CN117298442A - Implantable blood non-contact type ventricular assist device - Google Patents
Implantable blood non-contact type ventricular assist device Download PDFInfo
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- CN117298442A CN117298442A CN202311305740.1A CN202311305740A CN117298442A CN 117298442 A CN117298442 A CN 117298442A CN 202311305740 A CN202311305740 A CN 202311305740A CN 117298442 A CN117298442 A CN 117298442A
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- 239000008280 blood Substances 0.000 title claims abstract description 73
- 210000004369 blood Anatomy 0.000 title claims abstract description 73
- 230000002861 ventricular Effects 0.000 title claims abstract description 32
- 210000000709 aorta Anatomy 0.000 claims abstract description 35
- 210000004712 air sac Anatomy 0.000 claims abstract description 6
- 238000000034 method Methods 0.000 claims description 14
- 238000004891 communication Methods 0.000 claims description 11
- 230000005540 biological transmission Effects 0.000 claims description 7
- 210000005240 left ventricle Anatomy 0.000 abstract description 11
- 230000008081 blood perfusion Effects 0.000 abstract description 9
- 208000015181 infectious disease Diseases 0.000 abstract description 7
- 210000000056 organ Anatomy 0.000 abstract description 7
- 230000035487 diastolic blood pressure Effects 0.000 abstract description 6
- 238000002513 implantation Methods 0.000 abstract description 6
- 230000008569 process Effects 0.000 description 13
- 230000033764 rhythmic process Effects 0.000 description 10
- 230000007246 mechanism Effects 0.000 description 8
- 230000000903 blocking effect Effects 0.000 description 7
- 238000012544 monitoring process Methods 0.000 description 7
- 210000005077 saccule Anatomy 0.000 description 7
- 210000001765 aortic valve Anatomy 0.000 description 5
- 210000004204 blood vessel Anatomy 0.000 description 5
- 230000006870 function Effects 0.000 description 4
- 230000002107 myocardial effect Effects 0.000 description 4
- 230000036284 oxygen consumption Effects 0.000 description 4
- 230000017531 blood circulation Effects 0.000 description 3
- 230000036770 blood supply Effects 0.000 description 3
- 238000007599 discharging Methods 0.000 description 3
- 238000001356 surgical procedure Methods 0.000 description 3
- 210000000115 thoracic cavity Anatomy 0.000 description 3
- 206010019280 Heart failures Diseases 0.000 description 2
- 210000002376 aorta thoracic Anatomy 0.000 description 2
- 230000000740 bleeding effect Effects 0.000 description 2
- 210000004556 brain Anatomy 0.000 description 2
- 230000008602 contraction Effects 0.000 description 2
- 230000003205 diastolic effect Effects 0.000 description 2
- 230000009977 dual effect Effects 0.000 description 2
- 238000001125 extrusion Methods 0.000 description 2
- 208000014674 injury Diseases 0.000 description 2
- 230000008733 trauma Effects 0.000 description 2
- 210000001835 viscera Anatomy 0.000 description 2
- 206010002383 Angina Pectoris Diseases 0.000 description 1
- 206010002388 Angina unstable Diseases 0.000 description 1
- 208000007814 Unstable Angina Diseases 0.000 description 1
- 206010047281 Ventricular arrhythmia Diseases 0.000 description 1
- 208000027418 Wounds and injury Diseases 0.000 description 1
- 230000005856 abnormality Effects 0.000 description 1
- 230000009471 action Effects 0.000 description 1
- 206010000891 acute myocardial infarction Diseases 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000000747 cardiac effect Effects 0.000 description 1
- 206010007625 cardiogenic shock Diseases 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 210000000038 chest Anatomy 0.000 description 1
- 230000004087 circulation Effects 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 239000012530 fluid Substances 0.000 description 1
- 239000007789 gas Substances 0.000 description 1
- 230000010247 heart contraction Effects 0.000 description 1
- 201000004332 intermediate coronary syndrome Diseases 0.000 description 1
- 230000007774 longterm Effects 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 210000004115 mitral valve Anatomy 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 230000010016 myocardial function Effects 0.000 description 1
- 208000031225 myocardial ischemia Diseases 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
- 238000005086 pumping Methods 0.000 description 1
- 210000001562 sternum Anatomy 0.000 description 1
- 238000012360 testing method Methods 0.000 description 1
- 230000002792 vascular Effects 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
- A61M60/20—Type thereof
- A61M60/295—Balloon pumps for circulatory assistance
-
- 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
- A61M60/497—Details relating to driving for balloon pumps for circulatory assistance
-
- 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
- A61M60/50—Details relating to control
- A61M60/508—Electronic control means, e.g. for feedback regulation
- A61M60/538—Regulation using real-time blood pump operational parameter data, e.g. motor current
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- Health & Medical Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Engineering & Computer Science (AREA)
- Cardiology (AREA)
- Biomedical Technology (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 utility model discloses an implantable blood non-contact type ventricular assist device, comprising: an airbag inflation device and an airbag assembly; the air sac assembly is wrapped on the ascending aorta; the air inlet pipe is arranged on the air inlet pipe; the end part of the air inlet pipe is provided with a connector, and the connector is provided with a cover cap; the air bag inflating device is detachably connected with the connector at the end part of the air inlet pipe through the air outlet pipe. When in use, the air bag counterpulsation device is detachably connected with the connector at the end part of the air inlet pipe through the air outlet pipe; the air bag counterpulsation device inflates the air bag component in the diastole and deflates the air bag component in the systole, so that the diastolic pressure of the aorta is increased, the blood perfusion pressure of each organ is increased, and the left ventricle does work. The device is not contacted with blood after implantation, reduces the risk of infection, and has great clinical use value.
Description
Technical Field
The utility model relates to the technical field of ventricular assist devices, in particular to an implantable blood non-contact ventricular assist device.
Background
For patients with cardiac insufficiency, myocardial ischemia or acute myocardial infarction complicated with cardiogenic shock, unstable angina, sudden angina during angiocardiography, intractable ventricular arrhythmia and the need of pump function support before and after cardiac operation, ventricular assist equipment is often adopted to improve the ejection function of ventricles; at present, a commonly used ventricular assist device is mainly an intra-aortic balloon counterpulsation device, which utilizes a balloon counterpulsation device to squeeze blood in a blood vessel according to the beat of a heart through an inflatable balloon implanted in the aorta, so as to improve the intra-aortic diastolic pressure, increase coronary blood supply and improve myocardial function;
the Chinese patent publication No. CN110180043A discloses a sequential balloon counterpulsation left heart auxiliary device; the device comprises a catheter, control equipment, electrocardiograph acquisition equipment, an A balloon, a B balloon and a C balloon which are arranged in the catheter, wherein each balloon is correspondingly provided with a pump body, one end of the pump body is communicated with the balloon, the other end of the pump body is communicated with a fluid source, and the pump bodies are all connected with the control equipment; the two ends of the catheter are communicated, one end is a blood inlet end, and the other end is a bleeding end.
In the scheme, the balloon A is used for simulating a mitral valve and controlling blood flowing into a catheter, the balloon B is used for simulating a left ventricle and simulating contraction and relaxation of the left ventricle, the balloon C is used for simulating an aortic valve and controlling blood flowing out of the catheter, the balloon A and the balloon B are deflated in diastole, the blood inlet side of the catheter 1 is opened, the balloon C is inflated, the bleeding side of the catheter is closed, and the blood flows into the catheter cavity. In systole, balloon A is inflated and the blood inlet side of the catheter is closed, and balloon C is deflated and balloon B is inflated first to gradually squeeze out the blood in the catheter from the blood inlet side to the outlet side and flow into the aorta. Immediately following inflation of balloon C, balloon a and balloon B are deflated and blood is re-flowed into the catheter. The process is repeated to obtain the pulsating blood flow, and the function of assisting the heart is completed.
The balloon A, the balloon B and the balloon C in the scheme are required to be arranged inside a blood vessel, the wound on the blood vessel is large during implantation, the risk of blood infection exists during long-time use, and the safety is low.
The Chinese patent with publication number of CN207708250U discloses an auxiliary blood circulation device for heart failure, in particular to a blood suction tube for drawing blood in heart, a counterpulsation saccule mechanism for counterpulsation of aorta, a blood drawing pump for drawing blood in heart through the blood suction tube and a control mechanism for controlling the operation of the circulation device; the blood suction tube is connected and communicated with the counterpulsation sacculus mechanism, a blood output tube is connected between the counterpulsation sacculus mechanism and the blood pump, and the blood pump is also connected with a blood input tube.
In the scheme, a blood suction tube is adopted for drawing blood in the heart, a counterpulsation saccule mechanism is arranged in a descending aorta, a body surface electrocardiosignal triggers the blood suction tube for aortic counterpulsation, a blood pump sends the blood sucked in a left ventricle to a rotary pump, the blood suction can be formed by compressing the outer wall of a tube cavity and can be pushed to flow forwards, the blood suction tube is used for drawing blood in the heart, and a control mechanism controls a circulating device to work; the blood suction tube is connected and communicated with the counterpulsation sacculus mechanism, a blood output tube is connected between the counterpulsation sacculus mechanism and the blood pump, the blood pump is also connected with a blood input tube, the whole system is driven by a motor, and the integrated circuit and the electronic panel are used for controlling, so that the functions of input/output flow control, counterpulsation frequency control, pressure monitoring and the like are realized.
In the above scheme, the blood pump and the blood suction tube are in contact with blood in the heart in the blood drawing process, and the risk of blood infection still exists.
The Chinese patent publication No. CN217612491U discloses an intra-aortic dual balloon counterpulsation catheter and an intra-aortic balloon counterpulsation device, and specifically discloses a dual balloon counterpulsation catheter which comprises a catheter and two balloons axially arranged at the far end of the catheter, wherein a near-end balloon is a blocking balloon, a far-end balloon is a counterpulsation balloon, a wire guide channel and two balloon channels respectively communicated with the blocking balloon and the counterpulsation balloon are arranged in the catheter, a connector is arranged at the near end of the catheter, and interfaces correspondingly communicated with the channels are arranged on the connector.
According to the scheme, the mutually independent counterpulsation sacculus and the blocking sacculus are arranged on the catheter, and the corresponding independent sacculus channels are arranged in the catheter, so that the pumping action on heart blood discharge can be enhanced by respectively and independently inflating or exhausting the blocking sacculus and the counterpulsation sacculus at different times, the heart blood discharge amount is further increased, the left ventricular blood discharge is improved, and the specific process is as follows: at the early stage of left ventricular ejection (when an aortic valve is opened), the counterpulsation saccule is exhausted and deflated, the intra-aortic pressure is greatly reduced, and the blocking saccule is still in a filling state at the moment so as to play a role in blocking the blood at the proximal end side of the blocking saccule, so that the negative pressure generated by the deflation of the counterpulsation saccule is mainly used for sucking the blood at the aortic valve side, the resistance of heart ejection is greatly reduced, and the heart is promoted to eject more blood; at the end of left ventricular ejection, the plugging saccule is exhausted and shrunken, so that more blood is further promoted to be ejected; early left ventricular diastole (when the aortic valve is closed), counterpulsation sacculus is inflated and filled, blood supply and perfusion of the aorta to the brain and organs of the whole body are promoted, and end left ventricular diastole (before the aortic valve is opened) is inflated and filled, so that blood supply and perfusion of the aorta to the brain and organs of the whole body are further promoted.
The occlusion and counterpulsation balloons involved in the protocol require blood contact and still present a high risk of infection during long term use or surgical implantation.
Therefore, there is a need for a highly safe ventricular assist device that is atraumatic to the patient's blood vessel, does not come into contact with blood.
Disclosure of Invention
Aiming at the problems that the ventricular assist device in the prior art has great trauma to blood vessels and is used for a long time to have the risk of blood infection, the utility model provides the implantable blood non-contact ventricular assist device which is not contacted with blood after implantation, reduces the risk of infection and is safe and reliable to use.
An implantable blood non-contact ventricular assist device comprising: an air bag counterpulsation device and an air bag assembly; the air sac assembly is wrapped on the ascending aorta; the air inlet pipe is arranged on the air inlet pipe; the end part of the air inlet pipe is provided with a connector, and the connector is provided with a cover cap;
when the device is installed, the air bag component is wrapped on an ascending aorta through thoracic surgery, the air inlet pipe is buried under the skin, the joint extends out of the body, when the device is not used, the air inlet pipe is sealed through the cap, and when the device is used, the air bag counterpulsation device is detachably connected with the joint at the end part of the air inlet pipe through the air outlet pipe; the air bag counterpulsation device inflates the air bag component in the diastole and deflates the air bag component in the systole, so that the diastolic pressure of the aorta is increased, the blood perfusion pressure of each organ is increased, and the left ventricle does work.
Preferably, the airbag module includes: the inner side of the wrapping layer is provided with an air bag structure; the air bag structure is communicated with an air inlet pipe arranged outside the wrapping layer.
Preferably, the air bag structure is an integral air chamber with a wavy top, and the integral air chamber is communicated with an air inlet pipe arranged at the outer side of the wrapping layer; wherein, the wave-shaped structure is convenient for the air chamber to be distributed on the periphery of the aorta in a ring shape; the integrated air chamber has large inflation amount, is inconvenient to bend, and is suitable for thicker adult ascending aorta.
Preferably, the gasbag structure be a plurality of bottom intercommunication rectangular form air chambers of arranging in proper order, each air chamber communicates with the intake pipe that sets up in the parcel layer outside, has the clearance between the adjacent air chamber, when making things convenient for the gasbag subassembly parcel, each air chamber becomes annular distribution at the aorta periphery, because the existence of clearance, its annular structure that forms is littleer, is applicable to thinner children initiative vessel.
Preferably, the inner side of one end of the wrapping layer is provided with a fixed sleeve, and the fixed sleeve is provided with a second slot groove; the first suture slot is arranged at the position opposite to the second suture slot and positioned on the back surface of the wrapping layer; and the suture is convenient.
Preferably, the air bag counterpulsation device comprises a control terminal and an inflation and deflation assembly; the control terminal is connected with the inflation and deflation assembly, and the inflation and deflation assembly is precisely controlled to inflate and deflate the air bag assembly through the control terminal; the air bag counterpulsation device is provided with a communication interface connected with the electrocardiograph monitor; the control terminal is connected with the communication interface. Inflation and deflation of the balloon assembly is achieved by monitoring the diastolic and systolic signals with an electrocardiograph monitor.
Preferably, the inflation and deflation assembly comprises a motor and a cylinder; the bottom of the cylinder is open, a piston is arranged in the cylinder and connected with a crankshaft through a connecting rod, the crankshaft is fixed on a first gear, and the first gear is driven by a motor through a second gear; the motor rotates to drive the crankshaft and the connecting rod to move, the connecting rod drives the piston to reciprocate in the cylinder to realize inflation and deflation, the top of the cylinder is provided with a vent pipe, the vent pipe is connected with the air outlet pipe and used for realizing gas exchange between the cylinder and the air bag, and the vent pipe is provided with a pressure sensor to realize monitoring of inflation and deflation pressure; the first gear is in transmission connection with the rotary encoder, the rotating speed of the first gear can be measured through the rotary encoder, the reciprocating speed of the piston is obtained, the motor is connected with a control terminal through a speed regulator, and the control terminal is respectively and electrically connected with the pressure sensor and the rotary encoder; the speed of the reciprocating motion of the piston in the cylinder can be controlled by controlling the rotating speed of the motor through the control terminal, so that the air charging and discharging speed of the air bag component is controlled;
preferably, the diameter of the first gear is larger than that of the second gear, so that the inflation and deflation rhythms of the air bag assembly can be accurately controlled.
Compared with the prior art, the utility model has the following beneficial effects:
the device realizes regular extrusion of the ascending aorta by inflating and deflating the air bag component wrapped around the ascending aorta, namely inflating the air bag component in the diastole of the heart and deflating the air bag component in the systole of the heart, so that the diastole of the aorta is improved, the blood perfusion pressure of each viscera is increased, the work of the left ventricle is reduced, and the myocardial oxygen consumption is reduced;
compared with the balloon counterpulsation left heart auxiliary device in the prior art, the device is not contacted with blood after being implanted, has small vascular trauma to a patient, reduces the risk of infection, and is safe and reliable to use.
The air bag counterpulsation device adopted by the device controls the air cylinder to charge and discharge the air bag component through the motor, and has simple structure and reliable working process; the rhythm of inflation and deflation can be realized by controlling the rotating speed of the motor, and the control process is simple.
Drawings
FIG. 1 is a perspective view of an implantable blood non-contact ventricular assist device of the present utility model;
FIG. 2 is a perspective view of a balloon assembly in a first embodiment of an implantable blood non-contact ventricular assist device in accordance with the present utility model;
FIG. 3 is an enlarged view of a portion of the retaining sleeve of FIG. 2;
FIG. 4 is a perspective view of a balloon assembly in a second embodiment of an implantable blood non-contact ventricular assist device in accordance with the present utility model;
FIG. 5 is a schematic illustration of an implanted balloon assembly of an implantable blood non-contact ventricular assist device of the present utility model;
FIG. 6 is a view showing the internal structure of a balloon counterpulsation apparatus in an implantable blood non-contact ventricular assist device according to the present utility model;
FIG. 7 is a schematic diagram of the electrical connection of a balloon counterpulsation apparatus in an implantable blood non-contact ventricular assist device according to the present utility model;
in the figure: 1. an air bag counterpulsation device; 2. an air outlet pipe; 3. an air inlet pipe; 4. a wrapping layer; 5. a long-strip-shaped air chamber; 51. an integral air chamber; 6. a control terminal; 7. a communication interface; 8. a joint; 9. a fixed sleeve; 10. capping; 11. an electrocardiograph monitor; 12. a rotary encoder; 13. a pressure sensor; 14. a speed governor; 15. a motor; 16. a second gear; 17. a first gear; 18. a connecting rod; 19. a piston; 20. a cylinder; 21. a vent pipe; 22. a crankshaft; 401. a first suture slot; 901. a second slot groove; 100. the aorta.
Detailed Description
Figures 1-7 of the drawings in the embodiments of the utility model are described below; the technical scheme in the embodiment of the utility model is clearly and completely described:
it should be noted that, in the description of the present utility model, the terms "center", "longitudinal", "lateral", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", and the like indicate orientations or positional relationships based on the orientations or positional relationships shown in the drawings, and are merely for convenience in describing the present utility model and simplifying the description, and do not indicate or imply that the apparatus or elements referred to must have a specific orientation, be configured and operated in a specific orientation, and thus should not be construed as limiting the present utility model. Furthermore, the terms "first," "second," and the like, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first", "a second", etc. may explicitly or implicitly include one or more such feature. In the description of the present utility model, unless otherwise indicated, the meaning of "a plurality" is two or more.
In the description of the present utility model, it should be noted that, unless explicitly specified and limited otherwise, the terms "mounted," "connected," and "connected" are to be construed broadly, and may be either fixedly connected, detachably connected, or integrally connected, for example; can be mechanically or electrically connected; can be directly connected or indirectly connected through an intermediate medium, and can be communication between two elements. The specific meaning of the above terms in the present utility model can be understood by those of ordinary skill in the art in a specific case.
The utility model will be described in detail below with reference to the attached drawings and in connection with embodiments;
embodiment one:
in a first embodiment of the utility model, an implantable blood non-contact ventricular assist device comprises: an air bag counterpulsation device 1 and an air bag component; the balloon assembly is wrapped around the ascending aorta 100; the air inlet pipe 3 is arranged on the air inlet pipe; the end part of the air inlet pipe 3 is provided with a joint 8, and the joint 8 is provided with a cover cap 10;
since the ascending aorta starts from the left half rear of the sternum, the joint surface of the 3 rd chest rib starts from the left ventricle obliquely to the right upper front and continues to the right near the 2 nd chest rib joint to form an aortic arch; therefore, when the air bag component is implanted, the air bag component can be directly wrapped on the ascending aorta 100 through thoracic surgery (as shown in fig. 5), the air inlet pipe 3 is buried under the skin, the connector 8 extends out of the body, the connector 8 is provided with the cap 10, when the air bag component is not used, the air inlet pipe 3 is sealed through the cap 10, and when the air bag counterpulsation device 1 is used, the air bag counterpulsation device is connected with the connector at the end part of the air inlet pipe 3 through the air outlet pipe 2.
The air bag counterpulsation device inflates the air bag component in the diastole and deflates the air bag component in the systole of the heart, so that the diastolic pressure of the aorta is improved, the blood perfusion pressure of each organ is increased, the work of the left ventricle is reduced, and the myocardial oxygen consumption is reduced; wherein, the air bag component (shown in figures 2 and 3) comprises: the air bag comprises a wrapping layer 4, wherein a plurality of strip-shaped air chambers 5 with bottoms communicated with each other are arranged on the inner side of the wrapping layer 4, each air chamber 5 is communicated with an air inlet pipe 3 arranged on the outer side of the wrapping layer 4, gaps are arranged between the adjacent air chambers 5, and when the air bag component is wrapped conveniently, each air chamber is distributed on the periphery of an aorta in an annular mode, and due to the gaps, an annular structure formed by the air chambers is smaller and is suitable for thinner children's active vessels;
when the air bag component is specifically manufactured, the wrapping layer 4 and the air chamber 5 are made of flexible materials, wherein the air chamber 5 has certain contractility, so that the air chamber is convenient to charge and discharge air, the wrapping layer 4 can be bent, and the air chamber is convenient to wrap the outer side of an ascending aorta;
in order to facilitate the stitching of the airbag module after implantation, the inner side of one end of the wrapping layer 4 is provided with a fixing sleeve 9, the fixing sleeve 9 is provided with a stitching groove II 901, the stitching groove I401 is arranged on the back surface of the wrapping layer 4 and at the position opposite to the stitching groove II 901; when in implantation, the air sac assembly is wrapped on the outer side of the aorta, the other end of the wrapping layer 4 passes through the fixing sleeve 9 on the inner side of one end, the tightness is adjusted, and the two ends of the wrapping layer 4 are sutured along the suture groove I401 and the suture groove II 901.
Specifically, as shown in fig. 6 and 7, in order to make the balloon counterpulsation apparatus 1 accurately control the inflation and deflation of the balloon assembly according to the diastole and the systole, the balloon counterpulsation apparatus 1 comprises a control terminal 6 and an inflation and deflation assembly;
the control terminal can adopt stm32F407 as a control module of the main control CPU, and at least comprises the following peripheral equipment:
(1) A 1-path UATR interface for programming;
(2) A 1-path analog input interface, such as a 4-20mA interface, for data input of the pressure sensor;
(3) A 1-path RS232 input interface for data input of the rotary encoder;
(4) A 1-path Ethernet interface for communicating with the electrocardiograph monitor 11;
(5) A 1-path alarm control interface for controlling alarm when the inflation and deflation pressure of the air bag component is unstable;
(6) The 1-path touch screen control interface is used for connecting with a touch screen, and is convenient for controlling the device.
(7) The 1-path PWM wave output interface is used for connecting a speed regulator and controlling the rhythm of inflation and deflation;
the control terminal 6 is connected with the inflation and deflation assembly; the control terminal 6 is mainly used for monitoring the running state of the inflation and deflation assembly in the inflation and deflation process and controlling the inflation and deflation rhythm;
wherein the monitored operating conditions include:
(1) Inflation and deflation pressure: monitoring by a pressure sensor, model LFT2800;
(2) Inflation and deflation speed: model E6B2-CWZ6C was monitored by rotary encoder.
Specifically, the air bag counterpulsation device 1 is provided with a communication interface 7 (Ethernet interface) connected with an electrocardiograph monitor 11; the control terminal 6 is connected with a communication interface 7. The heart diastole and contraction signals are monitored by the electrocardiograph monitor 11 to control the inflation and deflation rhythm of the air bag component; the inflation and deflation assembly comprises a motor 15 and a cylinder 20; wherein, the motor that uses is the speed governing motor of power 90W, model: 5IK90RGN-CF;
specifically, in order to facilitate inflation and deflation of the air bag assembly, the bottom of the air cylinder 20 is opened, and the top of the air cylinder is provided with a vent hole, so that the air cylinder can conveniently extend into the actuating element from the bottom of the air cylinder to control the piston;
in the concrete implementation, a piston 19 is arranged in a cylinder 20, the piston 19 is connected with a crankshaft 22 through a connecting rod 18, the crankshaft 22 is fixed on a first gear 17, and the first gear 17 is in transmission connection with a motor 15 through a second gear 16; the motor 15 rotates to drive the crankshaft 22 and the connecting rod 18 to move, the connecting rod 18 drives the piston 19 to reciprocate in the cylinder 20, the top of the cylinder 20 is provided with the vent pipe 21, and the vent pipe 21 is connected with the air outlet pipe 2; during specific work, in the inflation process, the piston 19 moves towards the top of the air cylinder 20, and air in the extrusion air cylinder moves towards the air bag component, so that the air bag component extrudes ascending aorta after expanding, the blood perfusion pressure of each viscera is increased, and the work of the left ventricle is reduced; during the deflation process, the piston 19 moves towards the bottom of the air cylinder 20, negative pressure is formed in the air cylinder 20 to draw back the air in the air bag component, the air bag component contracts, the ascending aorta is not pressed by the air bag component any more, and the diastolic pressure is improved.
Specifically, in the process of controlling the speed of inflation and deflation through the motor 15, the control terminal 6 controls the motor 15 to rotate through the speed regulator 14, the motor 15 rotates to drive the gear II 16, the gear II 16 rotates to drive the gear I17, the transmission ratio of the gear II 16 to the movable gear I17 can be set according to the rotating speed of the motor 15 and the speed of inflation and deflation, in the actual operation process, the motor drives the piston 19 to reciprocate at a higher speed in the normal operation process, so that the inflation and deflation speed of the air bag component exceeds the normal heart rate rhythm, and therefore, the motor 15 can adjust the inflation and deflation speed of the air cylinder 20 for convenience by controlling the speed of the motor 15, and the diameter of the gear I17 is larger than that of the gear II 16.
The pressure sensor 13 is arranged on the vent pipe 21 to realize the monitoring of the inflation and deflation pressure, the pressure sensor 13 is provided with a 4-20mA analog output interface which is matched with the interface on the control terminal, the pressure value is accurately detected, and when the maximum value or the minimum value of the pressure cannot be matched with the pressure when the air bag component is inflated and deflated normally, the control terminal gives an alarm to avoid accidents;
for example, when the pressure value exceeds the maximum pressure set value during the inflation of the air bag module, at this time, the motor 15 is controlled to stop moving, and then an alarm is sent to avoid rupture of the air bag module after the air bag module receives excessive pressure;
when the pressure value is smaller than the set minimum pressure value in the air bag component air discharging process, the motor 15 is controlled to stop moving, and then an alarm is sent out, so that the influence of excessive pressure on the tightness between the piston and the air cylinder is avoided;
the first gear 17 is in transmission connection with the rotary encoder 12, the rotating speed of the first gear 17 can be measured through the rotary encoder 12, the reciprocating speed of the piston 19 is obtained, and the motor 15 is connected with the control terminal 6 through the speed regulator 14;
in specific implementation, the speed regulator 14 is provided with a PWM interface, and the current at the output end (the connection end with the motor) of the speed regulator 14 can be controlled by adjusting the duty ratio of PWM waves in specific control, so that the control of the rotating speed of the motor 15 is realized;
the control terminal 6 is respectively and electrically connected with the pressure sensor 13 and the rotary encoder 12; the speed of the reciprocating motion of the piston 19 in the cylinder 20 can be controlled by controlling the rotating speed of the motor 15 through the control terminal 6, so that the air charging and discharging speed of the air bag assembly is controlled; the diameter of the first gear 17 is larger than that of the second gear 16, so that the speed of the motor 15 is controlled, and the inflation and deflation rhythm of the air bag assembly can be accurately controlled.
Embodiment two:
in a second embodiment of the present utility model, an implantable blood non-contact ventricular assist device includes: an air bag counterpulsation device 1 and an air bag component; the balloon assembly is wrapped around the ascending aorta 100; the air inlet pipe 3 is arranged on the air inlet pipe; the end part of the air inlet pipe 3 is provided with a joint 8, and the joint 8 is provided with a cover cap 10; when the device is installed, the air bag component is wrapped on the ascending aorta 100 through thoracic surgery, the air inlet pipe 3 is buried under the skin, the joint 8 extends out of the body, the joint 8 is provided with the cap 10, when the device is not used, the air inlet pipe 3 is sealed through the cap 10, and when the device is used, the air bag counterpulsation device 1 is detachably connected with the joint at the end part of the air inlet pipe 3 through the air outlet pipe 2; the air bag counterpulsation device inflates the air bag component in the diastole and deflates the air bag component in the systole of the heart, so that the diastole pressure of the aorta is increased, the blood perfusion pressure of each organ is increased, the work of the left ventricle is reduced, and the myocardial oxygen consumption is reduced.
Wherein, the air bag module (shown in fig. 4) comprises: the inner side of the wrapping layer 4 is provided with an integral air chamber 51 with a wavy top, and the integral air chamber 51 is communicated with the air inlet pipe 3 arranged on the outer side of the wrapping layer 4.
The wave-shaped structure is easier to bend, so that the air chamber is conveniently wrapped on the periphery of the aorta in a ring shape; the integral air chamber 51 has a large inflation volume, but is inconvenient to bend and is suitable for thicker adult aorta. When in use, the air sac assembly is wrapped on the outer side of the aorta, and after the tightness is adjusted, the two ends of the wrapping layer 4 are sewed.
In order to accurately control the inflation and deflation of the balloon assembly according to the diastole and the systole of the balloon counterpulsation apparatus 1, as shown in fig. 6 and 7, the balloon counterpulsation apparatus 1 comprises a control terminal 6 (embedded processor module) and an inflation and deflation assembly; the control terminal 6 is connected with the inflation and deflation assembly, and the inflation and deflation assembly is precisely controlled to inflate and deflate the air bag assembly through the control terminal 6;
wherein, the air bag counterpulsation device 1 is provided with a communication interface 7 (RJ 45) connected with the electrocardiograph monitor 11; the control terminal 6 is connected with a communication interface 7.
The rhythm of inflation and deflation of the balloon assembly is controlled by monitoring the diastolic and systolic signals by the electrocardiograph monitor 11.
Specifically, the inflation and deflation assembly comprises a motor 15 and a cylinder 20; the bottom of the air cylinder 20 is open, a piston 19 is arranged in the air cylinder 20, the piston 19 is connected with a crankshaft 22 through a connecting rod 18, the crankshaft 22 is fixed on a first gear 17, and the first gear 17 is in transmission connection with a motor 15 through a second gear 16; the motor 15 rotates to drive the crankshaft 22 and the connecting rod 18 to move, the connecting rod 18 drives the piston 19 to reciprocate in the cylinder 20, the top of the cylinder 20 is provided with the vent pipe 21, and the vent pipe 21 is connected with the air outlet pipe 2.
In order to facilitate the pressure detection, the breather pipe 21 is provided with a pressure sensor 13.
In order to conveniently detect the speed of inflation and deflation, the first gear 17 is in transmission connection with the rotary encoder 12, the rotating speed of the first gear 17 can be measured through the rotary encoder 12, and then the reciprocating speed of the piston 19 is obtained, the motor 15 is connected with the control terminal 6 through the speed regulator 14, the control terminal 6 is respectively and electrically connected with the pressure sensor 13 and the rotary encoder 12, namely, a communication interface related to the control terminal 6 is connected with interfaces on the pressure sensor 13 and the rotary encoder 12;
specifically, the speed of the reciprocating motion of the piston 19 in the cylinder 20 can be controlled by controlling the rotating speed of the motor 15 through the control terminal 6, so that the inflation and deflation speeds of the air bag assembly are controlled; the diameter of the first gear 17 is larger than that of the second gear 16, so that the speed of the motor 15 is controlled, and the inflation and deflation rhythm of the air bag assembly can be accurately controlled.
When the two embodiments are implemented in practice, the air bag component is wrapped on the ascending aorta according to the illustration in fig. 5 through an open chest operation, the air inlet pipe 3 is buried under the skin, and the joint is exposed and connected with the air outlet pipe 2 of the air bag counterpulsation device 1; the control terminal 6 controls the rotating speed of the motor 15 through the speed regulator 14 according to the heart contraction or relaxation signals output by the electrocardiograph monitor 11, and the rotary encoder 12 is used for testing during speed regulation to realize closed-loop control, so that the air sac assembly inflation and deflation rhythm is consistent with the heart, the diastolic pressure of the aorta is improved, the blood perfusion pressure of each organ is increased, the left ventricle work is reduced, and the myocardial oxygen consumption is reduced; the pressure sensor 13 monitors the pressure change condition in real time in the operation process, and alarms through the control terminal 6 when abnormality occurs.
The foregoing description is only a preferred embodiment of the present utility model, but the scope of the present utility model is not limited thereto, and any person skilled in the art should be able to apply equivalents and modifications according to the technical scheme and the modified concept of the present utility model within the scope of the present utility model.
Claims (8)
1. An implantable blood non-contact ventricular assist device comprising: an airbag inflation device and an airbag assembly; the method is characterized in that: the air sac assembly is wrapped on the ascending aorta; the air inlet pipe is arranged on the air inlet pipe; the end part of the air inlet pipe is provided with a connector, and the connector is provided with a cover cap; the air bag inflating device is detachably connected with a connector at the end part of the air inlet pipe through an air outlet pipe; the balloon inflator inflates the balloon assembly during diastole and deflates the balloon assembly during systole.
2. An implantable blood non-contact ventricular assist device as in claim 1 wherein: the airbag module includes: the inner side of the wrapping layer is provided with an air bag structure; the air bag structure is communicated with an air inlet pipe arranged outside the wrapping layer.
3. An implantable blood non-contact ventricular assist device as in claim 1 wherein: the air bag structure is an integral air chamber with the top being wavy, and the integral air chamber is communicated with an air inlet pipe arranged on the outer side of the wrapping layer.
4. An implantable blood non-contact ventricular assist device as in claim 1 wherein: the air bag structure is a plurality of strip-shaped air chambers with mutually communicated bottoms which are sequentially arranged, each air chamber is communicated with an air inlet pipe arranged on the outer side of the wrapping layer, and gaps are formed between the adjacent air chambers.
5. An implantable blood non-contact ventricular assist device as in claim 2 wherein: the inner side of one end of the wrapping layer is provided with a fixing sleeve, and the fixing sleeve is provided with a second slot groove; the first suture slot is arranged at the position opposite to the second suture slot and positioned on the back surface of the wrapping layer.
6. An implantable blood non-contact ventricular assist device as in claim 1 wherein: the air bag counterpulsation device comprises a control terminal and an inflation and deflation assembly; the control terminal is connected with the inflation and deflation assembly, and the inflation and deflation assembly is precisely controlled to inflate and deflate the air bag assembly through the control terminal; the air bag counterpulsation device is provided with a communication interface connected with the electrocardiograph monitor; the control terminal is connected with the communication interface.
7. An implantable blood non-contact ventricular assist device as in claim 6 wherein: the inflation and deflation assembly comprises a motor and an air cylinder; the bottom of the cylinder is open, a piston is arranged in the cylinder and connected with a crankshaft through a connecting rod, the crankshaft is fixed on a first gear, and the first gear is driven by a motor through a second gear; the top of the air cylinder is provided with a vent pipe which is connected with an air outlet pipe, and a pressure sensor is arranged on the vent pipe; the first gear is in transmission connection with the rotary encoder, the motor is connected with a control terminal through a speed regulator, and the control terminal is respectively and electrically connected with the pressure sensor and the rotary encoder.
8. An implantable blood non-contact ventricular assist device as in claim 7 wherein: the diameter of the first gear is larger than that of the second gear.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311305740.1A CN117298442A (en) | 2023-10-10 | 2023-10-10 | Implantable blood non-contact type ventricular assist device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311305740.1A CN117298442A (en) | 2023-10-10 | 2023-10-10 | Implantable blood non-contact type ventricular assist device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN117298442A true CN117298442A (en) | 2023-12-29 |
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Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202311305740.1A Pending CN117298442A (en) | 2023-10-10 | 2023-10-10 | Implantable blood non-contact type ventricular assist device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN117298442A (en) |
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2023
- 2023-10-10 CN CN202311305740.1A patent/CN117298442A/en active Pending
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