CN117427268A - Separated heart auxiliary device through aorta - Google Patents
Separated heart auxiliary device through aorta Download PDFInfo
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- CN117427268A CN117427268A CN202311693255.6A CN202311693255A CN117427268A CN 117427268 A CN117427268 A CN 117427268A CN 202311693255 A CN202311693255 A CN 202311693255A CN 117427268 A CN117427268 A CN 117427268A
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- impeller
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- aortic
- shell
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- 210000000709 aorta Anatomy 0.000 title claims abstract description 21
- 230000005540 biological transmission Effects 0.000 claims abstract description 22
- 210000001308 heart ventricle Anatomy 0.000 claims abstract description 4
- 238000007789 sealing Methods 0.000 claims description 4
- 230000017531 blood circulation Effects 0.000 abstract description 17
- 210000004369 blood Anatomy 0.000 abstract description 15
- 239000008280 blood Substances 0.000 abstract description 15
- 210000000056 organ Anatomy 0.000 abstract description 8
- 230000006378 damage Effects 0.000 abstract description 7
- 230000036772 blood pressure Effects 0.000 abstract description 5
- 230000015271 coagulation Effects 0.000 abstract description 3
- 238000005345 coagulation Methods 0.000 abstract description 3
- 230000035790 physiological processes and functions Effects 0.000 abstract description 3
- 238000000926 separation method Methods 0.000 abstract description 3
- 230000004872 arterial blood pressure Effects 0.000 abstract description 2
- 230000010412 perfusion Effects 0.000 abstract description 2
- 210000001147 pulmonary artery Anatomy 0.000 abstract 1
- 210000001765 aortic valve Anatomy 0.000 description 8
- 210000004351 coronary vessel Anatomy 0.000 description 8
- 230000010349 pulsation Effects 0.000 description 6
- 230000002861 ventricular Effects 0.000 description 6
- 206010019280 Heart failures Diseases 0.000 description 5
- 238000010586 diagram Methods 0.000 description 5
- 208000027418 Wounds and injury Diseases 0.000 description 4
- 208000014674 injury Diseases 0.000 description 4
- 238000009434 installation Methods 0.000 description 4
- 208000032843 Hemorrhage Diseases 0.000 description 3
- 230000006870 function Effects 0.000 description 3
- 238000002513 implantation Methods 0.000 description 3
- 206010058558 Hypoperfusion Diseases 0.000 description 2
- 208000031481 Pathologic Constriction Diseases 0.000 description 2
- 208000006011 Stroke Diseases 0.000 description 2
- 208000007536 Thrombosis Diseases 0.000 description 2
- 208000034158 bleeding Diseases 0.000 description 2
- 230000000740 bleeding effect Effects 0.000 description 2
- 210000004204 blood vessel Anatomy 0.000 description 2
- 230000004087 circulation Effects 0.000 description 2
- 230000007547 defect Effects 0.000 description 2
- 230000035487 diastolic blood pressure Effects 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 208000028867 ischemia Diseases 0.000 description 2
- 230000003907 kidney function Effects 0.000 description 2
- 230000033001 locomotion Effects 0.000 description 2
- 230000035485 pulse pressure Effects 0.000 description 2
- 230000036262 stenosis Effects 0.000 description 2
- 208000037804 stenosis Diseases 0.000 description 2
- 230000035488 systolic blood pressure Effects 0.000 description 2
- 208000024172 Cardiovascular disease Diseases 0.000 description 1
- 206010008190 Cerebrovascular accident Diseases 0.000 description 1
- 206010019663 Hepatic failure Diseases 0.000 description 1
- 206010053159 Organ failure Diseases 0.000 description 1
- 208000001647 Renal Insufficiency Diseases 0.000 description 1
- 210000001367 artery Anatomy 0.000 description 1
- 239000002473 artificial blood Substances 0.000 description 1
- 230000001746 atrial effect Effects 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000005779 cell damage Effects 0.000 description 1
- 208000037887 cell injury Diseases 0.000 description 1
- 230000003205 diastolic effect Effects 0.000 description 1
- 230000004064 dysfunction Effects 0.000 description 1
- 230000002497 edematous effect Effects 0.000 description 1
- 210000003743 erythrocyte Anatomy 0.000 description 1
- 230000000004 hemodynamic effect Effects 0.000 description 1
- 230000001771 impaired effect Effects 0.000 description 1
- 201000006370 kidney failure Diseases 0.000 description 1
- 210000005240 left ventricle Anatomy 0.000 description 1
- 210000004185 liver Anatomy 0.000 description 1
- 208000007903 liver failure Diseases 0.000 description 1
- 208000030159 metabolic disease Diseases 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000000149 penetrating effect Effects 0.000 description 1
- 238000005086 pumping Methods 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 230000004083 survival effect Effects 0.000 description 1
- 238000002054 transplantation Methods 0.000 description 1
- 210000001835 viscera Anatomy 0.000 description 1
Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
- A61M60/135—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel inside a blood vessel, e.g. using grafting
- A61M60/139—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel inside a blood vessel, e.g. using grafting inside the aorta, e.g. intra-aortic balloon pumps
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
- A61M60/135—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel inside a blood vessel, e.g. using grafting
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/20—Type thereof
- A61M60/205—Non-positive displacement blood pumps
- A61M60/216—Non-positive displacement blood pumps including a rotating member acting on the blood, e.g. impeller
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/40—Details relating to driving
- A61M60/403—Details relating to driving for non-positive displacement blood pumps
- A61M60/408—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable
- A61M60/411—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being mechanical, e.g. transmitted by a shaft or cable generated by an electromotor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/802—Constructional details other than related to driving of non-positive displacement blood pumps
- A61M60/804—Impellers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/80—Constructional details other than related to driving
- A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
- A61M60/857—Implantable blood tubes
Landscapes
- Health & Medical Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Cardiology (AREA)
- Mechanical Engineering (AREA)
- Anesthesiology (AREA)
- Hematology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Vascular Medicine (AREA)
- Transplantation (AREA)
- External Artificial Organs (AREA)
Abstract
The invention relates to the technical field of medical equipment, and discloses an aortic split heart auxiliary device which comprises an axial flow driving system and a flow guiding module, wherein one end, which faces to a heart ventricle, is defined as a proximal end, the other end is defined as a distal end, the axial flow driving system comprises a driving module and an impeller, a transmission shaft of the driving module is connected with the impeller, the impeller comprises a hub and impeller blades, and the impeller blades are spirally arranged around the periphery of the hub; the flow guide module comprises a hollow sleeve, the impeller is positioned in the proximal end of the sleeve, the driving module extends towards the distal end of the sleeve and penetrates out, and a spiral guide vane is fixedly arranged on the inner wall of the distal end of the sleeve; the periphery of the driving module is connected with a fixed ring through a connecting rod. The invention can be arranged at the ascending aorta or the pulmonary artery, and forms a serial structure with the heart after being arranged, the generated blood pressure waveform is more similar to the pulse waveform in the physiological state, the average arterial pressure is larger, and the perfusion of tissue and organs is facilitated; the separation of the motor and the paddle increases the blood flow space, the required rotating speed of the paddle is reduced, and the damage to blood and coagulation is reduced.
Description
Technical Field
The invention relates to the technical field of medical equipment, in particular to an aortic split type heart auxiliary device.
Background
Heart failure (heart failure) is a terminal course of all cardiovascular diseases, and is manifested by: the systolic and/or diastolic functions of the heart are impaired and the pumping volume of the heart is reduced. This aspect can lead to hypoperfusion of vital organs throughout the body, causing dysfunction of the organs; on the other hand, the heart can not pump out blood in time, so that the blood of the heart is blocked, the venous blood is accumulated in a venous system, the organs are edematous, the metabolic disorder of the tissues and organs is further aggravated, and finally, the whole body organ failure and death are caused. Heart transplantation is generally considered to be the best treatment for patients with end-stage heart failure, but is limited by the extreme shortage of heart donors, with only a small proportion of heart failure patients hopefully undergoing heart transplant surgery.
In the extreme absence of heart donors, mechanical circulatory support devices (mechanical circulatory support, MCS) bring new survival promise for end-stage heart failure patients. The basic principle is to pump blood from the failing heart into the main arterial system. The heart auxiliary device that adopts clinically at present all sets up the entry in left ventricular apex portion, connects artifical auxiliary pump by artificial blood vessel, and the export all is located the ascending aorta, and the left ventricle that blood flow was passed through the failure by artifical auxiliary pump and is walked around the aortic valve and reach the aorta, forms a bypass circulation, constitutes the parallel structure with the heart, continuously carries blood flow to whole body arterial system, carries out circulation support. However, due to the design of the device, the following challenges in the clinic remain to be resolved: 1) The parallel structure results in hemodynamic changes and does not produce physiological-like systolic and diastolic pressures with small pulse pressure differences, because of the very small arterial pulsations, a patient fitted with such a pump is also referred to as a "pulseless person". However physiological pulsations are extremely important to the human body: the alternation of systolic pressure and diastolic pressure is the main motive force of capillary vessel opening, and when the motive force is lost, the capillary vessel opening is difficult, so that the tissue and organ are not filled enough, and a series of complications such as liver and kidney failure can occur to patients; 2) The blood flow has pump-ventricular contending flow, which leads to a series of complications such as organ hypoperfusion, thrombosis and the like; 3) Right heart assist cannot be implemented; 4) Pump speed is difficult to control to a proper level, and pump stall or blood flow cessation may occur; or too fast pump speed, exacerbates red blood cell damage and increases bleeding risk.
The US patent application 20150231318A1 discloses a trans-aortic artificial heart assist device. The device is installed in the aorta and forms a series structure with the heart, which helps to avoid the defects of parallel heart assist devices to a certain extent. However, the blood flow inlet of this patent is located on the aortic valve, which inevitably requires re-routing of the coronary opening, increasing the surgical difficulty and the risks associated with coronary re-implantation. The left ventricular outflow tract and the aorta are thin, long and straight channels, the space at the root of the aorta is smaller, and how to ensure a sufficient blood flow channel and effective pulse volume becomes a difficult problem in clinical application.
Disclosure of Invention
In order to solve the defects in the prior art, the invention provides a miniaturized split type heart auxiliary device through the aorta.
In order to achieve the technical purpose, the invention adopts the following technical scheme:
the split heart auxiliary device comprises an axial flow driving system and a flow guiding module, wherein one end, which faces towards a heart ventricle, of the split heart auxiliary device is defined to be a proximal end, the other end is defined to be a distal end, the axial flow driving system comprises a driving module and an impeller, a transmission shaft of the driving module is connected with the impeller, the impeller comprises a hub and impeller blades, and the impeller blades are spirally arranged around the periphery of the hub; the flow guide module comprises a hollow sleeve, the impeller is positioned in the proximal end of the sleeve, the driving module extends towards the distal end of the sleeve and penetrates out, and a spiral guide vane is fixedly arranged on the inner wall of the distal end of the sleeve; the periphery of the driving module is connected with a fixing ring through a connecting rod.
Further, a connecting portion is provided at the outer periphery of the distal end of the sleeve.
Preferably, the connecting portion is in the shape of an annular groove.
Preferably, the connecting part is in an annular convex edge shape.
Further, at least two connecting rods are arranged and circumferentially distributed around the driving module.
Further, a supporting rod is connected between the driving module and the sleeve.
Further, the driving module comprises a shell, an annular motor is arranged in an inner cavity of the shell, an annular permanent magnet is coaxially arranged on the inner side of the annular motor, a transmission shaft penetrates through the annular permanent magnet, two ends of the transmission shaft penetrate out of two ends of the annular permanent magnet respectively, the proximal end of the transmission shaft penetrates out of the shell, bearings are respectively arranged at two ends in the shell, two ends of the transmission shaft penetrate into the bearings respectively, and a sealing ring is arranged between an opening of the proximal end of the shell and the transmission shaft.
Further, the motor further comprises a wire, one end of the wire is communicated with the annular motor, and the other end of the wire extends out of the shell along the connecting rod to be communicated with an external power supply.
Further, the shell of the driving module comprises a rugby-shaped far end and a near end of an slender shaft, and the annular motor and the annular permanent magnet are arranged in the far end of the shell.
The invention has the beneficial effects that:
the aortic split heart auxiliary device is in a serial structure with the heart after being installed, the pulsation effect can be achieved, the blood pressure waveform generated by the serial structure is closer to the pulsation waveform in a physiological state, the pulse pressure difference is higher, the pulse blood flow enables the viscera to be well perfused, the pump-heart competing flow relationship is changed into a cooperative relationship, all blood passes through the heart-pump-aorta, the full blood flow avoids thrombosis in the pump, and therefore, a series of related complications such as renal function injury, apoplexy and the like brought by the parallel structure can be effectively avoided by the serial structure.
The transaortic split type heart auxiliary device provided by the invention has the advantages that the blood flow inlet is positioned below the left ventricular outflow tract and the aortic valve, and the coronary artery ischemia is avoided without the need of diversion of the coronary artery opening, so that the operation difficulty is reduced, the risk of stenosis and injury after the coronary artery re-implantation operation is reduced, and the occurrence of the related risk of the coronary artery operation is avoided.
The invention adopts a separated structure, so that the surgical installation is more convenient, and the surgical mode is like aortic valve replacement; hemorrhage due to aortic replacement is avoided.
In the invention, the separation of the motor and the blade greatly increases the blood flow space, so that the required rotation speed of the blade is reduced, and the damage to blood and coagulation is reduced; at the same time, the diameter does not need to be increased to achieve the auxiliary function, so that the device is suitable for being installed on a left ventricular outflow tract and an aorta.
According to the split type heart auxiliary device through the aorta, the spiral guide vanes are arranged in the sleeve of the flow guide module, so that the rotary motion of blood driven by the impeller can be eliminated, the blood becomes to move along the axial direction of the aorta, and the blood flow kinetic energy loss is reduced.
Drawings
In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings that are needed in the embodiments will be briefly described below, it being understood that the following drawings only illustrate some embodiments of the present application and therefore should not be considered limiting the scope, and that other related drawings may be obtained according to these drawings without inventive effort for a person skilled in the art.
FIG. 1 is a schematic diagram of an embodiment of the present invention;
FIG. 2 is a schematic diagram of the connection of a drive module to a stationary ring;
fig. 3 is a schematic cross-sectional view of the drive module of the embodiment of fig. 1.
FIG. 4 is a schematic diagram of another embodiment;
FIG. 5 is a schematic cross-sectional view of the drive module of the embodiment of FIG. 4;
FIG. 6 is a schematic diagram of the invention in an applied state;
fig. 7 is a schematic view of blood pressure waveforms after installation of the device of the present invention.
Reference numerals: the device comprises a 1-driving module, a 11-connecting rod, a 12-fixed ring, a 13-shell, a 14-annular motor, a 15-annular permanent magnet, a 2-impeller, a 21-hub, 22-impeller blades, a 3-transmission shaft, a 4-sleeve, 41-guide vanes, a 42-connecting part, a 5-aorta, a 6-supporting rod, a 7-aortic valve, an 8-coronary artery and a 9-sealing ring.
Detailed Description
For the purposes of making the objects, technical solutions and advantages of the embodiments of the present application more clear, the technical solutions of the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application, and it is apparent that the described embodiments are some embodiments of the present application, but not all embodiments. The components of the embodiments of the present application, which are generally described and illustrated in the figures herein, may be arranged and designed in a wide variety of different configurations. Thus, the following detailed description of the embodiments of the present application, as provided in the accompanying drawings, is not intended to limit the scope of the application, as claimed, but is merely representative of selected embodiments of the application. All other embodiments, which can be made by one of ordinary skill in the art without undue burden from the present disclosure, are within the scope of the present disclosure.
The aortic split type heart assisting device comprises an axial flow driving system and a flow guiding module, wherein one end, which faces towards a heart ventricle, of the heart is defined to be a proximal end, the other end is defined to be a distal end, the axial flow driving system comprises a driving module 1 and an impeller 2, a transmission shaft 3 of the driving module 1 is connected with the impeller 2, the impeller 2 comprises a hub 21 and impeller blades 22, and the impeller blades 22 are spirally arranged around the periphery of the hub 21; the flow guide module comprises a hollow sleeve 4, the impeller 2 is positioned in the proximal end of the sleeve 4, the driving module 1 extends towards the distal end of the sleeve 4 and penetrates out, and a spiral guide vane 41 is fixedly arranged on the inner wall of the distal end of the sleeve 4; the periphery of the driving module 1 is connected with a fixed ring 12 through a connecting rod 11. When the device is installed, the periphery of the sleeve 4 is connected with the aorta by stitching, and the fixing ring 12 of the driving module 1 is abutted against the inner wall of the aorta 5.
The impeller blades 22 have a first helical direction around the hub 21 and the guide vanes 41 have a second helical direction around the sleeve 4, said first helical direction being opposite to the second helical direction. The outlet end of the guide vane 41 has a partial area extending along the axial direction of the sleeve 4, so that the direction of blood at the outlet end of the guide vane 41 is consistent with the axial direction of the sleeve 4, the outflow direction of blood is consistent with the central axis direction of a blood vessel, the rotational movement of the blood after the blood flows out is reduced, and the energy loss is reduced.
Preferably, the outer periphery of the sleeve 4 is provided with a connecting part 42, and the connecting part 42 is in a shape of an annular groove or a convex edge, so that the connecting part is convenient to fix with the aorta during suture.
At least two connecting rods 11 are arranged and circumferentially distributed around the driving module 1. Preferably, as shown in fig. 2, three connecting rods 11 are provided. The longitudinal section of the connecting rod 11 is circular or elliptical, and the blood flow is smooth and has small resistance.
Further, a supporting rod 6 is connected between the driving module 1 and the sleeve 4, and the supporting rod 6 fixes the driving module 1 and the sleeve 4 so as to ensure that the coaxial relative position relationship between the driving module 1 and the sleeve 4 is always kept. At least 2 support rods 6 are arranged and uniformly distributed around the periphery of the driving module 1, and preferably 2, 3 or 4 support rods 6 are arranged. The support rod 6 has a circular or oval longitudinal section, so that the resistance of blood flowing through the support rod is reduced.
The driving module 1 is shown in fig. 3, and comprises a shell 13, an annular motor 14 is arranged in the inner cavity of the shell 13, an annular permanent magnet 15 is coaxially arranged on the inner side of the annular motor 14, a transmission shaft 3 is arranged inside the annular permanent magnet 15 in a penetrating mode, two ends of the transmission shaft 3 respectively penetrate out of two ends of the annular permanent magnet 15, the proximal end of the transmission shaft 3 penetrates out of the shell 13, bearings are respectively arranged at two ends of the shell 13, two ends of the transmission shaft 3 respectively penetrate into the bearings, and a sealing ring 9 is arranged between the opening of the proximal end of the shell 13 and the transmission shaft 3. The device also comprises a wire, one end of the wire is communicated with the annular motor 14, and the other end of the wire extends out of the shell 13 along the connecting rod 11 to be communicated with an external power supply; preferably, the connecting rod 11 is internally provided with a hollow passage through which the wire passes. The external power supply is started to supply power to the annular motor 14, the annular motor 14 is electrified to generate a magnetic field, the annular permanent magnet 15 is rotated through the magnetic field, the annular permanent magnet 15 rotates to drive the transmission shaft 3 to rotate, the transmission shaft 3 further drives the impeller 2 to rotate, blood is pumped into the sleeve 4, and the blood flows into the aorta through the sleeve 4.
In one embodiment, as shown in fig. 1 and 3, the housing 13 of the driving module 1 includes a rugby-shaped distal end and a proximal end of an elongated shaft, the ring motor 14 and the ring permanent magnet 15 are disposed inside the distal end of the housing 13, and the transmission shaft 3 is connected to the impeller through the proximal end. In another embodiment, as shown in fig. 4 and 5, the housing 13 of the driving module 1 is in an elongated cylindrical shape, the proximal end of the housing 13 abuts against the hub of the impeller, the ring motor 14 and the ring permanent magnet 15 are disposed in the housing 13, and the distal end of the housing 13 is in a semi-ellipsoidal convergence shape.
When the device is installed, the sleeve 4 of the flow guiding module is fixedly installed below the aortic valve 7 at the root of the aorta 5, the driving module 1 passes through the aortic valve 7, the fixing ring 12 is abutted against the inner wall of the aorta 5, and the installation schematic diagram is shown in fig. 6. The split heart auxiliary device through the aorta is in a serial structure with the heart after being installed, so that the pulsation effect can be achieved, the blood pressure waveform generated by the serial structure is closer to the pulsation waveform in a physiological state, the average arterial pressure is larger, the tissue and organ perfusion is facilitated, the blood pressure waveform is shown in figure 7 (LVP: left ventricular pressure; AOP: intra-aortic pressure; LAP: left atrial pressure), and the fluctuation of intra-aortic pressure is obviously increased as can be seen from the second half of figure 7. Therefore, the series structure can effectively avoid a series of related complications such as stroke, renal function injury and the like caused by the parallel structure.
The blood flow outlet is positioned at the aortic valve 7, and the opening diversion of the coronary artery 8 is not needed, so that the coronary artery ischemia is avoided, the operation difficulty is reduced, the risk of stenosis and injury after the coronary artery re-implantation is reduced, and the occurrence of the related risk of the coronary artery operation is avoided. The invention adopts a separated structure, so that the surgical installation is more convenient, and the surgical mode is like aortic valve replacement; but also avoid bleeding caused by aortic replacement.
In the invention, the separation of the motor and the blade greatly increases the blood flow space, so that the required rotation speed of the blade is reduced, and the damage to blood and coagulation is reduced; at the same time, the diameter does not need to be increased to achieve the auxiliary function, so that the device is suitable for being installed on a thin, long and straight left ventricular outflow tract and an aorta.
Of course, the present invention is capable of other various embodiments and its several details are capable of modification and variation in light of the present invention by one skilled in the art without departing from the spirit and scope of the invention as defined in the appended claims.
Claims (9)
1. The split heart auxiliary device through aorta is characterized in that: the device comprises an axial flow driving system and a flow guiding module, wherein one end, which faces towards a heart ventricle, is defined as a proximal end, the other end is defined as a distal end, the axial flow driving system comprises a driving module and an impeller, a transmission shaft of the driving module is connected with the impeller, the impeller comprises a hub and impeller blades, and the impeller blades are spirally arranged around the periphery of the hub; the flow guide module comprises a hollow sleeve, the impeller is positioned in the proximal end of the sleeve, the driving module extends towards the distal end of the sleeve and penetrates out, and a spiral guide vane is fixedly arranged on the inner wall of the distal end of the sleeve; the periphery of the driving module is connected with a fixing ring through a connecting rod.
2. The trans-aortic split heart assist device according to claim 1, wherein: the outer periphery of the distal end of the sleeve is provided with a connecting part.
3. The trans-aortic split heart assist device according to claim 2, wherein: the connecting part is in an annular groove shape.
4. The trans-aortic split heart assist device according to claim 2, wherein: the connecting part is in an annular convex edge shape.
5. The trans-aortic split heart assist device according to claim 1, wherein: at least two connecting rods are arranged and circumferentially distributed around the driving module.
6. The trans-aortic split heart assist device according to claim 1, wherein: a supporting rod is connected between the driving module and the sleeve.
7. The trans-aortic split heart assist device according to claim 1, wherein: the driving module comprises a shell, an annular motor is arranged in an inner cavity of the shell, an annular permanent magnet is coaxially arranged on the inner side of the annular motor, a transmission shaft penetrates through the annular permanent magnet, two ends of the transmission shaft penetrate out of two ends of the annular permanent magnet respectively, the proximal end of the transmission shaft penetrates out of the shell, bearings are respectively arranged at two ends in the shell, two ends of the transmission shaft penetrate into the bearings respectively, and a sealing ring is arranged between an opening at the proximal end of the shell and the transmission shaft.
8. The trans-aortic split heart assist device of claim 7, wherein: the motor also comprises a wire, one end of the wire is communicated with the annular motor, and the other end of the wire extends out of the shell along the connecting rod to be communicated with an external power supply.
9. The trans-aortic split heart assist device of claim 7, wherein: the shell of the driving module comprises a rugby-shaped far end and a slender shaft near end, and the annular motor and the annular permanent magnet are arranged in the far end of the shell.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311693255.6A CN117427268A (en) | 2023-12-11 | 2023-12-11 | Separated heart auxiliary device through aorta |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311693255.6A CN117427268A (en) | 2023-12-11 | 2023-12-11 | Separated heart auxiliary device through aorta |
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| Publication Number | Publication Date |
|---|---|
| CN117427268A true CN117427268A (en) | 2024-01-23 |
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| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202311693255.6A Pending CN117427268A (en) | 2023-12-11 | 2023-12-11 | Separated heart auxiliary device through aorta |
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| CN (1) | CN117427268A (en) |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1253837A (en) * | 1999-12-21 | 2000-05-24 | 马惠生 | Method for making assisted circulation of ventriculus cordis and its device |
| CN104069555A (en) * | 2014-06-27 | 2014-10-01 | 长治市久安人工心脏科技开发有限公司 | Accessory axial-flow type blood pump for heart |
| CN104274873A (en) * | 2014-10-13 | 2015-01-14 | 长治市久安人工心脏科技开发有限公司 | Miniature apex cordis axial-flow blood pump and implanting method thereof |
| CN114177516A (en) * | 2021-12-22 | 2022-03-15 | 江苏大学 | High-flow two-stage catheter pump for left ventricle assistance and using method thereof |
-
2023
- 2023-12-11 CN CN202311693255.6A patent/CN117427268A/en active Pending
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1253837A (en) * | 1999-12-21 | 2000-05-24 | 马惠生 | Method for making assisted circulation of ventriculus cordis and its device |
| CN104069555A (en) * | 2014-06-27 | 2014-10-01 | 长治市久安人工心脏科技开发有限公司 | Accessory axial-flow type blood pump for heart |
| CN104274873A (en) * | 2014-10-13 | 2015-01-14 | 长治市久安人工心脏科技开发有限公司 | Miniature apex cordis axial-flow blood pump and implanting method thereof |
| CN114177516A (en) * | 2021-12-22 | 2022-03-15 | 江苏大学 | High-flow two-stage catheter pump for left ventricle assistance and using method thereof |
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