Detailed Description
The following description of the embodiments of the present invention will be made clearly and completely with reference to the accompanying drawings, in which it is apparent that the embodiments described are only some embodiments of the present invention, but not all embodiments. The following description of at least one exemplary embodiment is merely exemplary in nature and is in no way intended to limit the invention, its application, or uses. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
The relative arrangement of the components and steps, numerical expressions and numerical values set forth in these embodiments do not limit the scope of the present invention unless it is specifically stated otherwise.
Meanwhile, it should be understood that the sizes of the respective parts shown in the drawings are not drawn in actual scale for convenience of description.
In addition, descriptions of well-known structures, functions and configurations may be omitted for clarity and conciseness. Those of ordinary skill in the art will recognize that various changes and modifications of the examples described herein can be made without departing from the spirit and scope of the present disclosure.
Techniques, methods, and apparatus known to one of ordinary skill in the relevant art may not be discussed in detail, but should be considered part of the specification where appropriate.
In all examples shown and discussed herein, any specific values should be construed as merely illustrative, and not a limitation. Thus, other examples of the exemplary embodiments may have different values.
The invention is described in detail below by reference to the attached drawings and in connection with the embodiments:
Example 1
As shown in fig. 1-2, an auxiliary circulation pump device for a ventricular 2 with an outgoing line 11 passing through a suture body comprises a heart blood pump 4 connected in series with a heart arterial tube 1, wherein the heart blood pump 4 comprises a motor shell 7 and an axial flow channel shell 6 coaxially sleeved outside the motor shell 7, the upper end of the axial flow channel shell 6 is provided with a flange part 5 which is radially outwards, the upper surface of the flange part 5 faces the lower surface of an aortic valve or a pulmonary valve 3 and is sutured with an aortic or pulmonary artery root 31, the outgoing line 11 is led out from the circumferential outer wall of the axial flow channel shell 6, the outgoing line 11 is close to the lower surface of the flange part 5 along the axial direction of the axial flow channel shell 6 on the circumferential outer wall, and the outgoing line 11 passes through the aortic or pulmonary artery root 31 along the radial direction of the flange part 5.
Further preferred technical scheme is that the upper surface or/and the lower surface of the flanging part 5 are pre-assembled or temporarily assembled with suture bodies, the suture bodies positioned on the upper surface are upper suture bodies 101 used for being sutured with the lower surface of the aortic or pulmonary artery root 31 or used for being sutured with the circumferential annular membrane of the heart blood pump 4, the circumferential annular membrane of the heart blood pump 4 is simultaneously used for being sutured with the aortic or pulmonary artery root 31, the suture bodies positioned on the lower surface are lower suture bodies 102 used for being sutured with the aortic or pulmonary artery root 31, and the outgoing line 11 passes through the suture bodies positioned on the lower surface and passes through the aortic or pulmonary artery root 31.
Further preferable technical scheme is that a plurality of assembling holes 51 are formed in the flanging part 5, the axial direction of the assembling holes 51 is the same as the axial direction of the axial flow channel shell 6, and the upper surface or/and the lower surface of the flanging part 5 is pre-assembled or temporarily assembled with a stitching body through the assembling holes 51.
The further preferable technical scheme is that the suture body is an annular medical terylene braid or an annular polytetrafluoroethylene braid or an annular artificial blood vessel.
Based on the above principle, the present embodiment is further described that, first, the heart blood pump 4 proposes a structure that the heart blood pump 4 is disposed in the ventricle 2 and below the aortic valve or pulmonary valve 3 based on a serial configuration, specifically, the serial configuration refers to that the heart blood pump 4 is connected in series with the heart arterial vessel 1, on this basis, a technical means of shortening a motor is adopted to shorten the motor into the ventricle 2, the motor does not need to be connected through a support rod passing through the ventricle 2, so that the heart blood pump 4 does not damage the ventricle 2 in the implantation process, and meanwhile, the operation difficulty is reduced. Compared with the prior art, the motor is also arranged below the aortic valve or pulmonary valve 3, so that the influence of the volume of the motor on the blood circulation can be reduced, the blood pumping quantity of the motor above the aortic valve or pulmonary valve 3 is prevented from being blocked, and the kinetic energy provided by the heart blood pump 4 can meet the blood pressure requirement of a patient.
Then, the heart blood pump 4 adopts a flanging process, the outer diameter size of the axial flow channel shell 6 is slightly equal to that of the heart arterial tube 1, the flanging process is adopted at the upper port of the axial flow channel shell 6 to form a flanging part 5, the flanging part 5 is not excessively wide, and the size of an upper axis and a lower axis can be formed on the flanging part 5. The flanging part 5 can be a horizontal linear type or edge bending type flanging, and at least 1 plane above and below the flanging part is provided with a suture body as a medium and is in suture connection with the root 31 of the aorta or the pulmonary artery or/and the heart arterial tube 1 by adopting a suture line. Wherein the assembly holes 51 are also used for suture threading.
It can be seen that the present invention lifts the heart blood pump 4 by means of the aortic or pulmonary artery root 31, which is the root portion of the heart valve that grows horizontally generally perpendicular to the heart vessel 1, which is relatively massive. The aortic or pulmonary root 31 is more flexible and can carry a heavier device, which is advantageous for ease of suturing, for subsequent safety, and for the area of suturing. Compared with the prior art that the heart blood pump 4 is directly sewed on the inner wall of the heart artery 1, the heart blood pump 4 is sewed on the root 31 of the aorta or the pulmonary artery to cause less damage to the heart artery 1. The suture line in the invention adopts a vertical suture line, and the suture line does not appear on the inner wall of the axial flow channel, so that the risk of thrombus can be avoided.
Specifically, the upper surface or/and the lower surface of the flanging part 5 is pre-assembled or temporarily assembled with a suturing body, the suturing body located on the upper surface is an upper suturing body 101 for suturing with the lower surface of the aortic or pulmonary artery root 31 or for suturing with the circumferential annular membrane of the heart blood pump 4, the circumferential annular membrane of the heart blood pump 4 is simultaneously used for suturing with the aortic or pulmonary artery root 31, and the suturing body located on the lower surface is a lower suturing body 102 for suturing with the inner surface of the cardiac artery 1.
The suturing body comprises a lower suturing body 102 and an upper suturing body 101, wherein the lower suturing body 102, the flanging part 5 and the upper suturing body 101 are vertically stacked to form a stacked assembly, the aortic root 31 or the pulmonary artery root 31 is also of a horizontal human tissue structure, and the aortic root 31 or the pulmonary artery root 31, the lower suturing body 102, the flanging part 5 and the upper suturing body 101 are vertically stacked to form a stacked assembly. Which constitutes a hanging mode, the cuff 5 corresponds to being embedded in a laminate assembly. The upper and/or lower sewing bodies 101 and 102 are preassembled or temporarily assembled on the upper and/or lower sides of the burring part 5 after passing through the assembly holes 51 by a suture.
The present invention is therefore based on the construction of a serial configuration of hoisting a heart blood pump 4 in a ventricle 2 and above an aortic valve or pulmonary valve 3 by suturing the cuff 5 with the aortic or pulmonary root 31, a new path is proposed for the lead-out wire 11, which lead-out wire 11 is usually referred to as a wire connected to a motor for driving the motor, in this embodiment, the lead-out wire 11 may be a wire connected to a motor for driving the motor, or may be a lead-out wire 11 led out of the axial flow channel housing 6, which lead-out wire 11 may be a wire of a motor located in the axial flow channel housing 6, or a wire of another device located in the axial flow channel housing 6, which lead-out wire 11 is led out of the axial flow channel housing 6.
As shown in fig. 1, when the above-described structure is adopted in the heart blood pump 4, the flange portion 5 of the heart blood pump 4 is sutured with the aortic or pulmonary artery root 31 via the up-down suturing body 102, and at this time, the lead-out wire 11 is connected to the circumferential outer wall of the axial flow channel housing 6, and first, the lead-out wire 11 is disposed on the circumferential outer wall so as to be close to the lower surface of the flange portion 5 in the axial direction of the axial flow channel housing 6, and the lead-out wire 11 is made to be closely attached to the outer wall of the axial flow channel housing 6 so as to extend to the lower surface of the flange portion 5, whereby the influence of the lead-out wire 11 on the blood flow channel can be reduced, and the routing is regular. Then, after the lead-out wire 11 approaches the lower surface of the burring part 5, the lead-out wire 11 is bent to be closely attached to the lower surface of the burring part 5 to extend along the radial direction of the burring part 5, the lead-out wire 11 can be guided through the lower surface of the burring part 5 to pass through the aortic or pulmonary artery root 31, and the lead-out wire 11 is led out from the aortic or pulmonary artery root 31 to the outer wall of the cardiac artery 1, so that compared with the prior art, the damage to the cardiac artery 1 can be reduced. In addition, in the process that the lead-out wire 11 is closely attached to the lower surface of the flanging part 5 and extends along the radial direction of the flanging part 5, the lead-out wire 11 extends in the lower suture body 102, and the wiring direction of the lead-out wire 11 can be fixed through the lower suture body 102, so that the lead-out wire 11 can conveniently pass through the aortic or pulmonary artery root 31.
The further preferable technical scheme is that the outgoing line 11 is led out from the motor housing 7, extends between the motor housing 7 and the axial flow channel housing 6, passes through the axial flow channel housing 6 and is led out from the circumferential outer wall of the axial flow channel housing 6.
As shown in fig. 2, the lead-out wire 11 refers to a wire connected to a motor for driving the motor to supply power, and the lead-out wire 11 is first led out from the motor housing 7, the lead-out wire 11 on the motor housing 7 is led out from the circumferential outer wall of the axial flow channel housing 6 through the axial flow channel housing 6, then the lead-out wire 11 is brought close to the lower surface of the burring 5 in the axial direction of the axial flow channel housing 6 on the circumferential outer wall, and the lead-out wire 11 passes through the aortic or pulmonary artery root 31 in the radial direction of the burring 5.
The further preferable technical scheme is that a fixed bracket 12 is further arranged between the axial flow channel shell 6 and the motor shell 7, the fixed bracket 12 comprises at least 1 tubular supporting rod, one end of the supporting rod is connected with the motor shell 7, the other end of the supporting rod is connected with the axial flow channel shell 6, and an outgoing line 11 led out from the motor shell 7 extends between the motor shell 7 and the axial flow channel shell 6 through the inside of the supporting rod and penetrates through the axial flow channel shell 6.
Specifically, the outgoing path of the outgoing line 11 is to be led out from the motor housing 7-through the inside of the support rod-onto the outer wall of the axial flow passage housing 6-on the circumferential outer wall near the lower surface of the burring part 5 in the axial direction of the axial flow passage housing 6-bent-through the aortic or pulmonary artery root 31 in the radial direction of the burring part 5.
A further preferable technical scheme is that a stator and a rotor are coaxially arranged in the motor shell 7, one of the rotor and the stator comprises a permanent magnet 16, the other of the rotor and the stator comprises a winding coil, the stator is connected with an outgoing line 11, and the outgoing line 11 passes through the axial flow channel shell 6 through the inside of the stator and the supporting rod.
Specifically, the outgoing path of the outgoing line 11 is to be led out from the stator-through the motor housing 7-through the inside of the support rod-onto the outer wall of the axial flow passage housing 6-on the circumferential outer wall near the lower surface of the burring part 5 in the axial direction of the axial flow passage housing 6-bent-through the aortic or pulmonary artery root 31 in the radial direction of the burring part 5.
The further preferable technical scheme is that a temperature sensor 18 is arranged in the motor shell 7, a pressure sensor 17 is arranged on the inner wall of the axial flow channel shell 6, and wires of the temperature sensor 18 and the pressure sensor 17 are clustered with the outgoing wires 11.
Example 2
Based on embodiment 1, in this embodiment, a heart blood pump 4 adopting a new path for the lead-out wire 11 is provided, as shown in fig. 3-7, and further preferred technical solutions are that an inner stator 81 and an outer rotor 82 rotatably mounted outside the inner stator 81 are coaxially configured in the motor housing 7, two ends of the inner stator 81 are fixed on the axial flow channel housing 6 through support rods, the lead-out wire 11 is connected on the inner stator 81, the temperature sensor 18 is adhered around the outer wall of the inner stator 81, and the lead-out wire 11 is led to the axial flow channel housing 6 through the inner stator 81, the outer rotor 82 and the inner parts of the support rods.
The heart blood pump 4 is arranged in the heart arterial tube 1 in a serial configuration, the heart blood pump 4 comprises an axial flow channel shell 6 and a motor shell 7, the length of the motor shell 7 in the axial direction is smaller than or equal to that of the axial flow channel shell 6 in the axial direction, the motor shell 7 is embedded in the axial flow channel shell 6, the motor shell 7 is arranged in the ventricle 2 and below the aortic valve or pulmonary valve 3, when the motor shell 7 provides kinetic energy, a blood flow channel is formed between the motor shell 7 and the axial flow channel shell 6, the aortic valve or pulmonary valve 3 above the flanging part 5 is opened, blood flows into an artery from the ventricle 2, for the prior art, the motor shell 7 is firstly shortened to be above the ventricle 2, so that the heart blood pump 4 does not need to penetrate through the ventricle 2 in the implantation process, the operation difficulty is reduced, the motor shell 7 is arranged below the aortic valve or the pulmonary valve 3, and the blood blocking effect of the size of the motor shell 7 on the circulation process is avoided.
The length of the motor housing 7 in the axial direction is smaller than or equal to the length of the axial flow channel housing 6 in the axial direction, the upper end and the lower end of the axial flow channel housing 6 are respectively provided with a fixed bracket 12, one end of the supporting rod is connected with the upper end or the lower end of the axial flow channel housing 6, and the other end of the supporting rod is connected with one end of the inner stator 81, so that the motor housing 7 is fixed on the axial flow channel housing 6 and positioned in the axial flow channel housing 6.
The further preferable technical scheme is that an outer rotor 82 and an inner stator 81 are arranged in the motor housing 7, one of the outer rotor 82 and the inner stator 81 comprises a permanent magnet 16, one of the outer rotor 82 and the inner stator 81 comprises a winding coil, the outer rotor 82 is rotatably arranged outside the inner stator 81, the outer rotor 82 is used as the housing of the motor housing 7, and an impeller 14 is arranged on the outer wall of the housing, so that the impeller 14 is driven to rotate while the outer rotor 82 rotates.
As shown in fig. 6, the motor housing 7 is internally provided with a stator located at the center and a rotor located at the outer side, that is, an inner stator 81 and an outer rotor 82, a winding coil may be disposed on the inner stator 81, a permanent magnet may be disposed on the outer rotor 82, and the outer rotor 82 is driven to rotate with the inner stator 81 as a central axis through the interaction generated by the winding coil and the permanent magnet, so that the impeller 14 on the outer wall of the outer rotor 82 is driven to rotate, blood in a blood channel is driven to rotate, pressure is formed by driving the blood to rise, and after the aortic valve or pulmonary valve 3 is opened, the blood is sprayed into the cardiac artery 1 from the inside of the ventricle 2.
In this embodiment, the volume of the heart blood pump 4 can be reduced, and meanwhile, the rotation of blood in the channel is realized, the configuration of the inner stator 81 and the outer rotor 82 is adopted in the motor housing 7, the inner stator 81 refers to the motor housing 7 taking the stator as a central axis, the outer rotor 82 refers to the motor housing 7 setting the rotor outside the stator, one of the stator and the rotor comprises the permanent magnet 16 and one of the rotor and the stator comprises a winding coil, so that the rotor located outside rotates, then the impeller 14 can be directly arranged on the outer wall of the rotor, and when the rotor rotates, the impeller 14 is driven to rotate. Specifically, the fixing brackets 12 at the front end and the rear end are adopted to set the inner stator 81 and the outer rotor 82 in the axial flow channel shell 6, the fixing brackets 12 are composed of a plurality of tubular supporting rods, as can be seen in fig. 4 and 5, the fixing brackets 12 are specifically shaped like a Chinese character 'ji', and are composed of three supporting rods, one ends of the three supporting rods are welded on the inner wall of the axial flow channel shell 6, the other ends of the three supporting rods are welded together to form a small disc, the side surface of the small disc facing the inner side of the axial flow channel shell 6 is connected with the inner stator 81, and the small disc has stronger stability, so that the fixed connection between the motor shell 7 and the inner wall of the axial flow channel shell 6 is realized. When the driving motor housing 7 provides kinetic energy, since the inner stator 81 is fixedly connected to the axial flow channel housing 6 through the fixing brackets 12 at both sides, a blood flow channel is formed between the outer rotor 82 and the axial flow channel housing 6, the outer rotor 82 drives the impeller 14 positioned in the blood flow channel to rotate, and the blood rotates through the blood flow channel, at this time, the aortic valve or pulmonary valve 3 above the flanging part 5 is opened, and the blood flows into the artery from the ventricle 2.
Based on the above principle, the lead-out wire 11 refers to a lead wire for supplying power to the driving motor housing 7, the lead wire needs to be led out to the outer wall of the cardiac artery 1 to realize that the driving motor housing 7 provides kinetic energy, when the lead-out wire 11 is led out from the motor housing 7, the lead-out wire 11 can enter the blood flow channel, if the routing of the lead-out wire 11 is not regulated, the existence of the lead-out wire 11 in the blood flow channel can influence the pumping amount of blood in the blood flow channel, for example, when the lead-out wire 11 appears more in the blood flow channel, the lead-out wire 11 can block the pumping of the blood in the blood flow channel, so that the lead-out wire 11 is combined with the fixed support 12 fixedly arranged on the motor housing 7, the fixed support 12 adopts a tubular support rod, the support rod can be a hollow rod, the lead-out wire 11 led out from the motor housing 7 is embedded in the hollow rod, so that the lead-out wire 11 does not directly run in the blood flow channel, the blood flow channel is prevented, and the influence on the blood flow is reduced.
The further preferable technical scheme is that a temperature sensor 18 is stuck around the motor shell 7, a pressure sensor 17 is fixedly arranged on the inner wall of the axial flow channel shell 6, and wires of the temperature sensor 18 and the pressure sensor 17 are clustered with the outgoing wires 11.
As shown in fig. 7, the heart blood pump 4 is further provided with a corresponding temperature sensor 18 and a pressure sensor 17, based on the wiring direction of the outgoing line 11, the temperature sensor 18 is adhered around the inside of the motor housing 7, so that the wires of the temperature sensor 18 are conveniently clustered with the outgoing line 11 at the position of the motor housing 7, the influence of the wires of the temperature sensor 18 on blood rotation in a blood flow channel is reduced, the temperature of the motor housing 7 can be monitored in real time through the temperature sensor 18, and when the temperature exceeds a limiting value, an alarm sound can be given, the device is prevented from being in long-term high-temperature work, and the service life of the device can be effectively prolonged.
Meanwhile, a groove is formed in the axial flow channel shell 6, pressure sensors 17 at two ends are respectively embedded in the groove, one pressure sensor 17 is close to the aortic valve or the pulmonary valve 3, the other pressure sensor 17 is close to the ventricle 2, namely, the pressure sensors 17 at two ends are respectively arranged at the inlet and the outlet of the blood flow channel, and the rotating speed of the inner rotor 92 can be adjusted according to pressure change. And, the extending direction of the groove where the pressure sensor 17 is located faces the outgoing line 11, so that the wires of the pressure sensor 17 can be conveniently clustered with the outgoing line 11 along the inside of the groove, and the influence of the wires of the pressure sensor 17 on blood rotation in the blood flow channel is reduced.
Example 3
Based on embodiment 1, a heart blood pump 4 adopting a new path for the outgoing line 11 is proposed in this embodiment, as shown in fig. 8-12, a further preferred technical scheme is that an inner rotor 92 and an outer stator 91 rotatably mounted outside the inner rotor 92 are coaxially configured in the motor housing 7, the outer wall of the outer stator 91 is fixed on the axial flow channel housing 6 through a supporting rod, the outgoing line 11 is connected on the outer stator 91, the temperature sensor 18 is adhered around the inner wall of the outer stator 91, and the outgoing line 11 is led to the axial flow channel housing 6 through the inner parts of the outer stator 91 and the supporting rod.
As shown in fig. 8, the heart blood pump 4 is disposed in the heart arterial tube 1 in a serial configuration, the heart blood pump 4 includes an axial flow channel shell 6 and a motor shell 7, the length of the motor shell 7 in the axial direction is greater than that of the axial flow channel, the motor shell 7 is divided into an upper half section and a lower half section, one end of the support rod is connected to the inner wall of the axial flow channel shell 6 to fix the motor shell 7 on the axial flow channel shell 6, and the other end of the support rod is connected to the outer wall of the upper half section of the motor shell 7 to enable the upper half section of the motor shell 7 to be disposed in the axial flow channel shell 6 and the lower half section of the motor shell 7 to be exposed outside the axial flow channel shell 6 and disposed in the ventricle 2.
The further preferable technical scheme is that the motor comprises a rotating part 19 connected with one end of the motor shell 7, an impeller 14 is arranged on the outer wall of the rotating part 19, an inner rotor 92 and an outer stator 91 are arranged in the motor shell 7, one of the inner rotor 92 and the outer stator 91 comprises a permanent magnet 16, one of the outer stators 91 of the inner rotor 92 comprises a winding coil, the inner rotor 92 is rotatably arranged in the outer stator 91, one end of the inner rotor 92 positioned in the axial flow channel shell 6 is connected with the rotating part 19, and the inner rotor 92 drives the impeller 14 to rotate while rotating.
As shown in fig. 9-10, the outer wall of the upper half section of the motor housing 7 is fixedly connected to the inner wall of the axial flow channel housing 6 through a fixing bracket 12, the lower half section of the motor housing 7 is exposed out of the axial flow channel housing 6, and presents a stepped shape to form a stepped heart blood pump 4, and the stepped heart blood pump 4 is arranged in the ventricle 2 and below the aortic valve or pulmonary valve 3. Based on the structure that the heart blood pump 4 is arranged in the ventricle 2 and below the aortic valve or pulmonary valve 3, a stepped auxiliary circulating pump device for the ventricle 2 is designed, wherein the stepped auxiliary circulating pump device comprises a step shape with the outer wall of the axial flow channel shell 6 and the outer wall of the lower half section of the motor shell 7 gradually decreasing, and a step shape with the outer wall of the power part and the outer wall of the lower half section of the motor shell 7 gradually increasing, and by the two step-shaped designs, the blood flow channel is formed between the motor shell 7 and the axial flow channel shell 6, and meanwhile, the pumping quantity of blood in the blood flow channel can be effectively improved.
Specifically, the step-shaped structure formed by the outer wall of the axial flow channel housing 6 and the outer wall of the lower half section of the motor housing 7 is mainly formed by a fixing bracket 12, in the invention, the motor housing 7 adopts the configuration of an inner rotor 92 and an outer stator 91, one of the inner rotor 92 and the outer stator 91 comprises a permanent magnet 16, and one of the inner rotor 92 and the outer stator 91 comprises a winding coil, the inner rotor 92 refers to the motor housing 7 that the rotor is arranged on a central shaft, the outer stator 91 refers to the motor housing 7 that the stator is arranged on the outer side of the rotor, and then the inner rotor 92 is rotatably arranged in the outer stator 91, and the inner rotor 92 rotates in an axial mode. Based on the configuration of the motor housing 7, a fixing bracket 12 can be directly welded on the housing of the motor housing 7, the fixing bracket 12 is composed of a plurality of supporting rods, as can be seen in fig. 9 and 10, the shape of the fixing bracket 12 is in a herringbone shape, and is composed of three supporting rods, one end of each supporting rod is welded on the inner wall of the axial flow channel housing 6, and the other end of each supporting rod is welded on the outer wall of the upper half section of the motor housing 7, so that the upper half section of the motor housing 7 is fixed in the axial flow channel housing 6, the lower half section of the motor housing 7 is exposed outside the axial flow channel housing 6, and as can be seen, based on the fixing bracket 12 connected between the motor housing 7 and the axial flow channel housing 6, the diameter of the motor housing 7 is smaller than the diameter of the axial flow channel housing 6, so that the outer wall of the axial flow channel housing 6 and the outer wall of the lower half section of the motor housing 7 form a decreasing step, blood circulation can be formed between the motor housing 7 and the axial flow channel housing 6, and the blood circulation can be effectively and the heart-shaped by adjusting the length of the supporting rods or the diameter of the motor housing 7.
Specifically, the outer wall of the rotating part 19 and the lower half outer wall of the motor housing 7 form a step shape, that is, a rotating part 19 is further added on the motor housing 7 in the arrangement of the inner rotor 92 and the outer stator 91 of the motor housing 7, the rotating part 19 is arranged in front of the motor housing 7, the impeller 14 is arranged on the rotating part 19, the rotation of the impeller 14 is realized through the inner rotor 92 connected with the rotating part 19, as shown in fig. 11 and 12, the front end of the inner rotor 92 faces the aortic valve or the pulmonary valve 3, the front end is connected with the rotating part 19 and is embedded into the rotating part 19, when the inner rotor 92 rotates, the front rotating part 19 can be driven to synchronously rotate, and the impeller 14 is arranged on the outer wall of the rotating part 19, and the impeller 14 rotates blood in a blood flow channel, so that the relative distance between the motor housing 7 and the aortic valve or the pulmonary valve 3 can be reduced by adding the rotating part 19 on the motor housing 7, and the aortic valve or the pulmonary valve 3 can be prevented from blocking the aortic valve or the pulmonary valve 3. And when the diameter of the rotating part 19 is smaller than that of the motor shell 7, the outer wall of the rotating part 19 and the outer wall of the lower half section of the motor shell 7 form a gradually increasing step shape, so that the diameter of the blood flow channel in the axial flow channel shell 6 is increased, and the blood flow channel is increased through the design of the step-shaped motor shell 7, so that the blood pumping quantity can be effectively improved.
As shown in fig. 11, the motor housing 7 is internally provided with a rotor located at the center and a stator located at the outer side, that is, an inner rotor 92 and an outer stator 91, a permanent magnet may be disposed on the inner rotor 92, a winding coil may be disposed in the outer stator 91, and the inner rotor 92 is driven to rotate in the axial direction through the interaction generated by the winding coil and the permanent magnet, so that the impeller 14 on the outer wall of the rotating portion 19 is synchronously driven to rotate, blood in the blood flow channel rotates, the blood is driven to form pressure upwards, and after the aortic valve or pulmonary valve 3 is opened, the blood is sprayed into the cardiac artery tube 1 from the interior of the ventricle 2.
The further preferable technical scheme is that the motor shell 7 is provided with an outgoing line 11 for driving the motor shell 7 to supply energy, the outgoing line 11 is led to the axial flow channel shell 6 through the inside of the supporting rod and penetrates through the axial flow channel shell 6 to the outer wall of the axial flow channel shell 6, and further extends outwards along the radial direction of the flanging part 5 until being led out from the root of the vascular valve and then led out from the root 31 of the aorta or the pulmonary artery.
As shown in fig. 11-12, the lead-out wire 11 refers to a lead wire for supplying power to a driving motor, the lead wire needs to be led out to the outer wall of the cardiac artery 1 to realize that the driving motor housing 7 provides kinetic energy, when the lead-out wire 11 is led out from the motor housing 7, the lead-out wire 11 can enter the blood flow channel, if the wiring of the lead-out wire 11 is not adjusted, the pumping amount of blood in the blood flow channel can be influenced by the existence of the lead-out wire 11 in the blood flow channel, for example, when the lead-out wire 11 appears more in the blood flow channel, the lead-out wire 11 can block the pumping of the blood in the blood flow channel, the lead-out wire 11 is combined with a fixing support 12 fixedly arranged on the motor housing 7, the fixing support 12 adopts a tubular support rod, the support rod can be a hollow rod, the lead-out wire 11 led out from the motor housing 7 is embedded in the hollow rod, so that the lead-out wire 11 does not directly run in the blood flow channel, the blocking of the blood flow in the blood flow channel can be avoided, and the influence on the blood flow is reduced.
The further preferable technical scheme is that a temperature sensor 18 is stuck around the motor shell 7, a pressure sensor 17 is fixedly arranged on the inner wall of the axial flow channel shell 6, and wires of the temperature sensor 18 and the pressure sensor 17 are clustered with the outgoing wires 11.
As shown in fig. 12, a corresponding temperature sensor 18 and a corresponding pressure sensor 17 are further arranged for the heart blood pump 4, the temperature sensor 18 is adhered around the inside of the motor housing 7 based on the wiring direction of the outgoing line 11, so that the wires of the temperature sensor 18 are conveniently clustered with the outgoing line 11 at the position of the motor housing 7, the influence of the wires of the temperature sensor 18 on blood rotation in a blood flow channel is reduced, the temperature of the motor housing 7 can be monitored in real time through the temperature sensor 18, and when the temperature exceeds a limiting value, an alarm sound can be given, the device is prevented from being in long-term high-temperature operation, and the service life of the device can be effectively prolonged.
Meanwhile, a groove is formed in the axial flow channel shell 6, pressure sensors 17 at two ends are respectively embedded in the groove, one pressure sensor 17 is close to the aortic valve or the pulmonary valve 3, the other pressure sensor 17 is close to the ventricle 2, namely, the pressure sensors 17 at two ends are respectively arranged at the inlet and the outlet of the blood flow channel, and the rotating speed of the inner rotor 92 can be adjusted according to pressure change. And, the extending direction of the groove where the pressure sensor 17 is located faces the outgoing line 11, so that the wires of the pressure sensor 17 can be conveniently clustered with the outgoing line 11 along the inside of the groove, and the influence of the wires of the pressure sensor 17 on blood rotation in the blood flow channel is reduced.
The foregoing description of the preferred embodiment of the invention is not intended to limit the invention in any way, but rather to cover all modifications, equivalents, improvements and alternatives falling within the spirit and principles of the invention.