• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    Cardiothoracic surgery simulator. The invention relates to a cardiothoracic surgery simulator (100) comprising: - a cardiopulmonary block (10), with an inert heart and lungs; and, - a closed hydraulic circuit (11) to reproduce a part of a cardiovascular system, with a fluid reservoir (20) in fluid connection with a pumping element (30) configured to produce a continuous flow of said fluid from the reservoir (20) towards two circuits: - a main circuit (41) that passes through the cardiopulmonary block (10) with a first flow control element (V1) upstream of the cardiopulmonary block (10) and a second flow control element (V2) downstream of the cardiopulmonary block (10), this first main circuit returning to the fluid reservoir (20) downstream of the second flow control element (V2); - an auxiliary circuit (42), parallel to the main circuit (41) with return to the fluid reservoir (20) and comprising a third flow control element (V3); the cardiothoracic surgery simulator also comprising control means (50) configured: - to alternately act on the first flow control element (V1) and the third flow control element (V3) producing an alternating flow of fluid between the main circuit (41) and the auxiliary circuit (42); and - to act out of phase on the first flow control element (V1) and on the second flow control element (V2) producing a pressure pulse within the cardiopulmonary block (10); so that a pulsatile flow of the fluid is produced through the cardiopulmonary block (10). (Machine-translation by Google Translate, not legally binding)
    公开号:ES2784447A1
    申请号:ES201930264
    申请日:2019-03-25
    公开日:2020-09-25
    发明作者:Rueda Fernando Viadero；Gozalo Sara Naranjo；Espiga Javier Sanchez；Oria Juan María Perez；Del Rincon Alfonso Fernandez；Fernandez Pablo Garcia；Palazuelos José Carlos Manuel
    申请人:Universidad de Cantabria；Fundacion Instituto de Investigacion Marques de Valdecilla；
    IPC主号:
    专利说明:

    [0004] FIELD OF THE INVENTION
    [0005] The present invention belongs to the field of devices and systems for surgical simulation. More specifically, the invention relates to devices and systems for simulating cardiac, cardiopulmonary or cardiothoracic functioning, both in a normal state and in a disease state.
    [0007] BACKGROUND OF THE INVENTION
    [0008] The cardiovascular systems in mammals are formed by a heart to pump blood throughout the body and by a vascular set formed by arteries, veins and other conduits to distribute blood to and from the heart.
    [0010] Cardiothoracic surgical operations are normally very complex and long-lasting. For this reason, it is often not possible to combine the surgery itself with training tasks for surgeons, nurses and other inexperienced medical personnel. For this reason, cardiopulmonary simulators are necessary to train surgeons and surgical teams in complex techniques and scenarios.
    [0012] RW Morris et al have proposed ( "Orpheus" Cardiopulmonary Bypass Simulation System, The Journal of The American Society of Extra-Corporeal Technology, JECT, 2007; 39: 228-233) a perfusion simulation system for drug administration for training of perfusionists. The system consists of a hydraulic simulator, an electronic interface and a computer to control the system. The hydraulic simulator consists of an electronic circuit arranged on a base plate. The hydraulic simulator does not interact with a cardiopulmonary block, either organic or inorganic, that is, it does not interact with any tissue.
    [0014] In turn, Paul S. Ramphal et al have proposed a cardiac surgery simulator ( Paul S. Ramphal et al, A high fidelity tissue-based cardiac surgical simulator, European Journal of Cardio-thoracic Surgery 27 ( 2005) 910-916) , which includes a porcine heart that, to simulate its pulsatility or beat, incorporates in the right and left ventricles both balloons connected to a computer controlled pneumatic pump. This simulator also includes a perfusion line through which a liquid that simulates blood circulates continuously through the coronary arteries, coronary veins and cavities of the heart. This fluid circulation - carried out by a hydraulic pump - remains constant, it lacks pulsatility, so it does not realistically reproduce the functioning of the vascular system.
    [0016] On the other hand, patent document WO-2016/019331-A1 discloses a cardiovascular simulator that, among others, comprises a cardiac simulator module, and two closed circuits, one hydraulic and the other pneumatic, configured to simulate the cardiovascular functioning of a human or other mammal.
    [0018] Patent document WO-2017/165969-A1 discloses an apparatus for simulating a cardiovascular system based on a closed-circuit fluid circulation system.
    [0020] Therefore, there is a need to develop a new cardiothoracic simulator system that provides greater realism than conventional devices and systems, especially that provides pulsatility in the vascular system. It is also desirable to achieve a cardiothoracic simulator system that is reusable and simple to construct.
    [0022] DESCRIPTION OF THE INVENTION
    [0023] The present disclosure provides a new cardiothoracic surgery simulator that overcomes the drawbacks of conventional cardiothoracic surgery simulation devices and systems, providing considerable realism in pulsatile functions.
    [0025] The problem posed by the existing solutions on the market is solved by the cardiothoracic surgery simulator of the present invention, which through the conjunction of a cardiopulmonary block (can be organic or artificial) and a controlled hydraulic circuit that reproduces a substantial part of the cardiovascular system , provides a perception of realism by users who use the simulator in the recreation of the movements and functions of the tissues that make up the cardiopulmonary block.
    [0026] In a first aspect of the present disclosure, a cardiothoracic surgery simulator is provided comprising:
    [0027] - a cardiopulmonary block, comprising at least one inert heart and two inert lungs; Y,
    [0028] - a closed hydraulic circuit, configured to reproduce a part of a cardiovascular system comprising:
    [0029] - a fluid reservoir;
    [0030] - a pumping element in fluid connection with said tank, the pumping element being configured to produce a continuous flow of said fluid from the tank towards two circuits:
    [0031] - a first main circuit that passes through the cardiopulmonary block and comprising a first flow control element located upstream of the cardiopulmonary block and a second flow control element located downstream of the cardiopulmonary block, this first main circuit returning to the fluid reservoir downstream of the second flow control element;
    [0032] - a second auxiliary circuit, parallel to the first main circuit with return to the fluid reservoir, and comprising a third flow control element;
    [0033] where the cardiothoracic surgery simulator also comprises configured control means:
    [0034] - to act alternately on the first flow control element and the third flow control element producing a pulsating flow between the first circuit, main circuit, and the second circuit, auxiliary circuit, evacuating the excess part of the fluid through the auxiliary circuit , the pulsating flow that circulates through the first, main circuit, in a proportion of between 25% and 40% of the total flow and through the second, auxiliary circuit, the rest of the flow, that is, between 60% and 75%. Y
    [0035] - to act out of phase on the first flow control element and on the second flow control element producing a pressure pulse within the cardiopulmonary block;
    [0036] so that through this dual control, a pulsatile flow of fluid is produced through the inert heart and lungs of the cardiopulmonary block.
    [0038] Thanks to this doubling of the continuous flow of the pumping element in the first main circuit and the second auxiliary circuit, it is possible to reproduce a pulsatile flow in the cardiopulmonary block.
    [0040] In the present cardiothoracic surgery simulator, this pressure relationship between the first main circuit and the second auxiliary circuit can be modified according to the characteristics of the cardiopulmonary block, adapting it to achieve the best possible degree of realism. This is done by properly programming the control means. In other words, the pressure relationship between circuits is carried out by means of the control software, acting on the variable characteristics of the elements arranged in the circuits, so that the operating parameters can be modified.
    [0042] The control means configured to act out of phase on the first flow control element and on the second flow control element may have an offset of between 100 and 250 milliseconds. These delayed actuation times can be adjusted according to the characteristics of the cardiopulmonary block (especially size and rigidity). This is done by properly programming the control means. The control software allows establishing time differences in the opening sequence of the flow control elements and thus being able to regulate the lag depending on the cardiothoracic group, taking into account its size and its variable physiology.
    [0044] The fluid can be a fluid with a viscosity and density similar to that of blood, to better reflect the actual behavior of a cardiovascular system. The fluid can have a density between 1040 and 1070 g / ml, and preferably between 1053 and 1060 g / ml.
    [0046] Thanks to this combination of closed hydraulic circuit and dual control of the cardiothoracic surgery simulator, a pulsatile flow is generated in the cardiopulmonary block, achieving the reproduction of the palpitation effect as well as pulsatility and filling of the heart in a dead (or artificial) heart and lungs. blood vessels with great realism, so that the training is in a scenario as close to reality. In other words, circulation is recreated through the inert heart and lungs, managing to work with the inert heart and lungs as if they were working, recreating in them the circulation and pulsatility of blood flow. Circulation through the inert heart and lungs is important, among other reasons, due to the incidence of fluid in the lung parenchyma, which has a determining influence on the inflation and deflation of lung tissue, in the recreation of lung ventilation. In addition, this movement of the lungs - inflated and deflated - increases the degree of realism of the simulator by affecting with its movement the positioning of the rest of the cardiopulmonary block.
    [0048] In some embodiments the first, second, and third flow control elements are implemented as all or nothing valves (eg, by solenoid valves). In this way, precise control of the fluid circulation is allowed, as well as frequent actuation, which is especially useful in the present simulator, since it allows the generation of different degrees of heart rate simulating different clinical situations.
    [0050] The pumping element can be a positive displacement pump, which makes it possible to provide a fluid flow with great accuracy, regardless of the fluid pressure through the closed hydraulic circuit; moreover, it is advantageous to circulate fluids with a certain viscosity, such as blood. This pumping element can be regulated with different ranges of pressures and pulsatility like those of the human body.
    [0052] In some embodiments, the cardiothoracic surgery simulator further comprises a fourth proportional flow control element in the second auxiliary circuit, downstream of the third flow control element, and two pressure sensors located respectively in the first main circuit and in the second. auxiliary circuit. This fourth element of proportional flow control allows the degree of opening to be varied according to the pressure measured by the pressure sensors (eg if there is a leak in the cardiopulmonary block), and thus, the working pressure of the simulator. It also helps the main and auxiliary circuits work properly.
    [0054] As mentioned, by suitably programming the control means, the pressure relationship between the first main circuit and the second auxiliary circuit can be modified as a function of the characteristics of the cardiopulmonary block. More specifically, for example, if the opening times of the first and second flow control elements and the opening degree of the fourth flow control element are modified, the operating conditions of the pumping equipment can be modified (flow and pressure ) and of the hydraulic circuits that make up the simulator, adapting in this way to the physiology of the cardiothoracic group used.
    [0056] In some embodiments, to promote heart movement and give more realism, the Cardiothoracic surgery simulator further comprises a pulsatile air system to pump air into the inert heart. The pulsating air system is regulated by the control means to produce a pulsatile air flow synchronized with the actuation of the first flow control element and the third flow control element. In this way, it is possible to favor the movement of the walls of the heart, improving the perception of realism of the movement of the heart. This pulsatile air system may comprise an occlusion balloon that can be inserted into the inert heart, usually the right ventricle. That is, the pulsatile air system acts directly on the inner wall of the heart.
    [0058] The cardiothoracic surgery simulator can also comprise a pulmonary ventilator to provide more movement to the two inert lungs (or two elements that simulate both lungs), improving the user's perception of the movement of the cardiopulmonary block.
    [0060] Thanks to the cardiothoracic surgery simulator of the present invention, the animal impact associated with this type of practice is reduced, since several interventions can be performed with each cardiopulmonary block. In this way, several different practices are allowed in the same session.
    [0062] On the other hand, this simulator makes it possible to work in a wide range of highly complex simulation scenarios. It is not just a setup for perfusion or for parts of more complex procedures, experimental validation certainly shows the possibility of its use for complex scenarios.
    [0064] In the cardiothoracic surgery simulator of the present invention, the inert heart and inert lungs can be inorganic models of elasto-plastic material, that is, in the event of a deformation they may not recover their original shape, and have a non-linear behavior. It may also be that both are organic models (ex vivo); They are dead, but they have been alive. It is also possible that the heart is organic and the lungs inorganic, or vice versa.
    [0066] The control means can be connected to a user-friendly input / output interface that makes it possible to easily modify the operating parameters of the different elements of the simulator, depending, for example, on the characteristics of the cardiopulmonary block.
    [0067] The different aspects and embodiments of the invention defined above can be combined with each other, provided they are mutually compatible.
    [0069] Additional advantages and features of the invention will be apparent from the detailed description that follows and will be pointed out particularly in the appended claims.
    [0071] BRIEF DESCRIPTION OF THE FIGURES
    [0072] To complement the description and in order to help a better understanding of the characteristics of the invention, according to an example of a practical embodiment thereof, a set of figures is attached as an integral part of the description, in which with character Illustrative and not limiting, the following has been represented:
    [0074] Figure 1 schematically shows the main elements of the cardiothoracic surgery simulator of the present invention.
    [0076] Figure 2 shows in more detail the different elements of the cardiothoracic surgery simulator of the present invention, according to a possible embodiment thereof.
    [0078] DETAILED DESCRIPTION OF THE INVENTION
    [0079] The description that follows is not to be taken in a limited sense, but is provided solely for the purpose of describing broad principles of the invention. The following embodiments of the invention will be described by way of example, with reference to the figures cited above, which show apparatus and results according to the invention.
    [0081] As shown in Figure 1, the cardiothoracic surgery simulator 100 of the present invention comprises a cardiopulmonary block 10, which can be organic or inorganic; an electro-hydraulic installation 11, and a control system 50 for controlling the electro-hydraulic installation. The arrow originating from the electrohydraulic installation 11 and destined for the cardiopulmonary block 10 represents the pulsatile inflow to the cardiopulmonary block 10. The arrow originating from the cardiopulmonary block 10 and destined for the electrohydraulic installation 11 represents the outlet drain. The arrow originating in the electrohydraulic installation 11 and destined for the control system 50 represents the input signals to the control system 50. The arrow originating in the control system 50 and destined for the electrohydraulic installation 11 represents the output signals of the control system 50.
    [0083] The cardiopulmonary block 10 is a conventional cardiopulmonary block. It can be organic or artificial, and in the example referred to here it includes (not illustrated) an exvivo organic heart (it can be, for example, pig or sheep), two lungs, also for example exvivo, for example pig or of sheep, correspondingly connected. The electrohydraulic installation 11 is connected to the cardiopulmonary block 10, specifically to the vena cava and aorta artery, not illustrated, thereof. The cardiopulmonary block 10 also has a trachebronchial shaft, not illustrated, connectable to a ventilator 80 in the event that a ventilator is used.
    [0085] As shown in Figure 2, the electro-hydraulic installation comprises hydraulic circuits fed by a positive displacement pump 30; This pump is connected to an open reservoir 20 that supplies the hydraulic circuits with a liquid similar to blood. For example, a mixture of glycerin and dye is used as the fluid, although other embodiments are possible. Pump 30 performs the pumping function that the heart performs in a living heart.
    [0087] This positive displacement pump 30 produces a continuous flow of said liquid from the reservoir 20 towards a conduit with a branch 40a in two hydraulic circuits:
    [0088] - a main circuit 41, and
    [0089] - an auxiliary circuit 42.
    [0091] To manage the operating parameters of this pump 30, a frequency variator 70 is included. By varying the working speed of the pump 30, the flow rate and, therefore, the pressure is acted upon.
    [0093] The main circuit 41 connects the pump 30 with the heart of the cardiopulmonary block 10 through conduits that culminate in a Foley catheter 13 that is connected to the vena cava of the cardiopulmonary block. That is, the Foley catheter 13 is inserted into the right atrium of the heart (not shown). After passing through the interior of the heart and lungs in a similar way to how the blood flow does in a mammal, The fluid is drained through the aorta artery of the cardiopulmonary block until its outlet 12, directing the flow back to the reservoir 20.
    [0095] The main circuit 41 includes a first valve V1 upstream of the cardiopulmonary block 10 and a second valve V2 downstream of the cardiopulmonary block 10. Both valves V1 and V2 are all-or-nothing solenoidal valves, so that the entry of liquid into the cardiopulmonary block 10 and its evacuation.
    [0097] The auxiliary circuit 42 allows the circulation of the liquid with direct return to the reservoir 20 along a line parallel to the main circuit 41 when in the cardiopulmonary block 10, and specifically in the heart, pressure relief has to be produced.
    [0099] In the auxiliary circuit 42 a third valve V3 is arranged (it is also an all or nothing solenoid valve), downstream of the branch 40a; downstream of this third valve V3 a fourth proportional valve V4 is arranged. Thanks to this fourth proportional valve V4, analogous conditions can be generated in both circuits 41, 42 by controlling the throttling of the passage through it, consequently achieving the rise of the nominal pressure inside the simulator, being able to control the pressure within the heart chambers and lungs.
    [0101] The control system 50 acts alternately on the first and third valves V1 and V3, that is, when the first valve V1 is open, the third valve V3 is closed, and vice versa. In this way, it is possible to provide the flow with pulsatility without the need to modify the operation of the pump 30, which can maintain the continuous flow of liquid. The control system 50 is configured so that, in each cycle, the opening ratio of the first and third valves is approximately 1 / 3-2 / 3 (although, of course, another ratio is acceptable), so that the most of the time the liquid circulates through the auxiliary circuit 42. In this way, the real functioning of a heart is reproduced, in which approximately two thirds of the total duration of the cycle corresponds to diastole and one third to systole.
    [0103] On the other hand, to achieve a rise in pressure within the heart, the opening of the second valve V2 is done in a phase out of phase with respect to the first valve V1 in order to have a pressure pulse: the control system acts on the first valve
    [0106] V1, opening it, and between 100 and 250 milliseconds later open the valve V2 to relieve the pressure and let the liquid circulate back to the reservoir.
    [0108] In this way, starting from a continuous flow of liquid that leaves the pump 30, it is possible to make the flow pulsatile, which translates into filling and pulsatility of blood vessels and tissues of the lungs. This facilitates the simulation of a bleeding during an intervention.
    [0110] In this exemplary embodiment, the control of the opening and closing of the first, second and third valves V1, V2, V3, is carried out with switching circuits where the position of the internal valve stem is controlled from relays. The control of the opening degree of the fourth proportional valve V4 is carried out in a conventional way from output signals of a microcontroller (in this case, by means of an Arduino Mega 2560 microcontroller); From digital voltage signals with a value between, for example, 0 and 10 V, the degree of opening of the valve is established.
    [0112] In the embodiment shown, the cardiothoracic surgery simulator 100 of the present invention further comprises a pair of pressure sensors S1, S2, located respectively in the main circuit 41 and in the auxiliary circuit 42. The first pressure sensor S1 is positioned at parallel to the cardiopulmonary block 10 to provide an approximate reading of the pressure therein; the second pressure sensor S2 is located in the auxiliary circuit 42 upstream of the fourth proportional valve V4 to give a reading similar to that of the main circuit 41 and thus determine if the pressure setting between the main and auxiliary circuits is correct to achieve analogous operation.
    [0114] The pressure data collection of these first and second sensors is carried out by the control system 50. For this reading of the pressure sensor signals, a standard circuit is used to condition the signal of, for example, 4-20 mA provided by the pressure sensors in a signal suitable for reading through the Arduino's analog inputs.
    [0116] The cardiothoracic surgery simulator 100 of Figure 2 further comprises a pulsatile air system 60 comprising a syringe and a linear actuator connected to a Fogarty occlusion catheter or balloon that is retrogradely introduced through the artery. aorta from cardiopulmonary block 10 and left in the left ventricle. The air that inflates the occlusion balloon acts directly on the inner wall of the heart. In this way, the movement of the heart walls is promoted, by means of the inflation and emptying of this balloon produced by the alternative linear movement of the actuator. The linear actuator incorporates a servomotor controlled by the control system 50 that allows its rotation to be controlled. In this way, thanks to this direct contact between the occlusion catheter and the heart wall, efforts can be transmitted that generate deformations, that is, movements in the heart from the internal pressure in the form of air that the catheter has.
    [0118] Finally, a lung ventilator 80 is used to give movement to the lung tissue; Although it does not have the function of oxygenation of the blood, it does provide the whole with the appropriate movement since the morphology of the cardiopulmonary block 10 makes the heart rest on the lungs and that their movement also affects it.
    [0120] In the present case, part of the elements of the cardiothoracic surgery simulator (or even all of it) is inserted inside a housing, specifically designed and constructed by 3D printing. The casing has an anthropomorphic shape on the outside, and includes holes and hooking systems to be able to carry out interventions. The casing is equipped with lateral holes of sufficient dimensions to be able to intervene and provide the necessary tools, as well as a pair of smaller holes to allow the introduction of the cameras used in minimally invasive surgeries. The upper part includes a rectangular-shaped hole, similar to the opening made for cardiac interventions.
    [0122] In this text, the term "comprises" and its derivations (such as "comprising", etc.) should not be understood in an exclusive sense, that is, these terms should not be interpreted as excluding the possibility that what is described and it is defined to include elements, additional stages, etc.
    [0124] In the context of the present invention, the term "approximately" and terms of its family (such as "approximate", etc.) should be interpreted as indicating values very close to those that accompany said term. That is, a deviation within reasonable limits from an exact value should be accepted, because an expert In the field you will understand that such a deviation from the indicated values may be unavoidable due to measurement inaccuracies, etc. The same applies to the terms "about", "about" and "substantially".
    [0126] The invention is not obviously limited to the specific embodiment (s) described, but also encompasses any variation that may be considered by any person skilled in the art (for example, in relation to the choice of materials, dimensions, components, configuration, etc.), within the general scope of the invention as defined in the claims.
    one
    权利要求:
    Claims (12)
    [1]
    1. Cardiothoracic surgery simulator (100) comprising:
    - a cardiopulmonary block (10), comprising at least one inert heart and two inert lungs; Y
    - a closed hydraulic circuit (11), configured to reproduce a part of a cardiovascular system, comprising:
    - a fluid reservoir (20);
    - a pumping element (30) in fluid connection with said tank, the pumping element being configured to produce a continuous flow of said fluid from the tank (20) towards two circuits:
    - a first main circuit (41) that passes through the cardiopulmonary block (10) and comprising a first flow control element (V1) located upstream of the cardiopulmonary block (10) and a second flow control element (V2) located downstream of the cardiopulmonary block (10), this first main circuit returning to the fluid reservoir (20) downstream of the second flow control element (V2);
    - a second auxiliary circuit (42), parallel to the first main circuit (41) with return to the fluid reservoir (20) and comprising a third flow control element (V3);
    where the cardiothoracic surgery simulator also comprises control means (50) configured:
    - to act alternately on the first flow control element (V1) and the third flow control element (V3) producing a pulsating flow between the first main circuit (41) and the second auxiliary circuit (42), the flow being pulsating in a proportion of between 25% and 40% by the first main circuit (41) and between 60% and 75% by the second auxiliary circuit (42); and - to act out of phase on the first flow control element (V1) and on the second flow control element (V2) producing a pressure pulse within the cardiopulmonary block (10);
    so that a pulsatile flow of the fluid is produced through the inert heart and inert lungs of the cardiopulmonary block (10).
    [2]
    The cardiothoracic surgery simulator (100) of claim 1, further comprising a fourth proportional flow control element (V4) in the second circuit auxiliary (42), downstream of the third flow control element (V3), and two pressure sensors (S1, S2), located respectively in the first main circuit (41) and in the second auxiliary circuit (42).
    [3]
    The cardiothoracic surgery simulator (100) of any of claims 1-2, further comprising a pulsatile air system (60) for pumping air into the inert heart, the pulsatile air system (60) being controlled by the control means (50) for producing a pulsatile air flow synchronized with the actuation of the first flow control element (V1) and the third flow control element (V3).
    [4]
    The cardiothoracic surgery simulator (100) of claim 3, wherein the pulsatile air system (60) comprises an inert heart-insertable occlusion balloon.
    [5]
    The cardiothoracic surgery simulator (100) of any of claims 1-4, further comprising a lung ventilator (80) to provide movement to the two inert lungs.
    [6]
    The cardiothoracic surgery simulator (100) of any of claims 1-5, wherein the pump element (30) is a positive displacement pump.
    [7]
    The cardiothoracic surgery simulator (100) of any of claims 1-6, wherein the fluid has a density similar to the density of blood.
    [8]
    8. The cardiothoracic surgery simulator (100) of any of claims 1-7, wherein the control means (50) configured to act out of phase on the first flow control element (V1) and on the second control element flow control (V2) apply an offset of between 100 and 250 milliseconds.
    [9]
    The cardiothoracic surgery simulator (100) of any of claims 1-8, wherein the inert heart comprises an inorganic heart of elastoplastic material.
    [10]
    The cardiothoracic surgery simulator (100) of any of claims 1-8, wherein the inert heart comprises an exvivo organic heart.
    one
    [11]
    The cardiothoracic surgery simulator (100) of any of claims 5-10, wherein the inert lungs comprise inorganic lungs of elastoplastic material.
    [12]
    12. The cardiothoracic surgery simulator (100) of any of claims 5-10, wherein the inert lungs comprise exvivo organic lungs.
    one
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    同族专利:
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    引用文献:
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    US20130196301A1|2012-01-31|2013-08-01|David Jeffrey Carson|Cardiac Simulation Device|
    US20170102846A1|2015-10-07|2017-04-13|MAQUET CARDIOPULMONARY GmbH|User interface system for a medical device|
    CN108682255A|2018-06-15|2018-10-19|同济大学|Pulsatile cardiac model and its ripple control method|
    CN109091147A|2018-09-26|2018-12-28|赖飞|A kind of respiration simulator for cardiopulmonary exercise functional test|
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