CN116099120A - Combined auxiliary treatment system for heart and kidney - Google Patents
Combined auxiliary treatment system for heart and kidney Download PDFInfo
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- CN116099120A CN116099120A CN202310145645.3A CN202310145645A CN116099120A CN 116099120 A CN116099120 A CN 116099120A CN 202310145645 A CN202310145645 A CN 202310145645A CN 116099120 A CN116099120 A CN 116099120A
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- way valve
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- valve clack
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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
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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
- A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
- A61M60/178—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart drawing blood from a ventricle and returning the blood to the arterial system via a cannula external to the ventricle, e.g. left or right ventricular assist devices
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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
- A61M60/20—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
- A61M60/30—Medical purposes thereof other than the enhancement of the cardiac output
- A61M60/31—Medical purposes thereof other than the enhancement of the cardiac output for enhancement of in vivo organ perfusion, e.g. retroperfusion
Abstract
The invention aims to provide a heart and kidney combined auxiliary treatment system capable of reducing ventricular load and generating pulsatile blood flow, which comprises a first blood circulation supporting unit positioned in a ventricle of a patient and a second blood circulation supporting unit positioned in a descending aorta of the patient, wherein the first blood circulation supporting unit pumps blood in the ventricle to the aorta, and the second blood circulation supporting unit is provided with a blood storage cavity and periodically sucks blood from the upstream of the descending aorta and discharges the blood to the downstream of the descending aorta. The two groups of blood circulation supporting units form a serial pump group, the second blood circulation supporting unit is provided with a blood storage cavity, and can periodically suck blood into the blood storage cavity and then discharge the blood, so that a sufficient pressure difference can be established between a blood inlet and a blood outlet, the rotating speed of the device in a ventricle can be effectively weakened and reduced, the hemolysis can be reduced, the heating of a motor and the non-physiological blood stress injury can be reduced, and the blood compatibility of the device can be improved.
Description
Technical Field
The invention relates to the technical field of medical equipment, in particular to a heart and kidney combined auxiliary treatment system.
Background
The occurrence of cardiovascular diseases can lead to heart failure, which is manifested by dysfunction of the systolic function and/or the diastolic function of the heart, and the venous return blood volume can not be fully discharged out of the heart, so that ventricular blood stasis is caused, and the arterial intervention type heart and kidney combined auxiliary system has insufficient blood perfusion, so that the heart blood circulation is impaired, and life hazards such as organ failure, shock and the like are caused. Currently, mechanical circulatory support devices, or blood pumps, are available that assist or replace cardiac pumping to provide life support based on hemodynamic forces for cardiogenic shock and acute heart failure. In operation of the blood pump, blood flows from the left ventricle through the aorta to the systemic organs. However, due to the special shape of the aortic arch, the blood needs to overcome the pressure difference between the left ventricle and the aortic arch to complete the blood flow discharging movement, if the pumping power of the blood pump is insufficient to support the blood to pass through the aortic arch, the phenomenon of blood reflux can occur, the ventricular pressure cannot be effectively unloaded, and the blood perfusion of the terminal organ is insufficient. Of course, when the blood pump is operated at a higher flow rate, the pressure of the heart chamber is more effectively unloaded, but the corresponding non-physiological stress damage to the blood by the device is greater.
The following technical solutions are disclosed in chinese patent application (hereinafter referred to as document 1) entitled "blood circulation assistance device and control System" (publication No. CN114259646 a): the device comprises a sheath tube and a first balloon which are arranged in a blood vessel, and a pump body arranged at the distal end of the sheath tube, wherein blood intermittently drives the first balloon to inflate and deflate in the process of flowing into the blood vessel from a ventricle under the dynamic action of the pump body, so that the inflation and deflation of the first balloon are periodically carried out, the first balloon is further enabled to periodically block and conduct the blood vessel, the blood is periodically blocked and conducted in the flowing process of the blood vessel, and the pulsating blood flow matched with the periodically diastole and systole characteristics of the heart is generated. The arrangement of the first saccule in the scheme plays a certain role in accelerating secondary blood flow, can weaken the requirement on the blood pumping capacity of the pump body to a certain extent, and reduces the requirement on the rotation speed of the pump body in the ventricle. It is known that when assisting pumping blood, a sufficient pressure difference needs to be established between the blood inlet and the blood outlet, but in document 1, since the first balloon has no tissue similar to a diaphragm, the pressure difference in the blood vessels upstream and downstream of the first balloon is small, the first balloon has limited assisting ability to pump blood, and finally, the pump body mainly relies on the ventricle to meet the blood flow requirement of the human body, so the effect of reducing the rotation speed of the pump body in the ventricle is very limited, and thus, the effects of reducing hemolysis, reducing the heating of the motor and reducing the non-physiological blood stress damage are also undesirable.
Disclosure of Invention
The invention aims to provide a heart and kidney combined auxiliary treatment system which can reduce ventricular load and generate pulsating blood flow.
In order to achieve the above purpose, the technical scheme adopted by the invention is as follows: a heart and kidney combination adjuvant therapy system includes a first blood circulation support unit located in a ventricle of a patient that pumps blood in the ventricle to the aorta and a second blood circulation support unit located in a descending aorta of the patient that has a blood storage chamber and periodically draws blood from upstream of the descending aorta and discharges blood downstream of the descending aorta.
The second blood circulation supporting unit comprises a shell, wherein a balloon is arranged in the shell, a cavity between the balloon and the balloon forms a blood storage cavity, the balloon is communicated with an external medium source through a wire tube, a first one-way valve clack is arranged at the far end of the shell, a second one-way valve clack is arranged at the near end of the shell, when the balloon is filled with a medium, the first one-way valve clack is closed, the second one-way valve clack is opened, and blood in the blood storage cavity is discharged from the second one-way valve clack to the downstream of a descending aorta; when the saccule discharges the medium, the first one-way valve clack is opened, the second one-way valve clack is closed, and blood at the upstream of the descending aorta enters the blood storage cavity from the first one-way valve clack.
The medium is gas, the balloon is deflated at the end diastole of the ventricle, and the balloon begins to inflate at the end systole/early diastole of the ventricle.
The shell comprises an expandable/contractible cage-shaped supporting frame, the periphery of the cage-shaped supporting frame is covered with a covering film, and the first one-way valve clack and the second one-way valve clack are both arranged on the covering film.
The first one-way valve clack is arranged on the inner wall of the tectorial membrane, the conduction direction of the first one-way valve clack is from the upstream of the descending aorta to the blood storage cavity, the second one-way valve clack is arranged on the outer wall of the tectorial membrane, the conduction direction of the second one-way valve clack is from the blood storage cavity to the downstream of the descending aorta, and the first one-way valve clack and the second one-way valve clack are uniformly arranged on the tectorial membrane along the circumferential direction and at intervals.
The first blood circulation support unit comprises a motor, the proximal end of the motor is connected with the catheter, the distal end of the motor is coaxially connected with the impeller, the periphery of the impeller is provided with a blood outflow cage, the distal end of the blood outflow cage is fixed with the proximal end of the blood inflow cage through the sleeve, and the distal end of the blood inflow cage is also connected with a tail pipe.
The catheter passes through the inner cavity of the shell and avoids the balloon, the proximal end of the shell is fixedly connected with the catheter, the distal end of the shell is led to the outside of the body through the sleeve, the proximal end of the balloon is connected with the wire tube, and the wire tube and the catheter are both positioned in the inner cavity of the sleeve.
The motor is provided with an optical fiber pressure sensor, a first signal wire of the optical fiber pressure sensor, the motor (a cleaning pipeline arranged at the proximal end and a PCB cable are arranged in the catheter, the balloon is also provided with an optical fiber pressure sensor, and a second signal wire of the optical fiber pressure sensor and a spool for supplying air to the balloon are arranged in a clamping cavity between the catheter and the sleeve.
The catheter is of a sectional structure, and comprises a first catheter section positioned between the motor and the balloon and a second catheter section positioned at the proximal end of the balloon and extending to the outside of the body, an inner tube is arranged in the inner cavity of the balloon, two ends of the inner tube extend to the outer parts of two ends of the balloon respectively and are connected with the first catheter section and the second catheter section respectively, and a cleaning pipeline and a PCB cable arranged at the proximal end of the motor enter the lumen of the inner tube from the inner cavity of the first catheter section and extend into the second catheter section.
The motor is provided with an optical fiber pressure sensor, a first signal wire of the optical fiber pressure sensor is consistent with the arrangement mode of the cleaning pipeline, the balloon is also provided with an optical fiber pressure sensor, and a second signal wire of the optical fiber pressure sensor and a spool tube for supplying air to the balloon are arranged in a second catheter section of the catheter.
Compared with the prior art, the invention has at least the following technical advantages and effects:
1. the two groups of blood circulation supporting units form a serial pump group, the second blood circulation supporting unit is provided with a blood storage cavity, and can periodically suck blood into the blood storage cavity and then discharge the blood, so that a sufficient pressure difference can be established between a blood inlet and a blood outlet, the rotating speed of the device in a ventricle can be effectively weakened and reduced, the hemolysis can be reduced, the heating of a motor and the non-physiological blood stress injury can be reduced, and the blood compatibility of the device can be improved.
2. The second blood circulation support unit is provided with a blood storage cavity, can periodically suck blood into the blood storage cavity and then discharge the blood, so that pulsating blood flow matched with the periodic diastole and contraction characteristics of the heart is generated, adverse effects caused by continuous blood flow generated by the traditional ventricular assist device are eliminated, simultaneously, the blood perfusion quantity of coronary artery and remote organs of a patient is improved, ventricular burden is reduced, the stability of physical signs of the patient in operation and postoperative rehabilitation are facilitated, and heart recovery of the patient is promoted.
3. The second blood circulation supporting unit generates pulsating blood flow, on the one hand, the inner wall surface of the blood vessel can be periodically washed, and the thrombus formation is reduced.
4. The medium is filled into the balloon, at the moment, the first one-way valve clack is closed and the second one-way valve clack is opened, so that when the blood in the blood storage cavity is discharged from the second one-way valve clack to the downstream of the descending aorta, the blood at the upstream of the descending aorta can not enter the blood storage cavity temporarily, and the blood supply of main organs such as heart, brain, lung and the like can be ensured to be sufficient.
5. Due to the existence of the shell, when the balloon is expanded, only the inner space of the shell is influenced, and the blood storage cavity space between the balloon and the shell is changed through the expansion and the retraction of the balloon, so that positive pressure and negative pressure states are presented, and blood is sucked and discharged; the external volume of the shell is not greatly changed, so that the blood space in the aorta is not occupied, the phenomenon that blood flows back into the left ventricle is effectively reduced, and the device is applicable to patients with aortic insufficiency.
Drawings
FIG. 1 is a schematic view of the use state of the heart and kidney combined auxiliary treatment system;
fig. 2 is a schematic structural diagram of a heart and kidney combined auxiliary treatment system;
FIG. 3 is a schematic structural view of the balloon in example 2;
FIG. 4 is a schematic view showing the structure of a first blood circulation support unit;
FIG. 5 is a cross-sectional view of the motor;
FIG. 6 is a cross-sectional view taken along the direction A-A of FIG. 2 in example 1;
FIG. 7 is a B-B cross-sectional view of FIG. 2 in example 1;
FIG. 8 is a cross-sectional view taken along the direction A-A of FIG. 2 in example 2;
fig. 9 is a B-B sectional view of fig. 2 in example 2.
Detailed Description
For ease of understanding, we first define the orientations referred to hereinafter: "proximal", "proximal" refers to the side proximal to the operator/physician and "distal" refers to the side distal to the operator/physician, i.e., the side proximal to the heart, as discussed in further detail below in connection with fig. 1-9.
A heart and kidney combination adjuvant therapy system includes a first blood circulation support unit 10 located in a ventricle of a patient, the first blood circulation support unit 10 pumping blood in the ventricle to the aorta, and a second blood circulation support unit 20 located in a descending aorta of the patient, the second blood circulation support unit 20 having a blood storage chamber and periodically drawing blood from upstream of the descending aorta and discharging blood downstream of the descending aorta.
The two sets of blood circulation support units form a series pump set, the second blood circulation support unit 20 is provided with a blood storage cavity, and can periodically suck blood into the blood storage cavity and then discharge the blood, so that a sufficient pressure difference can be established between a blood inlet and a blood outlet, the requirement of the first blood circulation support unit 10 on the blood pumping capacity can be effectively weakened, the rotating speed of a device in a ventricle is reduced, hemolysis is reduced, heating of a motor and non-physiological blood stress damage are facilitated, and the blood compatibility of the device is improved. Meanwhile, the pumping initial speed of blood is ensured by the first blood circulation supporting unit 10, and the secondary blood flow acceleration is realized by the second blood circulation supporting unit 20 positioned in the descending aorta, so that the pressure difference between the left ventricle and the aorta can be easily overcome by the blood flow, the blood flow discharging movement is completed, the ventricular load is reduced, the blood circulation of the descending aorta is improved, the ventricular pressure is effectively unloaded, the blood perfusion quantity of the terminal organs such as the kidney is increased, and the heart and kidney functions are improved.
Meanwhile, the second blood circulation support unit 20 has a blood storage chamber, and can periodically suck blood into the blood storage chamber and then discharge the blood, so that pulsating blood flow matched with the periodically diastole and systole characteristics of the heart is generated, adverse effects caused by continuous blood flow generated by the traditional ventricular assist device are eliminated, simultaneously, the blood perfusion quantity of coronary artery and remote organs of a patient is improved, ventricular load is reduced, the stability of physical signs of the patient in operation and postoperative rehabilitation are facilitated, and heart recovery of the patient is promoted.
As a preferred embodiment of the present invention, the second blood circulation support unit 20 includes a housing 21, a balloon 22 is disposed inside the housing 21, and a chamber between the two forms a blood storage chamber, the balloon 22 is communicated with an external medium source (the medium may be a liquid or a gas) through a conduit 23, a first unidirectional valve flap 24 is disposed at a distal end of the housing 21, a second unidirectional valve flap 25 is disposed at a proximal end of the housing 21, and when the balloon 22 is filled with the medium, the first unidirectional valve flap 24 is closed and the second unidirectional valve flap 25 is opened, and blood in the blood storage chamber is discharged from the second unidirectional valve flap 25 to the downstream of the descending aorta; when the balloon 22 is discharging medium, the first one-way flap 24 is opened and the second one-way flap 25 is closed, blood upstream of the descending aorta from the first one-way flap 24 into the blood storage chamber.
The first 24 and second 25 unidirectional flaps act as diaphragm tissue, thus creating a sufficient pressure differential between the blood inlet and the blood outlet to meet the auxiliary pumping requirements. When the balloon 22 discharges the medium, the balloon 22 is retracted at this time, the blood storage cavity space between the shell 21 and the balloon 22 is enlarged, and the blood is drawn from the upstream of the descending aorta in a negative pressure state, and enters the blood storage cavity from the first one-way valve clack 24 for storage (at this time, the second one-way valve clack 25 is closed); the medium is filled into the balloon 22, at this time, the balloon 22 is inflated, the blood storage cavity space between the shell 21 and the balloon 22 is compressed and is in a positive pressure state, and at this time, the first one-way valve clack 24 is closed and the second one-way valve clack 25 is opened, so that blood in the blood storage cavity can be discharged from the second one-way valve clack 25 to the downstream of the descending aorta, and the blood flow can easily overcome the pressure difference between the upstream of the descending aorta and the downstream of the descending aorta, thereby completing the blood flow discharging movement, being beneficial to reducing the ventricular load and improving the blood circulation of the aorta.
The volume of the balloon 22 is changed by flushing or discharging the medium into the balloon 22, the pressure change caused by the volume change is changed, and the pressure of the blood storage cavity is changed, so that the blood can be periodically extruded and the pulsating blood flow can be generated while the extra pumping blood energy is provided, on the one hand, the surface of the inner wall of the blood vessel can be periodically flushed, the thrombus formation is reduced, and on the other hand, the balloon 22 is filled with the medium, at the moment, the first one-way valve clack 24 is closed and the second one-way valve clack 25 is opened, so that when the blood in the blood storage cavity can be discharged from the second one-way valve clack 25 into the descending aorta, the blood at the upstream of the descending aorta can not enter the blood storage cavity temporarily, and the blood supply of main organs such as heart, brain, lung and the like can be ensured to be sufficient.
Due to the existence of the shell 21, when the balloon 22 is expanded, only the internal space of the shell 21 is influenced, and the blood storage cavity space between the balloon 22 and the shell 21 is changed through the expansion and the retraction of the balloon 22, so that positive pressure and negative pressure states are presented, and the blood is sucked and discharged; the outer volume of the housing 21 is not greatly changed, so that the blood space in the aorta is not occupied, the phenomenon that blood flows back into the left ventricle is effectively reduced, and the device is applicable to patients with the insufficiency of the aortic valve.
The heart can be mainly divided into two phases of a systolic phase and a diastolic phase in one cardiac cycle, and in the diastolic phase, the mitral valve is opened, the arterial valve is closed, and blood flows from an atrium to a ventricle to realize filling; during systole, the valve is open, the mitral valve is closed, the ventricle contracts, and the blood inside the ventricle is pumped to the arterial vessel location. The heart mainly provides kinetic energy for blood through the acting mode so as to realize the circulation of blood in the whole body. The medium is a gas and balloon 22 is deflated during ventricular end diastole and balloon 22 begins to inflate during ventricular end systole/early diastole. The inflation and deflation time of the balloon 22 is consistent with the diastole and contraction time of the heart, the pump for controlling the inflation and deflation of the balloon 22 needs to perform electrocardiographic gating, and is triggered by an electrocardiogram rising branch R wave, namely, the ventricular systole early begins to exhaust, namely, suction is performed, the ventricular diastole early begins when the T wave begins, at the moment, the arterial valve is closed to start inflation, at the moment, the arterial valve is closed, blood is discharged into an artery, the left ventricular systole process is simulated and synchronized, the left ventricular blood is assisted, and the left ventricular preload is lightened. The gas is preferably nitrogen, and the nitrogen is continuously cooled outside and then is subjected to inflation and deflation.
The housing 21 is an expandable/contractible cage-shaped supporting frame, the periphery of the cage-shaped supporting frame is covered with a covering film, and the first one-way valve clack 24 and the second one-way valve clack 25 are both arranged on the covering film. It will be appreciated that since the cage-like support frame is made of a memory metal material, it can be folded and compressed into the guide tube and can be automatically unfolded when delivered to the blood vessel, i.e. in a folded and unfolded position. Meanwhile, the covering film is a film and can deform along with the deformation of the cage-shaped supporting frame, so that the cage-shaped supporting frame can be conveyed into a blood vessel in a guide tube implantation mode.
The first one-way valve clack 24 is arranged on the inner wall of the tectorial membrane, the conduction direction of the first one-way valve clack 24 is from an arterial arch to a blood storage cavity, the second one-way valve clack 25 is arranged on the outer wall of the tectorial membrane, the conduction direction of the second one-way valve clack 25 is from the blood storage cavity to a descending aorta, and the first one-way valve clack 24 and the second one-way valve clack 25 are uniformly arranged on the tectorial membrane along the circumferential direction at intervals. When the balloon 22 is deflated, the negative pressure and the pressure of blood cooperate to automatically open the first one-way valve flap 24 and close the second one-way valve flap 25, and when the balloon 22 is inflated, the positive pressure automatically closes the first one-way valve flap 24 and opens the second one-way valve flap 25. In order to increase the flow rate of blood and also to ensure the uniformity of the drawn blood, the first and second unidirectional valve flaps 24 and 25 are uniformly and alternately arranged in the circumferential direction of the coating film.
The first blood circulation support unit 10 comprises a motor 11, a proximal end of the motor 11 is connected with a catheter 30, a distal end of the motor is coaxially connected with an impeller 12, a blood outflow cage 13 is arranged on the periphery of the impeller 12, a distal end of the blood outflow cage 13 is fixed with a proximal end of a blood inflow cage 15 through a sleeve 14, and a tail pipe 16 is further connected to the distal end of the blood inflow cage 15. The pigtail 16 is abutted against the inner wall of the ventricle to play a role in positioning, the motor 11 acts to drive the impeller 12 to rotate, blood in the ventricle is sucked from the blood inflow cage 15, enters the sleeve 14 and is discharged from the blood outflow cage 13 at the proximal end into the aorta, and auxiliary pumping is realized.
Example 1
The catheter 30 passes through the inner cavity of the shell 21 and avoids the balloon 22, the proximal end of the shell 21 is fixedly connected with the catheter 30, the distal end of the shell is communicated with the outside through the outer tube 40, the proximal end of the balloon 22 is connected with the wire tube 23, and the wire tube 23 and the catheter 30 are both positioned in the inner cavity of the outer tube 40. In this way, the catheter 30 passes directly through the clamping cavity between the housing 21 and the balloon 22, and various connecting wires are conveniently arranged, but the catheter 30 positioned in the clamping cavity can deform along with the contraction and expansion of the housing 21.
The motor 11 is provided with an optical fiber pressure sensor for detecting ventricular blood flow pressure and improving physiological information monitoring effectiveness, a first signal wire 19 of the optical fiber pressure sensor, a cleaning pipeline 17 arranged at the proximal end of the motor 11 and a PCB cable 18 are arranged in the catheter 30, the balloon 22 is also provided with an optical fiber pressure sensor for detecting blood storage cavity pressure and improving physiological information monitoring effectiveness, and a second signal wire 26 of the optical fiber pressure sensor and a conduit 23 for supplying air to the balloon 22 are arranged in a clamping cavity between the catheter 30 and the outer tube 40. Since the catheter 30 is of unitary construction and the second signal wire 26 and the conduit 23 are disposed at the proximal end of the balloon 22, an outer tube 40 is attached to the proximal end of the housing 11 to encase the catheter 30, the second signal wire 26 and the conduit 23. Of course, the catheter 30 may be omitted after extending a distance into the outer tube 40, leaving the cleaning tubing 17, PCB cable 18, first signal wire 19, second signal wire 26 and conduit 23 in the proximal outer tube 40.
Example 2
The catheter 30 is of a sectional structure, and comprises a first catheter section 31 positioned between the motor 11 and the balloon 22 and a second catheter section 32 positioned at the proximal end of the balloon 22 and extending to the outside of the body, an inner tube 27 is arranged in the inner cavity of the balloon 22, two ends of the inner tube 27 respectively extend to the outside of two ends of the balloon 22 and are respectively connected with the first catheter section 31 and the second catheter section 32, and a cleaning pipeline 17 and a PCB cable 18 arranged at the proximal end of the motor 11 enter the lumen of the inner tube 27 from the inner cavity of the first catheter section 31 and extend into the second catheter section 32. The balloon 22 is easy to shake due to fluctuation generated during inflation and deflation, however, the position of the balloon 22 is expected to be relatively fixed, so that the inner tube 27 is arranged to serve as a supporting member of the balloon 22 to limit the position of the balloon 22, and serve as a passage for the cleaning pipeline 17, the PCB cable 18 and the first signal wire 19 to pass through, and the cleaning pipeline 17, the PCB cable 18 and the first signal wire 19 cannot have any adverse effect on the inside of the balloon due to the inner tube 27, so that the normal operation of the balloon 22 is ensured.
The motor 11 is provided with an optical fiber pressure sensor for detecting the ventricular blood pressure and improving the physiological information monitoring effectiveness, the first signal line 19 of the optical fiber pressure sensor is consistent with the arrangement mode of the cleaning pipeline 17, the balloon 22 is also provided with an optical fiber pressure sensor for detecting the blood storage cavity pressure and improving the physiological information monitoring effectiveness, and the second signal line 26 of the optical fiber pressure sensor and the conduit 23 for supplying air to the balloon 22 are arranged in the second conduit section 32 of the conduit 30.
It will be understood by those skilled in the art that the present invention is not limited to the details of the foregoing exemplary embodiments, but includes other specific forms of the same or similar structures that may be embodied without departing from the spirit or essential characteristics thereof. The present embodiments are, therefore, to be considered in all respects as illustrative and not restrictive, the scope of the invention being indicated by the appended claims rather than by the foregoing description, and all changes which come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein. Any reference sign in a claim should not be construed as limiting the claim concerned.
Furthermore, it should be understood that although the present disclosure describes embodiments, not every embodiment is provided with a separate embodiment, and that this description is provided for clarity only, and that the disclosure is not limited to the embodiments described in detail below, and that the embodiments described in the examples may be combined as appropriate to form other embodiments that will be apparent to those skilled in the art.
Claims (10)
1. A combined heart and kidney adjunctive therapy system comprising a first blood circulation support unit (10) located in a ventricle of a patient and a second blood circulation support unit (20) located in a descending aorta of the patient, the first blood circulation support unit (10) pumping blood in the ventricle to the aorta, characterized in that: the second blood circulation support unit (20) has a blood storage chamber and periodically draws blood from upstream of the descending aorta and discharges blood downstream of the descending aorta.
2. A heart and kidney combination adjuvant therapy system according to claim 1, wherein: the second blood circulation support unit (20) comprises a shell (21), wherein a balloon (22) is arranged in the shell (21) and a cavity between the balloon (22) and the shell forms a blood storage cavity, the balloon (22) is communicated with an external medium source through a wire tube (23), a first one-way valve clack (24) is arranged at the far end of the shell (21), a second one-way valve clack (25) is arranged at the near end of the shell, and when the balloon (22) is filled with a medium, the first one-way valve clack (24) is closed and the second one-way valve clack (25) is opened, and blood in the blood storage cavity is discharged from the downstream of a descending aorta from the second one-way valve clack (25); when the balloon (22) discharges the medium, the first one-way valve flap (24) is opened and the second one-way valve flap (25) is closed, and blood upstream of the descending aorta enters the blood storage cavity from the first one-way valve flap (24).
3. A heart and kidney combination adjuvant therapy system according to claim 2, wherein: the medium is a gas, the balloon (22) is deflated at the end diastole of the ventricle, and the balloon (22) begins to inflate at the end systole/early diastole of the ventricle.
4. A heart and kidney combination adjuvant therapy system according to claim 2, wherein: the housing (21) comprises an expandable/contractible cage-shaped supporting frame, the periphery of the cage-shaped supporting frame is covered with a covering film, and the first one-way valve clack (24) and the second one-way valve clack (25) are both arranged on the covering film.
5. A combined heart and kidney adjunctive therapy system according to claim 3, wherein: the first one-way valve clack (24) is arranged on the inner wall of the tectorial membrane, the conducting direction of the first one-way valve clack (24) is from the upstream of the descending aorta to the blood storage cavity, the second one-way valve clack (25) is arranged on the outer wall of the tectorial membrane, the conducting direction of the second one-way valve clack (25) is from the blood storage cavity to the downstream of the descending aorta, and the first one-way valve clack (24) and the second one-way valve clack (25) are uniformly arranged on the tectorial membrane along the circumferential direction and at intervals.
6. A heart and kidney combination adjuvant therapy system according to claim 1 or 2, wherein: the first blood circulation support unit (10) comprises a motor (11), the proximal end of the motor (11) is connected with a catheter (30), the distal end of the motor is coaxially connected with an impeller (12), the periphery of the impeller (12) is provided with a blood outflow cage (13), the distal end of the blood outflow cage (13) is fixed with the proximal end of the blood inflow cage (15) through a sleeve (14), and the distal end of the blood inflow cage (15) is further connected with a pigtail tube (16).
7. A heart and kidney combination adjunctive therapy system according to claim 6, wherein: the catheter (30) passes through the inner cavity of the shell (21) and is avoided with the balloon (22), the proximal end of the shell (21) is fixedly connected with the catheter (30), the distal end of the shell is led to the outside of the body through the outer tube (40), the proximal end of the balloon (22) is connected with the wire tube (23), and the wire tube (23) and the sleeve (30) are both positioned in the inner cavity of the outer tube (40).
8. A heart and kidney combination adjuvant therapy system according to claim 7, wherein: an optical fiber pressure sensor is arranged on the motor (11), a first signal wire (19) of the optical fiber pressure sensor, a cleaning pipeline (17) arranged at the proximal end of the motor (11) and a PCB cable (18) are arranged in the catheter (30), an optical fiber pressure sensor is also arranged on the balloon (22), and a second signal wire (26) of the optical fiber pressure sensor and a wire tube (23) for supplying air to the balloon (22) are arranged in a clamping cavity between the catheter (30) and the outer tube (40).
9. A heart and kidney combination adjunctive therapy system according to claim 6, wherein: the catheter (30) is of a sectional structure, and comprises a first catheter section (31) positioned between the motor (11) and the balloon (22) and a second catheter section (32) positioned at the proximal end of the balloon (22) and extending to the outside of the body, an inner tube (27) is arranged in the inner cavity of the balloon (22), two ends of the inner tube (27) respectively extend to the outer parts of two ends of the balloon (22) and are respectively connected with the first catheter section (31) and the second catheter section (32), and a cleaning pipeline (17) and a PCB cable (18) which are arranged at the proximal end of the motor (11) enter the lumen of the inner tube (27) from the inner cavity of the first catheter section (31) and extend into the second catheter section (32).
10. A heart and kidney combination adjuvant therapy system according to claim 9, wherein: an optical fiber pressure sensor is arranged on the motor (11), a first signal wire (19) of the optical fiber pressure sensor is consistent with the arrangement mode of the cleaning pipeline (17), an optical fiber pressure sensor is also arranged on the balloon (22), and a second signal wire (26) of the optical fiber pressure sensor and a wire tube (23) for supplying air to the balloon (22) are arranged in a second conduit section (32) of the conduit (30).
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202310145645.3A CN116099120A (en) | 2023-02-15 | 2023-02-15 | Combined auxiliary treatment system for heart and kidney |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202310145645.3A CN116099120A (en) | 2023-02-15 | 2023-02-15 | Combined auxiliary treatment system for heart and kidney |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN116099120A true CN116099120A (en) | 2023-05-12 |
Family
ID=86256012
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202310145645.3A Pending CN116099120A (en) | 2023-02-15 | 2023-02-15 | Combined auxiliary treatment system for heart and kidney |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN116099120A (en) |
-
2023
- 2023-02-15 CN CN202310145645.3A patent/CN116099120A/en active Pending
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