CN218793560U - Extracorporeal lung membrane power pump and extracorporeal lung oxygenation device - Google Patents
Extracorporeal lung membrane power pump and extracorporeal lung oxygenation deviceDownload PDFInfo
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- CN218793560U CN218793560UCN202221339154.XUCN202221339154UCN218793560UCN 218793560 UCN218793560 UCN 218793560UCN 202221339154 UCN202221339154 UCN 202221339154UCN 218793560 UCN218793560 UCN 218793560U
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Abstract
Description
Technical Field
The utility model relates to the technical field of medical equipment, especially, relate to an external pulmonary membrane power pump and external pulmonary membrane oxygenation device.
Background
Extracorporeal membrane oxygenation (ECMO) is a medical emergency device that has been widely used in clinical critical emergencies for many years. The device can provide continuous external respiration and circulation for the patient to maintain life and prolong the treatment time. The ECMO has the core that an oxygen supply tube, a membrane lung oxygenator and a blood pump respectively play the roles of an artificial lung and an artificial heart, and the ECMO has the main working principle that venous blood in a patient body is led to the outside of the body to be oxygenated, and the oxygenated blood is returned to the inside of the body to be used for oxygen supply of the body, so that the ECMO can temporarily replace the function of the heart and lung to support the heart and lung of the patient with serious heart-leaf functional failure for a long time. ECMO is currently the most central support for cardiopulmonary failure. However, in the prior art, the blood pumps of the ECMO are driven by electromagnetism and rotate at a constant speed to generate advection blood flow, the blood supply mode is not in accordance with a physiological blood flow mode, and the advection blood flow is used for supplying blood for a body for a long time, so that complications such as thrombus and the like can be caused, the blood health is deteriorated, long-term adverse effects on the health of patients can be caused, and the blood pumps also comprise von willebrand disease, aortic valve insufficiency and diffuse nerve cell change in the brain.
SUMMERY OF THE UTILITY MODEL
The embodiment of the utility model provides an external pulmonary membrane power pump and external pulmonary membrane oxygenation device for ECMO adopts the centrifugal pump to produce the problem that advection blood flow influences patient's blood health among the solution prior art.
According to the utility model discloses external pulmonary membrane power pump, include:
an atrial mimic structure, an inner space being partitioned into an atrial membrane chamber having an inlet for inflow of blood and a first fluid chamber having a first communicating channel by a first inflatable membrane;
a ventricular analog structure, an inner space of which is divided into a ventricular membrane chamber and a second fluid chamber by a second expansion membrane, the ventricular membrane chamber is communicated with the atrial membrane chamber, the ventricular membrane chamber is provided with an outlet for blood to flow out, and the second fluid chamber is provided with a second communication channel; the second fluid chamber and the first fluid chamber both contain fluid;
a first actuator slidably disposed through the first communication passage to seal the first fluid chamber;
a second actuator slidably disposed through the second communication channel to seal the second fluid chamber;
and the driving piece is used for driving the first actuating piece and the second actuating piece to move.
According to some embodiments of the invention, the atrium simulation structure comprises a first structural section and a second structural section, the cross-section of the second structural section being smaller than the cross-sectional area of the first structural section, the upper end of the second structural section being connected and communicating with the lower end of the first structural section;
the first expansion membrane is arranged in the first structure section to divide the internal space of the first structure section into a first sub-cavity and a second sub-cavity which are arranged up and down, the first sub-cavity is constructed to form the atrial membrane chamber, and the second sub-cavity and the internal space of the second structure section are constructed to form the first fluid chamber;
the ventricular simulation structure comprises a third structure section and a fourth structure section, wherein the cross section of the fourth structure section is smaller than that of the third structure section, and the upper end of the fourth structure section is connected and communicated with the lower end of the third structure section;
the second expansion film is arranged in the third structure section to divide the internal space of the third structure section into a third sub-cavity and a fourth sub-cavity which are arranged from top to bottom, the third sub-cavity is formed by the structure of the third sub-cavity, and the fourth sub-cavity and the internal space of the fourth structure section are formed by the structure of the second fluid cavity.
According to some embodiments of the invention, the second structural section and the fourth structural section all extend in a vertical direction.
According to some embodiments of the invention, the atrium simulation structure has a third communication channel, one end of the third communication channel is in communication with the inlet, the other end of the third communication channel is adapted to be in communication with a membrane lung oxygenator;
the ventricle simulation structure is provided with a fourth communication channel, and one end of the fourth communication channel is communicated with the outlet;
the ventricular membrane chamber is communicated with the atrial membrane chamber through a fifth communication channel;
the third communicating channel, the fourth communicating channel and the fifth communicating channel are all provided with one-way valves.
According to some embodiments of the invention, the third communication channel, the fourth communication channel and the fifth communication channel are all provided at the top of the ventricular membrane chamber and/or the atrial membrane chamber.
According to some embodiments of the invention, the inner wall surface of the ventricular membranous cavity and the inner wall surface of the atrial membranous cavity are both provided with an anti-thrombogenic coating.
According to some embodiments of the invention, the first and second inflatable membranes are anti-thrombogenic membranes.
According to some embodiments of the invention, the driving member drives the first actuating member and the second actuating member to move based on a pulse signal.
According to some embodiments of the invention, a sealing member is provided between the first actuating member and the inner wall of the first communication passage;
and a second sealing element is arranged between the second actuating element and the inner wall of the second communication channel.
According to the utility model discloses external membrane lung oxygenation device, include:
an extracorporeal lung membrane power pump as described above;
and the membrane lung oxygenator is communicated with the inlet of the in vitro lung membrane power pump.
Adopt the embodiment of the utility model provides a, the mode through using the hydraulic pump comes the pump blood, compares in traditional blood pump, can reduce the damage to the blood cell. In addition, by arranging the double chambers of the atrial membrane chamber and the ventricular membrane chamber, the blood in the ventricular membrane chamber can be pumped into the patient, and simultaneously, the atrial membrane chamber can suck the blood oxygenated by the membrane oxygenator.
The above description is only an overview of the technical solutions of the present invention, and in order to make the technical means of the present invention more clearly understood, the present invention may be implemented according to the content of the description, and in order to make the above and other objects, features, and advantages of the present invention more obvious and understandable, the following detailed description of the present invention is given.
Drawings
Various other advantages and benefits will become apparent to those of ordinary skill in the art upon reading the following detailed description of the embodiments. The drawings are only for purposes of illustrating the preferred embodiments and are not to be construed as limiting the invention. In the drawings:
fig. 1 is a schematic structural view of an extracorporeal lung membrane power pump in an embodiment of the present invention.
Detailed Description
Exemplary embodiments of the present invention will be described in more detail below with reference to the accompanying drawings. While exemplary embodiments of the invention are shown in the drawings, it should be understood that the invention can be embodied in various forms and should not be limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art.
As shown in fig. 1, the extracorporeal pulmonary membrane power pump of the embodiment of the present invention includes: an atrial mimic structure, a ventricular mimic structure, afirst actuator 51, asecond actuator 52, and adrive member 6.
The inner space of the atrial mimic structure is separated into anatrial membrane chamber 21 and afirst fluid chamber 31 by a firstinflatable membrane 11. The interior of the atrial mimic structure forms a cavity. The firstinflatable membrane 11 is arranged inside the atrial mimic structure, the firstinflatable membrane 11 dividing the inner space of the atrial mimic structure into two separate spaces, anatrial membrane chamber 21 and afirst fluid chamber 31. Theatrial membrane chamber 21 and thefirst fluid chamber 31 are independent of each other and do not communicate with each other. The firstinflatable membrane 11 has elasticity and can expand and contract.
Theatrial membrane chamber 21 has an inlet for inflow of blood. Blood may flow from the inlet into theatrial membrane chamber 21. Thefirst fluid chamber 31 contains a fluid, i.e., a substance having fluidity, such as a gas or a liquid.
Thefirst fluid chamber 31 has afirst communication passage 41.
A ventricular mimic structure, the interior space being separated into aventricular membrane chamber 22 and asecond fluid chamber 32 by a secondinflatable membrane 12. The interior of the ventricular mimic structure is formed with a cavity. The secondinflatable membrane 12 is disposed inside the ventricular mimic structure, and the secondinflatable membrane 12 divides the interior space of the ventricular mimic structure into two separate spaces, theventricular membrane chamber 22 and thesecond fluid chamber 32. Theventricular membrane chamber 22 and thesecond fluid chamber 32 are independent of each other and do not communicate with each other. The secondinflatable membrane 12 has elasticity and can be stretched. The secondinflatable membrane 12 may be made of the same material as the firstinflatable membrane 11, but may of course be made of a different material.
Theventricular membrane chamber 22 communicates with theatrial membrane chamber 21. Blood in theatrial membrane chamber 21 may flow into theventricular membrane chamber 22.
Theventricular membrane chamber 22 has an outlet for blood to flow out. Blood within theventricular membrane chamber 22 can flow out of the outlet. Thesecond fluid chamber 32 contains a fluid, i.e., a substance having fluidity, such as a gas or a liquid. The fluid contained in thesecond fluid chamber 32 may be the same as the fluid contained in thefirst fluid chamber 31, or may be different.
Thesecond fluid chamber 32 has asecond communication passage 42.
Afirst actuator 51 is slidably disposed through thefirst communication channel 41 to seal thefirst fluid chamber 31.
Thefirst fluid chamber 31 is opened to the outside through thefirst communication passage 41, and when thefirst actuator 51 is fitted into thefirst communication passage 41 after the fluid is filled in thefirst fluid chamber 31, thefirst actuator 51 completes the sealing of thefirst fluid chamber 31, and thefirst fluid chamber 31 forms a sealed chamber. By sliding thefirst actuator 51, the pressure in thefirst fluid chamber 31, and thus the pressure in theatrial membrane chamber 21, is varied by the firstinflatable membrane 11 to control the flow of blood in theatrial membrane chamber 21 to theventricular membrane chamber 22.
Asecond actuator 52 is slidably disposed through thesecond communication channel 42 to seal thesecond fluid chamber 32.
Thesecond fluid chamber 32 is opened to the outside through thesecond communication passage 42, and when thesecond actuator 52 is fitted into thesecond communication passage 42 after the fluid is filled in thesecond fluid chamber 32, thesecond actuator 52 completes the sealing of thesecond fluid chamber 32, and thesecond fluid chamber 32 forms a sealed chamber. By sliding thesecond actuator 52, the pressure in thesecond fluid chamber 32 and thus in theventricular membrane chamber 22 via the secondinflatable membrane 12 can be varied to control the outflow of blood from theatrial membrane chamber 21 through the outlet.
Thefirst actuator 51 and thefirst fluid chamber 31 are structural elements of an atrial hydraulic blood pump.Second actuator 52 and secondfluid chamber 32 are structural components of a ventricular hydraulic blood pump.
The drivingmember 6 is used for driving thefirst actuating member 51 and thesecond actuating member 52 to move. It will be appreciated that thedriver 6 is used to provide drive signals to thefirst actuator 51 and thesecond actuator 52.
Adopt the embodiment of the utility model provides a, the mode through using the hydraulic pump comes the pump blood, compares in traditional blood pump, can reduce the damage to the blood cell. In addition, by arranging the double chambers of the atrial membrane chamber and the ventricular membrane chamber, the atrial membrane chamber can suck the blood oxygenated by the membrane oxygenator while the blood in the ventricular membrane chamber is pumped into the patient, and compared with a single chamber, the design can prevent the over-large difference between the systolic pressure and the diastolic pressure of the patient.
On the basis of the above-described embodiment, various modified embodiments are further proposed, and it is to be noted herein that, in order to make the description brief, only the differences from the above-described embodiment are described in the various modified embodiments.
As shown in fig. 1, according to some embodiments of the present invention, the atrium simulation structure comprises a first structural section and a second structural section, the second structural section having a cross-sectional area smaller than the cross-sectional area of the first structural section, the upper end of the second structural section being connected to and communicating with the lower end of the first structural section;
thefirst expansion membrane 11 is arranged in the first structure section to divide the internal space of the first structure section into a first sub-cavity and a second sub-cavity which are arranged up and down, the first sub-cavity is configured to form theatrial membrane chamber 21, and the second sub-cavity and the internal space of the second structure section are configured to form thefirst fluid chamber 31; the second structural section is configured to form afirst communication channel 41.
The ventricular simulation structure comprises a third structure section and a fourth structure section, wherein the cross section of the fourth structure section is smaller than that of the third structure section, and the upper end of the fourth structure section is connected and communicated with the lower end of the third structure section;
thesecond expansion film 12 is disposed in the third structure section to divide the internal space of the third structure section into a third sub-chamber and a fourth sub-chamber arranged from top to bottom, the third sub-chamber is configured to form theventricular membrane chamber 22, and the fourth sub-chamber and the internal space of the fourth structure section are configured to form thesecond fluid chamber 32. The fourth structural section is configured to form asecond communication channel 42.
As shown in fig. 1, according to some embodiments of the invention, the second structural section and the fourth structural section both extend in a vertical direction.
Under the action of the first actuating member and the second actuating member without power driving, the fluid in the first fluid cavity and the fluid in the second fluid cavity, the first actuating member and the second actuating member slide downwards under the action of self gravity, the pressure in the atrial membrane cavity and the pressure in the ventricular membrane cavity are reduced, and blood is sucked in respectively. Wherein, before pumping the blood in the atrial membrane chamber into the ventricular membrane chamber, the blood in the ventricular membrane chamber is sucked, after the atrial hydraulic blood pump pumps the blood in the atrial membrane chamber into the ventricular membrane chamber, the pressure in the ventricular membrane chamber reaches the peak value, and the pumped blood is pumped back into the patient body by the ventricular hydraulic blood pump, so that the pumped blood can reach higher pumping force more easily. The initial positions of the actuating elements of the atrial hydraulic blood pump and the ventricular hydraulic blood pump can be set according to basic information such as age, height, weight and the like of a patient, and the actuating elements stop sliding down after sliding down to the set initial positions, so that blood is prevented from being excessively sucked into an atrial membrane chamber and a ventricular membrane chamber.
As shown in fig. 1, according to some embodiments of the present invention, the atrium simulation structure has a third communication channel, one end of which communicates with the inlet, the other end of which is adapted to communicate with amembrane lung oxygenator 7;
the ventricle simulation structure is provided with a fourth communication channel, and one end of the fourth communication channel is communicated with the outlet;
theventricular membrane chamber 22 communicates with theatrial membrane chamber 21 through a fifth communication channel;
the third communicating channel, the fourth communicating channel and the fifth communicating channel are all provided with one-way valves. The check valve functions to prevent backflow of blood.
According to some embodiments of the invention, the third communication channel, the fourth communication channel and the fifth communication channel are all provided at the top of the ventricular membrane chamber and/or the atrial membrane chamber.
According to some embodiments of the invention, the inner wall surface of the ventricular membranous cavity and the inner wall surface of the atrial membranous cavity are both provided with an anti-thrombogenic coating.
According to some embodiments of the invention, the first and second inflatable membranes are anti-thrombogenic membranes.
According to some embodiments of the invention, a drive member drives the first and second actuating members to move based on a pulse signal.
In some embodiments of the present invention, the drivingmember 6 may be used for: an electrocardiogram of the patient is obtained, and a first pulse signal and a second pulse signal corresponding to the electrocardiogram are generated, wherein the first pulse signal is used for controlling thefirst actuator 51 to move, and the second pulse signal is used for controlling thesecond actuator 52 to move.
Further, thedriver 6 is used for:
respectively extracting a P wave band and an R wave band from the electrocardiogram;
taking the interval between two adjacent R wave bands as the period length, and taking the duty cycle of the P wave band as the emission period of the first pulse signal;
and taking the interval between two adjacent R bands as the period length, and the duty cycle of the R band as the transmission period of the first pulse signal.
Thedriver 6 may be a programmable signal controller for outputting a first pulse signal and a second pulse signal. The signal frequency of the first pulse signal and the signal frequency of the second pulse signal may be determined according to the rhythm of P-wave and R-wave of the electrocardiogram of the patient.
The lengths of the P-band and the QRS-band are extracted by acquiring sinus rhythm signals of the patient, i.e., electrocardiogram signals, respectively. The R-R interval is taken as the cycle length of signal repetition. The P wave band duty cycle provides a high-level electric signal for the atrium hydraulic blood pump through the driving part, so that the atrium hydraulic blood pump is driven to work, the first driving part is driven to move, and blood in the atrium membrane cavity is pumped into the ventricle membrane cavity. The R wave band duty cycle provides an electric signal for the ventricular hydraulic blood pump through the driving part, the electric signal is at a high level, so that the ventricular hydraulic blood pump is driven to work, the second driving part is driven to move, and the blood in the ventricular membrane cavity is pumped back to the patient. The driver can generate corresponding first pulse control signal and second pulse control signal according to the rhythm programming of the patient electrocardiogram P wave and R wave, thereby simulating the pumping frequency and pumping mode of the heart of the patient.
The driving piece is divided into two paths for output: (1) "OUT-P" controls atrial hydraulic blood pumps, and "OUT-R" controls ventricular hydraulic blood pumps. In an R-R interval period, two blood pumps are respectively controlled in different time periods to finish the control of the rhythm ejection of blood.
According to some embodiments of the invention, the drive member is configured to:
personal information of a patient is acquired, and initial positions of the first actuating piece and the second actuating piece are set according to the personal information.
For example, the personal information may include the patient's age, height, weight, and the like. The initial position is different, and the pumping force and the blood pumping amount are different. From this, can provide different pump power and blood pump volume according to patient's individual condition, the single pump blood volume of control that can be more accurate can be applicable to the patient of different age brackets, and application range is wider.
According to some embodiments of the invention, a sealing member is provided between the first actuating member and the first communicating channel inner wall. This improves the sealing property of the first fluid chamber.
And a second sealing element is arranged between the second actuating element and the inner wall of the second communication channel.
This improves the sealing property of the second fluid chamber.
The seal may be a gasket.
According to the utility model discloses external membrane lung oxygenation device, include:
an extracorporeal lung membrane powered pump as described above;
and the membrane lung oxygenator is communicated with the inlet of the in vitro lung membrane power pump.
The utility model discloses external membrane lung oxygenation device can draw the venous blood in the patient body to carry out the oxygenation through membrane lung oxygenator in vitro, and the blood after will oxygenating again is passed through external membrane power pump and is returned internally with the mode pump sending of pulse blood flow.
It is noted that although some of the embodiments described herein include some but not other features included in other embodiments, combinations of features of different embodiments are meant to be within the scope of the invention and form different embodiments. The particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples. For example, in the claims, any of the claimed embodiments may be used in any combination.
The in vitro pulmonary membrane power pump according to an embodiment of the present invention is described in detail in a specific embodiment with reference to fig. 1. It is to be understood that the following description is illustrative only and is not intended as a specific limitation on the invention. All adopt the utility model discloses a similar structure and similar change all should be listed in the protection scope of the utility model.
The ECMO mainly comprises an intravascular catheter, a connecting tube, a power pump (artificial heart), an oxygenator (artificial lung), an oxygen supply tube, a monitoring system and the like, and the ECMO mainly adopts the working principle that venous blood in the patient body is led to the outside of the body for oxygenation, and the oxygenated blood is returned to the body for oxygen supply so as to temporarily replace the function of the heart and the lung, wherein the power pump provides power to drive the blood to flow in the pipeline.
The power pumps used clinically at present comprise a centrifugal blood pump and a magnetic suspension blood pump. The centrifugal blood pump drives blood to rotate in a mode that a rotor rotates around a shaft, and finally, the blood leaves the blood pump from an output tube at the outermost periphery to enter a human body under the action of centrifugal force. The magnetic suspension blood pump can reduce the damage to blood cells due to friction by mounting a magnetic body on a rotor, mounting the magnetic body with the same magnetism as the magnetic body on the rotor below the rotor, and suspending the rotor in the blood pump by using the principle that like poles repel each other and using repulsion force.
In summary, the conventional blood pump has the following disadvantages:
1. the patient supplies blood to the body through advection type blood flow for a long time, and complications such as thrombus and the like are easily formed.
2. The blood pumping mode of the traditional blood pump has great damage to blood cells in blood, so that the blood quality of a patient is poor.
3. The traditional blood pump pumps a large amount of blood into a patient body at one time, so that the blood in the patient body is excessive, and the blood pressure is changed violently, so that the patient is uncomfortable. 4. Conventional blood pumps fail to simulate the blood supply pattern of the heart from the patient's electrocardiogram.
Based on the above problems, the embodiment of the present invention provides an extracorporeal lung membrane power pump, which pumps blood in a hydraulic driving manner, and continuously compresses the volume of blood through fluid, so as to extrude the blood out of a pump body and shoot the blood into a patient body, and the manner not only can provide a large pumping force for blood flow, but also has no friction force, so as to reduce the damage of blood cells, and solve the problem of the damage of the traditional blood pump to blood cells; set up two blood cavities, when the blood pump was internal with blood pump pumping patient, another cavity can be retrieved the internal surplus blood of patient, prevents that the internal blood pressure of patient from sharply changing.
In detail, the utility model discloses external lung membrane power pump of embodiment includes: a drivingpiece 6, a retractable membrane heart chamber, an atrium hydraulic blood pump and a ventricle hydraulic blood pump. The retractable membrane heart chamber integrates two heart chambers, simulating an atrium and a ventricle, respectively, which are configured as anatrial membrane chamber 21 and aventricular membrane chamber 22, respectively, as shown in fig. 1. The atrial hydraulic blood pump includes afirst fluid chamber 31 and afirst actuator 51. The ventricular hydraulic blood pressure pump includes asecond fluid chamber 32 and asecond actuator 52.
As shown in FIG. 1, theatrial membrane chamber 21 is separated from thefirst fluid chamber 31 by the firstinflatable membrane 11. Theventricular membrane chamber 22 is spaced from thesecond fluid chamber 32 by the secondinflatable membrane 12. The firstinflatable membrane 11 and the secondinflatable membrane 12 are each a highly elastic and highly airtight flexible thin membrane made of a material that is antithrombotic and compressible and expandable.
It will be appreciated that theatrial membrane chamber 21 and thefirst fluid chamber 31 share a single flexible membrane, making them two chambers that are sealed from each other. Theventricular membrane chamber 22 and thesecond fluid chamber 32 share a common flexible membrane, which, in the same way, makes them two chambers that are sealed from each other. The flexible membrane deforms in response to changes in pressure within the fluid chamber, transmitting the pressure within the fluid chamber into either theatrial membrane chamber 21 or theventricular membrane chamber 22.
The inner walls of theatrial membrane chamber 21, theventricular membrane chamber 22 and other sites in direct contact with blood are provided with thromboresistant coatings.
As shown in fig. 1, the blood flow inlet of the membrane-lung oxygenator 7, the space between the membrane-lung oxygenator 7 and theatrial membrane chamber 21, the space between theatrial membrane chamber 21 and theventricular membrane chamber 22, and the blood flow outlet of theventricular membrane chamber 22 are all provided with one-way valves. The one-way valve may be a duckbill valve. The one-way valve acts to prevent backflow of blood, which can only pass from the blood inlet through themembrane oxygenator 7 into theatrial membrane chamber 21, from where it is pumped from theatrial membrane chamber 21 into theventricular membrane chamber 22, and from where it is pumped back into the patient.
Thefirst actuator 51 and thesecond actuator 52 are each provided with a sealing assembly. The seal assembly may be a seal ring. The actuating member (thefirst actuating member 51 or the second actuating member 52) and the corresponding fluid chamber (thefirst fluid chamber 31 or the second fluid chamber 32) form a closed space, fluid is injected into the closed space, the actuating member can slide up and down in the pipeline of the fluid chamber, the fluid in the fluid chamber is pressed by controlling the actuating member to slide upwards, the corresponding flexible film (thefirst expansion film 11 or the second expansion film 12) is deformed to compress theatrial membrane chamber 21 or theventricular membrane chamber 22, the pressure generated by the actuating member is transmitted to theatrial membrane chamber 21 or theventricular membrane chamber 22 through the fluid in the fluid chamber, and blood in theatrial membrane chamber 21 or theventricular membrane chamber 22 is pumped out under the action of the pressure. The hydraulic blood pump can effectively protect blood cells through fluid conduction pressure and reduce the loss of the blood cells in the working process of the blood pump.
The hydraulic blood pump can control the blood volume and the blood pumping force of single pumping respectively by controlling the pushing distance and the driving force of the actuating element, can customize and adjust various parameters of the hydraulic blood pump according to the information of age, sex, height, weight, electrocardiogram and the like of a patient, generally the pumping volume of the heart of a normal person per beat is about 80ml, so an operator can adjust the advancing distance parameter of the blood pump actuating element to a corresponding value to simulate the pumping volume of the heart of the normal person per beat, can determine the blood pumping force of the heart of the patient according to the information of the height, the weight, the age and the like of the patient, adjust the pushing force parameter of the hydraulic blood pump actuating element to a corresponding value to simulate the pumping force of the heart of the patient, and prevent the blood supply insufficiency of tissues at the far end of the heart.
The amount of blood pumped by the atrial hydraulic pump into the ventricular membrane chamber is less than the amount of blood pumped by the ventricular blood pump out of the ventricular membrane chamber. Since the human atrium is smaller than the ventricle, they will expand when both the atrial and ventricular myocardium are in a relaxed state, drawing blood into them, and the regurgitated blood will be drawn into the atrium and directly through them into the ventricle even before the atrium contracts. Similarly, when the R square wave and the P square wave are both at a low level, the fluid and the actuator in the two fluid chambers slide downward under the action of their own gravity, the pressures in the atrial membrane chamber and the ventricular membrane chamber are both reduced, blood is respectively sucked into the fluid and the actuator, blood is already sucked into the ventricular membrane chamber before the blood in the atrial membrane chamber is pumped into the ventricular membrane chamber, and after the blood in the atrial membrane chamber is pumped into the ventricular membrane chamber by the atrial hydraulic blood pump, the pressure in the ventricular membrane chamber reaches a peak value and the blood is pumped back into the patient by the ventricular hydraulic blood pump, so that the pumped back blood can reach a higher pumping force more easily. The initial positions of the actuating pieces of the atrial hydraulic blood pump and the ventricular hydraulic blood pump can be set according to basic information of the age, the height, the weight and the like of a patient, and the actuating pieces stop sliding down after sliding down to the set initial positions, so that blood is prevented from being excessively sucked into an atrial membrane chamber and a ventricular membrane chamber.
The drivingmember 6 can be a programmable signal controller for controlling the hydraulic blood pumps, and the signal frequency can output control square waves according to the rhythms of P waves and R waves of electrocardiograms input to a patient to respectively control the two hydraulic blood pumps.
The lengths of the P-band and the QRS-band are extracted by acquiring sinus rhythm signals of the patient, i.e., electrocardiogram signals, respectively. The R-R interval is taken as the cycle length of signal repetition. The electric signal provided by the atrium hydraulic blood pump is high level through the driving part in the P wave band duty cycle, so that the atrium hydraulic blood pump is driven to work, and the blood in the atrium membrane chamber is pumped into the ventricle membrane chamber. The R wave band duty cycle provides an electric signal for the ventricular hydraulic blood pump through the driving part, the electric signal is high level, so that the ventricular hydraulic blood pump is driven to work, the blood pump in the ventricular membrane cavity is sent back to a patient body, and the driving part can generate corresponding control square waves according to rhythm programming of patient electrocardiogram P waves and R waves, so that the pumping frequency and the pumping mode of the heart of the patient are simulated.
The driving piece is divided into two paths for output: (1) The OUT-P controls an atrial hydraulic blood pump, and the OUT-R controls a ventricular centrifugal blood pump. In an R-R interval period, two blood pumps are respectively controlled in different time periods to finish the control of the rhythm ejection of blood.
The utility model discloses in vitro lung membrane power pump's working process includes:
the blood in the femoral vein is oxygenated by a membrane oxygenator.
The driving piece outputs pulse signals to control the hydraulic blood pump of the atrium and the hydraulic blood pump of the ventricle to work.
Controlling the first actuating member to advance, wherein the fluid in the first fluid cavity transmits the advancing pressure of the first actuating member to the flexible film of the atrial membranous cavity, so that the blood in the atrial membranous cavity is pumped to the ventricular membranous cavity.
Under the pushing of the first actuating part without external force, the fluid in the first fluid cavity slides downwards under the action of the gravity of the first actuating part, the atrial membrane contracts downwards, the pressure in the atrial membrane cavity is reduced, and the blood in the membrane-lung oxygenator is sucked into the atrial membrane cavity.
The second actuator is controlled to advance, and the fluid in the second fluid cavity transmits the advancing pressure of the second actuator to the flexible film of the ventricular membrane chamber, so that the blood in the ventricular membrane chamber is pumped back to the femoral artery of the patient to the whole body.
Under the condition that the second actuating piece is not pushed by external force, the fluid in the second fluid cavity slides downwards under the action of the gravity of the second actuating piece, the atrial membrane contracts downwards, the pressure in the atrial membrane cavity is reduced, and the blood in the atrial membrane cavity is sucked into the ventricular membrane cavity.
The circulation thereby provides pulsatile blood flow to the patient.
The utility model discloses external pulmonary membrane power pump has following beneficial effect:
1. by respectively controlling the atrium blood pump and the ventricle blood pump, the pulsatile blood flow is output, and the blood flow is more consistent with a physiological blood flow mode. 2. The utility model discloses be equipped with atrium membrane chamber and ventricle membrane chamber, when the blood pump in the ventricle membrane chamber goes into the patient internal, atrium membrane chamber can be with the blood suction through membrane lung oxygenator oxygenation, compares with single chamber, and this design can prevent that patient's systolic pressure and diastolic pressure phase difference are too big. 3. The hydraulic blood pump is used for providing power for pumping blood, the fluid in the fluid cavity is used for transmitting the pressure generated by the actuating piece to the atrial membrane cavity and the ventricular membrane cavity and extruding the chambers out, and compared with mechanical transmission, the hydraulic blood pump can reduce the damage to blood cells and avoid complications such as thrombus. 4. One-way valves are arranged at the blood flow inlet of the membrane lung oxygenator, between the membrane lung oxygenator and the atrial membrane chamber, between the atrial membrane chamber and the ventricular membrane chamber and at the blood flow outlet of the ventricular membrane chamber, and the one-way valves are used for preventing blood from flowing back. 5. The parts of the device which are in direct contact with blood are all internally coated with anti-coagulation thrombus coatings.
It should be noted that the above-mentioned embodiments are only preferred embodiments of the present invention, and are not intended to limit the present invention, and those skilled in the art can make various modifications and changes. Any modification, equivalent replacement, or improvement made within the spirit and principle of the present invention should be included in the protection scope of the present invention.
Claims (10)
1. An extracorporeal lung membrane power pump, comprising:
an atrium-simulating structural member having an inner space divided into an atrial membrane chamber having an inlet for inflow of blood and a first fluid chamber having a first communicating channel by a first inflatable membrane;
a ventricular analog structure, an inner space of which is divided into a ventricular membrane chamber and a second fluid chamber by a second expansion membrane, the ventricular membrane chamber is communicated with the atrial membrane chamber, the ventricular membrane chamber is provided with an outlet for blood to flow out, and the second fluid chamber is provided with a second communication channel; the second fluid chamber and the first fluid chamber both contain fluid;
a first actuator slidably disposed through the first communication passage to seal the first fluid chamber;
a second actuator slidably disposed through the second communication channel to seal the second fluid chamber;
and the driving piece is used for driving the first actuating piece and the second actuating piece to move.
2. The extracorporeal lung membrane power pump of claim 1, wherein the atrial mimic structure comprises a first structural section and a second structural section, the second structural section having a cross-sectional area smaller than the cross-sectional area of the first structural section, the upper end of the second structural section being connected to and in communication with the lower end of the first structural section;
the first expansion membrane is arranged in the first structure section to divide the internal space of the first structure section into a first sub-cavity and a second sub-cavity which are arranged up and down, the first sub-cavity is constructed to form the atrial membrane chamber, and the second sub-cavity and the internal space of the second structure section are constructed to form the first fluid chamber;
the ventricular simulation structure comprises a third structure section and a fourth structure section, wherein the cross section of the fourth structure section is smaller than that of the third structure section, and the upper end of the fourth structure section is connected and communicated with the lower end of the third structure section;
the second expansion film is arranged in the third structure section to divide the internal space of the third structure section into a third sub-cavity and a fourth sub-cavity which are arranged from top to bottom, the third sub-cavity is formed by the structure of the third sub-cavity, and the fourth sub-cavity and the internal space of the fourth structure section are formed by the structure of the second fluid cavity.
3. The extracorporeal lung membrane power pump of claim 2, wherein the second structural section and the fourth structural section each extend in a vertical direction.
4. The extracorporeal lung membrane power pump of any one of claims 1-3, wherein the atrium simulation structure has a third communication channel, one end of the third communication channel is in communication with the inlet, the other end of the third communication channel is adapted to be in communication with a membrane lung oxygenator;
the ventricle simulation structure is provided with a fourth communication channel, and one end of the fourth communication channel is communicated with the outlet;
the ventricular membrane chamber is communicated with the atrial membrane chamber through a fifth communication channel;
the third communicating channel, the fourth communicating channel and the fifth communicating channel are all provided with one-way valves.
5. The extracorporeal lung membrane power pump of claim 4, wherein the third communication channel, the fourth communication channel and the fifth communication channel are all provided at the top of the ventricular membrane chamber and/or the atrial membrane chamber.
6. The extracorporeal pulmonary membrane power pump of claim 1, wherein the inner wall surface of the ventricular membrane chamber and the inner wall surface of the atrial membrane chamber are each provided with an anti-thrombogenic coating.
7. The extracorporeal lung membrane power pump of claim 1, wherein the first and second inflatable membranes are both anti-thrombogenic membranes.
8. The extracorporeal lung membrane power pump of claim 1, wherein the drive member drives the first and second actuator members to move based on a pulse signal.
9. The extracorporeal lung membrane power pump of claim 1, wherein a seal is disposed between the first actuator and the inner wall of the first communication channel;
and a second sealing element is arranged between the second actuating element and the inner wall of the second communication channel.
10. An extracorporeal membrane lung oxygenation device, comprising:
the extracorporeal lung membrane power pump of any one of claims 1-9;
and the membrane lung oxygenator is communicated with the inlet of the in-vitro lung membrane power pump.
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| Application Number | Priority Date | Filing Date | Title |
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| CN202221339154.XUCN218793560U (en) | 2022-05-31 | 2022-05-31 | Extracorporeal lung membrane power pump and extracorporeal lung oxygenation device |
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| CN202221339154.XUCN218793560U (en) | 2022-05-31 | 2022-05-31 | Extracorporeal lung membrane power pump and extracorporeal lung oxygenation device |
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| CN218793560Utrue CN218793560U (en) | 2023-04-07 |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN115068807A (en)* | 2022-05-31 | 2022-09-20 | 绍兴梅奥心磁医疗科技有限公司 | Pulse type in vitro pulmonary membrane power pump and in vitro pulmonary oxygenation device |
- 2022
- 2022-05-31CNCN202221339154.XUpatent/CN218793560U/enactiveActive
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN115068807A (en)* | 2022-05-31 | 2022-09-20 | 绍兴梅奥心磁医疗科技有限公司 | Pulse type in vitro pulmonary membrane power pump and in vitro pulmonary oxygenation device |
| CN115068807B (en)* | 2022-05-31 | 2024-05-28 | 绍兴梅奥心磁医疗科技有限公司 | Pulse type external pulmonary membrane power pump and external pulmonary oxygenation device |
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