CN117357727A - Pulse blood flow generating device for synchronizing cardiac cycle - Google Patents
Pulse blood flow generating device for synchronizing cardiac cycle Download PDFInfo
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- CN117357727A CN117357727A CN202311342342.7A CN202311342342A CN117357727A CN 117357727 A CN117357727 A CN 117357727A CN 202311342342 A CN202311342342 A CN 202311342342A CN 117357727 A CN117357727 A CN 117357727A
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- blood
- outer sleeve
- ecmo
- cardiac cycle
- blood flow
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- 230000017531 blood circulation Effects 0.000 title claims abstract description 36
- 230000000747 cardiac effect Effects 0.000 title claims abstract description 25
- 239000008280 blood Substances 0.000 claims abstract description 47
- 210000004369 blood Anatomy 0.000 claims abstract description 47
- 238000002618 extracorporeal membrane oxygenation Methods 0.000 claims abstract description 40
- 230000000740 bleeding effect Effects 0.000 claims abstract description 21
- 230000001360 synchronised effect Effects 0.000 claims abstract description 10
- 238000009423 ventilation Methods 0.000 claims description 21
- 230000000541 pulsatile effect Effects 0.000 claims description 5
- VYPSYNLAJGMNEJ-UHFFFAOYSA-N Silicium dioxide Chemical compound O=[Si]=O VYPSYNLAJGMNEJ-UHFFFAOYSA-N 0.000 claims description 3
- 230000036772 blood pressure Effects 0.000 claims description 3
- 239000000741 silica gel Substances 0.000 claims description 3
- 229910002027 silica gel Inorganic materials 0.000 claims description 3
- 238000010009 beating Methods 0.000 claims 1
- 238000000034 method Methods 0.000 abstract description 7
- 230000010412 perfusion Effects 0.000 abstract description 6
- 208000032843 Hemorrhage Diseases 0.000 abstract 2
- 206010028024 Mouth haemorrhage Diseases 0.000 abstract 1
- 230000001276 controlling effect Effects 0.000 description 4
- 230000007423 decrease Effects 0.000 description 4
- 210000000056 organ Anatomy 0.000 description 3
- 230000002861 ventricular Effects 0.000 description 3
- 210000002376 aorta thoracic Anatomy 0.000 description 2
- 230000008602 contraction Effects 0.000 description 2
- 210000001105 femoral artery Anatomy 0.000 description 2
- 230000002706 hydrostatic effect Effects 0.000 description 2
- 238000000338 in vitro Methods 0.000 description 2
- 208000014674 injury Diseases 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000002685 pulmonary effect Effects 0.000 description 2
- 230000001105 regulatory effect Effects 0.000 description 2
- 230000008733 trauma Effects 0.000 description 2
- 210000001835 viscera Anatomy 0.000 description 2
- 208000028399 Critical Illness Diseases 0.000 description 1
- 206010024119 Left ventricular failure Diseases 0.000 description 1
- 208000009525 Myocarditis Diseases 0.000 description 1
- 206010037423 Pulmonary oedema Diseases 0.000 description 1
- 206010049418 Sudden Cardiac Death Diseases 0.000 description 1
- 208000007536 Thrombosis Diseases 0.000 description 1
- 206010000891 acute myocardial infarction Diseases 0.000 description 1
- 230000003042 antagnostic effect Effects 0.000 description 1
- 210000000709 aorta Anatomy 0.000 description 1
- 210000001765 aortic valve Anatomy 0.000 description 1
- 206010007625 cardiogenic shock Diseases 0.000 description 1
- 230000007012 clinical effect Effects 0.000 description 1
- 238000010276 construction Methods 0.000 description 1
- 125000004122 cyclic group Chemical group 0.000 description 1
- 230000006837 decompression Effects 0.000 description 1
- 230000007812 deficiency Effects 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 238000006073 displacement reaction Methods 0.000 description 1
- 230000004064 dysfunction Effects 0.000 description 1
- 210000003191 femoral vein Anatomy 0.000 description 1
- 210000005240 left ventricle Anatomy 0.000 description 1
- 230000002107 myocardial effect Effects 0.000 description 1
- 208000005333 pulmonary edema Diseases 0.000 description 1
- 238000011084 recovery Methods 0.000 description 1
- 238000004088 simulation Methods 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 208000014221 sudden cardiac arrest Diseases 0.000 description 1
- 238000002054 transplantation Methods 0.000 description 1
Abstract
The utility model provides a synchronous heart cycle's beat blood flow generating device, connect between ECMO's bleeding mouth and arterial cannula, including the cylinder outer tube, the inside of outer tube is equipped with interior bag pipe, the both ends of outer tube are equipped with into blood check valve and bleed check valve, the entry end that goes into blood check valve links into the blood interface, go into the outlet port of blood interface connection ECMO, bleed the outlet port of check valve and connect the bleeding interface, bleeding interface connection arterial cannula is equipped with the interface of ventilating on the pipe wall of outer tube, the interface of ventilating is connected to the vent pipe of air pump, the control signal of air pump is heart cycle. The invention solves two problems of mismatching of ECMO blood flow and heart beat blood flow and poor perfusion of lower body viscerSup>A caused by IABP cannulSup>A in the V-A ECMO auxiliary process, and the device is convenient to install and simple to operate, and can generate beat blood flow of synchronous cardiac cycle by controlling air flow through IABP only by connecting the device into an ECMO pipeline, thereby being convenient for popularization and application in hospitals at all levels.
Description
Technical Field
The invention belongs to the technical field of medical appliances, and particularly relates to a pulsating blood flow generating device for synchronizing cardiac cycle, which is suitable for the process of ECMO auxiliary for left ventricular failure.
Background
ECMO (extracorporeal membrane oxygenation) is the most common mechanical circulatory assist in cases of cardiogenic shock, sudden cardiac arrest, waiting for heart transplantation, etc. caused by fulminant myocarditis, acute myocardial infarction, etc. The use of femoral vein and femoral artery cannulation to establish ECMO is common in the clinic. However, the blood flow of ECMO into the femoral artery is reversed with the blood flow during systole, competing with each other. The cyclic assistance in this mode is prone to the following deficiencies: the continuous reverse blood flow increases the left ventricle work, which is unfavorable for myocardial recovery; (II) increased left ventricular afterload and left ventricular end-diastole pressure, possibly leading to pulmonary edema; (III) patients with severe pump dysfunction require an ultra-high ECMO output flow (exceeding heart displacement 2/3), which may result in failure of the systolic aortic valve to open, and thus cause left ventricular internal thrombosis.
In critically ill patients, a better clinical effect is achieved by adopting the mode of combining ECMO with IABP. IABP works by changing blood volume and pressure in the aorta, by antagonizing the decrease in output flow of ECMO during diastole, but not directly decrease in output flow of ECMO during systole, while the implanted IABP aortic balloon increases the risk of poor perfusion of the lower body organs.
At present, the domestic device capable of generating the pulsatile blood flow is mostly realized by mode setting and rotation speed adjustment in a simulation mode, and is difficult to synchronize with the pulsatile blood flow of the cardiac cycle. However, in the ECMO assist process, synchronizing the pulsatile flow of the cardiac cycle is of great clinical significance in maintaining a high ECMO output flow during diastole and reducing ECMO output flow during systole.
Disclosure of Invention
The invention mainly solves the technical problems existing in the prior art and provides a pulse blood flow generating device for synchronizing cardiac cycles.
The technical problems of the invention are mainly solved by the following technical proposal: the pulse blood flow generating device comprises a cylindrical outer sleeve, an inner sac tube is arranged in the outer sleeve, end covers are arranged at two ends of the outer sleeve, an end cover hole is arranged at the center of the end cover, a blood inlet check valve is arranged on the end cover hole of one end cover, a blood outlet check valve is arranged on the end cover hole of the other end cover, an outlet end of the blood inlet check valve extends into the outer sleeve, an inlet end of the blood inlet check valve extends into the outer sleeve, two ends of the inner sac tube are respectively connected with the outlet end of the blood inlet check valve and the inlet end of the blood inlet check valve, the inlet end of the blood inlet check valve is connected with a blood inlet port, the blood inlet port is connected with the blood outlet port of the ECMO, the blood inlet port is connected with the arterial cannula, a ventilation port is arranged on the wall of the outer sleeve, the ventilation port is connected with a ventilation pipeline of an air pump, and a control signal of the air pump is a cardiac cycle.
Preferably, the air pump is an IABP pump and the cardiac cycle is from an electrocardiograph or a blood pressure monitor.
Preferably, the outer sleeve is made of hard plastic, the caliber of the outer sleeve is 4.8-5.2cm, the inner bag tube is made of soft silica gel and is long fusiform, the caliber of two ends of the inner bag tube is 8.7-9.8mm, the caliber of the inner bag tube is 1.4-1.6cm, and the length of the inner bag tube is 15-17cm.
Preferably, the caliber of the ventilation interface is 6-10mm, and the ventilation interface is arranged at the position which is close to one end of the blood inflow one-way valve and is 0.8-1.2cm away from the outer end of the outer sleeve, so that the ventilation interface can be prevented from being blocked when the inner bag tube is expanded, and the gas flow obstruction is avoided.
Preferably, the blood inlet connector and the bleeding connector are hard plastic round tubes, and the length of the hard plastic round tubes is 3-4cm.
The working principle of the invention is as follows: when the ventricle is in the systolic phase, the output blood flow of the heart increases, the blood flow pressure at the arterial connection side of the bleeding interface increases, and simultaneously, the cardiac cycle signal triggers the IABP pump to perform gas suction on the outer sleeve through the ventilation interface, the pressure in the outer sleeve decreases, the two jointly act to enable the bleeding check valve to be closed, the blood inlet check valve to be opened, the inner bag tube is expanded under the pressure loss, and the blood storage quantity increases. When the ventricle is in diastole, the output blood flow of the heart is reduced, the blood flow pressure at the arterial connection side of the bleeding interface is reduced, meanwhile, the cardiac cycle signal triggers the IABP pump to pressurize the gas to the outer sleeve through the ventilation interface, the pressure in the outer sleeve is increased, the two work together to open the bleeding one-way valve, the blood inlet one-way valve is closed, the inner sac tube is compressed and contracted, and the bloodflow is perfused into the viscera of the human body. The size of the inner sac tube is designed to ensure that the maximum capacity difference of the inner sac tube can reach 80ml under two states of expansion and contraction, and the requirement of each stroke volume of the heart can be met.
The invention is mainly applied to the V-A ECMO auxiliary process, effectively combines the advantages of ECMO auxiliary and IABP control, generates pulsating blood flow of synchronous cardiac cycle in Sup>A generating device, can maintain higher ECMO output flow in diastole and reduce or even block ECMO output flow in systole, thereby reducing heart and ECMO opposite impact work, reducing hydrostatic pressure of pulmonary capillaries and meeting physiological requirements.
The invention skillfully utilizes the inflation and deflation functions of the IABP pump to realize in-vitro control, does not need additional descending aorta catheterization, avoids the trauma of re-catheterization, reduces the risk of poor perfusion of lower body organs caused by the IABP catheterization, and simultaneously saves the medical cost of additional catheterization.
The invention solves two problems of mismatching of ECMO blood flow and heart beat blood flow and poor perfusion of lower body viscerSup>A caused by IABP cannulSup>A in the V-A ECMO auxiliary process, and the device is convenient to install and simple to operate, and can generate beat blood flow of synchronous cardiac cycle by controlling air flow through IABP only by connecting the device into an ECMO pipeline, thereby being convenient for popularization and application in hospitals at all levels.
The invention has the advantages that the operation mode is convenient to switch, the flow of inflation and deflation can be regulated according to specific illness states, thereby controlling the output flow of ECMO in the systolic period, and when the inflation and deflation are stopped, the ECMO can be assisted to recover to the normal mode.
Drawings
FIG. 1 is a schematic diagram of a split construction of the present invention;
FIG. 2 is a schematic illustration of a structure in which the inner bladder tube of the present invention is compressed and contracted;
FIG. 3 is a schematic illustration of a structure for decompression expansion of an inner balloon catheter according to the present invention.
In the figure, the outer sleeve is 1-, the end cover is 2-, the end cover is 3-, the ventilation port is 4-, the inner bag tube is 5-, the blood inlet port is 6-, the blood inlet one-way valve is 7-, the bleeding port is 8-and the bleeding one-way valve is 9-.
Detailed Description
The technical scheme of the invention is further specifically described below through examples and with reference to the accompanying drawings.
Examples: referring to fig. 1-3, a pulsating blood flow generating device for synchronizing cardiac cycle is connected between a bleeding port of an ECMO and an arterial cannula, and comprises a cylindrical outer sleeve, an inner sac tube is arranged in the outer sleeve, end covers are arranged at two ends of the outer sleeve, an end cover hole is arranged at the center of the end cover, a blood inlet check valve is arranged on the end cover hole of one end cover, a bleeding check valve is arranged on the end cover hole of the other end cover, the outlet port of the blood inlet check valve extends into the outer sleeve, the inlet port of the bleeding check valve extends into the outer sleeve, two ends of the inner sac tube are respectively connected with the outlet port of the blood inlet check valve and the inlet port of the bleeding check valve, the inlet port of the blood inlet check valve is connected with a blood inlet port, the outlet port of the bleeding check valve is connected with the arterial cannula, a ventilation port is arranged on the wall of the outer sleeve, the ventilation port is connected with a ventilation pipeline of an air pump, and a control signal of the air pump is cardiac cycle. The air pump is an IABP pump, and the cardiac cycle is from an electrocardiograph or a blood pressure monitor; the outer sleeve is made of hard plastic, the caliber of the outer sleeve is 4.8-5.2cm, the inner bag tube is made of soft silica gel and is long fusiform, the caliber of the two ends of the inner bag tube is 8.7-9.8mm, the caliber of the middle part of the inner bag tube is 1.4-1.6cm, and the length of the inner bag tube is 15-17cm; the caliber of the ventilation interface is 6-10mm, and the ventilation interface is arranged at the position which is close to one end of the blood inflow one-way valve and is 0.8-1.2cm away from the outer end of the outer sleeve, so that the ventilation interface can be prevented from being blocked when the inner bag tube is expanded, and gas flow obstruction is avoided; the blood inlet port and the bleeding port are hard plastic round tubes, and the length of the blood inlet port and the bleeding port is 3-4cm.
The working principle of the invention is as follows: when the ventricle is in the systolic phase, the output blood flow of the heart increases, the blood flow pressure at the arterial connection side of the bleeding interface increases, and simultaneously, the cardiac cycle signal triggers the IABP pump to perform gas suction on the outer sleeve through the ventilation interface, the pressure in the outer sleeve decreases, the two jointly act to enable the bleeding check valve to be closed, the blood inlet check valve to be opened, the inner bag tube is expanded under the pressure loss, and the blood storage quantity increases. When the ventricle is in diastole, the output blood flow of the heart is reduced, the blood flow pressure at the arterial connection side of the bleeding interface is reduced, meanwhile, the cardiac cycle signal triggers the IABP pump to pressurize the gas to the outer sleeve through the ventilation interface, the pressure in the outer sleeve is increased, the two work together to open the bleeding one-way valve, the blood inlet one-way valve is closed, the inner sac tube is compressed and contracted, and the bloodflow is perfused into the viscera of the human body. The size of the inner sac tube is designed to ensure that the maximum capacity difference of the inner sac tube can reach 80ml under two states of expansion and contraction, and the requirement of each stroke volume of the heart can be met.
The invention is mainly applied to the V-A ECMO auxiliary process, effectively combines the advantages of ECMO auxiliary and IABP control, generates pulsating blood flow of synchronous cardiac cycle in Sup>A generating device, can maintain higher ECMO output flow in diastole and reduce or even block ECMO output flow in systole, thereby reducing heart and ECMO opposite impact work, reducing hydrostatic pressure of pulmonary capillaries and meeting physiological requirements.
The invention skillfully utilizes the inflation and deflation functions of the IABP pump to realize in-vitro control, does not need additional descending aorta catheterization, avoids the trauma of re-catheterization, reduces the risk of poor perfusion of lower body organs caused by the IABP catheterization, and simultaneously saves the medical cost of additional catheterization.
The invention solves two problems of mismatching of ECMO blood flow and heart beat blood flow and poor perfusion of lower body viscerSup>A caused by IABP cannulSup>A in the V-A ECMO auxiliary process, and the device is convenient to install and simple to operate, and can generate beat blood flow of synchronous cardiac cycle by controlling air flow through IABP only by connecting the device into an ECMO pipeline, thereby being convenient for popularization and application in hospitals at all levels.
The invention has the advantages that the operation mode is convenient to switch, the flow of inflation and deflation can be regulated according to specific illness states, thereby controlling the output flow of ECMO in the systolic period, and when the inflation and deflation are stopped, the ECMO can be assisted to recover to the normal mode.
Finally, it should be noted that the above embodiments are merely representative examples of the present invention. Obviously, the invention is not limited to the above-described embodiments, but many variations are possible. Any simple modification, equivalent variation and modification of the above embodiments according to the technical substance of the present invention should be considered to be within the scope of the present invention.
Claims (5)
1. The pulse blood flow generating device comprises a cylindrical outer sleeve, and is characterized in that an inner sac tube is arranged in the outer sleeve, end covers are arranged at two ends of the outer sleeve, an end cover hole is formed in the center of the end cover, a blood inlet one-way valve is arranged on the end cover hole of one end cover, a blood outlet one-way valve is arranged on the end cover hole of the other end cover, an outlet end of the blood inlet one-way valve extends into the outer sleeve, an inlet end of the blood inlet one-way valve extends into the outer sleeve, two ends of the inner sac tube are respectively connected with the outlet end of the blood inlet one-way valve and the inlet end of the blood inlet one-way valve, the inlet end of the blood inlet one-way valve is connected with a blood inlet port, the blood inlet port is connected with a blood outlet port of the ECMO, the blood outlet port is connected with the arterial cannula, a ventilation port is arranged on the wall of the outer sleeve, the ventilation port is connected with a ventilation pipeline of an air pump, and a control signal of the air pump is a cardiac cycle.
2. The synchronized beating blood flow generating device of claim 1, wherein said air pump is an IABP pump, and said cardiac cycle is derived from an electrocardiograph or a blood pressure monitor.
3. The device for generating pulsating blood flow during synchronous cardiac cycle according to claim 1 or 2, wherein the outer sleeve is made of hard plastic, has a caliber of 4.8-5.2cm, the inner sac tube is made of soft silica gel, is long fusiform, has a caliber of 8.7-9.8mm at two ends, has a caliber of 1.4-1.6cm at the middle, and has a length of 15-17cm.
4. A synchronous cardiac cycle pulsatile flow generating device according to claim 1 or 2, characterized in that the ventilation port has a caliber of 6-10mm and is arranged at a distance of 0.8-1.2cm from the outer end of the outer sleeve near one end of the blood inflow non-return valve.
5. A synchronous cardiac cycle pulsatile flow generating device according to claim 1 or 2 and characterized in that said blood inlet and bleeding interface are rigid plastic round tubes of 3-4cm length.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311342342.7A CN117357727A (en) | 2023-10-16 | 2023-10-16 | Pulse blood flow generating device for synchronizing cardiac cycle |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311342342.7A CN117357727A (en) | 2023-10-16 | 2023-10-16 | Pulse blood flow generating device for synchronizing cardiac cycle |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN117357727A true CN117357727A (en) | 2024-01-09 |
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Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202311342342.7A Pending CN117357727A (en) | 2023-10-16 | 2023-10-16 | Pulse blood flow generating device for synchronizing cardiac cycle |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN117357727A (en) |
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2023
- 2023-10-16 CN CN202311342342.7A patent/CN117357727A/en active Pending
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