WO2012130052A1 - Dispositif d'induction d'une insuffisance cardiaque chez un animal - Google Patents

Dispositif d'induction d'une insuffisance cardiaque chez un animal Download PDF

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Publication number
WO2012130052A1
WO2012130052A1 PCT/CN2012/072437 CN2012072437W WO2012130052A1 WO 2012130052 A1 WO2012130052 A1 WO 2012130052A1 CN 2012072437 W CN2012072437 W CN 2012072437W WO 2012130052 A1 WO2012130052 A1 WO 2012130052A1
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WIPO (PCT)
Prior art keywords
heart failure
ventricle
chamber
animal
animal heart
Prior art date
Application number
PCT/CN2012/072437
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English (en)
Chinese (zh)
Inventor
杨碧波
Original Assignee
Yang Bibo
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Filing date
Publication date
Application filed by Yang Bibo filed Critical Yang Bibo
Publication of WO2012130052A1 publication Critical patent/WO2012130052A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A01—AGRICULTURE; FORESTRY; ANIMAL HUSBANDRY; HUNTING; TRAPPING; FISHING
    • A01K—ANIMAL HUSBANDRY; AVICULTURE; APICULTURE; PISCICULTURE; FISHING; REARING OR BREEDING ANIMALS, NOT OTHERWISE PROVIDED FOR; NEW BREEDS OF ANIMALS
    • A01K67/00—Rearing or breeding animals, not otherwise provided for; New or modified breeds of animals
    • A01K67/027—New or modified breeds of vertebrates
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
    • A61F2/2478—Passive devices for improving the function of the heart muscle, i.e. devices for reshaping the external surface of the heart, e.g. bags, strips or bands
    • A—HUMAN NECESSITIES
    • A01—AGRICULTURE; FORESTRY; ANIMAL HUSBANDRY; HUNTING; TRAPPING; FISHING
    • A01K—ANIMAL HUSBANDRY; AVICULTURE; APICULTURE; PISCICULTURE; FISHING; REARING OR BREEDING ANIMALS, NOT OTHERWISE PROVIDED FOR; NEW BREEDS OF ANIMALS
    • A01K2207/00—Modified animals
    • A01K2207/30—Animals modified by surgical methods
    • A—HUMAN NECESSITIES
    • A01—AGRICULTURE; FORESTRY; ANIMAL HUSBANDRY; HUNTING; TRAPPING; FISHING
    • A01K—ANIMAL HUSBANDRY; AVICULTURE; APICULTURE; PISCICULTURE; FISHING; REARING OR BREEDING ANIMALS, NOT OTHERWISE PROVIDED FOR; NEW BREEDS OF ANIMALS
    • A01K2227/00—Animals characterised by species
    • A01K2227/10—Mammal
    • A—HUMAN NECESSITIES
    • A01—AGRICULTURE; FORESTRY; ANIMAL HUSBANDRY; HUNTING; TRAPPING; FISHING
    • A01K—ANIMAL HUSBANDRY; AVICULTURE; APICULTURE; PISCICULTURE; FISHING; REARING OR BREEDING ANIMALS, NOT OTHERWISE PROVIDED FOR; NEW BREEDS OF ANIMALS
    • A01K2267/00—Animals characterised by purpose
    • A01K2267/03—Animal model, e.g. for test or diseases
    • A01K2267/035—Animal model for multifactorial diseases
    • A01K2267/0375—Animal model for cardiovascular diseases
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/38—Applying electric currents by contact electrodes alternating or intermittent currents for producing shock effects
    • A61N1/385—Devices for inducing an abnormal cardiac function, e.g. fibrillation

Definitions

  • the present invention relates to an animal heart failure inducing device, and more particularly to an animal heart failure inducing device for simulating a pathophysiological process of heart failure caused by a major human heart disease.
  • Heart failure is a syndrome caused by various cardiovascular diseases leading to cardiac mechanical systolic dysfunction.
  • the reason is that the decrease in myocardial contractility causes the blood volume of the heart to fail to meet the needs of the body's metabolism.
  • the systolic blood flow declines, the blood remains in the ventricle, the diastolic blood filling decreases, and the ventricular contractile-diastolic volume change rate decreases.
  • Blood accumulation in the heart makes the endocardial pressure increase and the heart chamber expands.
  • the further reduction of myocardial contractility is aggravated by cardiac dysfunction, resulting in blockage of the circulation and pulmonary circulation, resulting in body and pulmonary circulation. Insufficient blood supply to the body and blood stasis in the body and pulmonary circulation will lead to metabolic disorders in the body.
  • Heart failure models such as rats, rabbits, cats, dogs, sheep, pigs, monkeys, baboons, and the like.
  • pigs and dogs and other large animals have larger individuals, more advanced cardiovascular system, better neurological fluid regulation, easier operation and observation, and are ideal experimental materials, which can be widely used in heart failure mechanism research and drug evaluation.
  • the pressure overload type heart failure model often achieves ventricular resistance load by narrowing the aorta and renal artery of experimental animals, and induces cardiomyocyte hypertrophy, which is suitable for studying the pathophysiological process of cardiac hypertrophy to heart failure.
  • the pressure overload type heart failure model is used to evaluate the value of the drug, and the experimental process is unstable and the cycle is long. It is difficult to carry out simulation experiments in large animals.
  • the capacity overload type heart failure model simulates the heart force caused by the expansion of the heart chamber during cardiac preload overload Depletion, commonly used to study changes in neuroendocrine mechanisms, water and electrolyte imbalances, and renal dysfunction in heart failure, has limited role in evaluating the efficacy of anti-heart failure drugs.
  • the method for preparing the volume overload type heart failure model includes the arteriovenous fistula method and the valve insufficiency method. Because the size of the fistula and the degree of regurgitation of the valve are difficult to grasp, the degree of heart failure is difficult to control, and the mortality of the animals being tested is high.
  • the myocardial contractility-deficient heart failure model is suitable for a variety of experimental animals, with good clinical approximation and easy control of heart failure, and has become the most widely used model.
  • Methods for achieving a myocardial contractility-deficient heart failure model include occlusion of coronary artery-induced ischemic cardiomyopathy and rapid ventricular pacing. Obstruction of coronary artery-induced ischemic cardiomyopathy can be performed by interventional embolization, without thoracotomy, small trauma, accurate positioning, suitable for large animals, and small animals need to open the chest to directly ligature the coronary artery.
  • Rapid ventricular pacing uses electrodes to rapidly pace the heart, causing severe disruption of hemodynamics, decreased myocardial blood supply, and decreased myocardial contractility, resulting in heart failure.
  • the rapid ventricular pacing method is mostly used for larger animals, with shorter production cycle, better controllability, and the animal can remain awake during model making. It is suitable for various studies of heart failure and can be used to evaluate drugs.
  • the spontaneous heart failure model has outstanding features for studying the natural occurrence of myocardial lesions and heart failure in animals, and is closer to the clinical situation than other models. It is suitable for studying myocardial biochemical metabolism, contractile properties and ultrastructural changes in debilitated heart, especially for cardiomyopathy. Mechanisms of occurrence and preventive treatment.
  • the animal model of spontaneous heart failure is limited in animal selection, and the heart failure process is difficult to regulate.
  • the invention provides an animal heart failure inducing device, which is used for implanting into an experimental animal, artificially causing heart failure of an experimental animal, thereby simulating a heart failure disease caused by a major human disease. Physiological processes.
  • a composite animal heart failure inducing device which can be implanted into an animal for simulating a pathophysiological process of human heart failure and evaluating a drug action, including: ventricular restriction a mechanism, the ventricular restriction mechanism configured to be implantable into the intraventricular, and comprising: a support device having a concave structure substantially adapted to an inner shape of the ventricle for implantation into the intraventricular; the telescopic device The telescoping device is partially housed within the concave structure of the support device; and an extracardiac chamber configured to be disposed outside of the ventricle or outside the animal and to be telescopic The device is in fluid communication through a connecting tube that includes an elastic member.
  • the retractable device retracts into the concave structure and drives the elastic member to contract by a driving medium; during diastole, the contracted elastic member drives the elastic medium through a driving medium A telescopic device expands from the concave structure.
  • the extracardiac chamber further includes: a closed hard outer casing; and a diaphragm, the diaphragm being disposed in the outer casing and partitioning an inner portion of the outer casing into a first chamber And a second chamber, the first chamber housing the drive medium and in fluid communication with the telescopic device through the connection tube, the resilient member being disposed within the second chamber and opposing the diaphragm Move and scale.
  • the animal heart failure inducing device further includes a conduit in communication with the first chamber to introduce the driving medium into the first chamber and the retractable device through the conduit or from the first chamber And driving the drive medium in a retractable device.
  • the outer casing has a concave shape matching the shape of the outer portion of the ventricle to attach the outer casing to the apex portion of the ventricle.
  • the supporting device is a flexible supporting net having a memory property which can be contracted into a tubular structure.
  • the supporting device is made of a material having a memory property.
  • the retractable device is a flexible capsular structure adapted to the ventricle morphology when expanded from the concave structure.
  • the retractable device is provided in a state in which the shape of the systole and the diastolic phase are fixed.
  • the capsule includes an action portion located at an upper portion and a non-operating portion at a lower portion housed in the support device, and an outer portion of the non-operating portion of the capsule is uniformly coated with a reinforcing film. The support net and the non-action part are firmly bonded.
  • the elastic modulus of the elastic member is set such that the pressure of the driving medium in the first chamber is maintained below the systolic pressure of the ventricle and higher than the diastolic pressure of the ventricle.
  • An animal heart failure inducing device can be implanted into an animal of an experiment, and since the heart of the experimental animal is implanted with a ventricular restriction mechanism including a supporting device, the amplitude of the contraction movement of the apical ventricular wall is limited. Reduces the ability of the heart to pump blood. At the same time, a certain degree of filling of the ventricular restriction mechanism increased the ventricular dead space, further reduced the heart and blood, artificially caused the heart failure of experimental animals.
  • FIG. 1 is a schematic view showing a state in which an animal heart failure inducing device is in a cardiac systole according to an exemplary embodiment of the present invention.
  • Fig. 2 is a schematic view showing a state in which an animal heart failure inducing device is in a cardiac diastolic phase according to an exemplary embodiment of the present invention.
  • Figure 3 is a schematic illustration of a ventricular restriction mechanism in a fully expanded state, in accordance with an exemplary embodiment of the present invention.
  • Fig. 4 is a partial cross-sectional view showing the supporting device of the ventricular restriction mechanism shown in Fig. 3.
  • Figure 5 is a schematic illustration of an embodiment of a support device when opened.
  • Fig. 6 is a schematic cross-sectional view showing the ventricular restriction mechanism as an embodiment of the retractable device when deployed.
  • Figure 7 is a schematic illustration of the ventricular restraint mechanism placed in the delivery tube after contraction.
  • Figure 8 is a schematic illustration of an animal heart failure inducing device according to the present invention implanted in an animal heart in a retracted state during cardiac contraction.
  • FIG. 9 is a schematic illustration of an animal heart failure inducing device according to the present invention implanted in an animal heart in an open state during diastole. detailed description
  • FIG. 1 is a schematic diagram of an animal heart failure inducing device in a systole phase according to an exemplary embodiment of the present invention
  • FIG. 2 is an animal heart failure inducing device in a diastolic phase according to an exemplary embodiment of the present invention.
  • An animal heart failure inducing device 100 according to an exemplary embodiment of the present invention is implanted into an animal, controllably restricting cardiac function of the experimental animal and inducing heart failure, for systematically and controllably reducing cardiac function of the experimental animal and Eventually leading to heart failure, including: ventricular restriction mechanism 1 and extraventricular chamber 2.
  • the ventricular restriction mechanism 1 is configured to be implanted into the ventricle 3 by surgery (see Figs.
  • the extracardiac chamber 2 is configured to be disposed outside the ventricle 3 (see Figs.
  • the extraventricular chamber 2 including an elastic member such as a spring twenty one.
  • the retractable device 12 in the systole of the experimental animal, the retractable device 12 is retracted into the concave structure 13 and drives the elastic member 21 to contract by the fluid-driven medium; during the diastolic phase, the contracted elastic member 21 is driven by the driving medium.
  • the telescopic device 12 is expanded from the concave structure 13.
  • the extracardiac chamber 2 further comprises: a closed hard outer casing 22 made of, for example, a metal material such as stainless steel, nickel titanium alloy, or a high molecular polymer material; and a flexible material
  • a diaphragm 23 is formed, the diaphragm 23 being disposed within the outer casing 22 and dividing the interior of the outer casing 22 into a first chamber 24 and a second chamber 25, the first chamber 24 containing a drive such as a liquid or a gas
  • the medium is in fluid communication with the telescopic device 12 through the connecting tube 4, and the elastic member 21 is disposed in the second chamber 25 and expands and contracts against the action of the diaphragm 23.
  • the pressure of the driving medium in the retractable device 12 and the first chamber 24 is increased by compression of the ventricular wall 33, thereby driving the elastic member 21 to contract; and during diastole, The pressure of the drive medium in the retractable device 12 and the first chamber 24 becomes smaller due to the relaxation of the ventricular wall 33, so that the contracted elastic member 21 is expanded from the concave structure 13 by the drive medium driving the retractable device 12.
  • the elastic modulus of the elastic member 21 is set such that the pressure of the liquid in the first chamber 24 is kept lower than the systolic pressure of the ventricle 3 and higher than the diastolic pressure of the ventricle 3, so that the elastic member 21 is in the systole phase. It is compressed under the push of the diaphragm 23, and stretches during the diastole and pushes the diaphragm 23 to move.
  • the outer casing 22, as shown in Figures 1 and 2 has a concave shape that matches the convex shape of the apex of the ventricle, e.g., a meniscus shape, to attach the outer casing 23 to the apex of the ventricle.
  • the concave shell 22 of the cardiac chamber 2 will be tightly bonded to the outside of the heart due to the formation of scar tissue on the surface of the heart. together.
  • the extraventricular chamber 2 can also be placed outside the animal body in fluid communication with the telescoping device 12 through the elongated connecting tube 4.
  • the retractable device 12, the connecting tube 4 and the first chamber 24 constitute a closed container containing a driving medium such as a liquid, which The shape can vary with the contraction and relaxation of the heart, but the volume remains essentially unchanged.
  • a driving medium such as a liquid
  • the retractable device 12 is retracted into the concave structure 13 of the support device 11 by compression of the ventricular wall 33, such that the amount of liquid in the telescopic device 12 is changed.
  • the apex of the ventricle is deformed little or even without deformation. It should be noted that the volume of the concave space in the concave structure 13 is smaller than the volume of the normal ventricle (i.e., the normal ventricle in which the ventricular restriction mechanism is not placed).
  • the retractable device 12 contracts into the concave structure 13, and a portion of the blood in the ventricle remains in the concave structure 13, so that the heart cannot be normalized.
  • the blood is pumped through the aortic valve 31 to the main (lung) artery, that is, the support device 11 limits the contraction of a portion of the ventricular wall 33, and the ineffective lumen of the ventricle 3 is enlarged; while during the diastolic phase, the retractable device 12
  • the concave structure 13 expands out, and the space in the ventricle for accommodating blood is reduced, so that a portion of the blood cannot enter the ventricle through the mitral valve 32. Therefore, since the support device 11 of the ventricular restriction mechanism 1 is implanted in the heart of the experimental animal, the amplitude of the contraction movement of the apical ventricular wall 33 is restricted, the blood pumping ability of the heart is lowered, and the heart failure of the experimental animal is artificially caused. experiment. Further, the combined use of the animal heart failure inducing device 100 of the present invention with coronary artery ligation and rapid pacing device can effectively improve the efficiency and stability of heart failure induction.
  • the retractable device 12 of the heart failure inducing device 100 can also be configured to be fixed in the shape of the systolic and diastolic phases.
  • the connecting tube 4 is closed by a valve mechanism, so that the liquid in the retractable device 12 cannot flow to the first chamber 24, so that the retractable device 12 does not move with the contraction and relaxation of the heart, and is always filled in the ventricle with a fixed volume. This still reduces the volume of the ventricle, reduces the ability of the heart to pump blood, and artificially causes heart failure in experimental animals.
  • the retractable device 12 can be set to a fixed state and a non-fixed state, and in a fixed state, the shape of the telescopic device 12 during systole and diastole is fixed.
  • the retractable device 12 retracts into the concave structure 13 and drives the elastic member 21 to contract by the driving medium; during diastole, the contracted elastic member 21 drives the said medium through the driving medium
  • the telescopic device 12 is expanded from the concave structure 13.
  • a conduit 26 is provided in communication with the first chamber 24, the conduit 26 being extendable outside the animal to introduce the drive medium into the first chamber 24 and the retractable device 12 through the conduit 26 or from the first chamber 24
  • the drive medium is derived within the retractable device 12. This adjusts the amount of drive medium in the first chamber 24 and the retractable device 12 to control the extent of heart failure, thereby assisting in heart failure induction and increased safety.
  • the end of the support tube 4 at the supporting means 11 is provided with a clogging preventing means 41 such as a mesh structure to prevent the retractable unit 12 from sticking to its inner wall and clogging the driving medium in and out of the connector 4 when retracted.
  • a clogging preventing means 41 such as a mesh structure to prevent the retractable unit 12 from sticking to its inner wall and clogging the driving medium in and out of the connector 4 when retracted.
  • FIG. 5 shows a schematic diagram of an exemplary embodiment of a support device 11.
  • the support device 11 is a flexible support mesh structure, and the support mesh is a non-operating portion of the ventricular restriction mechanism 1 for supporting the action of the telescopic device 12 to ensure the directional telescopic movement of the telescopic device 12.
  • the support device 11 has a certain rigidity and flexibility to ensure reliable contact with the ventricular wall 33 to facilitate surgical fixation.
  • the support device 11 supporting the mesh structure can be contracted into a tubular structure under certain conditions and placed in the delivery tube 5, so that the operator can transport the tube 5 and the delivery through the incision at the apex of the heart.
  • the tube 5 is contracted into a thin tubular support mesh and a retractable device 12 retracted within the support mesh - implanted into the ventricle, and expanded to a concave shape as shown in Figure 5 after implantation at a blood temperature greater than 32 degrees Celsius Structure 13 is in contact with ventricular wall 33.
  • FIG. 6 shows a schematic diagram of an exemplary embodiment of a telescopic device 12.
  • the retractable device 12 of the ventricular restriction mechanism in the unfolded state is a flexible capsule 16 of a substantially ellipsoidal or semi-ellipsoidal shape.
  • the bladder 16 comprises a three-layer structure, namely an inner layer 17 for contacting the driving medium, an outer layer 19 for contacting the blood, and a sandwich between the inner layer 17 and the outer layer 19 and for supporting the inside. Layer 17 and middle layer 18 of outer layer 19.
  • the capsule 16 has one or two layers, or even more layers, as long as the capsule 16 is ensured to be airtight, stretchable, flex resistant, and biocompatible.
  • the lower portion of the bladder 16 is circulated with the connecting pipe 4.
  • the bladder 16 of the retractable device 12 of the ventricular restriction mechanism is made of a medically high polymer material having good biosafety such as medical polyurethane having three layers of thickness and physical and chemical properties.
  • the bladder 16 of the retractable device 12 as the ventricular restriction mechanism includes an action portion 161 located in the upper half and a non-action portion 162 housed in the support web as the support device 11 in the lower half.
  • the support mesh and the non-action portion 162 are firmly adhered by uniformly coating the reinforcing film 14 made of, for example, medical polyurethane on the outside of the support mesh and the non-action portion 162.
  • the combination is combined and the strength of the non-action portion 162 and the biocompatibility with the tissue of the ventricular wall 33 are increased.
  • a sensor for detecting the function of the heart function and the heart failure inducing device 1 may be provided on the heart failure inducing device 100 implanted inside the heart, for example, the sensor includes the following sensors At least one of: a sensor for detecting an electrocardiographic signal, a sensor for detecting a pressure in the intracardiac, a sensor for detecting a pressure within the heart failure inducing device 100, and a sensor for detecting a volume of the ventricle and for Detect blood oxygen saturation sensor in the heart chamber and so on.
  • the signals generated by these sensors can be separately transmitted to an external monitoring device (not shown) provided in the animal to be tested.
  • the monitoring device analyzes the cardiac function state and the working state of the heart failure inducing device 100 and the matching state of the two based on the detection results of these sensors, The basis for the amount of liquid in the first chamber 24 and the telescopic device 12, the modulus of elasticity of the elastic member 21, and the treatment of heart failure are provided.
  • the size of the heart chamber of the experimental animal such as the left ventricle is measured before surgery, and the retractable device 12 and the supporting device 11 of the corresponding size are produced;
  • the support device 11 of the support mesh structure is contracted into a tubular structure and placed in the delivery tube 5 under low temperature conditions of 0-5 degrees Celsius; the experiment shrinks the delivery tube 5 and the delivery tube 5 into a thin tubular shape through the incision at the apex.
  • the supporting device 11 and the telescopic device 12 contracted in the supporting device 11 are implanted into the ventricle 3; after the implantation, the delivery tube 5 is pulled out, and one end of the connecting tube 4 is exposed outside the ventricular wall 33, and the support is The device 11 and the retractable device 12 remain in the ventricle 3; the support device 11 is deployed at the blood temperature to form the concave structure 13 shown in Fig. 5, and is in contact with the ventricular wall 33; the support device 11 is sutured by medical sutures
  • the ventricular wall 33 is fixed to the support device 11; the exposed end of the connecting tube 4 is connected to the housing 21 of the external chamber 2 and communicates with the first chamber 24;
  • the suture housing 21 of the base 33 is sewn to the outer ventricular wall.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Cardiology (AREA)
  • Environmental Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Animal Husbandry (AREA)
  • Zoology (AREA)
  • Transplantation (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Biodiversity & Conservation Biology (AREA)
  • Vascular Medicine (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • External Artificial Organs (AREA)
  • Prostheses (AREA)

Abstract

La présente invention concerne un dispositif d'induction (100) d'une insuffisance cardiaque chez un animal qui comprend un mécanisme de limitation ventriculaire (1) et une chambre ventriculaire externe (2). Le mécanisme de limitation ventriculaire (1) peut être implanté dans un ventricule (3), et comprend : un dispositif de support (11) ayant une structure concave (13) s'adaptant fondamentalement à la structure interne du ventricule; et un dispositif rétractable (12), se trouvant partiellement dans la structure concave (13) du dispositif de support (11). La chambre ventriculaire externe (2) est disposée à l'extérieur du ventricule (3) ou à l'extérieur d'un corps animal, et se trouve en communication fluidique avec le dispositif rétractable (12) via un tube de connexion (4). La chambre ventriculaire externe (2) comprend un élément élastique (21). Lorsque le cœur se contracte, le dispositif rétractable (12) se rétracte sur la structure concave (13) et entraîne, par un milieu d'entraînement, la rétraction de l'élément élastique (21); et lorsque le cœur se relâche, l'élément élastique rétracté (21) entraîne, par le milieu d'entraînement, le déploiement du dispositif rétractable (12) de la structure concave (13). Le dispositif peut être implanté dans le corps d'un animal expérimental, et entrainer manuellement une insuffisance cardiaque de l'animal expérimental, de manière à simuler la procédure liée à l'insuffisance cardiaque chez un humain.
PCT/CN2012/072437 2011-03-25 2012-03-16 Dispositif d'induction d'une insuffisance cardiaque chez un animal WO2012130052A1 (fr)

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CN 201110078129 CN102247218B (zh) 2011-03-25 2011-03-25 动物心力衰竭诱导装置
CN201110078129.0 2011-03-25

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WO2018217921A1 (fr) * 2017-05-23 2018-11-29 Harmony Development Group, Inc. Dispositif implantable attaché ayant un ballonnet de réglage de vitesse intracardiaque tourbillonnaire
US10940002B2 (en) 2017-06-28 2021-03-09 Harmony Development Group, Inc. Force transducting inflatable implant system including a dual force annular transduction implant
US11167122B2 (en) 2018-03-05 2021-11-09 Harmony Development Group, Inc. Force transducting implant system for the mitigation of atrioventricular pressure gradient loss and the restoration of healthy ventricular geometry

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CN103519786B (zh) * 2013-10-11 2015-04-22 上海交通大学 用于自由运动动物的微型脑卒中病理诱导系统

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