CN214633386U

CN214633386U - Ventricular assist blood pumping apparatus and system

Info

Publication number: CN214633386U
Application number: CN202023079378.5U
Authority: CN
Inventors: 闫小珅
Original assignee: Suzhou Xinling Meide Medical Technology Co ltd
Current assignee: Suzhou Xinling Meide Medical Technology Co ltd
Priority date: 2020-12-17
Filing date: 2020-12-17
Publication date: 2021-11-09
Anticipated expiration: 2030-12-17

Abstract

The utility model provides a ventricular assist blood pumping apparatus and a system, relating to the technical field of medical apparatus, wherein the ventricular assist blood pumping apparatus comprises an internal component which comprises a supporting cover and an impeller mechanism; the in-vivo component has a folded state and an unfolded state, when the in-vivo component is arranged at the connecting position of the aorta and the left ventricle or in the left ventricle, the in-vivo component is arranged in the unfolded state, the film and the support cover form a blood flow channel, the impeller mechanism rotates to promote the pressure of blood in the blood flow channel to rise, and then the in-vivo component can be used as a blood pump to promote the blood in the left ventricle to flow to the aorta; meanwhile, the internal component has a folded state, and in the folded state, the impeller mechanism and the support cover are folded, so that the size is small, the impeller mechanism and the support cover can be implanted into the connecting position of the aorta and the left ventricle or the left ventricle through the catheter, a thoracotomy operation is not needed, the operation time is short, the wound is small, and the recovery of a patient is fast.

Description

Ventricular assist blood pumping apparatus and system

Technical Field

The utility model belongs to the technical field of the medical instrument technique and specifically relates to a ventricular assist pump blood apparatus and system is related to.

Background

The heart is an important organ that powers the blood circulation of the human body. The heart is divided into left and right portions, each of which contains a ventricle and an atrium. The left ventricle and the right ventricle are interrupted by the interventricular septum, and the left atrium and the right atrium are interrupted by the interatrial septum. The direction of blood flow between the left atrium and the left ventricle is regulated by the mitral valve, which is a sound mitral valve that ensures that oxygen-rich blood flows from the left atrium to the left ventricle and then is pumped by the left ventricle to the systemic arteries. The direction of blood flow between the right atrium and the right ventricle is regulated by the tricuspid valve, which contains venous blood containing rich carbon dioxide, flows from the right atrium to the right ventricle, and then is pumped from the right ventricle to the pulmonary artery.

In high-risk cardiac surgery patients and heart failure patients, the blood pumping capacity of the heart is reduced, so that insufficient blood supply of other organs such as brain, kidney and the like is easily caused, and the viscera of the whole body are damaged. Particularly, heart failure is a disease seriously threatening human life, about 1/5 heart disease patients all over the world can finally develop the heart failure, and the heart failure incidence rate in China reaches 0.9 percent at present. And 5 years mortality rate exceeds 60%. Over a long period of time, the number of patients with advanced heart failure will be much greater than the number of donors that can provide heart transplantation, while the left ventricular assist device not only saves the patient's life, but also provides a great help for the patient to find a suitable donor, or to strive for surgical time.

Since the clinical application in the 60's last century, through years of research and clinical application, the application of left ventricular assist devices has expanded from resuscitation after cardiovascular surgery, transition or replacement of heart transplantation, to restoration of myocardial function and even permanent treatment of heart failure. The left ventricle auxiliary device not only can be used as a bridge for transition before heart transplantation and lead to a canoe for myocardial recovery, but also can improve the life quality of patients with heart failure and is used for treating the patients with heart failure. The main current left ventricular assist device is to create a pathway outside the heart at the apex of the left ventricle and the aortic location, using a centrifugal pump to pump blood from the left ventricle to the aortic location. Since the access is outside the heart, the procedure needs to be completed by an open chest procedure. The open chest surgery has a large trauma to patients, and more patients with senile heart failure cannot tolerate the trauma caused by the surgery, so the healing is poor.

SUMMERY OF THE UTILITY MODEL

An object of the utility model is to provide a ventricular assist pump blood apparatus and system to solve present ventricular assist device and need open the chest, the long and big problem of wound of operation time.

The utility model provides a ventricular assist blood pumping apparatus, which comprises an internal component, wherein the internal component comprises a support cover and an impeller mechanism;

the support cover comprises a hollowed-out cover body and a covering film, the covering film covers the hollowed-out cover body, the impeller mechanism is arranged in the hollowed-out cover body, and the impeller mechanism comprises a rotating shaft and blades connected with the rotating shaft;

the in-vivo assembly having a collapsed state in which the support shroud is folded inwardly over the impeller mechanism and the blades are folded over the rotational axis, and an expanded state; in the unfolding state, the supporting cover is unfolded outwards to form a blood flowing channel, and the blades are unfolded in the supporting cover relative to the rotating shaft and used for rotationally pumping blood so as to promote the blood in the left ventricle to be conveyed to the aorta;

the intracorporeal component is configured to be catheterized into a junction of the aorta and a left ventricle or a left ventricle in a folded state, and configured to be disposed in a deployed state with the support cover disposed at the junction of the aorta and the left ventricle or the left ventricle.

Further, the fretwork cover body includes the body frame body, the transversal annular setting of personally submitting of the body frame body, just the body frame body is latticed fretwork setting, the axial both ends of the body frame body are inwards drawn in along the direction that deviates from each other respectively, the blade corresponds the setting and is in the body frame body.

Furthermore, the middle part of the main frame body is covered with the covering film, and the two ends of the main frame body respectively form an inlet and an outlet of blood.

The hollow cover body further comprises a connecting frame, the inner diameter of the connecting frame is smaller than that of the hollow cover body in the unfolded state, the cross section of the connecting frame is annularly arranged, the connecting frame is connected to one side, close to the aorta, of the main frame body, and one end, far away from the main frame body, of the connecting frame is used for being arranged in the aorta;

the main frame body and the connecting frame are covered with the coating, one end of the main frame body, far away from the connecting frame, is exposed to form an inlet of blood, and the coating, located at one end of the connecting frame, far away from the main frame body, forms an outlet of the blood; or, the connecting frame is hollow tubular setting, the body frame body coats and is stamped the tectorial membrane, just the body frame body is kept away from the one end of connecting frame is exposed to form the import of blood, the connecting frame is kept away from the one end opening of the body frame body, in order to form the export of blood.

Further, the connecting frame comprises a first section and a second section, and the first section is connected between the second section and the main frame body;

the first section has an outer diameter smaller than an outer diameter of the second section, the first section being configured to correspond to an aortic valve.

Further, the outlet comprises a central hole, and the axis of the central hole is consistent with the axis of the connecting frame; or, the outlet comprises a plurality of through holes, the axes of the through holes are consistent with the axis of the connecting frame, and the through holes are arranged in a honeycomb shape.

Furthermore, a first support sleeve and a third support sleeve are respectively arranged at two ends of the main frame body;

the rotation axis is worn to establish in the body frame body first support sleeve pipe and second support sleeve pipe, just first support sleeve pipe and third support sleeve pipe are used for supporting the rotation axis.

Further, the ventricular assist blood pumping device further comprises a pressure measuring mechanism for monitoring the pressure in the left ventricle corresponding to the inlet, the pressure in the aorta corresponding to the outlet and/or the pressure in the blood flow channel;

the pressure measuring mechanism is arranged in the body; or the pressure measuring mechanism is arranged outside the body and is communicated with the position needing pressure measurement through a conduction pipe.

Furthermore, the number of the blades is one or more, the blades are fixedly connected with the rotating shaft, and the blades are made of memory alloy so as to be folded or unfolded;

and/or

The blade with the axis of rotation is articulated to be connected, the blade with be provided with the piece that resets between the axis of rotation, under the exogenic action, the blade can compress the piece that resets to make the blade is in fold condition, the piece that resets makes the blade have relatively the trend that the axis of rotation expandes.

Further, the ventricular assist blood pumping device further comprises a driving assembly, wherein the driving assembly is connected with the rotating shaft and is configured to be arranged in the support cover, or the driving assembly is configured to be arranged outside the body and is connected with the rotating shaft through a transmission piece.

Further, the impeller mechanism comprises a plurality of impeller mechanisms which are arranged in sequence, each impeller mechanism comprises a blade and a rotating shaft, and the rotating shafts of the impeller mechanisms are fixedly connected or can be relatively rotatably connected.

Furthermore, the number of the impeller mechanisms is two, and the rotating shafts of the two impeller mechanisms are configured to be in rotatable connection, so that the two impeller mechanisms can respectively and independently rotate;

the number of the driving assemblies is two, the two driving assemblies are respectively connected with the two rotating shafts in a one-to-one correspondence mode, and the two driving assemblies are respectively connected with two ends, deviating from each other, of the rotating shafts.

Furthermore, one end or two ends of the supporting cover are connected with a sheath tube, and the bending degree of the sheath tube is adjustable.

Furthermore, the ventricular assist blood pumping apparatus further comprises a control box, and the control box is respectively connected with the pressure measuring mechanism and a driving assembly for driving the impeller mechanism to rotate through a signal transmission unit.

Further, the hollowed-out cover body is made of memory alloy, and the covering film is a plastic film or a biological tissue film.

the support cover comprises a hollow cover body, the impeller mechanism is arranged in the hollow cover body, and the impeller mechanism comprises a rotating shaft and blades connected with the rotating shaft;

the in-vivo assembly having a collapsed state in which the support shroud is folded inwardly over the impeller mechanism and the blades are folded over the rotational axis, and an expanded state; in the unfolding state, the supporting cover is unfolded outwards, and the blades are unfolded in the supporting cover relative to the rotating shaft and used for rotationally pumping blood so as to promote the blood in the left ventricle to be conveyed to the aorta;

the intracorporeal component is configured to be implanted through a catheter into the aorta in a folded state, and configured to be in an expanded state with the support cover interference fit within the aorta.

The utility model provides a ventricular assist blood pumping system, including ECG and the utility model provides a ventricular assist blood pumping apparatus.

The utility model provides a ventricular assist blood pumping apparatus, which comprises an internal component, wherein the internal component comprises a support cover and an impeller mechanism; the support cover comprises a hollow cover body and a covering film, the covering film covers the hollow cover body, the impeller mechanism is arranged in the hollow cover body, and the impeller mechanism comprises a rotating shaft and blades connected with the rotating shaft; the in-vivo component has a folded state and an unfolded state, in the folded state, the support cover is folded inwards on the impeller mechanism, and the blades are folded on the rotating shaft; in the unfolding state, the supporting cover is unfolded outwards to form a blood flow channel, and the blades are unfolded in the supporting cover relative to the rotating shaft and used for rotationally pumping blood so as to promote the blood in the left ventricle to be conveyed to the aorta; the interbody assembly is configured to be catheterized into a junction of the aorta and the left ventricle or the left ventricle in a collapsed state, and configured such that in an expanded state, the support shield is disposed within the junction of the aorta and the left ventricle or the left ventricle. The internal component of the ventricular assist blood pumping apparatus of the utility model has a folding state and an unfolding state, when the internal component is arranged at the connecting position of the aorta and the left ventricle or in the left ventricle, the internal component is arranged in the unfolding state, the film and the supporting cover form a blood flow channel, the rotation of the impeller mechanism can promote the pressure of the blood in the blood flow channel to rise, and the internal component can be used as a blood pump to promote the blood in the left ventricle to flow to the aorta; meanwhile, the internal component has a folded state, and in the folded state, the impeller mechanism and the support cover are folded, so that the size is small, the impeller mechanism and the support cover can be implanted into the connecting position of the aorta and the left ventricle or the left ventricle through the catheter, a thoracotomy operation is not needed, the operation time is short, the wound is small, and the recovery of a patient is fast.

The utility model provides a ventricular assist blood pumping apparatus, which comprises an internal component, wherein the internal component comprises a support cover and an impeller mechanism; the support cover comprises a hollow cover body, the impeller mechanism is arranged in the hollow cover body, and the impeller mechanism comprises a rotating shaft and blades connected with the rotating shaft; the in-vivo component has a folded state and an unfolded state, in the folded state, the support cover is folded inwards on the impeller mechanism, and the blades are folded on the rotating shaft; in the unfolding state, the supporting cover is unfolded outwards, and the blades are unfolded in the supporting cover relative to the rotating shaft and used for rotationally pumping blood so as to promote the blood in the left ventricle to be conveyed to the aorta; the intracorporeal component is configured to be implanted into the aorta through the catheter in a folded state, and configured to be in an unfolded state with the support cover being interference fit within the aorta. The internal component of the ventricular assist blood pumping apparatus of the utility model has a folding state and an unfolding state, when the internal component is arranged at the connecting position of the aorta and the left ventricle or in the left ventricle, the internal component is arranged in the unfolding state, the supporting cover is matched with the blood vessel of the aorta to form a blood flow channel, the impeller mechanism rotates to promote the pressure of the blood in the blood flow channel to rise, and the internal component can be used as a blood pump to promote the blood in the left ventricle to flow to the aorta; meanwhile, the internal component has a folded state, and in the folded state, the impeller mechanism and the support cover are folded, so that the size is small, the impeller mechanism and the support cover can be implanted into the connecting position of the aorta and the left ventricle or the left ventricle through the catheter, a thoracotomy operation is not needed, the operation time is short, the wound is small, and the recovery of a patient is fast.

The utility model provides a ventricular assist blood pumping system, including ECG with the utility model provides a ventricular assist blood pumping apparatus, with the utility model provides a ventricular assist blood pumping apparatus has the same beneficial effect.

Drawings

In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the embodiments or the technical solutions in the prior art will be briefly described below, and it is obvious that the drawings in the following description are some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to these drawings without creative efforts.

Fig. 1 is a schematic view illustrating a usage state of a ventricular assist blood pumping device according to an embodiment of the present invention;

fig. 2 is a schematic view of a ventricular assist blood pumping device according to an embodiment of the present invention;

fig. 3 is a partial schematic view of an impeller mechanism of a ventricular assist blood pumping device according to an embodiment of the present invention in one direction of a folded state;

FIG. 4 is a schematic view in another orientation of FIG. 3;

FIG. 5 is a schematic view of the impeller mechanism of FIG. 3 in a deployed state;

fig. 6 is a schematic view of an intracorporeal component of a ventricular assist blood pumping device according to an embodiment of the present invention;

fig. 7 is a schematic structural diagram of a covering film of a ventricular assist blood pumping device according to an embodiment of the present invention;

fig. 8 is another schematic structural diagram of a covering film of a ventricular assist blood pumping device according to an embodiment of the present invention;

FIG. 9 is a schematic diagram of a first form of a hollow-out cover of a ventricular assist blood pumping device according to an embodiment of the present invention;

FIG. 10 is a schematic diagram illustrating a second form of a hollowed-out cover for a ventricular assist blood pumping device in accordance with an embodiment of the present invention;

FIG. 11 is a schematic diagram illustrating a third form of a hollow-out cover of a ventricular assist blood pumping device according to an embodiment of the present invention;

fig. 12 is a schematic view of an installation form of a driving assembly of a ventricular assist blood pumping device according to an embodiment of the present invention;

fig. 13 is a schematic view illustrating another installation form of the driving assembly of the ventricular assist blood pumping device according to an embodiment of the present invention;

fig. 14 is a schematic view of a second embodiment of the present invention showing a state of use of the ventricular assist blood pumping device;

FIG. 15 is a schematic view of another exemplary embodiment of a ventricular assist pump device;

fig. 16 is a schematic view of a ventricular assist blood pumping device provided in accordance with a second embodiment of the present invention;

fig. 17 is a schematic view of a state of use of the ventricular assist blood pumping apparatus according to the third embodiment of the present invention;

fig. 18 is a schematic view illustrating another usage state of the ventricular assist blood pumping apparatus according to the third embodiment of the present invention;

fig. 19 is a schematic view of a state of use of the ventricular assist blood pumping apparatus according to the fourth embodiment of the present invention;

fig. 20 is a schematic view illustrating another usage state of the ventricular assist blood pumping apparatus according to the fourth embodiment of the present invention.

Icon: 1-left ventricle; 2-aorta; 100-an intracorporeal component; 101-an outlet; 102-an inlet; 103-a central hole; 104-a through hole; 110-a support cage; 111-hollowing out the cover body; 1111-the main frame body; 1112-a connecting frame; 1113-first section; 1114-a second segment; 112-film covering; 113-a first support sleeve; 114-a second support sleeve; 115-a third support sleeve; 116-sheath; 200-an impeller mechanism; 210-a blade; 220-a rotating shaft; 221-mounting holes; 222-a notch; 300-a drive assembly; 310-a transmission member; 400-a controller; 500-a signal box; 600-a catheter; 700-a wire; 800-ECG.

Detailed Description

The technical solution of the present invention will be described clearly and completely with reference to the following embodiments, and it should be understood that the described embodiments are some, but not all embodiments of the present invention. Based on the embodiments in the present invention, all other embodiments obtained by a person skilled in the art without creative work belong to the protection scope of the present invention.

The main ventricular assist devices at present are mainly at the apex of the left ventricle 1 and the aorta 2, a passage is established outside the heart, and blood is pumped from the left ventricle 1 to the aorta 2 by means of a centrifugal pump. Since the access is outside the heart, the procedure needs to be completed by an open chest procedure. The open chest surgery is poor after healing for the wounds of patients and the wounds caused by the surgery which can not be tolerated by more patients with senile heart failure.

The utility model provides an apparatus implanted through pipe can implant through femoral artery, and the operation process wound is little, and the time is short, and the wound that causes the patient is little.

Example one

As shown in fig. 1-13, the present embodiment provides a ventricular assist blood pumping device, which includes an intracorporeal component 100, the intracorporeal component 100 including a support housing 110 and an impeller mechanism 200. The supporting cover 110 comprises a hollow cover body 111 and a coating film 112, the coating film 112 is coated on the hollow cover body 111, the impeller mechanism 200 is arranged in the hollow cover body 111, and the impeller mechanism 200 comprises a rotating shaft 220 and blades 210 connected with the rotating shaft 220. The in-vivo assembly 100 has a folded state in which the support housing 110 is folded inward on the impeller mechanism 200 and the blades 210 are folded on the rotation shaft 220; in the deployed state, the support housing 110 is deployed outward to form a blood flow path, and the vane 210 is deployed in the support housing 110 with respect to the rotation shaft 220 for rotationally pumping blood to promote the transfer of the blood of the left ventricle 1 to the aorta 2. The intracorporeal component 100 is configured to be catheterized into the junction of the aorta 2 and the left ventricle 1 or into the left ventricle 1 in a folded state, and is configured to be disposed with the support mask 110 in the junction of the aorta 2 and the left ventricle 1 or into the left ventricle 1 in an unfolded state.

The covering film 112 may cover the inner surface of the hollow cover 111, or may cover the outer surface of the hollow cover 111. The film 112 is made of a soft material, and may be a soft plastic film, that is, a polymer material, such as PET (condensation polymer of phthalic acid and ethylene glycol), efpp (ethylene-tetrafluoroethylene copolymer); or a biological tissue membrane, such as one or more membranes made of animal pericardial materials, and the membrane 112 is fused to the hollow cover 111 by sewing, bonding, or heat fusing. When the impeller mechanism 200 rotates, a pressure drop is formed inside the coating 112, so that blood flow is sucked from the left ventricle 1 to the aorta 2, and the left ventricle is assisted.

The in-vivo component 100 of the ventricular assist blood pumping apparatus of the present embodiment has a folded state and an unfolded state, when the in-vivo component 100 is disposed at a connection position of the aorta 2 and the left ventricle 1 or in the left ventricle 1, the covering film 112 and the support cover 110 form a blood flow channel, the impeller mechanism 200 rotates to promote the pressure of blood in the blood flow channel to rise, and the in-vivo component 100 can be used as a blood pump to promote the blood in the left ventricle 1 to flow to the aorta 2. Meanwhile, the intracorporeal module 100 has a folded state in which the impeller mechanism 200 and the support cover 110 are folded, has a small volume, can be implanted into the connection position of the aorta 2 and the left ventricle 1 or the left ventricle 1 through a catheter, does not need an open chest operation, has short operation time, small wound, and enables the patient to recover quickly.

The material of the hollowed-out cover 111 may be a memory alloy, such as nitinol, and the change of the folded state and the unfolded state of the hollowed-out cover 111 is realized by using the memory and self-expansion performance of the memory alloy.

The number of the blades 210 is one or more, and when there are a plurality of the blades 210, the plurality of the blades 210 are arranged at intervals in the circumferential direction or the axial direction of the rotating shaft 220. The blades 210 are switched between a folded state and an unfolded state, and the blades 210 may be made of memory alloy, and the blades 210 are fixedly connected to the rotating shaft 220, so that the blades 210 can be folded or unfolded. Specifically, one end of the blade 210 is fixedly connected with the rotating shaft 220, the blade 210 is made of memory alloy, a notch 222 is formed in the rotating shaft 220, the blade 210 is arranged corresponding to the notch 222, and the blade 210 is folded in the notch 222 in the folding posture; in the unfolded state, the end of the vane 210, which is away from the end fixedly connected to the rotating shaft 220, is extended outward away from the rotating shaft 220, and the vane 210 is finally disposed at an acute or right angle to the rotating shaft 220, i.e. the vane 210 can be used as a driving plate.

The blades 210 can be switched between the folded state and the unfolded state by a mechanical driving method, for example, the blades 210 are hinged to the rotating shaft 220, a reset member is arranged between the blades 210 and the rotating shaft 220, and under the action of an external force, the blades 210 can compress the reset member to enable the blades 210 to be in the folded state, and the reset member enables the blades 210 to have a tendency to be unfolded relative to the rotating shaft 220. Specifically, as shown in fig. 3, 4 or 5, one end of the blade 210 is hinged to the rotating shaft 220, and a restoring member is disposed between the blade 210 and the rotating shaft 220, so that the blade 210 can be compressed by the restoring member under the action of an external force to make the blade 210 in a folded posture, and the restoring member makes the blade 210 have a tendency to unfold relative to the rotating shaft 220. Wherein, the reset member may be a torsion spring, and the torsion spring may be disposed in the mounting hole 221. The torsion spring is compressed when the blade 210 is in the folded posture, and the elasticity of the torsion spring can keep the blade 210 stable in the unfolded state. It will be appreciated that in this form, the rotating shaft 220 may still be provided with a notch 222, the vane 210 is hinged in the notch 222, and the side wall of the notch 222 corresponding to the hinged end of the vane 210 can be used as a limit when the vane 210 is opened, so that the vane 210 can be clamped on the side wall of the notch 222 under the action of the torsion spring when the vane 210 is opened.

Further, the hollowed-out cover body 111 comprises a main frame body 1111 and a connecting frame 1112, the cross section of the main frame body 1111 is annularly arranged, the main frame body 1111 is arranged in a grid-shaped hollowed-out manner, and two axial ends of the main frame body 1111 are inwardly folded along the directions deviating from each other. In the unfolding state, the inner diameter of the connecting frame 1112 is smaller than that of the hollow cover 111, the cross section of the connecting frame 1112 is annularly arranged, the connecting frame 1112 is connected to one side of the main frame 1111 close to the aorta 2, and one end of the connecting frame 1112 far away from the main frame is arranged in the aorta 2.

The main frame 1111 forms a large radial space, and the impeller mechanism 200 is disposed in the main frame 1111, so that the blades 210 have a large blade area, which is beneficial to improving the blood transportation capacity at the same rotation speed. The attachment frame 1112 is primarily for draining blood into the aorta 2, and the end of the attachment frame 1112 remote from the main frame 1111 is disposed through the aortic valve in the aorta 2. The connecting frame 1112 can have various forms, for example, in the first form, as shown in fig. 9, the connecting frame 1112 is a straight rod shape and is provided with a hollow grid, the main frame body and the connecting frame 1112 are covered with the coating 112, one end of the main frame body far away from the connecting frame 1112 is exposed to form the blood inlet 102, and the coating 112 is located at one end of the connecting frame 1112 far away from the main frame body to form the blood outlet 101. For another example, in the second form, as shown in fig. 10, the connecting frame 1112 is a straight cylinder, that is, a hollow tube, the main frame body is covered with the coating 112, and one end of the main frame body away from the connecting frame 1112 is exposed to form the blood inlet 102, and one end of the connecting frame 1112 away from the main frame body is opened to form the blood outlet 101.

The connecting frame 1112 may also have a variable cross section with a different cross section, and the outer diameter of the connecting frame 1112 is generally smaller at the position corresponding to the aortic valve. For example, the first form shown in fig. 9 may be deformed into the third form shown in fig. 11. In a third form, the linking frame 1112 includes a first segment 1113 and a second segment 1114, the first segment 1113 being coupled between the second segment 1114 and the main frame body; the first section 1113 has an outer diameter less than the outer diameter of the second section 1114, and the first section 1113 is configured to correspond to an aortic valve arrangement. It can be understood that the aortic valve is often less in clearance, the outer diameter of the connecting frame 1112 arranged at the aortic valve position is less, the normal work of the aortic valve can be ensured, the aortic valve is not easy to be damaged, the second section 1114 with a larger outer diameter is arranged at the position behind the aortic valve, and when the outer diameter of the second section 1114 is increased, the inner diameter is often increased correspondingly, the flow rate of blood can be reduced, and the energy loss can be reduced.

It should be noted that the connecting frame 1112 needs to pass through the aorta 2, so the diameter of the connecting frame 1112 is not too large, and the diameter (outer diameter) of the connecting frame 1112 in this embodiment is in the range of 2-10 mm.

As shown in fig. 1, when the ventricular assist blood pumping device of the present embodiment is used, the main frame 1111 is disposed in the left ventricle 1, and the main frame 1111 protects the vanes 210. The connecting frame 1112 is connected between the aorta 2 and the main frame 1111, so that the blood flow path formed by the covering film 112 extends from the left ventricle 1 to the aorta 2, and thus when the impeller mechanism 200 rotates, the blood in the left ventricle 1 enters the blood flow path from the inlet 102 of the main frame 1111 and enters the aorta 2 along the blood flow path under the driving action of the impeller mechanism 200 to assist the pumping of the blood.

It can be understood that the ventricular assist blood pumping device of the present embodiment can pump blood in real time, and is not affected by the aortic valve, for example, when the aortic valve fails pathologically, and cannot maintain automatic opening or closing, or when the left ventricle 1 fails, the ventricular assist blood pumping device of the present embodiment can still pump blood in real time through the blood flow channel.

When blood flows into the aorta 2, a large change in cross section facilitates high-speed blood flow and a large loss of fluid energy, and the outflow cross section is increased by the connecting frame 1112 in this embodiment. That is, the connecting frame 1112 serves as a spreader mechanism, so that the blood flow channel through which blood flows to the aorta 2 is enlarged, the area of the channel through which blood flows out is increased, and the flow rate is reduced, thereby reducing pressure and energy loss, and when the same amount of pumped blood is required, the rotation speed of the impeller mechanism 200 is reduced, thereby reducing the possibility that the blood is damaged by a large shearing force due to an excessively large rotation speed of the impeller mechanism 200.

In order to improve the directionality of the blood during its transportation, the blood outlet 101 includes a central hole 103, the axis of the central hole 103 coincides with the axis of the connecting frame 1112; or, the outlet 101 includes a plurality of through holes 104, the axes of the plurality of through holes 104 are coincident with the axis of the connecting rack 1112, and the plurality of through holes 104 are arranged in a honeycomb shape. That is, as for the outflow end structure of the coating film 112, as shown in fig. 7, a center hole 103 may be provided, and the center hole 103 may be a through hole structure. It is also possible that, as shown in fig. 8, a plurality of through holes 104 are provided, the plurality of through holes 104 form a honeycomb structure, and the normal direction of each through hole 104 is parallel to the axial direction of the coating film 112.

It will be appreciated that the plurality of through holes 104 are generally preferred because the blood is rotationally agitated by the blades 210, and has a large number of rotational and non-uniform flow rates, and the plurality of through holes 104 are formed in a honeycomb shape to rectify the flow of the fluid supplied to the aorta 2, thereby serving as a stable flow field.

Since the support cover 110 of the ventricular assist blood pumping device of the present embodiment is a hollow structure, the space formed by the hollow structure is often large, and when the rotating shaft 220 is disposed in the support shaft, an unstable situation may occur. In order to solve the problem, in this embodiment, a first support sleeve 113 and a third support sleeve 115 are respectively disposed at two ends of the main frame body 1111, wherein the first support sleeve 113 is disposed at one end of the main frame body 1111 close to the connection frame 1112, the connection frame 1112 is connected to the first support sleeve 113, and the second support sleeve 114 is disposed at one end of the connection frame 1112 far from the main frame body; the rotating shaft 220 is inserted into the main frame 1111, the first support sleeve 113, the connection frame 1112, and the second support sleeve 114, and the first support sleeve 113, the second support sleeve 114, and the third support sleeve 115 are used to support the rotating shaft 220.

As shown in fig. 2 or 9, the diameters of the first support sleeve 113, the second support sleeve 114, and the third support sleeve 115 are smaller than the diameter of the coupling frame 1112 or the main frame 1111, that is, the support cover 110 is retracted in the positions of the first support sleeve 113, the second support sleeve 114, and the third support sleeve 115 so that the first support sleeve 113 and the second support sleeve 114 can support the rotation shaft 220. The first support sleeve 113, the second support sleeve 114, and the third support sleeve 115 correspond to bushings, so that the rotation shaft 220 can rotate with respect to the support housing 110, and has good stability when rotating. In addition, the structure of the coating 112 is adapted to the hollow cover 111, and as shown in fig. 2, the coating 112 is smoothly transited at the position of the first support sleeve 113 and is spaced from the first support sleeve 113, so that a blood flow channel is formed between the coating 112 and the first support sleeve 113, and blood smoothly flows from the main frame 1111 into the connecting frame 1112 without blood flow resistance.

Further, the ventricular assist blood pumping device of the present embodiment further includes a pressure measuring mechanism for monitoring the pressure in the left ventricle 1 corresponding to the inlet 102, the pressure in the aorta 2 corresponding to the outlet 101, and/or the pressure in the blood flow path.

It will be appreciated that the pressure measurement mechanism may be used to assess the operation of the blood pump formed by the impeller mechanism 200 in cooperation with the blood flow path by monitoring the pressure at various points. The pressure of the blood at the inlet 102 can be known by monitoring the pressure in the left ventricle 1 corresponding to the inlet 102, and the pressure at which the blood flows out can be known by monitoring the pressure in the aorta 2 corresponding to the outlet 101. By monitoring the pressure within the blood flow path, the pressure within the blood flow path can be known. These pressure measurement positions can be selectively set as desired. In the present embodiment, a plurality of pressure measurement points are provided in the blood flow passage, and as shown in fig. 2, a first measurement point P1 is provided on the first support sleeve 113, a second measurement point P2 is provided at a position of the end of the connecting frame 1112 near the outlet 101, and a third measurement point P3 is provided at the outlet 101. The first measurement point P1 shows the pressure of blood entering the blood flow channel formed by the connecting frame 1112 and the coating 112 under the action of the impeller mechanism 200, so that it can be determined whether the driving pressure of the impeller mechanism 200 is appropriate or not according to the pressure. By the second measurement point P2, the third measurement point P3, and the area a of the blood flow channel formed by the connecting frame 1112 cooperating with the covering film 112 (i.e. the inner cross-sectional area of the blood flow channel formed by the connecting frame 1112 cooperating with the covering film 112, as shown in fig. 2 at a-a), the blood flow rate pumped by the apparatus can be calculated, and thus the real-time flow rate of the blood pumping apparatus can be evaluated. The calculation formula of the blood flow rate of the auxiliary pumping of the ventricular auxiliary pumping device is as follows:

the formula I is as follows: the pressure difference Δ P is equal to the pressure value P2 of the second measurement point P2 minus the pressure value P3 of the third measurement point P3, i.e., Δ P is P2-P3;

the formula II is as follows: the pressure difference Δ P is equal to 4 times the square of the blood flow velocity V, i.e. Δ P-4 × V²；

The formula III is as follows: the blood flow Q is equal to the blood flow velocity V multiplied by the area a, i.e. Q V a.

The pressure value P2 of the second measurement point P2 and the pressure value P3 of the third measurement point P3 are obtained through measurement, so that the blood flow speed V can be calculated by combining the formula one with the formula two; the area a is a known quantity that is measured or calculated in advance, so the blood flow can be obtained by calculating using formula three after the blood flow velocity V is obtained.

The working flow of the ventricular assist blood pumping device can be monitored in real time, so that the output flow of the device can be judged according to the heart failure degree of a patient, and then the rotating speed of the blades 210 is controlled through the control box, so that the ideal flow is adjusted.

It should be noted that the pressure measuring mechanism includes a pressure sensor, and the pressure measuring mechanism may be disposed in the body, where the pressure sensor is directly communicated with the corresponding pressure measuring point. The pressure measuring mechanism can also be arranged outside the body, and at the moment, the pressure measuring mechanism is communicated with the position needing pressure measurement, namely the corresponding pressure measuring point, through the conduction pipe.

Further, the ventricular assist blood pumping device of the embodiment further includes a sheath 116, the sheath 116 is fixedly connected to the support cover 110, and the sheath 116 is provided with corresponding functional holes, through which the conduction tube, the transmission member 310, the lead 700 and the like can pass.

Sheath 116 may be configured as a curvature-adjustable sheath, i.e., in addition to sheath 116 having flexibility to bend with the bending of the blood vessel, sheath 116 may also artificially adjust the curvature. As shown in fig. 2, a guide wire is provided on the sheath 116, and the artificial curvature adjustment of the sheath 116 can be realized by the pulling action of the guide wire. The curvature of the sheath 116 is adjustable, and the position of the support cover 110 and the impeller mechanism 200 in the left ventricle 1 and the straightness of the rotating shaft 220 can be adjusted accordingly.

The sheath 116 may also be coupled to a catheter 600 to facilitate connection of the in vivo assembly 100 to an extracorporeal member and to facilitate placement of a connection between the in vivo assembly 100 and the extracorporeal member.

Further, the ventricular assist blood pumping device of the present embodiment further includes a driving assembly 300, the driving assembly 300 is connected to the rotating shaft 220, the driving assembly 300 is configured to be disposed inside the support housing 110, or the driving assembly 300 is configured to be disposed outside the body and connected to the rotating shaft 220 through a transmission member 310.

Specifically, the number of the impeller mechanism 200 of the ventricular assist blood pumping device of the present embodiment may be one, the number of the blades 210 of one impeller mechanism 200 may be one or more, and the plurality of blades 210 may be sequentially arranged along the circumferential direction of the rotating shaft 220, or may be sequentially arranged along the axial direction of the rotating shaft 220. The rotating shaft 220 of the impeller mechanism 200 is connected to a driving assembly 300, and the driving assembly 300 is typically a motor, and the motor may be a micro motor, and in this case, the motor may be disposed in the support housing 110 at one end of the support housing 110 or at both ends of the support housing 110. The driving assembly 300 may also be disposed outside the body, and at this time, the driving assembly 300 is connected to the rotating shaft 220 through a driving member 310 formed by a driving wire, and the driving wire is rotatably inserted into the functional hole of the sheath 116.

The impeller mechanism 200 of the ventricular assist blood pumping device of the present embodiment may also include a plurality of impeller mechanisms 200 arranged in sequence, in one mode, the rotating shafts 220 of the impeller mechanisms 200 are configured to be fixedly connected, and in this case, each impeller mechanism 200 may be driven by one driving assembly 300, and the impeller mechanisms 200 rotate synchronously. In another mode, the rotating shafts 220 of the impeller mechanisms 200 are configured to be connected in a relatively rotatable manner, and the impeller mechanisms 200 can be driven separately.

As shown in fig. 12 or 13, the number of the impeller mechanisms 200 is two, and the rotating shafts 220 of the two impeller mechanisms 200 are rotatably connected to each other. Specifically, the two rotating shafts 220 are rotatably connected by a connecting shaft so that the two impeller mechanisms 200 can be independently rotated, respectively. The number of the driving assemblies 300 is two, the two driving assemblies 300 are respectively connected with the two rotating shafts 220 in a one-to-one correspondence manner, and the two driving assemblies 300 are respectively connected with two ends of the two rotating shafts 220 which are deviated from each other. Wherein, the one end that two axis of rotation 220 are close to each other is provided with notch 222, and two impeller mechanism 200's blade 210 sets up the one end of keeping away from each other at two notches 222 respectively, and the both ends of connecting axle are established in two axis of rotation 220 through the position cover of notch 222 respectively, and two axis of rotation 220 respectively with connecting axle clearance fit, and be provided with spacing portion on the connecting axle for the axial displacement of two axis of rotation 220 of restriction.

Wherein, the two impeller mechanisms 200 are arranged at intervals in sequence along the flow direction of blood, the blade 210 located at the upstream of the flow direction of blood (wherein, the arrow in fig. 1 and 6 indicates the flow direction of blood, the upstream of the flow direction of blood is the lower side shown in fig. 1, and the left side shown in fig. 6) plays a role of blowing blood between the two impeller mechanisms 200, and the blade 210 located at the downstream of the flow direction of blood (the upper side shown in fig. 1, and the right side shown in fig. 6) plays a role of sucking blood between the two impeller mechanisms 200.

As shown in fig. 12, two driving assemblies 300 may be simultaneously disposed in the body, in which case, the two driving assemblies 300 are disposed in the two ends of the support housing 110 in a one-to-one correspondence, and any one of the driving assemblies 300 is connected to the rotating shaft 220 adjacent to the driving assembly 300. As shown in fig. 13, two driving assemblies 300 may be simultaneously disposed outside the body, in this case, the two ends of the support cover 110 are respectively connected to the sheath tubes 116, the driving assemblies 300, the driving wires and the sheath tubes 116 are disposed in a one-to-one correspondence, the driving wires are inserted into the functional holes of the sheath tubes 116, and any one of the driving assemblies 300 drives the corresponding rotating shaft 220 to rotate through the connected driving wire.

It is understood that the two impeller mechanisms 200 are driven independently and can form a pressure difference, the upstream impeller mechanism 200 (the left impeller mechanism 200 shown in fig. 2) mainly blows fluid into the coating 112, the downstream impeller mechanism 200 (the right impeller mechanism 200 shown in fig. 2) is used for sucking fluid into the interior, and the two impeller mechanisms 200 are matched to realize large-flow delivery by using a small rotating speed. Meanwhile, whether the two blades 210 work or not can be selected according to needs, for example, the upstream impeller mechanism 200 is reserved, namely the function of blowing blood is realized, and the downstream impeller mechanism 200 is reserved, namely the function of pumping blood is realized, so that the blood pumping regulation range of the ventricular assist blood pumping device is enlarged. Moreover, after one impeller mechanism 200 fails, the other impeller mechanism 200 can still be used normally, so that the reliability of the ventricular assist blood pumping device is improved; meanwhile, the two driving assemblies 300 can work alternately and independently in a discontinuous way to improve the overall service life of the ventricular assist blood pumping device. Further, the blood is pressurized by the rotation of the two impeller mechanisms 200, and compared with the mode that one impeller mechanism 200 rotates at a high speed, the problem that the cells in the blood are damaged by large shearing force caused by the blades 210 rotating at a high speed can be avoided. In addition, the two impeller mechanisms 200 are connected into a whole through the connecting shaft, so that the two connecting shafts have better supporting stability at the ends close to each other.

It should be noted that in the case of a plurality of impeller mechanisms 200, one or more, preferably two, blades 210 may be provided on the same rotating shaft 220. The connecting shaft and the two rotating shafts 220 are coaxially arranged, so that the running stability of the device during blood conveying is improved. The two impeller mechanisms 200 can rotate in the same direction or different directions, and the controller 400 can control the rotation of the two impeller mechanisms 200 in the same direction or different directions.

As shown in fig. 1, the ventricular assist blood pumping apparatus of the present embodiment further includes a control box, and the control box is connected to the pressure measuring mechanism and the driving assembly 300 for driving the impeller mechanism 200 to rotate through signal transmission units. The control box is usually arranged outside the body, and the signal transmission unit may be an independently arranged signal box 500 or a signal transmission module integrated in the control box.

The signal transmission unit collects the pressure of the corresponding measuring point through the pressure measuring mechanism and feeds the pressure back to the control box, and the control box is provided with a corresponding controller 400, a control knob and the like so as to control and adjust the pressurization amount and the blood flow of the ventricular assist blood pumping device. Specifically, the controller 400 may automatically adjust the rotation speed of the driving assembly 300 according to the built-in program setting and the feedback of the signal transmission unit, or manually adjust the rotation speed of the driving assembly 300 according to the feedback of the signal transmission unit as needed, so as to achieve the purpose of adjusting the boost amount.

It should be noted that, when the driving assembly 300 is disposed outside the body, it may also be integrated in the control box, so as to facilitate the integrated disposition of the external portion of the ventricular assist blood pumping apparatus, and improve the inconvenience in carrying caused by the scattered parts.

In summary, the ventricular assist blood pumping device of the present embodiment is a ventricular assist device that is inserted through a catheter, and can be used for treating heart failure of a patient, and can increase control flow, relieve pressure or blood pumping load of the heart, gradually recover the cardiac muscle, and help to restore the heart. The impeller mechanism 200 and the support cover 110 form a blood pump, the blood pump is a vane pump structure, the vanes 210 are foldable vanes 210, and a self-expansion mode of nickel-titanium alloy can be adopted, and a mechanical bouncing device can also be adopted. The rotating speed of the vane pump can be controlled by adjusting the control box, so that the flow regulation of the blood pump is realized; and, blood pump can realize the transport of large-traffic under the lower rotational speed, realization. The signal box 500 is used for detecting the real-time flow and the rotating speed of the blood pump, feeding the real-time flow and the rotating speed back to the control box, and adjusting the rotating speed of the blood pump by using the control box, thereby achieving the purpose of adjusting the flow. Three pressure measuring points are arranged on the instrument, and can be used for monitoring the pressure change inside and around the instrument, and simultaneously monitoring the flow of the instrument according to the pressure values of the first measuring point P2 and the second measuring point P3. The instrument adopts a double-impeller structure driven by double motors, one impeller is used for blowing fluid into a blood flow channel, the other impeller is used for sucking the fluid, and each impeller can work independently and can realize the function of pumping blood; the overall reliability of the system is improved by the design of the double motors, and meanwhile, the motors can be designed in vivo and can also be arranged outside the body in a driving wire transmission mode. The blood flow channel is composed of a support cover 110 and a coating film 112, both ends of the coating film 112 are in through hole structures, wherein the outflow end can be in a through structure and also can be designed into a honeycomb round hole structure, and the honeycomb round hole structure can play a good role in rectification. The support cover 110 includes a main frame 1111 and a connection frame 1112, the main frame 1111 is used for protecting the impeller, and the connection frame 1112 can increase the sectional area of the blood outlet 101 and improve the delivery efficiency of the device. The instrument is also connected with an adjustable sheath 116 to realize the function of bending adjustment and facilitate passing through the position of the aortic arch when being implanted.

Example two

As shown in fig. 14 to 16, the present embodiment provides a ventricular assist blood pumping device, which is different from the first embodiment only in that a support cover 110 includes a main frame 1111, the main frame 1111 is not connected to a connecting frame 1112, a middle portion of the main frame 1111 is covered with a coating film 112, and both ends of the coating film 112 are opened to form an inlet 102 and an outlet 101 for blood at both ends of the main frame 1111, respectively.

The ventricular assist blood pumping device can be implanted through femoral artery or heart apex, and the principle of the ventricular assist blood pumping device is mainly that blood at the bottom of a ventricle is pumped to the position close to the outflow tract of the aorta 2 when the heart contracts, so that the blood passing amount at the position of an aortic valve is increased. The specific principle is that the contraction or relaxation state of the heart is judged by detecting ECG800(ECG, namely electrocardiogram equipment) signals of a patient, the control box judges which state the heart is in by receiving the ECG800 signals, and when the heart is in the contraction state, the control box sends out pulse signals, and the motor rotates, so that the blood pumping function of the ventricular auxiliary blood pumping device is realized. When the heart begins to relax, the electric motor is turned off immediately.

It should be noted that the arrows in fig. 14 and 15 indicate the flow of blood, fig. 14 shows a transfemoral implantation, and fig. 15 shows a transapical implantation.

The arrangement of other components of the ventricular assist blood pumping device of the embodiment can be realized according to the first embodiment. The ventricular assist blood pumping device has the advantages of the ventricular assist blood pumping device.

EXAMPLE III

As shown in fig. 17 to 18, the present embodiment provides a ventricular assist blood pumping device, which is the same as the embodiment except that a support cover 110 is inserted into the junction between the aorta 2 and the left ventricle 1 in an interference manner, or can be understood as being in the aorta 2. That is, the support cover 110 passes through the aortic valve, one end of the main frame 1111 exposed outside the covering film 112 is communicated with the left ventricle 1 to form an inlet 102 of blood, and the other end of the main frame 1111 exposed outside the covering film 112 is communicated with the aorta 2 to form an outlet 101 of blood.

The ventricular assist blood pumping device of the embodiment can be provided with two pressure measurement points, wherein one pressure measurement point P4 is arranged at one end of the main frame 1111 exposed outside the covering membrane 112 and communicated with the left ventricle 1, the other pressure measurement point P5 is arranged at one end of the main frame 1111 exposed outside the covering membrane 112 and communicated with the aorta 2, and the pressure measurement mechanism is used for measuring the pressures of the two points, so that the state of the blood pump can be known. Meanwhile, according to the pressure values of the two measurement points, the blood flow of the ventricular assist blood pumping device can be calculated by combining the cross sectional area of the inner side of the main frame 1111 (the cross sectional area is also the cross sectional area of the aorta 2 because the main frame 1111 is arranged in the aorta 2 in an interference mode), so that the blood flow can be adjusted according to the heart failure degree of the patient. In this embodiment, reference may be made to the description of the first embodiment for a specific calculation manner of the blood flow rate of the ventricular assist blood pumping device.

Similarly, the ventricular assist pump device of the present embodiment may be implanted through the femoral artery, as shown in fig. 17; i.e., transapical implantation, as shown in fig. 18.

The arrangement of other components of the ventricular assist blood pumping device of the present embodiment can be implemented with reference to the first embodiment or the second embodiment. The ventricular assist blood pumping device has the advantages of the ventricular assist blood pumping device. In addition, the blood pump formed by the support cover 110 and the impeller mechanism 200 of the ventricular assist blood pumping device of the embodiment can directly replace an aortic valve, not only can treat heart failure, but also can replace the left ventricle 1 to realize the blood pumping function. Because many heart failure patients may have calcification of the aorta 2 or regurgitation, the ventricular assist blood pumping device of the embodiment can be used for treating the patients, namely, the aortic valve is directly replaced by the in-vivo component 100 of the device, the fixation is realized at the position of the aorta 2, the function of the aortic valve is replaced by the suction function of the device, the unidirectional flow of blood flow can be ensured, and the heart failure can be treated.

Example four

As shown in fig. 19 or fig. 20, the present embodiment provides a ventricular assist blood pumping device, which is different from the first embodiment in that the ventricular assist blood pumping device of the present embodiment is disposed in the aorta 2, and the blood flow path is formed by the blood vessel wall of the aorta 2 in combination with the main frame 1111, without providing the coating film 112.

Specifically, the ventricular assist blood pumping device of the present embodiment includes an in-vivo assembly 100, the in-vivo assembly 100 includes a support cover 110 and an impeller mechanism 200; the supporting cover 110 comprises a hollow cover body 111, the impeller mechanism 200 is arranged in the hollow cover body 111, and the impeller mechanism 200 comprises a rotating shaft 220 and blades 210 connected with the rotating shaft 220; the in-vivo assembly 100 has a folded state in which the support housing 110 is folded inward on the impeller mechanism 200 and the blades 210 are folded on the rotation shaft 220; in the deployed state, the support housing 110 is deployed outward, and the blades 210 are deployed in the support housing 110 relative to the rotation shaft 220 for rotationally pumping blood to promote the blood of the left ventricle 1 to be delivered to the aorta 2; the interbody assembly 100 is configured to be transcatheter implanted within the aorta 2 in a collapsed state, and is configured such that the support shield 110 is interference fit within the aorta 2 in an expanded state.

The intracorporeal component 100 of the ventricular assist blood pumping device of the present embodiment can be placed at the position of the aorta 2, more precisely, at the connection position between the aorta 2 and the outflow tract of the left ventricle 1, and the device is fixed through the aorta 2. The instrument may utilize a circular channel at the location of the vessels and outflow tract of the aorta 2 to create a pressure drop inside the channel to perfuse blood to the location of the aorta 2.

The same ventricular assist pump device of this embodiment can be implanted through the femoral artery, as shown in fig. 19; i.e., transapical implantation, as shown in fig. 20.

EXAMPLE five

The present embodiment provides a ventricular assist pumping system, which includes an ECG800 and the ventricular assist pumping apparatus provided in any one of the first to fourth embodiments.

The ECG800 is connected to the control box of the ventricular assist pump. The ECG800 may employ existing conventional equipment. The ventricular assist blood pumping system is used for monitoring the electrocardiogram of the heart of a patient through a signal receiving module of the ECG800, receiving signals, sending the received electrocardiogram signals to the control box, converting the electrocardiogram signals into digital signals by the control box, judging the contraction and relaxation states of the heart, converting the converted digital signals into control instructions and sending the control instructions to the driving assembly 300, and driving the impeller mechanism 200 to rotate through the driving assembly 300, so that the purpose of assisting the left ventricle 1 to pump blood to the aorta 2 is achieved.

Finally, it should be noted that: the above embodiments are only used to illustrate the technical solution of the present invention, and not to limit the same; although the present invention has been described in detail with reference to the foregoing embodiments, it should be understood by those skilled in the art that: the technical solutions described in the foregoing embodiments may still be modified, or some or all of the technical features may be equivalently replaced; such modifications and substitutions do not depart from the spirit and scope of the present invention.

Claims

1. A ventricular assist blood pumping apparatus, comprising an intrabody assembly (100), the intrabody assembly (100) comprising a support housing (110) and an impeller mechanism (200);

the support cover (110) comprises a hollow cover body (111) and a coating film (112), the coating film (112) is coated on the hollow cover body (111), the impeller mechanism (200) is arranged in the hollow cover body (111), and the impeller mechanism (200) comprises a rotating shaft (220) and blades (210) connected with the rotating shaft (220);

the in-vivo assembly (100) has a folded state in which the support shroud (110) is folded inwardly over the impeller mechanism (200) and the blades (210) are folded over the rotational shaft (220), and an unfolded state; in the unfolding state, the supporting cover (110) is unfolded outwards to form a blood flow channel, and the blades (210) are unfolded in the supporting cover (110) relative to the rotating shaft (220) and used for rotationally pumping blood so as to promote the blood of the left ventricle (1) to be conveyed to the aorta (2);

the intracorporeal component (100) is configured to be catheterized into a junction of the aorta (2) and the left ventricle (1) or into the left ventricle (1) in a folded state, and configured to be disposed with the support cover (110) in a deployed state at the junction of the aorta (2) and the left ventricle (1) or into the left ventricle (1).

2. A ventricular assist blood pumping apparatus according to claim 1, wherein the hollow-out cover body (111) includes a main frame body (1111), the cross section of the main frame body (1111) is in an annular arrangement, the main frame body (1111) is in a grid-shaped hollow-out arrangement, two axial ends of the main frame body (1111) are respectively folded inwards along the directions departing from each other, and the blades (210) are correspondingly arranged in the main frame body (1111).

3. A ventricular assist pump blood device according to claim 2, characterized in that the main frame (1111) is covered with the coating (112) in the middle, and the two ends of the main frame (1111) form the inlet (102) and outlet (101) of blood, respectively.

4. A ventricular assist blood pumping apparatus according to claim 2, wherein the hollow cover (111) further comprises a connection frame (1112), in the deployed state, the inner diameter of the connection frame (1112) is smaller than the inner diameter of the hollow cover (111), the cross section of the connection frame (1112) is disposed in a ring shape, the connection frame (1112) is connected to the side of the main cover (1111) close to the aorta (2), and the end of the connection frame (1112) far away from the main cover (1111) is used for being disposed in the aorta (2);

the connecting frame (1112) is arranged in a hollow grid manner, the main frame body (1111) and the connecting frame (1112) are covered with the covering film (112), one end of the main frame body (1111), which is far away from the connecting frame (1112), is exposed to form an inlet (102) of blood, and the covering film (112), which is positioned at one end of the connecting frame (1112), which is far away from the main frame body (1111), forms an outlet (101) of blood; or, the connecting frame (1112) is arranged in a hollow tubular shape, the main frame body (1111) is covered with the coating (112), one end, far away from the connecting frame (1112), of the main frame body (1111) is exposed to form an inlet (102) of blood, and one end, far away from the connecting frame (1111), of the connecting frame (1112) is opened to form an outlet (101) of blood.

5. A ventricular assist blood pumping apparatus according to claim 4, characterized in that the connection frame (1112) comprises a first segment (1113) and a second segment (1114), the first segment (1113) being connected between the second segment (1114) and the main frame body (1111);

the first section (1113) has an outer diameter smaller than an outer diameter of the second section (1114), the first section (1113) being configured to correspond to an aortic valve.

6. A ventricular assist pump blood device according to claim 4 or 5, characterized in that the outlet (101) comprises a central hole (103), the axis of the central hole (103) coincides with the axis of the connection frame (1112); or the outlet (101) comprises a plurality of through holes (104), the axes of the through holes (104) are consistent with the axis of the connecting frame (1112), and the through holes (104) are arranged in a honeycomb shape.

7. A ventricular assist blood pumping apparatus according to any one of claims 2-5, characterized in that the main frame body (1111) is provided at its two ends with a first support sleeve (113) and a third support sleeve (115), respectively;

the rotating shaft (220) is arranged in the main frame body (1111), the first supporting sleeve (113) and the second supporting sleeve (114) in a penetrating mode, and the first supporting sleeve (113) and the third supporting sleeve (115) are used for supporting the rotating shaft (220).

8. A ventricular assist pump according to claim 4 or 5, characterized in that it further comprises a pressure measurement mechanism for monitoring the pressure in the left ventricle (1) corresponding to the inlet (102), the pressure in the aorta (2) corresponding to the outlet (101) and/or the pressure in the blood flow path;

9. A ventricular assist pump blood apparatus according to claim 1, characterized in that the number of the blades (210) is one or more, the blades (210) are fixedly connected with the rotating shaft (220), the material of the blades (210) is memory alloy, so that the blades (210) can be folded or unfolded;

and/or

Blade (210) with axis of rotation (220) are articulated to be connected, blade (210) with be provided with the piece that resets between axis of rotation (220), under the exogenic action, blade (210) can compress the piece that resets to make blade (210) are in folded state, the piece that resets makes blade (210) have relatively axis of rotation (220) the trend of expanding.

10. A ventricular assist pump device according to claim 1, characterized in that it further comprises a drive assembly (300), the drive assembly (300) being connected to the rotational shaft (220);

the drive assembly (300) is configured to be disposed within a support housing (110); alternatively, the driving assembly (300) is configured to be disposed outside the body and connected to the rotating shaft (220) through a transmission member (310).

11. A ventricular assist pump blood device according to claim 10, characterized in that the impeller mechanism (200) comprises a plurality of impeller mechanisms (200) arranged in sequence, and the rotating shafts (220) of the impeller mechanisms (200) are fixedly connected with each other or the rotating shafts (220) of the impeller mechanisms (200) are rotatably connected with each other.

12. A ventricular assist pump blood device according to claim 11, characterized in that the number of the impeller mechanisms (200) is two, and the rotating shafts (220) of the two impeller mechanisms (200) are configured to be rotatably connected with each other, so that the two impeller mechanisms (200) can rotate independently;

the number of the driving assemblies (300) is two, the two driving assemblies (300) are respectively connected with the two rotating shafts (220) in a one-to-one correspondence mode, and the two driving assemblies (300) are respectively connected with two ends, deviating from each other, of the two rotating shafts (220).

13. A ventricular assist pump blood device according to claim 1, characterized in that a sheath (116) is connected to one or both ends of the support shield (110), and the curvature of the sheath (116) is adjustable.

14. A ventricular assist pump blood device according to claim 8, characterized in that it further comprises a control box connected to the pressure measuring mechanism and the drive assembly (300) for driving the impeller mechanism (200) to rotate, respectively, through signal transmission units.

15. A ventricular assist blood pumping apparatus according to claim 1, wherein the hollow cover (111) is made of memory alloy, and the cover film (112) is a plastic film or a biological tissue film.

16. A ventricular assist pump device, characterized in that it comprises an intracorporeal component (100), the intracorporeal component (100) comprising a support housing (110) and an impeller mechanism (200);

the support cover (110) comprises a hollow cover body (111), the impeller mechanism (200) is arranged in the hollow cover body (111), and the impeller mechanism (200) comprises a rotating shaft (220) and blades (210) connected with the rotating shaft (220);

the in-vivo assembly (100) has a folded state in which the support shroud (110) is folded inwardly over the impeller mechanism (200) and the blades (210) are folded over the rotational shaft (220), and an unfolded state; in the unfolding state, the supporting cover (110) is unfolded outwards, and the blades (210) are unfolded in the supporting cover (110) relative to the rotating shaft (220) and used for rotationally pumping blood so as to promote the blood of the left ventricle (1) to be conveyed to the aorta (2);

the intracorporeal component (100) is configured to be transcatheter implanted into the aorta (2) in a collapsed state, and configured to be in a deployed state with the support cover (110) interference fit within the aorta (2).

17. A ventricular assist pumping system comprising an ECG (800) and a ventricular assist pumping apparatus according to any one of claims 1-16.