CN220159038U - Circulation auxiliary device for providing pulsating blood flow - Google Patents
Circulation auxiliary device for providing pulsating blood flow Download PDFInfo
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- CN220159038U CN220159038U CN202321349312.4U CN202321349312U CN220159038U CN 220159038 U CN220159038 U CN 220159038U CN 202321349312 U CN202321349312 U CN 202321349312U CN 220159038 U CN220159038 U CN 220159038U
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- valve clack
- cavity
- catheter
- accommodating cavity
- flow path
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- 230000017531 blood circulation Effects 0.000 title claims abstract description 25
- 230000004087 circulation Effects 0.000 title abstract description 13
- 230000002457 bidirectional effect Effects 0.000 claims abstract description 12
- 230000000541 pulsatile effect Effects 0.000 claims description 7
- 239000002504 physiological saline solution Substances 0.000 claims description 3
- 239000012780 transparent material Substances 0.000 claims description 3
- 238000007789 sealing Methods 0.000 claims description 2
- 239000012528 membrane Substances 0.000 abstract description 25
- 210000004369 blood Anatomy 0.000 description 10
- 239000008280 blood Substances 0.000 description 10
- 210000003734 kidney Anatomy 0.000 description 8
- 230000000747 cardiac effect Effects 0.000 description 5
- 210000000056 organ Anatomy 0.000 description 5
- 208000011580 syndromic disease Diseases 0.000 description 5
- 230000036772 blood pressure Effects 0.000 description 4
- 206010007625 cardiogenic shock Diseases 0.000 description 4
- 210000005240 left ventricle Anatomy 0.000 description 4
- 206010019280 Heart failures Diseases 0.000 description 3
- 230000004064 dysfunction Effects 0.000 description 3
- 210000000709 aorta Anatomy 0.000 description 2
- 210000002376 aorta thoracic Anatomy 0.000 description 2
- 230000007547 defect Effects 0.000 description 2
- 238000002618 extracorporeal membrane oxygenation Methods 0.000 description 2
- 210000001105 femoral artery Anatomy 0.000 description 2
- 239000007789 gas Substances 0.000 description 2
- 230000002107 myocardial effect Effects 0.000 description 2
- 230000036284 oxygen consumption Effects 0.000 description 2
- 230000010412 perfusion Effects 0.000 description 2
- 210000005259 peripheral blood Anatomy 0.000 description 2
- 239000011886 peripheral blood Substances 0.000 description 2
- 238000005086 pumping Methods 0.000 description 2
- 206010007556 Cardiac failure acute Diseases 0.000 description 1
- 206010058558 Hypoperfusion Diseases 0.000 description 1
- 206010021143 Hypoxia Diseases 0.000 description 1
- 206010034567 Peripheral circulatory failure Diseases 0.000 description 1
- 208000001647 Renal Insufficiency Diseases 0.000 description 1
- 208000002847 Surgical Wound Diseases 0.000 description 1
- 208000007536 Thrombosis Diseases 0.000 description 1
- 206010052428 Wound Diseases 0.000 description 1
- 208000027418 Wounds and injury Diseases 0.000 description 1
- 230000001154 acute effect Effects 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000036770 blood supply Effects 0.000 description 1
- 210000005242 cardiac chamber Anatomy 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 201000010099 disease Diseases 0.000 description 1
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 230000006870 function Effects 0.000 description 1
- 208000019622 heart disease Diseases 0.000 description 1
- 230000007954 hypoxia Effects 0.000 description 1
- 238000002513 implantation Methods 0.000 description 1
- 208000028867 ischemia Diseases 0.000 description 1
- 208000017169 kidney disease Diseases 0.000 description 1
- 201000006370 kidney failure Diseases 0.000 description 1
- 230000003907 kidney function Effects 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
- 208000030159 metabolic disease Diseases 0.000 description 1
- 230000000474 nursing effect Effects 0.000 description 1
- 210000002345 respiratory system Anatomy 0.000 description 1
- 210000001835 viscera Anatomy 0.000 description 1
- 230000003313 weakening effect Effects 0.000 description 1
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- External Artificial Organs (AREA)
Abstract
The utility model discloses a circulation auxiliary device for providing pulsating blood flow, which comprises an implanted single-cavity catheter, a valve component and an external membrane type cavity, wherein the implanted single-cavity catheter comprises a first catheter and a second catheter, the valve component is connected between the first catheter and the second catheter, one end of the first catheter is provided with an inflow port and an inflow side hole, the valve component comprises a catheter body and a valve clack, the catheter wall of the catheter body is provided with an outflow window, the catheter body is hinged with the valve clack, the valve clack corresponds to the outflow window, the valve clack comprises a flow path extending side and an unconstrained side, the flow path extending side extends into a cavity of the catheter body, the horizontal distance between the hinge point of the valve clack and the unconstrained side is larger than the horizontal distance between the hinge point and the flow path extending side, the external membrane type cavity comprises an upper independent accommodating cavity and a lower independent accommodating cavity, the upper accommodating cavity and the lower accommodating cavity of the external membrane type cavity are separated by a diaphragm, the lower accommodating cavity of the external membrane type cavity is communicated with an upper pipeline joint, the lower accommodating cavity of the external membrane type cavity is communicated with a lower pipeline joint, the lower pipeline joint is connected with the second catheter, and the upper pipeline joint is communicated with a bidirectional pump.
Description
Technical Field
The utility model relates to the field of medical instrument circulation auxiliary devices, in particular to a circulation auxiliary device for providing pulsating blood flow.
Background
Serious weakening and loss of cardiac pumping function can lead to a drastic reduction in cardiac blood supply and cause acute peripheral circulatory failure, causing the patient to develop cardiogenic shock. Cardiac output cannot maintain important organs and tissues due to cardiac pumping failure of patients suffering from cardiogenic shock, and causes ischemia, hypoxia, metabolic disorder and damage to the important organs of the patient, which seriously threatens the life of the patient, and the mortality rate of the disease is reported to be as high as 70%. The circulation auxiliary device which can be implanted in a minimally invasive way and can quickly improve the blood circulation of the patient is an effective means for curing the patient suffering from the cardiogenic shock. Currently, in the field of emergency circulation assisted heart failure treatment, the application of intra-aortic balloon counterpulsation (IABP) and extracorporeal membrane oxygenator (extracorporeal membraneoxy-generation, ECMO) is relatively wide. The main defects of the IABP are insufficient auxiliary flow, and the main defects of the ECMO are thrombosis in a pump, large volume and weight of a host, inconvenience in carrying, implantation, complex nursing and the like. Therefore, the portable circulation auxiliary device which can be used in a short period and a middle period, is quickly implanted and removed through peripheral blood vessels, has sufficient auxiliary flow and has important significance.
Heart failure can cause damage not only to the circulatory and respiratory systems, but also to kidney function. The heart and kidney are important viscera of human body, heart and kidney diseases are mutually influenced to form heart-kidney syndrome, and the syndrome that the dysfunction of one organ of the heart or the kidney leads to the dysfunction of the other organ is called heart-kidney syndrome. Clinical studies indicate that about 30% of patients with acute decompensated heart failure are associated with renal insufficiency. Heart and kidney syndrome has a high rate of mortality due to dysfunction of vital organs of both heart and kidney. Heart failure results in decreased cardiac output, resulting in hypoperfusion of the kidneys.
Disclosure of Invention
The utility model aims to provide a circulation auxiliary device for providing pulsating blood flow, which can reduce left chamber load and myocardial oxygen consumption and enhance blood circulation or kidney perfusion of a patient.
In order to achieve the above purpose, the present utility model adopts the following technical scheme:
a circulation auxiliary device for providing pulsating blood flow comprises an implanted single-cavity catheter, a valve component and an external membrane type cavity, wherein the implanted single-cavity catheter comprises a first catheter and a second catheter, the valve component is connected between the first catheter and the second catheter, the free end of the first catheter is provided with an inflow port, the side wall of the first catheter close to the inflow port is provided with an inflow side hole, the valve component comprises a tube body and a valve clack, the tube wall of the tube body is provided with an outflow window, the tube body is hinged with the valve clack, the valve clack corresponds to the outflow window, the valve clack comprises an extending-in flow path side and an unconstrained side, the extending-in flow path side extends into a cavity of the tube body, so that the extending-in flow path side of the valve clack can not rotate the cavity of the tube body, the horizontal distance between the hinge point of the valve clack and the unconstrained side is larger than the horizontal distance between the hinge point and the extending-in flow path side, the external membrane type cavity comprises an upper independent accommodating cavity and a lower accommodating cavity, the upper membrane type accommodating cavity and the lower accommodating cavity are separated by a diaphragm, the upper accommodating cavity and the lower accommodating cavity are communicated with the upper accommodating cavity of the external pipeline, the lower membrane type accommodating cavity is communicated with the lower joint of the external cavity,
the lower pipeline joint is connected with the second guide channel, and the upper pipeline joint is communicated with the external bidirectional pump.
And a pressure sensor is arranged on a pipeline of the external bidirectional pump and the upper pipeline joint.
The external diaphragm type cavity comprises an upper containing shell with an upper flange plate on the circumference and a lower containing shell with a lower flange plate on the circumference, the diaphragms are pressed between the upper flange plate and the lower flange plate and are connected through bolts in a sealing mode, the upper containing shell and the lower containing shell form a spherical shell body which is made of transparent materials, the diaphragms comprise an upper flexible diaphragm and a lower flexible diaphragm, physiological saline is pre-filled between the upper flexible diaphragm and the lower flexible diaphragm, and when the upper flexible diaphragm and the lower flexible diaphragm are in an original natural state, the volume between the upper containing cavity and the upper flexible diaphragm is smaller than the volume between the lower containing cavity and the lower flexible diaphragm.
The outflow window is symmetrical along the axis direction, the bottom of the outflow window is narrow and the top is wide, two opposite pipe walls below the bottom wall of the outflow window are provided with aligned pin shaft holes, pin shafts are fixedly inserted on the two pin shaft holes, a valve clack corresponding to the outflow window is hinged on the pin shafts, the bottom of the valve clack is narrow and the top is wide, the left end wall surface of the valve clack is arc-shaped, the left end of the valve clack extends into the flow path side, the right end of the valve clack is an unconstrained side, the unconstrained side is an opening end, when blood flows in through the inflow opening on the left side of a pipe body, the valve clack closes the outflow window, the right opening end of the valve clack cannot rotate downwards, when the blood flows in the right side of the pipe body, the valve clack rotates anticlockwise to be in a vertical state around the pin shaft, and the left end surface of the valve clack is contacted with the inner wall of the pipe body, so that the blood flows out of the outflow window.
The connecting line of the central points of the two pin shaft holes is perpendicular to the axis.
The gap between the valve clack and the inner wall of the pipe body is 0.1cm.
The utility model has the beneficial effects that: the utility model is a device which is introduced from short-term, full-percutaneous and femoral artery, blood is drained and pumped back through an implanted single-cavity catheter, and the femoral artery has small wound during puncture; the left ventricle can be directly unloaded by adopting a pneumatic or hydraulic mode to pump the blood drained from the left ventricle back to the circulatory system of the human body through the valve component, and simultaneously, the pulsating blood flow is generated in the ascending aorta (or the descending aorta) so as to provide pulsating blood flow support for the circulatory system of the patient.
Drawings
In order to more clearly illustrate the embodiments of the present utility model, the present embodiments will be described below with reference to the accompanying drawings.
Fig. 1 is a schematic structural view of the present utility model (valve flap closed).
Fig. 2 is a schematic structural view of a first catheter of the present utility model.
Fig. 3 is a schematic plan view of the valve assembly of the present utility model in a closed state.
Fig. 4 is a schematic perspective view showing the closed state of the inventive assembly.
Fig. 5 is a schematic view of the valve assembly of the present utility model in an open configuration.
Fig. 6 is a schematic perspective view of the valve assembly without the valve flap and pin.
Fig. 7 is a schematic perspective view of a valve flap.
Fig. 8 is a schematic plan view of a valve flap.
Fig. 9 is a schematic structural view of an extracorporeal membrane chamber.
Fig. 10 is a schematic structural view of a diaphragm.
Detailed Description
The following examples are given to illustrate possible embodiments of the present utility model, but are not intended to limit the scope of the utility model.
As shown in fig. 1 to 9, which are preferred embodiments of the present utility model, a circulation assistance device for providing pulsatile blood flow comprises an implantable single lumen catheter 1, a valve assembly 2, an extracorporeal membrane lumen 3 and an extracorporeal bi-directional pump 4.
The implanted single-cavity catheter 1 comprises a first catheter 11 and a second catheter 12, a valve component 2 is connected between the first catheter 11 and the second catheter 12, the first catheter 11 is bent, the free end of the first catheter 11 is provided with an inflow port 111, and the side wall of the first catheter close to the inflow port is provided with an inflow side hole 112.
As shown in fig. 3 to 8, the valve assembly 2 includes a pipe body 21 and a valve flap 22, the pipe wall of the pipe body 21 is provided with an outflow window 211, the outflow window 211 is symmetrical along the axis direction, the bottom of the outflow window 211 is narrow and the top is wide, two opposite pipe walls are provided with aligned pin shaft holes 212 below the bottom wall of the outflow window, the connecting line of the central points of the two pin shaft holes is perpendicular to the axis of the pipe body, a pin shaft 20 is inserted into the two pin shaft holes 212, the pin shaft 20 is hinged with a valve flap 22 corresponding to the outflow window 211, the valve flap 22 corresponds to the outflow window 211, a gap is reserved between the valve flap 22 and the inner wall of the pipe body is 0.1cm, the valve flap 22 includes a left end extending flow path side 221 and a right end unconstrained side 222, the extending flow path side 221 extends into the hole of the pipe body, so that the extending flow path side 221 of the valve flap 22 cannot rotate, the extending path side 221 of the valve flap is close to the first conduit side, the unconstrained side is the opening end, the bottom of the valve flap is wide, the left end wall is wide and the left end wall is mounted at a horizontal distance L2 from the arc-shaped hole 223;
when the valve assembly 2 is placed in the human circulatory system: if the blood pressure P1 of the outer arc surface 223 of the valve clack 22 is higher than the blood pressure P2 of the inner arc surface 224 of the valve clack, the pressure f1= (P1-P2) ×l1 born between the flow path extending side 221 of the valve clack and the mounting hole 225, the pressure f2= (P1-P2) ×l2 born between the unconstrained side 222 of the valve clack and the mounting hole 225, the directions of the F2 and the F1 are all from the outer arc surface 223 of the valve clack to the inner arc surface 224 of the valve clack, because L2 is larger than L1 and P1 is larger than P2, F2 is larger than F1, at this time, the unconstrained side 222 of the valve clack is intended to rotate in the flow path, but the inner wall of the flow path has a limit effect on the flow path extending side of the valve clack, so the valve clack does not rotate, but keeps a closed state, so that the blood in the flow path flows along the arrow direction shown in fig. 1; if the blood pressure P1 of the flap outer arc surface 223 is lower than the blood pressure P2 of the flap inner arc surface 224, the pressure f1= (P1-P2) L1, F2 and F1 force applied between the side of the flap extending into the flow path and the pin mounting hole are all directed from the inner arc surface of the flap to the flap outer arc surface, the pressure f2= (P1-P2) L2 applied between the unconstrained side 24 of the flap and the pin mounting hole 25, and F2 is greater than F1 because L2 is greater than L1 and P1 is less than P2, at this time the flap 22 rotates in the side of the extending flow path, and the flap 22 opens, and because the structure of the flap extending into the side of the flow path is geometrically consistent with the inner wall of the flow path, blood in the flow path is blocked by the side of the flap extending into the flow path and flows out from the outflow window, as shown by the arrow in fig. 5.
As shown in fig. 9 and 10, the external membrane chamber 3 comprises an upper housing shell 31 with an upper flange plate on the circumference and a lower housing shell 31 with a lower flange plate on the circumference, the upper housing shell 31 and the lower housing shell 32 are separated into an upper housing cavity and a lower housing cavity by a membrane 33 arranged between the upper flange plate and the lower flange plate, the upper housing shell 31 and the lower housing shell 32 are connected through a bolt seal, the upper housing shell 31 and the lower housing shell 32 form a spherical housing, the lower housing shell is made of transparent materials, the volume of the lower housing shell is larger than that of the upper housing shell, the membrane 33 comprises an upper flexible membrane 331 and a lower flexible membrane 332, the upper flexible membrane and the lower flexible membrane are pre-filled with physiological saline 333, and when the upper flexible membrane and the lower flexible membrane are in an original natural state, the volume between the upper housing cavity and the upper flexible membrane is smaller than that between the lower housing cavity and the lower flexible membrane.
The upper holding shell of the external membrane cavity is communicated with an upper pipeline joint 311, the lower holding shell of the external membrane cavity is communicated with a lower pipeline joint 321, the lower pipeline joint 321 is connected with a second guide way 12, the upper pipeline joint 311 is communicated with a bidirectional pump 4, and the external bidirectional pump is in driving connection with a servo motor.
The direction of the conveying medium can be changed by controlling the conveying direction of the gas or the liquid through the external bidirectional pump, and the outlet and the inlet of the external bidirectional pump are mutually changed, so that the direction of the conveying medium is changed.
When the external bidirectional pump starts to press the flexible diaphragm of the external diaphragm type cavity without air supply, the valve clack on the valve component is closed under the action of the pressure difference between the inside and the outside of the pipe body, blood in the left ventricle flows into the lower accommodating cavity through the inlet port and the inflow side hole under the action of the pressure in the left ventricle, then the bidirectional pump positively rotates to apply work to pump air into the upper accommodating cavity, the flexible diaphragm extrudes the blood under the action of the air pressure to extrude the blood into the pipe, at the moment, the valve clack on the valve component is opened under the action of the pressure difference between the inside and the outside of the pipe body, the blood in the pipe body is discharged to the ascending aorta (or the descending aorta), and the flexible diaphragm is attached to the inner wall of the lower accommodating shell; then the bidirectional pump reversely rotates to apply work to pump out the gas in the accommodating cavity, the blood in the left heart chamber flows into the lower accommodating cavity again, and when the flexible diaphragm is attached to the inner wall of the upper accommodating shell, the bidirectional pump positively rotates to apply work to inflate, so that the air is repeatedly pumped out and inflated.
Aiming at clinical demands such as cardiogenic shock and heart kidney syndrome, the utility model aims to provide the circulation auxiliary device which can be implanted through peripheral blood vessels in a minimally invasive and rapid way and provides pulsating blood flow, so that the left chamber load and myocardial oxygen consumption are reduced, the blood circulation or kidney perfusion of a patient is enhanced, and the problems of large surgical wound, large blood damage, complex operation and portability of the traditional circulation auxiliary device are solved.
Claims (6)
1. A circulatory assist device for providing pulsatile blood flow, comprising: the valve assembly comprises a pipe body and a valve clack, an outflow window is formed in the pipe wall of the pipe body, the valve clack is hinged to the outflow window, the valve clack comprises an extending flow path side and an unconstrained side, the extending flow path side extends into the cavity of the pipe body, so that the extending flow path side of the valve clack cannot rotate the cavity of the pipe body, the extending flow path side of the valve clack is close to the first pipe side, the horizontal distance between the hinge point of the valve clack and the unconstrained side is larger than the horizontal distance between the hinge point of the valve clack and the extending flow path side, the external film type cavity comprises an upper independent accommodating cavity and a lower independent accommodating cavity, the upper accommodating cavity and the lower accommodating cavity of the film type cavity are separated by a diaphragm, the upper accommodating cavity of the film type cavity is communicated with an upper pipeline joint, the lower accommodating cavity of the film type cavity is communicated with a lower pipeline, the lower accommodating cavity is communicated with a second pipeline joint of the film type pump is connected with the external pump, and the external film type pump is connected with the external pump joint.
2. A circulatory assist device for providing pulsatile blood flow as in claim 1, wherein: and a pressure sensor is arranged on a pipeline of the external bidirectional pump and the upper pipeline joint.
3. A circulatory assist device for providing pulsatile blood flow as in claim 1, wherein: the external diaphragm type cavity comprises an upper containing shell with an upper flange plate on the circumference and a lower containing shell with a lower flange plate on the circumference, the diaphragms are pressed between the upper flange plate and the lower flange plate and are connected through bolts in a sealing mode, the upper containing shell and the lower containing shell form a spherical shell body which is made of transparent materials, the diaphragms comprise an upper flexible diaphragm and a lower flexible diaphragm, physiological saline is pre-filled between the upper flexible diaphragm and the lower flexible diaphragm, and when the upper flexible diaphragm and the lower flexible diaphragm are in an original natural state, the volume between the upper containing cavity and the upper flexible diaphragm is smaller than the volume between the lower containing cavity and the lower flexible diaphragm.
4. A circulatory assist device for providing pulsatile blood flow as in claim 1, wherein: the outflow window is symmetrical along the axis direction, the bottom of the outflow window is narrow and the top is wide, two opposite pipe walls below the bottom wall of the outflow window are provided with aligned pin shaft holes, pin shafts are fixedly inserted on the two pin shaft holes, a valve clack corresponding to the outflow window is hinged on the pin shafts, the bottom of the valve clack is narrow and the top is wide, the left end wall surface of the valve clack is arc-shaped, the left end of the valve clack extends into the flow path side, the right end of the valve clack is an unconstrained side, the unconstrained side is an opening end, when blood flows in through the inflow opening on the left side of a pipe body, the valve clack closes the outflow window, the right opening end of the valve clack cannot rotate downwards, when the blood flows in the right side of the pipe body, the valve clack rotates anticlockwise to be in a vertical state around the pin shaft, and the left end surface of the valve clack is contacted with the inner wall of the pipe body, so that the blood flows out of the outflow window.
5. A circulatory assist device for providing pulsatile blood flow as in claim 4, wherein: the connecting line of the central points of the two pin shaft holes is perpendicular to the axis.
6. A circulatory assist device for providing pulsatile blood flow as in claim 5, wherein: the gap between the valve clack and the inner wall of the pipe body is 0.1cm.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202321349312.4U CN220159038U (en) | 2023-05-30 | 2023-05-30 | Circulation auxiliary device for providing pulsating blood flow |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202321349312.4U CN220159038U (en) | 2023-05-30 | 2023-05-30 | Circulation auxiliary device for providing pulsating blood flow |
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| CN220159038U true CN220159038U (en) | 2023-12-12 |
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| Application Number | Title | Priority Date | Filing Date |
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| CN202321349312.4U Active CN220159038U (en) | 2023-05-30 | 2023-05-30 | Circulation auxiliary device for providing pulsating blood flow |
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| CN (1) | CN220159038U (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN117339098A (en) * | 2023-05-30 | 2024-01-05 | 中国医学科学院阜外医院深圳医院(深圳市孙逸仙心血管医院) | Circulation assistance device for providing pulsatile blood flow |
-
2023
- 2023-05-30 CN CN202321349312.4U patent/CN220159038U/en active Active
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN117339098A (en) * | 2023-05-30 | 2024-01-05 | 中国医学科学院阜外医院深圳医院(深圳市孙逸仙心血管医院) | Circulation assistance device for providing pulsatile blood flow |
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