CN113018543B - Diversion control system - Google Patents

Diversion control system Download PDF

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Publication number
CN113018543B
CN113018543B CN202110228806.6A CN202110228806A CN113018543B CN 113018543 B CN113018543 B CN 113018543B CN 202110228806 A CN202110228806 A CN 202110228806A CN 113018543 B CN113018543 B CN 113018543B
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Prior art keywords
valve
state
channel
balloon
side hole
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CN202110228806.6A
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CN113018543A (en
Inventor
李晓坤
徐玲
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Jiangsu Saiteng Medical Technology Co ltd
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Jiangsu Saiteng Medical Technology Co ltd
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Priority to CN202110228806.6A priority Critical patent/CN113018543B/en
Priority to PCT/CN2021/092296 priority patent/WO2022183590A1/en
Publication of CN113018543A publication Critical patent/CN113018543A/en
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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
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A61M1/1601—Control or regulation
    • A61M1/1603—Regulation parameters
    • 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
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A61M1/1698—Blood oxygenators with or without heat-exchangers
    • 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
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3653—Interfaces between patient blood circulation and extra-corporal blood circuit
    • A61M1/3659—Cannulae pertaining to extracorporeal circulation
    • 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
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3666—Cardiac or cardiopulmonary bypass, e.g. heart-lung machines
    • 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
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3334—Measuring or controlling the flow rate

Abstract

The disclosure relates to the technical field of fluid control, in particular to a diversion control system. The system comprises a conduit, an adjusting device, a monitoring device and a controller, wherein the conduit is provided with an outlet, an inlet and a side hole, the adjusting device comprises a moving part and a driving part, the moving part is arranged in the conduit, the driving part is connected with the moving part and the controller, the monitoring device is used for collecting the activity period of a target object, the controller controls the driving part according to the activity period, the driving part is enabled to drive the moving part to be switched between a first state and a second state, the flowing direction of fluid in a channel is ensured to be matched with the activity period of the target object, and the effect of flexibly adjusting the flow direction and the flow rate of the fluid based on the activity period of the target object is realized.

Description

Diversion control system
Technical Field
The disclosure relates to the technical field of fluid control, in particular to a diversion control system.
Background
Extracorporeal heart lung support (ECMO) is a percutaneous mechanical circulatory assist technique. An extracorporeal cardiopulmonary support assist system is generally composed of three parts, a main frame, a pump head and a membrane oxygenator. The main machine controls and monitors the operation of the cardiopulmonary support assist system, the pump head is used for circulating blood inside and outside the body, and the membrane oxygenator is used for providing oxygen and exchanging carbon dioxide in the blood discharged from the body. The extracorporeal cardiopulmonary support auxiliary system mainly drains venous blood in a patient body to the outside of the body, and the blood is oxygenated by the membrane oxygenator and carbon dioxide in the blood is removed and then returned to the patient body. Depending on the route of blood return, the cardiopulmonary support assistance system in vitro is mainly in the form of venous-venous (VV-ECMO) and venous-arterial (VA-ECMO), the former having only respiratory assistance and the latter having both circulatory and respiratory assistance.
The main problems of patients with acute heart failure are that the blood and oxygen supply of main organs including the heart is insufficient, and the insufficient oxygen supply of the heart further reduces the cardiac output to further aggravate symptoms, and finally the patients die due to exhaustion of heart energy. At present, VA-ECMO (femoral arteriovenous cannula) and IABP (Intra-Aortic Balloon Therapy) methods are generally adopted clinically for life support and improvement of heart failure. However, this method has several major drawbacks:
(1) the oxygenated blood with high oxygen content returned through the femoral artery is far away from the coronary artery inlet, which is not helpful to improve the blood oxygenation near the coronary artery inlet, so that the condition of insufficient oxygen supply of the heart cannot be improved. Also, due to the presence of the IABP balloon, it is not possible to infuse high oxygen content blood into the heart by cannulating the subclavian artery or other arterial circuits closer to the coronary portal.
(2) Due to the defect (1), when the oxygenation is insufficient due to the defect of the lung function of a patient, blood extruded into the coronary artery by the IABP balloon is blood with low oxygen content, so that the blood supply of the heart is increased, but the IABP balloon does not help to fundamentally relieve the problem of insufficient oxygen supply of the heart, and the development of the heart failure cannot be or cannot be corrected.
(3) The IABP balloon disturbs the aortic blood flow greatly, which is likely to cause poor perfusion of organs (liver, kidney) and the like, causing complications and being unfavorable for patient prognosis.
It can be seen that there is a lack of solutions in the related art to effectively solve or improve the problem of insufficient oxygen supply to the heart itself.
Disclosure of Invention
In view of the defects of the prior art, the present disclosure is directed to a diversion control system capable of flexibly adjusting the flow direction and flow rate of a fluid based on the activity period of a target object. When the medicine is used for assisting in vitro heart and lung support, the problem of insufficient oxygen supply of the heart can be solved or improved.
The present disclosure provides a flow guide control system, comprising:
the catheter comprises a catheter wall, a channel limited by the catheter wall and a side hole formed on the catheter wall, wherein one end of the channel is an inlet, the other end of the channel is an outlet, the side hole is communicated with the channel and is positioned between the inlet and the outlet,
the adjusting device comprises a movable piece and a driving piece, the movable piece is arranged in the channel, the driving piece can drive the movable piece to be in a first state or a second state, when the movable piece is in the first state, the movable piece at least partially blocks the channel to increase the amount of fluid discharged through the side hole, and when the movable piece is in the second state, the movable piece reduces the blocking of the channel to increase the amount of fluid discharged through the outlet;
the monitoring device is used for acquiring the activity period of the target object and transmitting the activity period to the controller;
the controller is connected with the driving piece, and the controller is used for controlling the driving piece to drive the movable piece to switch between a first state and a second state according to the activity period so that the flow direction of the fluid in the channel is matched with the activity of the target object.
According to the method, the activity cycle of the target object is obtained through the monitoring device, the driving piece is controlled to act according to the activity cycle of the target object, so that the moving piece is driven to switch between the first state and the second state, when the moving piece is in the first state, the moving piece at least partially blocks the channel of the guide pipe, most of fluid can be discharged through the side hole of the guide pipe, when the moving piece is in the second state, the blocking effect of the moving piece on the channel is reduced or relieved, most of fluid can be discharged through the outlet of the guide pipe, and the effect of flexibly changing the flow direction and/or flow rate of the fluid in the guide pipe according to the activity cycle of the target object is achieved.
When the flow guide control system is used for assisting in vitro cardiopulmonary support, the side hole on the catheter is pushed to a part close to a coronary artery in a blood vessel, the moving part is driven to block the catheter channel in the contraction period of the heart, oxygenated blood is forced to be perfused from the side hole to the direction of the coronary artery, the moving part is driven to remove the blockage of the catheter channel in the relaxation period of the heart, and the oxygenated blood is guided to other visceral organs, so that the blood pressure and blood flow pulsation generated by the heart pulsation are simulated, and the problem of insufficient oxygen supply of the heart is solved.
Drawings
In order to more clearly illustrate the technical solution of the present disclosure, the drawings used in the description of the embodiment or the prior art will be briefly described below. It is apparent that the drawings in the following description are only some embodiments of the disclosure, and that other drawings may be derived from those drawings by a person of ordinary skill in the art without inventive effort.
Fig. 1 is a schematic structural diagram of a diversion control system provided in an embodiment of the present disclosure;
fig. 2 is a schematic structural diagram of a flow guiding device in a first state according to an embodiment of the present disclosure;
fig. 3 is a schematic structural diagram of a flow guiding device in a second state according to an embodiment of the present disclosure;
FIG. 4 is a schematic view of a use state of the deflector apparatus shown in FIG. 2;
FIG. 5 is a schematic view of another use of the deflector device of FIG. 2;
fig. 6 is another schematic structural diagram of a flow guiding device in a first state according to an embodiment of the present disclosure;
fig. 7 is another schematic structural diagram of a flow guiding device in a second state according to an embodiment of the present disclosure;
FIG. 8 is a schematic view of a use state of the deflector device shown in FIG. 6;
FIG. 9 is a schematic view of another use of the deflector device of FIG. 6;
fig. 10 is another schematic structural diagram of a flow guiding device in a first state according to an embodiment of the present disclosure;
fig. 11 is another schematic structural diagram of a flow guiding device in a second state according to an embodiment of the present disclosure;
FIG. 12 is a schematic view of a use state of the deflector apparatus shown in FIG. 10;
fig. 13 is a schematic view of another state of use of the deflector device of fig. 10.
In the figure: 1-a diversion device, 2-a catheter, 3-a regulating device, 4-a movable member, 5-a driving member, 6-a monitoring device, 7-a controller, 8-a subclavian artery, 9-a coronary artery, 21-a vessel wall, 22-a channel, 23-an inlet, 24-an outlet, 25-a side hole, 26-a valve plate, 41-a balloon, 42-a valve, 43-an elastic member, 51-a trachea, 52-a first air source, 53-a second air source, 54-a first valve, 55-a second valve, 56-a pull rope and 57-a positioning member.
Detailed Description
In order to make the technical solutions of the present disclosure better understood by those skilled in the art, the technical solutions of the embodiments of the present disclosure will be clearly and completely described below with reference to the drawings in the embodiments of the present disclosure, and it is obvious that the described embodiments are only some embodiments of the present disclosure, not all embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments disclosed herein without making any creative effort, shall fall within the protection scope of the present disclosure.
It should be noted that the terms "first," "second," and the like in the description and claims of the present disclosure and in the drawings are used for distinguishing between similar elements and not necessarily for describing a particular sequential or chronological order. It is to be understood that the data so used is interchangeable under appropriate circumstances such that the embodiments of the disclosure described herein are capable of operation in sequences other than those illustrated or otherwise described herein. Furthermore, the terms "comprising" and "having," as well as any variations thereof, are intended to cover non-exclusive inclusions.
The main problem of patients with acute heart failure is insufficient blood and oxygen supply for organs including the heart, and the VA-ECMO combined IABP method adopted clinically at present can solve the problem of blood supply for the heart but cannot improve the problem of oxygen supply for the heart.
The key to improving the problem of cardiac oxygenation is to introduce blood with high oxygen content into the coronary arteries, and the blood oxygenated extracorporeally is higher than the arterial blood, which inevitably improves cardiac oxygenation if the extracorporeally oxygenated blood is directed into the coronary arteries. However, when the blood cannula is used for back-feeding blood, the flow rate of the blood flow is determined by the power source such as an extracorporeal blood pump and the pressure flow resistance, the blood flow direction is determined by the tube placing position, the cannula opening and the like, and the blood flow direction in the blood conveying process cannot be changed. That is, existing cannulae do not meet the need for delivering high oxygen content blood in close proximity to the coronary arteries. Therefore, the embodiment of the present disclosure provides a diversion control system, which can change the flow direction of oxygenated blood in a human body, increase blood oxygen supply to coronary arteries during cardiac ejection, increase the effect of blood oxygen supply to other organs besides cardiac ejection, simulate blood pressure and blood flow pulsation generated by cardiac pulsation, and improve or eliminate the problem of cardiac hypoxia.
Fig. 1 is a schematic structural diagram of a flow guide control system provided in an embodiment of the present disclosure. Referring to fig. 1, the diversion control system includes a catheter 2, a regulating device 3, a monitoring device 6, and a controller 7. The catheter 2 comprises a catheter wall 21, a channel 22 defined by the catheter wall 21 and a side hole 25 formed in the catheter wall 21, wherein one end of the channel 22 is an inlet 23, the other end of the channel 22 is an outlet 24, and the side hole 25 is communicated with the channel 22 and is located between the inlet 23 and the outlet 24. The adjusting device 3 comprises a movable member 4 and a driving member 5, the movable member 4 is disposed in the passage 22, the driving member 5 can drive the movable member 4 to be in a first state or a second state, when the movable member 4 is in the first state, the movable member 4 at least partially blocks the passage 22 to increase the amount of fluid discharged through the side hole 25, and when the movable member 4 is in the second state, the movable member 4 reduces the blocking of the passage 22 to increase the amount of fluid discharged through the outlet 24. The monitoring device 6 is used to acquire the activity period of the target object and transmit the activity period to the controller 7. The controller 7 is connected with the driving member 5, and the controller 7 is used for controlling the driving member 5 to drive the movable member 4 to switch between the first state and the second state according to the activity cycle, so that the flow direction of the fluid in the channel 22 is matched with the activity of the target object.
In a feasible implementation manner, the monitoring device 6 may be an electrocardiograph, and the systolic and diastolic cycles are obtained by monitoring an electrocardiograph signal of the heart.
In another possible implementation, the monitoring device 6 may include a sensor and a processor, the sensor being in communication with the processor; the sensor is arranged near the side hole 25 and used for acquiring a pressure signal of the coronary artery and transmitting the acquired pressure signal to the processor; the processor is used for extracting periodic data according to the pressure signals of the coronary artery, and taking the extracted periodic data as the activity period of the heart. Specifically, the sensor may be a pressure sensor or a pressure sensitive device (e.g., a Mems pressure sensor chip), the pressure variation data is obtained by continuously acquiring pressure values near the side hole 25, and the processor may extract the pressure variation data according to a pressure signal of the coronary artery, and determine an activity cycle of the heart according to the pressure variation data, where the pressure increase period is a contraction period of the heart and the pressure decrease period is a relaxation period of the heart. The processor can generate a pressure change curve according to the pressure change data, the pressure change curve is used for representing the change of the pressure value along with time, when the pressure change at the next moment needs to be predicted, the pressure change values at the current moment and the previous moment can be matched with the pressure value in the pressure change curve, the pressure change trend at the next moment is predicted according to the matching result, and therefore the state of the moving part is adjusted according to the pressure change trend, and the moving part can move synchronously with the cardiac ejection.
The diversion control system provided by the present disclosure can be used for in vitro cardiopulmonary support assistance to improve or solve the problem of heart failure patients with hypoxia. The method specifically comprises the following steps: connecting one end of the catheter 2 to a blood supply module, such as a membrane oxygenator, and placing the other end of the catheter 2 into the body from the subclavian artery, so that the side hole 25 on the catheter 2 is located in the aorta opposite to the heart; acquiring an activity cycle of the heart by using a monitoring device; controlling the movable member 4 in the catheter 2 to switch between a first state and a second state according to the activity cycle of the heart; when the movable element 4 is in the first state, the movable element 4 at least partially blocks the channel 22 of the catheter 2, blood oxygenated in vitro is blocked by the movable element 4 and forced to be discharged towards the side hole 25 when being injected into the body through the catheter 2, so that the amount of blood perfused to the coronary artery is increased, when the movable element 4 is in the second state, the movable element 4 reduces the blockage of the channel 22, and most oxygenated blood can be discharged from the outlet 24 of the channel 22, so that the amount of blood perfused to other organs is increased. The embodiment of the present disclosure is described by taking an example of inserting a catheter from a subclavian artery, and in practical applications, the scheme provided by the embodiment of the present disclosure can be adopted when other parts are cannulated and the blood flow direction needs to be changed. The embodiment of the disclosure alternately perfuses oxygenated blood to the heart or other organs based on the heart beat cycle, and simulates the blood pressure and blood flow beat generated by the heart beat, thereby not only improving the blood oxygen supply of the heart, but also ensuring the blood flow perfusion effect of downstream organs.
Fig. 2 and 3 show one possible configuration of the above-described catheter 2 and the adjustment device 3. Referring to fig. 2 and 3, a flow guiding device 1 is shown, wherein the flow guiding device 1 comprises a conduit 2 for guiding blood and a regulating means 3 for regulating the flow direction and/or the flow rate of the blood in the conduit 2. Wherein, the conduit 2 is made of flexible material and is a bendable hose. The catheter 2 comprises a catheter wall 21, a channel 22 defined by the catheter wall 21 and a side hole 25 formed in the catheter wall 21, wherein one end of the channel 22 is an inlet 23, the other end of the channel is an outlet 24, and the side hole 25 is communicated with the channel 22 and is positioned between the inlet 23 and the outlet 24. Alternatively, the side holes 25 may be strip-shaped holes arranged along the length of the catheter 2 to minimize the effect of the side holes 25 on the cross-section of the channel 22, ensuring that as little blood as possible leaks into the side holes 25 as it flows from the inlet 23 to the outlet 24. The adjustment device 3 may comprise a gas source, a balloon 41 and a trachea 51, the balloon 41 being arranged within the passage 22 between the outlet 24 and the side hole 25; the air source is connected with the saccule 41 through an air pipe 51 and is used for inflating or deflating the saccule 41; the balloon 41 expands after inflation to at least partially occlude the passageway 22, increasing the amount of fluid expelled through the side aperture 25, and the balloon 41 contracts after deflation to reduce the obstruction of the passageway 22, increasing the amount of fluid expelled through the outlet 24. Optionally, the gas source includes a first gas source 52 and a second gas source 53, the first gas source 52 is used for inflating the balloon 41, the second gas source 53 is used for deflating the balloon 41, the first gas source 52 may be a high pressure gas source, the second gas source 53 may be a negative pressure gas source or an atmosphere, and both the first gas source 52 and the second gas source 53 are disposed outside the channel 22. One end of the air tube 51 is connected to the balloon 41, and the other end is a branch line including a first branch tube and a second branch tube, the first branch tube is connected to the first air source 52, and the second branch tube is connected to the second air source 53. The first branch pipe is provided with a first valve 54, the second branch pipe is provided with a second valve 55, the first valve 54 is used for communicating or closing gas transmission between the first gas source 52 and the balloon 41, and the second valve 55 is used for communicating or closing gas transmission between the second gas source 53 and the balloon 41.
Further, the first valve 54 and the second valve 55 are connected to the controller 7 to control the air source to inflate or deflate the balloon 41, so as to switch the balloon 41 between the first state and the second state, wherein the controller 7 may be a solenoid valve. Specifically, under the control of the controller 7 that the first valve 54 is opened and the second valve 55 is closed, the first air source 52 inflates the balloon 41, so that the balloon 41 is inflated to block the passage 22, and at this time, the balloon 41 is in the first state, as shown in fig. 3; when the controller 7 controls the first valve 54 to be closed and the second valve 55 to be opened, the balloon 41 is connected to the outside air or a negative pressure source, and the gas in the balloon 41 is rapidly discharged due to the self-contraction force of the balloon 41 and the suction action of the negative pressure source, so that the balloon 41 is in the second state, as shown in fig. 2.
Fig. 3 and 4 show a state diagram of the use of the air guiding device 1 in fig. 2. Referring to fig. 4, the catheter is inserted from the subclavian artery 8, the side hole is stopped at the position facing the coronary artery in the aorta, during systole, the controller 7 controls the first valve 54 to open and the second valve 55 to close, the first air source 52 inflates the balloon 41, the balloon 41 inflates to block the channel 22, and blood is forced to flow from the side hole 25 to the coronary artery 9 to increase the blood oxygen supply to the heart; referring to fig. 5, during diastole, the controller 7 controls the first valve 54 to close, the second valve 55 to open, the balloon 41 to contract to reduce or eliminate obstruction of the channel 22, and blood flows from the outlet 24 of the channel 22 to organs other than the heart. In practical applications, the degree of the blockage of the channel 22 by the balloon 41 can be adjusted by controlling the inflation amount, when the balloon 41 does not completely block the channel 22, the blood can flow out from the side hole 25 and the outlet 24 at the same time, and when the balloon 41 completely blocks the channel 22, the blood can flow out from the side hole 25 only.
Fig. 6 and 7 show another possible configuration of the catheter 2 and the adjustment device 3 described above. Referring to fig. 6 and 7, a flow guiding device 1 is shown, wherein the flow guiding device 1 comprises a conduit 2 and a regulating device 3, the conduit 2 is used for guiding blood, and the regulating device 3 is used for regulating the flow direction and/or the flow rate of the blood in the conduit 2.
The catheter 2 comprises a catheter wall 21, a channel 22 limited by the catheter wall 21, a side hole 25 arranged on the catheter wall 21 and a valve plate 26 arranged near the side hole 25, wherein one end of the channel 22 is an inlet 23, the other end of the channel 22 is an outlet 24, the side hole 25 is communicated with the channel 22 and is positioned between the inlet 23 and the outlet 24, one side of the valve plate 26 is connected with the edge of the side hole 25, and the other side of the valve plate 26 is a movable side. The catheter in the disclosed embodiments is made of a flexible material that can be bent to conform to the path of a blood vessel during placement in the blood vessel.
The adjusting device 3 comprises a gas source, a balloon 41 and a trachea 51, wherein the balloon 41 is arranged in the channel 22 and is positioned between the outlet 24 and the side hole 25; a gas source is connected to the balloon 41 via a trachea 51 for inflating or deflating the balloon 41. The gas source includes a first gas source 52 for inflating the balloon 41 and a second gas source 53 for deflating the balloon 41, and specifically, the first gas source 52 may be a high-pressure gas source, and the second gas source 53 may be a negative-pressure gas source or an atmosphere. One end of the air tube 51 is connected with the balloon 41, the other end is a branch tube, the branch tube comprises a first branch tube and a second branch tube, the first branch tube is connected with the first air source 52, the second branch tube is connected with the second air source 53, and the first air source 52 and the second air source 53 are both arranged outside the channel 22. A first valve 54 is provided in the first branch and a second valve 55 is provided in the second branch, the first valve 54 being adapted to communicate/close the gas transfer between the first gas source 52 and the balloon 41, and the second valve 55 being adapted to communicate/close the gas transfer between the second gas source 53 and the balloon 41. It should be noted that the air tube 51 may be disposed along the inner wall or the outer wall of the catheter 2, and of course, the tube wall 21 of the catheter 2 may be provided with the air tube channel 22, and the catheter 2 may be inserted into the channel 22 of the catheter from the air tube channel 22, so that the inner wall of the catheter 2 may be smooth, and the obstruction of the air tube to the fluid in the channel 22 may be reduced as much as possible. Furthermore, the shape and size of the valve plate 26 are matched with the side hole 25, when the valve plate 26 blocks the side hole 25, the outer wall of the valve plate 26 is flush with the outer wall of the catheter 2, so that the blood vessel tissue is prevented from being hooked when the catheter 2 is pulled out.
In a possible realization, the valve plate 26 is connected to the edge of the lateral hole 25 by means of an elastic element. When the balloon 41 is inflated, the inflated balloon 41 blocks the channel 22 to prevent the fluid from being discharged from the outlet 24, the pressure applied by the fluid accumulated in the channel 22 to the tube wall 21 is increased, and when the pressure is larger than the supporting force of the elastic element, the movable side of the valve plate 26 deflects away from the side hole 25, and the fluid in the channel 22 is discharged from the side hole 25. When the balloon 41 is deflated, the obstruction in the channel 22 is gradually eliminated, the fluid can be smoothly discharged from the outlet 24, so that the pressure of the fluid on the tube wall 21 is reduced, the pressure applied on the valve plate 26 is also reduced, and when the pressure applied on the valve plate 26 is smaller than the supporting force of the elastic member, the elastic member drives the movable side of the valve plate 26 to close the side hole 25, so as to recover the initial position, thereby achieving the effect of automatic resetting.
The first valve 54 and the second valve 55 are both connected to the controller 7, and the controller 7 controls the opening and closing of the first valve 54 and the second valve 55 to inflate or deflate the balloon 41 to switch the balloon 41 between the first state and the second state, wherein the controller 7 may be an electromagnetic valve. Specifically, under the control of the controller 7 that the first valve 54 is opened and the second valve 55 is closed, the first air source 52 inflates the balloon 41, so that the balloon 41 is inflated to block the passage 22, and at this time, the balloon 41 is in the first state, as shown in fig. 7; when the controller 7 controls the first valve 54 to be closed and the second valve 55 to be opened, the balloon 41 is connected to the outside air or a negative pressure source, and the gas in the balloon 41 is rapidly discharged due to the self-contraction force of the balloon 41 and the suction action of the negative pressure source, so that the balloon 41 is in the second state, as shown in fig. 6.
Fig. 8 and 9 show a state diagram of the use of the air guiding device 1 in fig. 6. Referring to fig. 8, the catheter is inserted from the subclavian artery 8, the side hole is stopped at the position facing the coronary artery in the aorta, during the systole period, the controller 7 controls the first valve 54 to open and the second valve 55 to close, the first air source 52 inflates the balloon 41, the balloon 41 inflates and expands to block the channel 22, the pressure of the blood on the vessel wall 21 from the channel inlet 23 to the balloon 41 section is gradually increased along with the continuous injection of the blood, and when the pressure is greater than the supporting force of the elastic member, the valve plate 26 is opened to expose the side hole 25, so that the blood flows from the side hole 25 to the coronary artery 9 of the heart, and the blood oxygen supply of the heart is increased; referring to fig. 9, during a diastole period, the controller 7 controls the first valve 54 to close and the second valve 55 to open, the balloon 41 gradually reduces the blockage of the channel 22 along with the contraction of the balloon 41, so that blood can flow to other organs except the heart through the outlet 24 of the channel 22, the pressure of the blood on the vessel wall 21 is gradually reduced, and when the pressure is smaller than the supporting force of the elastic member, the elastic member drives the valve plate 26 to reset to block the side hole 25, and the blood is blocked from flowing out of the side hole 25. In practical applications, the degree of the blockage of the channel 22 by the balloon 41 can be adjusted by controlling the inflation amount, when the balloon 41 does not completely block the channel 22, the blood can flow out from the side hole 25 and the outlet 24 at the same time, and when the balloon 41 completely blocks the channel 22, the blood can flow out from the side hole 25 only.
In another possible implementation, the movable side of the valve plate 26 is attached to a pull cable that extends towards the entrance 23 of the channel 22. When the pull cable is in a relaxed state, the movable side of the valve plate 26 deflects away from the side opening 25, thereby opening the side opening 25 and allowing fluid to flow out of the side opening 25, and when the pull cable is in a tightened state, the movable side of the valve plate 26 abuts the side opening 25, thereby sealing the side opening 25 and preventing fluid from flowing out of the side opening 25. Specifically, when the balloon 41 is inflated and expanded, the valve plate 26 is controlled to be opened through the traction cable, so that the fluid in the channel 22 can be discharged through the side hole 25, and when the balloon 41 is deflated, the valve plate 26 is controlled to be closed through the traction cable, so that the fluid in the channel 22 is discharged from the outlet 24.
Further, the controller 7 may include a solenoid valve and a stepping motor, the first valve 54 and the second valve 55 are connected to the solenoid valve, the traction cable is connected to the stepping motor, and the solenoid valve and the stepping motor cooperate. Namely: the first valve 54 is controlled to be opened and the second valve 55 is controlled to be closed by the electromagnetic valve, the stepping motor is controlled to be reversely rotated, so that the traction cable is in a slack state, the valve plate 26 is opened at the moment, the side hole 25 is exposed, the balloon 41 is inflated by the first air source 52, the balloon 41 is inflated to be expanded to block the channel 22, the balloon 41 is in a first state (shown in fig. 8), and most of blood injected from the channel inlet 23 can flow out of the side hole 25; when the first valve 54 is controlled to be closed and the second valve 55 is controlled to be opened by the electromagnetic valve, the stepping motor is controlled to rotate forward, so that the traction cable is in a tight state, at the moment, the valve plate 26 blocks the side hole 25, the balloon 41 is connected with the external atmosphere or a negative pressure source, gas in the balloon 41 is rapidly exhausted due to the self-contraction force of the balloon 41 and the adsorption action of the negative pressure source, so that the balloon 41 is in a second state (as shown in fig. 9), and most of blood injected from the channel inlet 23 can flow out from the channel 22 outlet 24. In practical applications, the degree of the blockage of the channel 22 by the balloon 41 can be adjusted by controlling the inflation amount, when the balloon 41 does not completely block the channel 22, the blood can flow out from the side hole 25 and the outlet 24 at the same time, and when the balloon 41 completely blocks the channel 22, the blood can flow out from the side hole 25 only. In the above example, the traction cable is tightened when the stepping motor rotates forward and loosened when the stepping motor rotates backward, and in practical application, the traction cable may be tightened when the stepping motor rotates backward and loosened when the stepping motor rotates forward, which is not limited in this embodiment.
Fig. 10 and 11 show an achievable construction of the above-described catheter 2 and the adjustment device 3. Referring to fig. 10 and 11, a flow guiding device 1 is shown, which comprises a conduit 2 and an adjusting device 3, wherein the conduit 2 is made of a flexible material, and comprises a conduit wall 21, a passage 22 defined by the conduit wall 21, and a side hole 25 opened on the conduit wall 21, one end of the passage 22 is an inlet 23, and the other end is an outlet 24, and the side hole 25 is communicated with the passage 22 and is located between the inlet 23 and the outlet 24. The regulating device 3 is used to regulate the flow direction and/or the flow rate of blood in the catheter 2. The adjusting device 3 comprises a valve 42, an elastic part 43 and a guy cable 56, wherein the valve 42 is provided with an active side and a connecting side, the connecting side of the valve 42 is connected with the edge of the side hole 25 through the elastic part 43, and the active side of the valve 42 is connected with the guy cable 56; with the pull cable 56 in the tightened state, the active side of the valve 42 deflects into the channel 22 to at least partially occlude the channel 22, increasing the amount of blood expelled through the side hole 25; when the pull cord 56 is in a relaxed state, the elastic member 43 deflects the movable lateral side hole 25 of the valve 42 to at least partially occlude the side hole 25, increasing the amount of blood expelled through the outlet 24.
The valve 42 is shaped to approximate or conform to the cross-section of the passage 22 in the catheter 2, and the valve 42 is sized to be close to or larger than the cross-sectional dimension of the passage 22, so that the valve 42 has a better effect of occluding the passage 22 when deflected into the passage 22, thereby blocking the flow of blood toward the outlet 24 and forcing the blood from the side hole 25 to the coronary artery 9. The shape of the side hole 25 may be similar to or identical to the cross-section of the channel 22, such as circular or oval, and the size of the side hole 25 is not larger than that of the valve 42, so that the valve 42 has a good effect of blocking the side hole 25 and blocking the blood from flowing out of the side hole 25.
The deflection direction of the valve 42 can be controlled by the pull cable 56, in order to realize the effect of pulling the pull cable 56 to make the valve 42 block the channel 22, the pull cable 56 can be positioned at the position on the inner side of the tube wall 21 opposite to the side hole 25, so that the movable end of the valve 42 can be deflected towards the channel 22 by pulling the pull cable 56, and the effect of blocking the channel 22 is realized.
In one possible implementation, a positioning member 57 may be provided on the inner side of the vessel wall 21 opposite the side hole 25, and the connecting end of the pulling cable 56 is connected to the movable end of the valve 42 after passing through the positioning member 57. On the basis, a limiting member can be further arranged in the pipe wall 21, the pull cable 56 penetrates through the limiting member and then penetrates into the positioning member 57, and the pull cable 56 can move relative to the limiting member and the positioning member 57. The inhaul cable 56 can be close to the pipe wall 21 through the limiting piece and the positioning piece 57, the moving path of the inhaul cable 56 is limited, and therefore the resistance of the inhaul cable 56 to the fluid in the pipe is reduced.
In another possible implementation, a guide tube may be provided on the tube wall 21, the upper end of the guide tube is close to the inlet 23 of the channel 22, the lower end of the guide tube is opposite to the side hole 25, and the pull cable 56 passes through the guide tube and then is connected to the movable end of the valve 42, and the pull cable 56 can move in the guide tube. Specifically, the guide tube may be disposed inside the tube wall 21, outside the tube wall 21, or in the tube wall 21, and when disposed in the tube wall 21, the lower end of the guide tube is communicated with the passage 22, and when disposed outside the tube wall 21, a through hole needs to be formed in the tube wall 21 so that the lower end of the guide tube is communicated with the through hole.
In addition, a support may be provided on the inner side of the vessel wall 21 opposite to the side hole 25, the support being located below the positioning member 57 or the guide tube, when the pull cable 56 is in the tightened state, the movable end of the valve 42 is located between the support and the limiting member, and when fluid is accumulated between the inlet 23 and the valve 42, the support can provide a supporting force for the valve 42.
In the embodiment of the present disclosure, one end of the pulling cable 56 is a connecting end, the other end is a pulling end, the connecting end of the pulling cable 56 penetrates through the channel 22 of the catheter 2 and then is connected to the connecting side of the valve 42, the pulling end of the pulling cable 56 is disposed outside the catheter 2 and is connected to the controller 7, the controller 7 is preferably a stepping motor, and the state of the valve 42 can be adjusted by rotating the stepping motor. As shown in fig. 13, the catheter is inserted from the subclavian artery 8, the side hole is stopped at the position facing the coronary artery in the aorta, during the contraction period of the heart, the stepping motor is rotated forward, the pull cable 56 is tightened, the valve 42 is switched from the side hole 25 to the channel 22 of the catheter 2, at this time, the valve 42 is in the first state, most of the blood injected from the channel inlet 23 is blocked by the valve 42, and then flows out from the side hole 25, so as to increase the perfusion of the coronary artery 9 of the heart; as shown in fig. 12, during the diastole of the heart, the stepping motor is reversed to release the pull cable 56, the valve 42 is reset under the driving of the elastic member 43, the channel 22 of the blocking catheter 2 is switched to block the side hole 25, at this time, the valve 42 is in the second state, most of the blood injected from the channel inlet 23 can flow out from the outlet 24, and the perfusion to the gas organs except the heart is increased. In the above example, the pull cable 56 is tightened when the stepping motor rotates forward, and the pull cable 56 is loosened when the stepping motor rotates backward, and in practical application, the setting may be: the stepping motor is not limited in this embodiment, and the pull cable 56 is tightened when rotating in the reverse direction and the pull cable 56 is loosened when rotating in the forward direction.
The technical features of the above embodiments can be arbitrarily combined, and for the sake of brevity, all possible combinations of the technical features in the above embodiments are not described, but should be considered as the scope of the present specification as long as there is no contradiction between the combinations of the technical features.
The above examples only show several embodiments of the present disclosure, and the description thereof is more specific and detailed, but not construed as limiting the scope of the invention. It should be noted that, for those skilled in the art, various changes and modifications can be made without departing from the concept of the present disclosure, and these changes and modifications are all within the scope of the present disclosure. Therefore, the protection scope of the present disclosure should be subject to the appended claims.

Claims (9)

1. A diversion control system, comprising:
the catheter comprises a catheter wall, a channel limited by the catheter wall and a side hole formed on the catheter wall, wherein one end of the channel is an inlet, the other end of the channel is an outlet, the side hole is communicated with the channel and is positioned between the inlet and the outlet,
the adjusting device comprises a movable piece and a driving piece, the movable piece is arranged in the channel, the driving piece can drive the movable piece to be in a first state or a second state, when the movable piece is in the first state, the movable piece at least partially blocks the channel to increase the amount of fluid discharged through the side hole, and when the movable piece is in the second state, the movable piece reduces the blocking of the channel to increase the amount of fluid discharged through the outlet;
the monitoring device is used for acquiring the activity period of the target object and transmitting the activity period to the controller;
the controller is connected with the driving piece and used for controlling the driving piece to drive the movable piece to switch between a first state and a second state according to the activity period so that the flow direction of the fluid in the channel is matched with the activity of the target object;
the fluid is blood, the object is a heart, and the activity cycle includes a systolic period and a diastolic period of the heart.
2. The system of claim 1, wherein the side hole of the catheter is directed at a coronary artery of the heart;
the controller is configured to: and controlling the driving piece to drive the movable piece to be in the first state in the contraction period of the heart, and controlling the driving piece to drive the movable piece to be in the second state in the diastole period of the heart.
3. The system of claim 1, wherein the monitoring device is an electrocardiograph.
4. The system of claim 2, wherein the monitoring device comprises a sensor and a processor, the sensor in communication with the processor; the sensor is arranged near the side hole and used for acquiring a pressure signal of the coronary artery and transmitting the acquired pressure signal to the processor; the processor is used for extracting periodic data according to the pressure signals of the coronary arteries, and the extracted periodic data is used as the activity period of the heart.
5. The system of claim 1, wherein the moveable member is an inflatable balloon, the balloon being positioned between the side aperture and the outlet;
the driving piece comprises an air source, an air pipe and a valve, the air source is connected with the saccule through the air pipe, the valve is arranged on the air pipe, the air source is used for inflating or exhausting the saccule, and the valve is used for communicating or shutting off the air transmission between the air source and the saccule.
6. The system of claim 5, wherein the gas source comprises a first gas source for inflating the balloon and a second gas source for deflating the balloon; one end of the air pipe is connected with the balloon, and the other end of the air pipe is a branch pipeline which comprises a first branch pipe and a second branch pipe, wherein the first branch pipe is connected with the first air source, and the second branch pipe is connected with the second air source; the valves include a first valve disposed on the first branch and a second valve disposed on the second branch.
7. The system of claim 6, wherein the first valve and the second valve are each connected to the controller;
the balloon is in the first state when the controller controls the first valve to be open and the second valve to be closed; the balloon is in the second state when the controller controls the first valve to close and the second valve to open.
8. The system of claim 1, wherein the moveable member is a deflectable valve having an active side and a connecting side, the connecting side of the valve being connected to the edge of the side hole by a resilient member;
the driving piece comprises a traction cable, one end of the traction cable is connected with the movable side of the valve, and the other end of the traction cable is connected with the controller;
when the controller controls the traction cable to be in a tightened state, the traction cable drives the movable side of the valve to deflect towards the inside of the channel, so that the valve is in the first state; when the controller controls the traction cable to be in a loose state, the elastic piece drives the movable side of the valve to deflect the side hole, so that the valve is in the second state.
9. The system of claim 1, wherein the conduit is made of a flexible material.
CN202110228806.6A 2021-03-02 2021-03-02 Diversion control system Active CN113018543B (en)

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