller 330, and the rotating shaft 314 can rotate relative to the supporting member 340; the rotor 313 is fixedly connected with the outer peripheral surface of the rotating shaft 314; the stator 312 is capable of generating a magnetic field that drives the rotor 313 to rotate.

The rotating shaft 314 is rotatably sleeved on the outer periphery of the supporting member 340, the distal end of the rotating shaft 314 penetrates out of the housing 311 to be fixedly connected with the secondary impeller 330, the rotor 313 is fixedly connected with the outer peripheral wall of the rotating shaft 314, and the stator 312 surrounds the outer periphery of the rotating shaft 314. The rotor 313, the stator 312, the sensor 360 and the secondary impeller 330 are all connected to the outer circumference of the rotating shaft 314, and the rotor 313, the sensor 360 and the stator 312 are all located inside the housing 311. The number of the rotors 313 is two, and the two rotors 313 are respectively positioned at two ends of the stator 312 and are fixedly connected with the rotating shaft 314. The housing 311 includes a cylindrical housing 311a, a proximal cap 311b, and a distal cap 311c; wherein a proximal cap 311b is coupled to the proximal end of the cylindrical housing 311a and a distal cap 311c is coupled to the distal end of the housing 311 to protect the rotor 313, the sensor 360 and the stator 312 from blood entering the interior of the housing 311.

Of course, in other embodiments, the secondary pumping device 300 may not include the secondary motor 310 and the impeller of the secondary pumping device 300 may be connected to the external motor by a flexible shaft.

The main stage pumping device 100 includes a main stage motor 110, a sleeve assembly, and a main stage impeller 130. Wherein the sleeve assembly comprises a main stage sleeve 120, an outlet pipe 150 provided with the first outlet 102 and an inlet pipe 140 provided with the first inlet 101 (as shown in fig. 17), the outlet pipe 150 connecting the main stage motor 110 and the proximal end of the main stage sleeve 120; the inlet tube 140 is connected to the distal end of the main stage sleeve 120 and the first conduit 200. A main stage impeller 130 is disposed within the outlet tube 150 and is coupled to a shaft 314 of the main stage motor 110. Optionally, the main stage sleeve 120 is an elastic tube; the secondary sleeve 320 is a rigid tube.

Through the design, the main-stage sleeve 120 has better elasticity and can adapt to the shape complete deformation of the blood vessel, so that the main-stage sleeve 120 can conveniently enter the ventricle. In addition, since the main stage sleeve 120 is clamped in the valve when the main stage pumping device 100 passes through the valve of the aorta 20 and enters the ventricle, the elasticity of the main stage sleeve 120 can buffer the acting force between the valve and the main stage sleeve 120, so that the reaction force applied to the valve is reduced, and the valve damage is avoided. Since the secondary cannula 320 of the secondary pumping device 300 is not in contact with the valve because the secondary pumping device 300 is entirely located in the artery, the secondary cannula 320 may be provided as a rigid tube, i.e., the secondary cannula 320 may be made of a metal material, so that the secondary cannula 320 is not easily deformed by compression, and smooth passage of blood is ensured.

As can be seen from this, the blood pump 10 according to the present application has a two-stage driving function by arranging the primary pumping device 100, the first conduit 200, the secondary pumping device 300, and the second conduit 400 and sequentially connecting the primary pumping device 100, the first conduit 200, the secondary pumping device 300, and the second conduit 400, and accelerating the blood at least twice by using the primary pumping device 100 and the secondary pumping device 300, so that the driving force of the blood pump 10 can be effectively enhanced, and the flow rate of the blood pumped by the blood pump 10 can be increased. Due to the presence of the secondary pumping device 300, the secondary pumping device 300 creates a negative pressure at the aortic arch 22, which accelerates the blood flow in the ascending portion 22 of the aorta 20 towards the descending portion 23 of the aorta 20, thereby increasing the blood flow.

In the blood pump of the present application, the support 340 is disposed inside the secondary stage pumping device 300, so that the secondary impeller 330 of the secondary stage pumping device 300 can be supported by the support 340, and the secondary impeller 330 can be stably rotated, thereby enhancing the stability of the secondary stage pumping device 300 during operation. Even if the second catheter 400 and the first catheter 200 are flung-swung by the blood flow, the secondary impeller 330 is supported by the support 340 without being easily deflected. Optionally, the supporting member 340 is made of metal, so that the supporting member 340 has better strength, is not easy to bend, and can stably support the secondary pumping device 300.

The technical features of the above-described embodiments may be arbitrarily combined, and all possible combinations of the technical features in the above-described embodiments are not described for brevity of description, however, as long as there is no contradiction between the combinations of the technical features, they should be considered as the scope of the description.

The above examples illustrate only a few embodiments of the application, which are described in detail and are not to be construed as limiting the scope of the claims. It should be noted that it will be apparent to those skilled in the art that several variations and modifications can be made without departing from the spirit of the application, which are all within the scope of the application. Accordingly, the scope of protection of the present application is to be determined by the appended claims.

Claims (12)

1. A blood pump comprising a primary pumping device, a first conduit, a secondary pumping device and a second conduit connected in sequence; wherein, the liquid crystal display device comprises a liquid crystal display device,

the secondary pumping device comprises a secondary sleeve, a support and an impeller arranged in the secondary sleeve; one end of the support is fixed to the proximal end of the secondary pumping device and the other end passes through the secondary impeller to be fixed to the distal end of the secondary pumping device, the secondary impeller being rotatable about the support.

2. The blood pump of claim 1, wherein the secondary pumping device further comprises a secondary motor connecting the secondary cannula and the second conduit; the secondary motor comprises a rotating shaft, and the rotating shaft extends out from the far end of the secondary motor and is fixedly connected with the secondary impeller; the rotating shaft is arranged as a hollow tube and is rotatably sleeved on the periphery of the supporting piece.

3. The blood pump of claim 2, wherein the proximal end of the secondary motor is configured with a stationary pin and a proximal bearing; wherein the fixing pin is fixedly connected with the second conduit; the near-end bearing is arranged on the fixed pin so as to be connected with the near end of the rotating shaft in a penetrating way; the proximal end of the supporting piece passes through the rotating shaft and the proximal end bearing to be fixedly connected with the fixing pin.

4. The blood pump of claim 1, wherein a distal end of the secondary cannula is provided with a connection end for connection fixation of the first catheter; the distal end of the support piece passes through the rotating shaft and the secondary impeller to be fixedly connected with the connecting end.

5. The blood pump of any one of claims 2 to 4, wherein a first flush tube is provided inside the first conduit to supply flushing fluid to the primary pumping device; a second flushing pipe is arranged in the second conduit to supply flushing liquid to the secondary stage pumping device; the support member is hollow to form an intermediate passage and communicates the first flush tube with the second flush tube.

6. The blood pump of claim 5, wherein the support member comprises a first intermediate section penetrating through the rotating shaft, a first gap is formed between the outer peripheral surface of the first intermediate section and the inner peripheral surface of the rotating shaft at intervals, and two ends of the first gap are respectively communicated with the second flushing pipe and the lumen of the secondary sleeve.

7. The blood pump of claim 6, wherein the secondary impeller is provided with a penetrating hole penetrating along the axial direction thereof, a proximal end portion of the penetrating hole is used for inserting and fixing the distal end of the rotating shaft, and a distal end portion of the penetrating hole is used for penetrating the supporting piece; the support piece further comprises a second middle section penetrating through the penetrating hole; a second gap is arranged between the outer peripheral surface of the second middle section and the inner peripheral surface of the penetrating hole, and the second gap communicates the first gap with the lumen of the secondary sleeve.

8. The blood pump of claim 7, wherein a sidewall of the first intermediate section is perforated with a first drain hole, the first drain hole in communication with the first gap; and/or a second drain hole is penetrated through the side wall of the second middle section, and the second drain hole is communicated with the second gap.

9. The blood pump of claim 8, wherein the number of first drain holes is a plurality, at least a portion of the first drain holes being arranged axially or circumferentially of the first intermediate section;

and/or the number of the second drain holes is a plurality, at least part of the second drain holes are distributed along the axial direction or the circumferential direction of the second middle section.

10. The blood pump of claim 8, wherein at least one of the first and second drain holes is helically wrapped around a peripheral wall of the support and extends in an axial direction of the support.

11. The blood pump of any one of claims 1 to 4, wherein an outer diameter of the support is smaller than an outer diameter of the first conduit; the outer diameter of the first conduit is smaller than the outer diameter of the second conduit.

12. The blood pump of any one of claims 1 to 4, wherein the support member is made of a metal material or a ceramic material.