WO2019024111A1

WO2019024111A1 - Cardiac simulation device

Info

Publication number: WO2019024111A1
Application number: PCT/CN2017/096093
Authority: WO
Inventors: 孙兴国
Original assignee: 中国医学科学院阜外医院
Priority date: 2017-08-04
Filing date: 2017-08-04
Publication date: 2019-02-07

Abstract

A cardiac simulation device comprises: a chamber (1) having a variable volume, the chamber having an entrance (11) and an exit (12), the entrance (1) being configured to allow a liquid to flow into the chamber (1) from the exterior, and the exit (12) being configured to allow the liquid to flow from the chamber (1) to the exterior; and a pulsating component (2) configured to increase or decrease the volume of the chamber (1). When the pulsating component (2) increases the volume of the chamber (1), the chamber (1) sucks in a liquid from the entrance (11). When the pulsating component (2) decreases the volume of the chamber (1), the chamber (1) pumps out the liquid from the exit (12). The pulsating component (2) is configured such that a contraction volume of the chamber (1) accounts for 10-90% of the maximum volume of the chamber (1) when stretched by the pulsating component (2).

Description

Cardiac analog device

Technical field

The present invention is in the field of medical devices, and in particular, the present invention relates to a cardiac simulation device.

Background technique

Heart disease has always been a disease that is difficult to cure and has a high mortality rate. In recent years, the number of patients suffering from heart disease has increased, and heart disease has become one of the most important diseases affecting human health. In heart disease, heart failure is the most threatening condition to the patient's life. Heart disease can eventually cause heart failure.

Although heart failure can be controlled to a certain extent, it cannot be cured. If you want permanent treatment, you can only use a heart transplant or a heart assist device. Heart transplants need to find the right heart and are more difficult. In recent years, mechanical assisted circulation equipment has gradually become an alternative treatment for heart failure, and it is expected to gradually develop into a permanent treatment for heart failure.

The existing ventricular assisted blood pump is mainly a flat flow blood pump according to the blood supply mode. Common advection blood pumps include centrifugal and axial flow ventricular assisted blood pumps. These advection blood pumps use blade rotation as a power mode to provide flow of blood to the flow. However, the shear stress generated by the high-speed rotation of the blade has a strong destructive force on blood cells such as red blood cells, and it is easy to form a thrombus, causing severe consequences such as stroke and multiple organ failure.

On the other hand, patients with heart failure are often accompanied by a condition of tidal breathing. Tidal breathing conditions can occur even after the patient has used mechanical assisted circulation equipment.

It can be seen that the existing cardiac assisted devices still have many defects, and it is necessary to improve the cardiac assisted devices.

Summary of the invention

It is an object of the present invention to provide a new technical solution for a cardiac simulation device.

According to a first aspect of the present invention, a cardiac simulation apparatus is provided, comprising:

a chamber configured to have a variable volume, the chamber having an inlet and an outlet configured to enable liquid to flow from the outside into the chamber, the outlet being configured to enable liquid Flowing out of the chamber to the outside;

a pulsating member configured to expand or contract the volume of the chamber, the chamber for drawing liquid from the inlet when the pulsating member enlarges the volume of the chamber, and the pulsating member reducing the volume of the chamber when the pulsating member is reduced The chamber pumps liquid from the outlet;

The pulsating member is configured to reduce the volume of the chamber by 10% to 90% of the maximum volume to which the pulsating member expands the chamber.

Optionally, the cardiac simulation device includes a sealing member, the chamber is located inside the sealing member, the inlet and the outlet are disposed on the sealing member, and the inlet and the outlet respectively connect the chamber to the outside Space connectivity.

Optionally, the sealing member comprises a cylinder body, one end of the cylinder body is a closed end, the pulsating component protrudes into the cylinder body and is slidably sealed with an inner wall of the cylinder body, and the chamber is located from the pulsating component To the area between the sealed ends, the pulsating member is configured to slide in the cylinder.

Optionally, a soft film is disposed between the beating member and the sealing end, and an edge of the soft film is sealingly connected to the sealing member, and an area enclosed between the soft film and the sealing end is used as The chamber.

Optionally, the sealing member comprises a cover plate sealed at one end of the cylinder to form the closed end.

Optionally, the inlet and the outlet are disposed on the cover plate;

Alternatively, the inlet and outlet are disposed on the cylinder.

Optionally, the sealing member comprises a cover plate sealed at one end of the cylinder body to form the closed end,

The edge of the soft film is attached to the inner wall of the cylinder;

Alternatively, the edge of the soft film is attached to the cover.

Optionally, the inlet is provided with an admission flap mechanism configured to allow only liquid to enter the chamber from the outside, the outlet being provided with a predetermined flap mechanism, The quasi-valve mechanism is configured to only allow liquid to flow from the chamber to the outside.

Optionally, the amount of reduction accounts for 40%-50% of the maximum volume to which the pulsating component expands the chamber;

Alternatively, the amount of reduction is from 55% to 70% of the maximum volume to which the pulsating member expands the chamber.

Optionally, the pulsating component is a piston, the cardiac simulation device further includes a rotating machine and a connecting rod assembly, the connecting rod assembly and the piston constitute a crank linkage mechanism, the rotating machine and the connecting rod assembly Connected, the piston is configured to reciprocate within the cylinder as the rotating machine rotates.

Optionally, the connecting rod assembly is distributed with a connecting hole, and the connecting hole is pivotally connected to the connecting rod assembly.

The inventors of the present invention have found that in the prior art, those skilled in the art recognize the concept of cardiac minute output, but have not found cardiac diastolic volume, end systolic volume, stroke volume, ejection fraction. Heart rate function indicators have important interrelated effects on blood circulation and respiration. If the cardiac assist device does not provide at least a similar ejection fraction to the heart, it may also cause neurological disorders in the human body, which may cause symptoms such as tidal breathing. The inventors of the present invention found the correlation therein and provided a cardiac simulation device. In addition to realizing the traditional device to regulate the amount of blood transported per unit time (cardiac output), the cardiac simulation device can at least achieve adjustment and control under high simulation conditions of the ejection fraction. Simulates the ejection fraction of a normal or abnormal heart in a highly high-bionic form. Therefore, the technical task to be achieved by the present invention or the technical problem to be solved is not thought of or expected by those skilled in the art, so the present invention is a new technical solution.

Other features and advantages of the present invention will become apparent from the Detailed Description of the <RTIgt;

DRAWINGS

The drawings incorporated in the specification and which form a part of the specification The examples, together with the description thereof, are used to explain the principles of the invention.

1 is a schematic structural view of a cardiac simulation device according to an embodiment of the present invention;

2 is a schematic structural diagram of a cardiac simulation device according to another embodiment of the present invention;

FIG. 3 is a schematic structural diagram of a cardiac simulation apparatus according to another embodiment of the present invention.

Detailed ways

Various exemplary embodiments of the present invention will now be described in detail with reference to the drawings. It should be noted that the relative arrangement of the components and steps, numerical expressions and numerical values set forth in the embodiments are not intended to limit the scope of the invention unless otherwise specified.

The following description of the at least one exemplary embodiment is merely illustrative and is in no way

Techniques, methods and apparatus known to those of ordinary skill in the relevant art may not be discussed in detail, but the techniques, methods and apparatus should be considered as part of the specification, where appropriate.

In all of the examples shown and discussed herein, any specific values are to be construed as illustrative only and not as a limitation. Thus, other examples of the exemplary embodiments may have different values.

It should be noted that similar reference numerals and letters indicate similar items in the following figures, and therefore, once an item is defined in one figure, it is not required to be further discussed in the subsequent figures.

The present invention provides a cardiac simulation device that is a functionally high bionic heart function simulation device. These include the chamber and the pulsating components. The volume of the chamber is variable and can be used to simulate the contraction and relaxation of the ventricle. The chamber has an inlet and an outlet for allowing liquid to flow from the outside into the chamber. The outlet is for allowing liquid to flow out of the chamber to the outside.

The pulsating member is for expanding or reducing the volume of the chamber. For example, the pulsating member may be driven by a rotating mechanism, a swinging mechanism, or a retracting mechanism to cause the chamber to reciprocate and expand. In a practical application, when the pulsating member controls the chamber When the volume is enlarged, the chamber is capable of drawing blood into the chamber from the inlet. And when the dial member controls the volume of the chamber to be reduced, blood in the chamber can be pumped from the outlet to the outside. Thus, the cardiac simulation device can at least simulate the contraction and relaxation of the ventricle and can replace the ventricular structure of the heart.

In particular, the present invention can change the amount of reduction that can be produced by the pulsating member by adjusting the pulsating member. When the pulsating member performs a reduction operation on the chamber, the volume of the chamber is reduced by 10% to 90% of the maximum volume to which the pulsating member can expand. For example, if the pulsating member is capable of expanding the volume of the chamber to 145 ml, the amount of reduction in the volume of the chamber can be adjusted from 14.5 ml to 130.5 ml. The proportion of the reduction amount may be adjusted within a range of 10% to 90% depending on the ventricle corresponding to the cardiac simulation device and the corresponding abnormal heart of the different situation.

For example, in the case of a cardiac simulation device for simulating a normal ventricle, the amount of reduction can be adjusted to account for 40%-80% of the maximum capacity that the chamber can expand; for a cardiac simulation device to simulate an abnormal ventricle or only In the case where a part of the function of the ventricle is provided, the amount of reduction can be adjusted to occupy a maximum capacity of 10% to 40%, or 80% to 90%, which the chamber can be expanded. The invention is not limited thereto.

In addition, the cardiac simulation device provided by the present invention can also adjust the reduction amount to 0%-100% of the maximum capacity of the chamber. The reduction of the limit of 0%, 1%, and 99%, 100% can also be achieved by the cardiac simulation device, which can be applied to the special case of simulating the heart, which is not limited by the present invention.

The cardiac simulation device provided by the present invention can be used to simulate a situation in which the ventricle has various ejection fractions. Whether in medical research or clinical use, it can provide good ejection fraction regulation.

More importantly, the cardiac simulation device can adjust the amount of reduction to a value corresponding to the ejection fraction of the actual heart to simulate the actual heart's pulsation action and ejection fraction. The inventors of the present invention have found that the ejection fraction of the ventricle is related to the human body's triggering of the breathing action. Normally, a person performs a complete breathing session with approximately 6 heartbeats during the period.

The inventors of the present invention have found that when the human body performs an "inhalation" action, the oxygen in the blood from the lungs to the aorta gradually rises under the push of the heart pumping function. Pivotal, In the case of a normal ejection fraction of the left ventricle, after about three beats in the left ventricle, the sensory system (aortic arch, carotid peripheral chemoreceptor) pumped from the left ventricle to the human body detects an increase in oxygen in the blood ( The result of lung inhalation), thus ending the "inhalation" action and starting the "exhalation" action; in the "exhalation" action, the oxygen content in the blood pumped from the left ventricle due to no oxygen inhalation Will be reduced one by one. The left ventricular pumped blood carries a drop in oxygen (pulmonary exhalation) signal that reaches the aorta. At this time, the human body's sensing system in the aorta detects the decrease in oxygen in the blood pumped by the left ventricle (the result of lung exhalation), thereby ending the "exhalation" action and starting the "inhalation" action. Thereby, the dynamic switching of the suction-call and the call-sucking is repeated, thereby achieving continuous and stable breathing of the human body. Critically, in the case of a normal ejection fraction of the left ventricle, after about three beats in the left ventricle, the oxygen content of the pumped blood will reach a high value. This cycle is repeated.

The inventors of the present invention have found that the breathing and heartbeat of the human body have the above-mentioned associated operational relationship, thereby completing regular breathing and heartbeat movements. The main feature controlling this association is the ejection fraction of the ventricles. If the ejection fraction is too high, it will cause fewer ventricular beats, and the oxygen content in the blood will reach a high or low value, which may cause the respiratory rate to rise. If the ejection fraction is too low, it will cause more ventricular beats, and the oxygen content in the blood can reach a high value or a low value, which will cause the respiratory rate to decrease. When the ejection fraction is lowered, the oxygen content in the blood pumped by the left ventricle may not be reduced to a low value, so that the next "inhalation" action cannot be triggered. It can be seen that the ejection fraction of the ventricle is an important condition in the whole heart and lung function.

However, the existing cardiac mechanical assisted circulation device does not reflect the ejection fraction of the heart, but continuously delivers the blood outward. This way of continuously outputting blood neglects the relationship between heartbeat and respiration, so it may cause disorder of the human nervous system, and can not trigger the respiratory action normally, thereby causing symptoms such as respiratory disorder and tidal breathing.

The inventors of the present invention have recognized this problem, and in turn have exhibited pulsation characteristics in the cardiac assisting device provided by the present invention. Also, in a preferred embodiment, the cardiac simulation device limits the amount of reduction of the chamber to between 40% and 80% to achieve a better simulated normal ventricular beat effect.

In the above description of the heartbeat and respiratory cycle, the normal ejection fraction of the left ventricle is between 55% and 70%, and the normal ejection fraction of the right ventricle is between 40% and 50%. Therefore, in the present invention In a preferred embodiment, the volume of the chamber can be reduced by 40%-50% of the maximum volume to which the pulsating component expands the chamber. This embodiment corresponds to the physiological normal condition of the cardiac simulation device simulation instead of the right ventricular functional state. . In another preferred embodiment of the present invention, the volume of the chamber can be reduced by 55% to 70% of the maximum volume to which the pulsating member expands the chamber, and the embodiment corresponds to the cardiac simulation device simulation instead of the left ventricular function state. The normal condition of physiology.

In the case of heart failure, the patient's ejection fraction may be reduced to 20%-30% or even lower. The amount of reduction of the cardiac simulation device can be adjusted in the range of 10% to 90%, and can basically simulate all the states of the left ventricular function, including the above-mentioned physiological normal conditions and severe pathophysiological abnormalities in heart failure. It is thus possible to study the extent to which all states of left ventricular function affect the respiratory function of the human body.

In addition to realizing the function of regulating blood volume (cardiac blood output) per unit time, the cardiac simulation device of the present invention can also realize physiological function indexes such as end-diastolic volume, end-systolic volume, stroke volume, ejection fraction, heart rate, and the like. Adjustment and control under high simulation conditions.

Alternatively, the cardiac simulation device may comprise a sealing member having a lumen for constituting the chamber. The chamber may occupy the entire inner cavity or a partial area occupying the inner cavity, which is not limited by the present invention. The inner cavity of the sealing member may be substantially closed, with only the necessary openings for communicating with the outside and for assembling other components. The inlet and outlet are disposed on the sealing member, and the inlet and outlet respectively communicate the chamber with an external space.

Alternatively, the present invention provides an embodiment. As shown in FIG. 1, the sealing member may include a cylinder block 31 having a cylindrical or other shaped inner cavity therein. One end of the cylinder block 31 is a closed end, and the closed end is substantially closed to the inner cavity, and only the necessary functional holes or fitting openings are provided. The pulsating member 2 projects into the inner cavity of the cylinder block 31, and the side surface of the pulsating member 2 is slidably and sealingly connected to the inner wall of the cylinder block 31. The pulsating member 2 is slidable within the cylinder block 31 and is kept sealed from the inner wall of the cylinder block 31. The chamber 1 is located in the region from the pulsating member 2 to the sealing end, may be completely occupied by this portion, or may be provided with other components such that the chamber 1 occupies only a portion of the above region. Thus, when the pulsating member 2 slides in the cylinder block 31, the volume of the chamber 1 changes, Thereby simulating the pulsation of the ventricle.

Further preferably, as shown in FIG. 1, a soft film 32 may be disposed between the pulsating member 2 and the sealing end, and an edge of the soft film 32 is sealingly connected to the sealing member. Thus, encapsulation between the soft film 32 and the sealed end forms a substantially sealed area that acts as the chamber 1. The pulsating member 2 can be directly connected to the soft film 32, so that when the pulsating member 2 is moved, the soft film 32 can be deformed to change the volume of the chamber 1. Of course, since the pulsating member 2 is sealingly fitted to the inner wall of the cylinder block 31, the pulsating member 2 may not be directly connected to the soft film 32. Due to the action of the air pressure, when the pulsating member 2 moves in the cylinder block 31, the soft film 32 is also deformed, and the volume of the chamber 1 is changed. An advantage of configuring the soft film is that the blood flowing into the chamber may not be in direct contact with the pulsating member. The gap fit between the pulsating member and the inner wall of the cylinder may damage blood cells as it moves. When a soft film is placed, the blood cells flow only in the space between the soft film and the closed end, and are not damaged by the beating parts.

Alternatively, in an embodiment of the present invention, as shown in Fig. 2, one end of the cylinder 31 to form a closed end is itself open. Correspondingly, the sealing member may further comprise a cover plate 33. The cover plate 33 is sealed on the end surface of the cylinder block 31 to form the closed end. This structural design facilitates the assembly and processing of the cardiac simulation device itself. In other embodiments, as shown in FIG. 1, the end of the cylinder 31 itself for forming the closed end may itself be closed, and generally no additional cover 33 is required. The structural characteristics of the cylinder block 31 can be adjusted according to actual production and use.

Further, in the embodiment in which the sealing member includes the cover plate 33, both the inlet and the outlet 12 may be formed on the cover plate 33 as shown in FIG. Alternatively, an inlet and an outlet 12 may be provided on the cylinder block 31. The choice of product structure and performance can be selected according to the specific implementation. Fig. 1 shows the manner in which the inlet and outlet 12 are directly disposed on the cylinder block 31 without the cover plate 33.

Alternatively, as shown in FIG. 2, in the embodiment in which the sealing member includes the cover plate 33, the edge of the soft film 32 may be directly sealed and connected to the cover plate 33. A space between the cover 33 and the soft film 32 serves as the chamber 1. Alternatively, the edge of the soft film 32 is also It can be sealingly connected to the cylinder block 31. The choice of product structure and performance can be selected according to the specific implementation. Figure 1 shows the manner in which the edge of the soft film 32 is directly attached to the cylinder 31 without the cover 33.

The present invention is not limited to the embodiment in which only the cylinder can be used as the sealing member to constitute a cardiac simulation device. In other embodiments, other configurations may be employed to form the chamber. For example, in one embodiment, the chamber may be formed directly from the interior space of the elastic spherical container, which is sandwiched on the outside of the spherical container, and the pulsating action is achieved by clamping and relaxing. Alternatively, in another embodiment, the chamber may be constructed of a box-like deformable mechanical mechanism with a sealing layer disposed therein for encapsulating blood. The box-shaped mechanism can perform a reciprocating deformation action to realize the control of the chamber volume and realize the pulsation action.

Alternatively, as shown in Figures 1 and 2, the inlet is for allowing blood to enter the chamber 1, so that the inlet may be provided with an access flap mechanism. The access flap mechanism is configured to only allow liquid to enter the chamber 1 from the outside. Such a flap mechanism may be a biomimetic valve, or may be other devices such as a solenoid valve that can restrict one-way flow, etc., which is not limited by the present invention. Correspondingly, an outlet flap mechanism 121 is also provided at the outlet 12, the quasi-valve mechanism 121 being configured to only allow liquid to flow out of the chamber 1 to the outside.

In an embodiment of the invention, the admission flap mechanism and the quasi-valve mechanism may be one-way flaps. As shown in Figures 1 and 2, at the inlet 11, one end of the one-way flap is connected to the inner wall of the inlet, and the other end of the one-way flap is a free end. The inner wall of the inlet 11 is provided with a rib that prevents the free end of the one-way flap from moving to the outside of the inlet. Thus, the one-way flap at the inlet is configured to only allow liquid, blood to flow into the chamber. Correspondingly, a rib is also provided on the inner wall of the outlet 12, the rib being able to prevent the free end of the one-way flap from moving to the inside of the outlet, so that the one-way flap at the outlet is configured to only allow Liquid and blood flow to the outside of the chamber.

In the embodiment in which the chamber 1 is formed using the cylinder 31, as shown in Figs. 1, 2, the pulsating member 2 is preferably a piston. Accordingly, the cardiac simulation device can also include a rotary machine and a linkage assembly 41 that forms a crank linkage with the piston. The rotating machine is coupled to the link assembly 41. When the rotating machine rotates, the link assembly 41 can The rotary motion is converted into a linear motion that urges the piston to reciprocate within the cylinder block 31. The volume of the chamber 1 can be repeatedly contracted and expanded. The rotational frequency of the rotating machine is the beat frequency of the cardiac analog device. In the case shown in Fig. 1, the piston is in the process of enlarging the chamber 1; in the case shown in Fig. 2, the piston is in a state of narrowing the chamber 1 to a minimum.

Optionally, as shown in FIG. 1 and FIG. 2 , the connecting rod assembly 41 may further have a connecting hole 42 , and the connecting hole 42 extends along the connecting rod assembly 41 . The connecting hole is pivotally connected to the two links of the connecting rod assembly. In the embodiment shown in Figures 1 and 2, the two links in the link assembly 41 are end-connected such that the difference between the lowest position and the highest position of the pulsating member 2 when the rotary machine is rotated Larger, the resulting reduction is larger and the maximum chamber capacity is greater. In other embodiments, the two links can also be pivotally connected by connection holes 42 at different positions. By adjusting the connection position of the two connecting rods, the parameters such as the capacity and the reduction amount of the chamber of the cardiac simulation device can be adjusted to adapt to the ventricles simulating different functional states and different capacities.

Further, in the embodiment shown in Figs. 1, 2, it is also possible to adjust the maximum capacity of the chamber by adjusting the assembly position of the rotation center of the link assembly in the cylinder. For example, the lower end portion of the link assembly 41 in Figs. 1 and 2 is coupled to the rotating machine, and if the lower end portion and the rotating machine as a whole are moved upward, the maximum capacity of the chamber is reduced. Conversely, if the lower end of the linkage assembly and the rotating machine as a whole are moved downward, the maximum capacity of the chamber is increased. The cylinder block 31 may be provided with an adjustment mechanism such as a rail or a rotating center mounting hole for adjusting the position of the link assembly and its center of rotation and the rotating machine. For example, the center of rotation of the link assembly and the rotating machine can slide along the track to adjust the position of the center of rotation; or the output shaft of the rotating machine can be inserted in the center of rotation assembly hole at different positions to adjust the position of the center of rotation .

Of course, the invention is not limited to the use of a piston as a pulsating member. In other embodiments, for example, a pneumatic device, a hydraulic device, a clamping device, or the like may be used as a power source for driving the cardiac simulation device to perform a pulsating motion.

In an embodiment of the invention, the pulsating member 2 may be a hydraulic device. As shown in FIG. 3, in this embodiment, a soft rubber film 32 is provided in the cylinder block 31, and the soft rubber film 32 is used to form a chamber with an upper region of the cylinder block 31. The lower end of the cylinder block 31 is closed. For example, it can be closed by a closure plate, or the lower end of the cylinder itself is a closed structure, which is not limited by the present invention. Specifically, the region of the soft film 32 to the lower end of the cylinder block 31 is the pressure chamber 35. A pulsation inlet and outlet 34 for the inflow and outflow of the pressurized fluid is opened in the pressure chamber 35. The hydraulic device may preferably be disposed outside the cylinder block 31, and the hydraulic device may pump pressurized fluid into the pressure chamber 35 by a hydraulic pump; and the pressure pump may pressurize the fluid from the pressure chamber 35. Extracted in the middle.

Since the soft film 32 has a deforming ability, when the pressure liquid is continuously charged into the pressure chamber 35, the soft film 32 is deformed upward by the hydraulic action, thereby reducing the space of the chamber 1. The liquid and blood in the chamber 1 are caused to flow out from the outlet 12. Conversely, when the hydraulic device draws the pressure fluid outward, the soft film 32 is deformed downward by the hydraulic action, thereby increasing the space of the chamber. Liquid and blood outside the inlet 11 can be drawn into the chamber 1. The advantage of using the hydraulic device as the pulsating member is that the liquid is difficult to be compressed, so that the capacity, the stroke amount, and the reduction amount of the chamber can be accurately controlled by controlling the amount of the pressure liquid to be filled or sucked out of the pressure chamber. The amount of liquid charged into the pressure chamber is substantially the same as the amount of liquid that is drawn from the chamber. In the application environment where the cardiac simulation device is used to replace the normal heart, the use of the hydraulic device as the pulsating component can more reliably ensure the accuracy of the chamber capacity, and reduce the functional abnormality caused by the abnormality of the volume and the stroke volume.

Optionally, only one pulsating inlet and outlet 34 may be opened on the pressure chamber 35, and the pressure fluid enters and exits the pressure chamber 35 through the pulsating inlet and outlet 34. Alternatively, the pulsation inlet and the pulsation outlet may be separately provided for respectively filling the pressure chamber into the pressure chamber and withdrawing the pressure chamber.

In another embodiment, the hydraulic device may not perform an extraction operation. Correspondingly, the pressure chamber can be separately provided with an air outlet. When it is desired to reduce the pressure in the pressure chamber, the vent opening opens to release the pressurized gas, thereby reducing the pressure in the pressure chamber.

Further, the hydraulic device can also control the speed at which the pressurized fluid is pumped into the pressure chamber, and the feed rate affects the pressure in the pressure chamber.

In another embodiment of the invention, the pulsating device 2 is a pneumatic device. In the embodiment in which the pneumatic device is used as the pulsating member, the overall structure of the cardiac simulation device is similar to that shown in Fig. 3, so the present embodiment still illustrates the structure of the cardiac simulation device in Fig. 3. In this embodiment, a soft film 32 is also required to be provided in the cylinder block 31. The lower end of the cylinder block 31 is closed, and the region of the soft film 32 to the lower end of the cylinder block 31 is a pressure chamber 35. Similarly, the pressure chamber 35 is provided with a pulsation inlet and outlet 34 for filling and discharging pressurized gas. The air pressure device may be disposed outside the cylinder block 31, and the air pressure device may charge the pressure gas into the pressure chamber 35 by means of a gas pump or the like; or extract the pressure gas from the pressure chamber 35.

Similar to the embodiment in which the hydraulic device is used, when the pressure gas is continuously charged into the pressure chamber 35 to cause the pressure to rise, the soft film 32 is deformed upward by the air pressure, and the space of the chamber is compressed to make the chamber 1 The liquid and blood flow out from the outlet 12. Conversely, when the air pressure device draws out the pressure gas outward, the soft film 32 is deformed downward by the negative pressure, thereby increasing the space of the chamber, so that liquid and blood can be drawn into the chamber 1 from the inlet 11.

In another embodiment, the pneumatic device may not perform a pumping operation. Correspondingly, the pressure chamber can be separately provided with an air outlet. When it is desired to reduce the pressure in the pressure chamber, the vent opening opens to release the pressurized gas, thereby reducing the pressure in the pressure chamber.

The advantage of using a pneumatic device as the pulsating member is that the pneumatic device is pressure controlled. Due to the pressure in the chamber, when the pneumatic device pumps the pressurized gas into the pressure chamber 35, the soft film 32 does not immediately deform and compress the chamber. The pressurized gas will first appear to be compressed. When the pressure of the pressure gas in the pressure chamber 35 is greater than the pressure in the chamber, the pressure gas deforms the soft film 32 upward, compressing the space of the chamber. When the air pressure device sucks out the pressure gas, the pressure gas first appears to expand in volume and decrease in pressure. Then, a negative pressure is generated in the pressure chamber 35 to deform the soft film 32 downward. The compression and expansion process of the pressurized gas can form a pressure buffer for the stroke and suction action of the chamber 1, so that the blood pressure at the outlet and the inlet of the chamber can be maintained at an appropriate pressure without sudden increase or sudden decrease in pressure. The phenomenon. Further, the pneumatic device can also control the speed at which the pressurized gas is pumped into the pressure chamber, and the intake speed affects the pressure in the pressure chamber. By controlling the intake air speed, the magnitude of the pressure output by the air pressure device can be limited to a predetermined value, which is the upper limit of the safe blood pressure at the outlet of the chamber. If the blood pressure of the chamber and its outlet reaches a predetermined value, the air pressure device cannot further inject the pressure gas into the pressure chamber 35, thereby preventing the blood pressure of the outlet from rising further and improving safety.

In addition, in an alternative embodiment of the invention, a pressure monitoring device may also be provided at the outlet or outside of the outlet. The pressure monitoring device is configured to form a circuit connection with the pulsating component or to effect transmission of a signal control signal by the control module. The pressure monitoring device is configured to detect blood pressure at or outside the outlet. If the blood pressure is detected to be too high and the safety range is exceeded, an alarm signal indicating that the blood pressure is too high may be transmitted to the pulsating member; or the alarm signal may be sent to the control module, which then sends a signal to the pulsating member. The pulsating member is configured to stop or slow the stroke of blood in the chamber after receiving an alarm signal from the pressure monitoring device or the control unit; or, the execution of the stroke action may be postponed. In this way, the pressure or blood pressure at the outlet of the chamber can be alleviated, preventing blood pressure from exceeding the safe range and causing harm.

The cardiac simulation device provided by the invention uses a pulsating output to pump out liquid or blood, which can better simulate the blood supply law of a normal heart. The damage to blood cells is small. Importantly, the cardiac simulation device of the present invention introduces the concept of ejection fraction, which controls the amount of reduction in the chamber, thereby reducing the likelihood of adverse effects in the human body.

While the invention has been described in detail with reference to the preferred embodiments of the present invention, it is understood that It will be appreciated by those skilled in the art that the above embodiments may be modified without departing from the scope and spirit of the invention. The scope of the invention is defined by the appended claims.

Claims

A cardiac simulation device, comprising:

a chamber configured to have a variable volume, the chamber having an inlet and an outlet configured to enable liquid to flow from the outside into the chamber, the outlet being configured to enable liquid Flowing out of the chamber to the outside;

a pulsating member configured to expand or contract the volume of the chamber, the chamber for drawing liquid from the inlet when the pulsating member enlarges the volume of the chamber, and the pulsating member reducing the volume of the chamber when the pulsating member is reduced The chamber pumps liquid from the outlet;

The pulsating member is configured to reduce the volume of the chamber by 10% to 90% of the maximum volume to which the pulsating member expands the chamber.
The cardiac simulation apparatus according to claim 1, wherein the cardiac simulation apparatus includes a sealing member, the chamber is located inside the sealing member, and the inlet and the outlet are provided on the sealing member, The inlet and the outlet respectively communicate the chamber with the external space.
The cardiac simulation apparatus according to claim 1 or 2, wherein the sealing member comprises a cylinder body, one end of the cylinder body is a closed end, and the pulsating member protrudes into the cylinder body and faces the inner wall of the cylinder block A sliding seal, the chamber being located in an area from the pulsating member to the sealed end, the pulsating member being configured to slide in the cylinder.
The cardiac simulation device according to any one of claims 1 to 3, characterized in that a soft film is disposed between the pulsating member and the sealing end, and an edge of the soft film is sealingly connected to the sealing member. The area enclosed between the soft film and the sealed end serves as the chamber.
A cardiac simulation apparatus according to any one of claims 1 to 4, wherein the sealing member comprises a cover plate which is sealed at one end of the cylinder to form the closed end.
A cardiac simulation apparatus according to any one of claims 1 to 5, wherein said inlet and outlet are provided on said cover plate;

Alternatively, the inlet and outlet are disposed on the cylinder.
A cardiac simulation apparatus according to any one of claims 1 to 6, wherein The sealing member includes a cover plate sealed at one end of the cylinder to form the closed end,

The edge of the soft film is attached to the inner wall of the cylinder;

Alternatively, the edge of the soft film is attached to the cover.
A cardiac simulation apparatus according to any one of claims 1 to 7, wherein the inlet is provided with an admission flap mechanism, the admission flap mechanism being configured to allow only liquid to enter the exterior from the outside A chamber, the outlet being provided with a quasi-valve mechanism configured to only allow liquid to flow from the chamber to the exterior.
The cardiac simulation apparatus according to any one of claims 1-8, wherein the reduction amount accounts for 40% to 50% of a maximum volume to which the pulsating member expands the chamber;

Alternatively, the amount of reduction is from 55% to 70% of the maximum volume to which the pulsating member expands the chamber.
A cardiac simulation apparatus according to any one of claims 1-9, wherein said pulsating member is a piston, said cardiac simulation device further comprising a rotating machine and a connecting rod assembly, said connecting rod assembly and said piston Forming a crank linkage mechanism, the rotary machine being coupled to the linkage assembly, the piston being configured to reciprocate within the cylinder when the rotary machine rotates A connecting hole for pivotally connecting the links of the link assembly.