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WO2016170543A1 - Cœur artificiel pouvant être réparé en cours de fonctionnement - Google Patents

Cœur artificiel pouvant être réparé en cours de fonctionnement Download PDF

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Publication number
WO2016170543A1
WO2016170543A1 PCT/IN2016/000100 IN2016000100W WO2016170543A1 WO 2016170543 A1 WO2016170543 A1 WO 2016170543A1 IN 2016000100 W IN2016000100 W IN 2016000100W WO 2016170543 A1 WO2016170543 A1 WO 2016170543A1
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WIPO (PCT)
Prior art keywords
artificial heart
pumping
pumping unit
tube
balloon
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/IN2016/000100
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English (en)
Inventor
Kumar Guha Sujoy
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Individual
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Individual
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Filing date
Publication date
Application filed by Individual filed Critical Individual
Publication of WO2016170543A1 publication Critical patent/WO2016170543A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/247—Positive displacement blood pumps
    • A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
    • A61M60/268—Positive displacement blood pumps including a displacement member directly acting on the blood the displacement member being flexible, e.g. membranes, diaphragms or bladders
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/424—Details relating to driving for positive displacement blood pumps
    • A61M60/427—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/196—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body replacing the entire heart, e.g. total artificial hearts [TAH]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
    • A61M60/89—Valves
    • A61M60/894—Passive valves, i.e. valves actuated by the blood

Definitions

  • an artificial heart may be mass- produced and is potentially more compatible with the host's immune system.
  • an artificial heart must be compact enough to fit in the chest cavity, and must consistently maintain proper blood flow based on the host's level of activity.
  • the input and output flow characteristics of the artificial heart must be sufficient to protect the blood cells from hemolysis [dissolution] and thrombosis [clotting].
  • the artificial heart mechanism must also be extremely reliable and durable.
  • the natural heart contracts and expands over one hundred thousand times per day.
  • the cumulative contraction/expansion cycle over a period of a few years is very high.
  • Each contraction/expansion cycle imposes mechanical stresses on the structures of the heart producing material fatigue and micro damage.
  • Sequential micro damage adds up and tends to breakdown the materials of the heart wall and also reduce the pumping action.
  • the walls of the natural heart are muscles having on-going repair and rejuvenating processes. Therefore in spite of the cumulative micro damage the continuing cellular repair function maintains the heart muscles in normal functional state for long.
  • the materials of the artificial heart mostly plastics and metals, do not have repair properties although research in that direction is underway. Therefore fatigue, functionality lowering permanent deformations and mechanical failure of materials making up the artificial heart is a commonly encountered phenomena.
  • An in-use repairable artificial heart combining in-use self repair with interventional repair comprising: at least two pumping units [1, 2] positioned in the thoracic cavity; at least two pump drive units [5, 6] configured for ingress and egress of drive fluid in pre-assigned pumping units; an array of tubes, joints and valve arrangement operably connected to said pumping units adapted for driving the drive fluid in and out of said pumping units; as well as sucking in and pumping out blood, wherein each of the pumping units comprises: a shell wall [105] comprises of an inner layer [107] and an outer layer [106] having spot joints [108] which are randomly distributed over the shell wall in such a manner that between the layers there is intercommunicating spaces leading to formation of the cavity; and wherein the inner layer forms a space [110] into which the blood inflows via an entry port [53] and outflows via an exit port [54] having a self-sealing valve; and the space [110] encloses two leak proof balloons [111,
  • an in-use self and interventional repairable, artificial heart with provision of in-use replacement of failing parts having a structure which is soft, flexible, collapsible and compact at the time of its implantation and by injecting a hardening chemical is transformed to a rigid structure after being implanted in the thoracic region, and for interventional repair can be transformed back to a soft, flexible and collapsible compact structure by injecting softening chemicals for removal through a keyhole opening in the thoracic wall.
  • FIG 1 Schematic of the total artificial heart. The pumping units are shown spaced apart for diagrammatic clarity only
  • Figure 3 a Cross-sectional view of tube leading to a Coupling/uncoupling tube joint
  • the natural human heart has four chambers: the left atrium; left ventricle; right atrium; and right ventricle.
  • Deoxygenated blood from the body is drawn into the right atrium and is pumped into the right ventricle.
  • the right ventricle pumps the deoxygenated blood into the blood vessels of the lungs where the blood is oxygenated.
  • the oxygenated blood flows back to the heart into the left atrium and thereon to the left ventricle. Strong contraction of the left ventricle pumps the blood into the blood vessels all over the body other than that of the lungs.
  • the artificial heart [Figure 1] comprises of multiple pumping units [1-4] positioned in the thoracic cavity , the preferred number of units being four but could be two or more.
  • Each pumping unit serves as a combined atrium and ventricle and in following description is referred to as "ventricle".
  • Pumping Unit [1] and Pumping unit [3] serve as the right ventricle .
  • Pumping unit [2] and Pumping unit [4] serve as the left ventricle.
  • the Pumping units [1-4] are in close proximity retained by the force exerted by the connecting tubings. For diagrammatic clarity the Pumping units are shown apart in Figure 1.
  • All pumping units could be identical in design. Or, to withstand the higher left ventricular pressure, the pumping units serving as the left ventricle could have stronger materials than that for those serving as right ventricle - the right ventricle having lower pressure than the left ventricle.
  • a drive fluid is driven into and sucked out from the pumping units [1-4] by means of drive pumps.
  • Drive pump [5] drives the drive fluid for the right ventricular pumping action.
  • Drive pump [6] drives the drive fluid for the left ventricular pumping action.
  • the drive pumps [5,6] are positioned in the abdominal region. From drive pump [5] drive fluid is transported by tube [7]. Tube [7] bifurcates into tube [9] and tube [10]. Tube [9] directs the drive fluid to Pumping unit [1] and tube [10] directs drive fluid to Pumping unit [3]. From Drive pump [6] drive fluid is transported by Tube [8]. Tube [8] bifurcates into Tube [11] and Tube [12]. Tube [11] Directs the drive fluid to Pumping unit [2] and tube [12] directs drive fluid to Pumping unit [4].
  • a Coupling/Uncoupling tube joint [13] is positioned to couple or uncouple Tube [9] with Tube [17].
  • Coupling/Uncoupling tube joint [14] couples or uncouples Tube [10] with Tube [18].
  • Another Coupling/Uncoupling tube joint [15] couples and uncouples tube [11] with tube [19].
  • Coupling/Uncoupling tube joint [16] couples and uncouples tube [12] with tube [20] .
  • Tube[17] bifurcates into tube [21] and [22].
  • Tube [18] bifurcates into tube [23] and tube [24].
  • Tube [19] bifurcates into tube [25] and [26] and Tube [20 ] bifurcates into Tube [27] and Tube [28].
  • a Bidirectional flow control valves [37;38;39;40;41;42;43; and 44] are positioned in the lumen of Tubes [21;22;23;24;25;26;27; and 28] respectively.
  • the cavity formed in between the two layers of the outer shell of Pumping unit [1] has an "Inter outer shell layer entry port (right) [45] and an Inter outer shell layer entry port (left) [46].
  • Corresponding entry [3] are: right [47]; left [48]; for Pumping unit 2 they are left [49]; right [50] ; and tor Pumping unit 4 tney are left[51]; right [52].
  • Pumping unit [1] has a Blood entry port [53] and a Blood exit port [54].
  • Corresponding ports for Pumping unit [3] are Blood entry port [55]; exit port [56].
  • For Pumping Unit [2] they are Blood entry port [57] and Blood exit port [58].
  • For Pumping unit [4] they are Blood entry port [59] and Blood exit port [60].
  • Tubing [61] links to port [53]; tubing 62 links to port 54; tubing 63 links to port [55]; tubing 64 links to port [56]; tubing [65] links to port[57]; tubing [66] links to port [58]; tubing [67] links to port [59]; and tubing [68] links to port [60].
  • Tube [61] is coupled/uncoupled with Tube [69] by means of a Coupling//uncoupling tube joint [77].
  • Tube [62] is coupled/uncoupled with Tube [70] by means of a Coupling/uncoupling tube joint [78]
  • Tube [63] is coupled/uncoupled with Tube [71] by means of a Coupling//uncoupling tube joint [79]
  • Tube [64] is coupled/uncoupled with Tube [72] by means of a Coupling//uncoupling tube joint [80]
  • Tube [65] is coupled/uncoupled with Tube [73] by means of a Coupling//uncoupling tube joint [81].
  • Tube [66] is coupled/uncoupled with Tube [74] by means of a Coupling//uncoupling tube joint [82].
  • Tube [67] is coupled/uncoupled with Tube [75] by means of a Coupling//uncoupling tube joint [83].
  • Tube [68] is coupled/uncoupled with Tube [76] by means of a Coupling//uncoupling tube joint [84]
  • Tube [69] has a Bidirectional flow control valve [85]
  • Tube [70] has a Bidirectional flow control valve [86]
  • Tube [71] has a Bidirectional flow control valve [87]
  • Tube [72] has a Bidirectional flow control valve [88]
  • Tube [73] has a Bidirectional flow control valve [89]
  • Tube [74] has a Bidirectional flow control valve [90]
  • Tube [75] has a Bidirectional flow control valve [91]
  • Tube [76] has a Bidirectional flow control valve [92]
  • Tubes [69 and 71] merge to form tube [93]
  • Tubes [70 and 72] merge to form tube [94]
  • Tubes [73 and 75] merge to form tube [95]
  • Tubes [74 and 76] merge to for Tube [96]
  • Tube [93] is provided with an unidirectional flow valve [97]which allows flow of blood into Pumping units [1 and 3].
  • Tube [94] is provided with an unidirectional flow valve [98] which allows flow of blood out of Pumping units [1 and 3].
  • Tube [95] is provided with an unidirectional flow valve [99] which allows flow of blood into Pumping units [2 and 4]
  • Tube [96] is provided with an unidirectional flow valve [100] which allows flow of blood out of Pumping units [2 and 4].
  • the blood vessel Vena cava [101] bringing deoxygenated blood from the body parts other than the lungs is connected to the Tube [93]. Thereby the deoxygenated blood can enter into the Pumping units [1 and 3].
  • the Pulmonary artery [102] which transports blood from the right ventricle (represented in the Artificial Heart by Pumping units 1 and 3 ⁇ to the lungs is connected to Tube [94]. Blood from the right ventricle (represented in the Artificial Heart by Pumping units 1 and 3) can flow out along the unidirectional valve [98] to flow into the lungs.
  • the pulmonary vein [1031 which transports oxygenated blood from the lungs is connected to Tube [95].
  • the oxygenated blood from the lungs can then flow into the left ventricle (represented in the Artificial Heart by Pumping units 2 and 4) via the unidirectional valve [99].
  • the Aorta [104] which transports blood from the left ventricle to body parts other than the lungs is connected to Tube [96]. Blood from the left ventricle (represented in the Artificial Heart by Pumping units 2 and 4) can flow out of the left ventricle (represented by Pumping units 2 and 4) via the unidirectional valve [100] into the Aorta [104],
  • FIG. 2 shows Pumping unit [1] in detail.
  • the outer shell has a Shell wall [105] which comprises of two layers [106, 107].
  • Fabric material used for the layers [106, 107] is thin, flexible non-stretchable and non porous to blood fabric.
  • One suitable material is Polyethylene terephthalate (trade name Dacron).
  • the two layers have Spot joints [108] which are randomly distributed over the Shell wall [105] in such a manner that between the layers [106, 107] there is intercommunicating spaces leading to the formation of a Cavity [109] between the layer [106, 107].
  • the Cavity [109] has two ports [45, 46]. Both the ports may be used as inlet/outlet to the Cavity [109]..
  • the ports [45, 46] have a self sealing valve such that a large diameter needle can be inserted into the port to inject or suck out hardening chemical fluid from the cavity [109] and on removal of the large diameter needle the port seals automatically.
  • the inner layer [107] forms a Space [110].
  • This Space [110] is the zone into which blood flows into via the Blood entry port [53] and flows out via the Blood exit port [54].
  • the balloons are made of thin, highly flexible and large cyclic bending stress reversal withstanding material such as medical grade polyurethanes.
  • the open end of the balloon [111] is joined with the Entry port (right side balloon) [29] in such a manner that fluid pumped via the Entry port (right side balloon) [29] flows into the balloon [111].
  • the open end of the balloon [112] is joined with the Entry port (right side balloon) [30] in such a manner that fluid pumped via the Entry port (right side balloon) [30] flows into the balloon [112],
  • the Anchor [113] prevents sagging of the Balloon [111].
  • Figure 3a shows the cross section of tube [7]. Within the wall of the Tube [7] there are Tubular spaces [115-122], The Tubular spaces run along the length of the tube. The Tubular spaces [115 - 118]] continue into Tube [9] and Tubular spaces [119-122] continue into tube [10].
  • Figure 3b shows the Coupling/Uncoupling tube joint [13]. Via Male tube member [133] the Tubular spaces [115-118] continue into Tube [17]. Beyond the bifurcation of Tube [17] the Tubular spaces [115, 116] continue into Tubular space within the wall of Tube [21]. Tubular space in Tube [21] reach up to Bidirectional flow control valve [37].
  • Tube [17] has a central Tube lumen [123] which distal to the Coupling/Uncoupling tube joint continues as the lumen of Tube [17].
  • the lumen of Tube [17] bifurcates to merge with the lumen of Tubes [21,22].
  • the Coupling/Uncoupling Tube joint [13] also incorporates coupling/uncoupling for optical fibres and electrical wire pairs.
  • the Optical fibre [124] reaches the end of Tube 21 just distal to Bidirectional flow control valve [37] to transilluminate Tube [21].
  • the Optical fibre [125] reaches the end of Tube [22] just distal to Bidirectional flow control valve [38] to transilluminate Tube [22].
  • the Optical fibre [126] reaches the end of Tube [23] just distal to Bidirectional flow control valve [39] to transilluminate Tube [23].
  • the Optical fibre [127] reaches the end of Tube [24] just distal to Bidirectional flow control valve [40] to transilluminate Tube [24],
  • the Electrical wire pair [128] ends in miniature Photoelectric light sensor (not shown in the Figures) to be positioned transversely across the Tube [21] at the termination point of the optical fibre.
  • the Electrical wire pair [129] ends in miniature Photoelectric light sensor (not shown in the Figures) to be positioned transversely across the Tube [22] at the termination point of the optical fibre.
  • the Electrical wire pair [130] ends in miniature Photoelectric light sensor (not shown in the Figures) to be positioned transversely across the Tube [23] at the termination point of the optical fibre.
  • the Electrical wire pair [131] ends in miniature Photoelectric light sensor [not shown in the Figures] to be positioned transversely across the Tube [24] at the termination point of the optical fibre
  • Figure 3b shows Coupling/uncoupling tube joint [13] positioned in between Tubes [9] and [17].
  • Male tube member [132] the lumen of Tube [9] is placed in continuity of the lumen of Tube [17].
  • the Male tube member [133] is shown in respect of continuity of Tubular spaces [115-118].
  • the Male member [134] is shown in respect of continuity of Tubular spaces [119-122]
  • All parts of the artificial heart are bar coded with embossing of radio opaque material such as barium sulfate so that they can be identified under Xray imaging.
  • the Pumping units [1-4] are placed in the thoracic cavity in a state with the cavities corresponding to Cavity [109] of Pumping unit [1] unfilled.
  • the wall of all pumping units corresponding to the Shell wall [105] of Pumping unit [1] will be soft and in a collapsed state.
  • a hardening chemical which is a mixture of chemicals which are light in weight mixed with bubbles of carbon dioxide gas and which becomes semi solid is - pumped into the Cavity [109[. Via ports [45-52].
  • An example of such a mixture is gelatine mixed with hydroxy apatite in which bubbles of carbon dioxide gas is dispersed.
  • the Shell wall thereby becomes semi solid and in cylindrical form.
  • the Pumps [5, 6 ⁇ have reservoir of drive fluid.
  • One form of drive fluid is degraded gelatin mixed with water.
  • the Bidirectional flow control valve [37] is opened for a short while by applying drive fluid pressure via Tubular space [115, 116]. Applying drive fluid pressure to Tubular space [115] opens the Bidirectional flow control valve [37] and applying drive fluid pressure to Tubular space [116] closes the Bidirectional fluid control valve [37].
  • the right side balloons of all the pumping units are partially filled so as to occupy 10-20 % of the volume of the cavity [110] of Pumping unit [1] and similar cavities of all the other pumping units.
  • the Bidirectional flow control valve [38] of Tube [22] is opened by suitably applying drive fluid pressure to Tubular space [117, 118].
  • the same steps are done for the other three pumping units. All the manipulations performed by magnetically opening and closing valves placed with the Pumps [5] and [6].
  • the volume of filling of the right side balloons of all pumping units is assessed by Xray imaging.
  • the Drive Pumps are run so that the drive fluid is pumped into and out of the left side balloons of all the pumping units. Drawing out drive fluid from the left side balloons lowers pressure in the cavities within the pumping units and draws in blood. Pumping in drive fluid into the left side balloon generates pressure inside the cavities of the pumping units thereby forcing out blood via the connected blood vessel.
  • the sum of the blood volume expelled by Pumping units [2 and 4] is the Stroke volume.
  • the Stroke volume multiplied by the number of pumps given by the Drive pumps per minute is the Cardiac Output per minute.
  • Leak can develop in the left side balloon but there will be no sudden rupture on account of the stress reducing mechanisms mentioned earlier. If a leak occurs then during the balloon filling phase the fluid inside the balloon will in small amount leak out and mix with blood. Since the drive fluid used in the drive pumps [5,6] and for the filling of the balloons is a fluid used clinically for blood volume expansion there is no risk in the mixing of a small amount of the fluid with the blood.
  • the balloon material on the inside has a layer of material, as for example styrene maleic anhydride, which will react with blood forming a fibrin clot.
  • the clot will seal the leak.
  • the blood leaking into the balloon mixes with the drive fluid altering the optical transmission properties of the drive fluid in a light frequency dependent manner.
  • the transmission of light between the optical fibre and the photoelectric sensor will change.
  • An electronic system with computational facility placed with the Drive pumps estimates the extent of the leak by analyzing the change in optical transmission through the drive fluid at different light frequencies which are given as input to the optical fibres.
  • a logic system assesses the progress of the leak and self repair. If repair takes place adequately the system is allowed to run without intervention. If the leak is substantial and increasing in magnitude the system program will effect suitable action which may be any one or combination of the following: i) For the pumping unit in which a leak has occurred the left side balloon will be brought to a static state in partially filled mode. The pumping action to be transferred to the right side balloon. The transfer to be achieved by the automatic operation of the Bidirectional flow control valve in the line of the left side balloon closing and the Bidirectional flow control valve in line with the right side balloon opening. The shift in the state of the Bidirectional control valves will be automatically mediated by control of pressure in the corresponding tubular spaces. ii) The pumping then occurs by the filling and drainage of the right side balloon. The left side balloon remains in static condition. In static condition the possibility of the self repair by formation of the small clot is greater than when in the dynamic state because the margins of the leak zone remain stationary when the balloon as a whole is in the stationary state.
  • the system may be programmed to automatically switch to the right side static and left side balloon dynamic. If the sensing system indicates that there is no leak then the system can so function with the right side balloon static and left side balloon active. If repair has not taken place switch back can automatically be effected. iii) The left side balloon may be emptied and brought to a static state. The right side balloon filling increased so that the right side balloon on full filling occupies the entire volume inside the Pumping unit. Thereby the entire pumping of that pumping unit is taken over by the right side balloon. It is to be noted that the other pumping unit which pairs with the faulty pumping unit is continuing to work normally and the stroke volume continues to be the sum of the outputs of the pair.
  • the output from the unaffected pumping unit of the pair can be increased and that of the defective pumping unit decreased to give partial rest to the defective pumping unit to help in self repair and/or reduce load on the defective pumping unit so as to check the increase of the leak.
  • Pumping unit [1J acts as the sole Right Ventricle and Pumping unit [2] acts as the sole Left Ventricle.
  • the Pumping unit (3] remains as a Stand by right ventricle and Pumping unit [4] remains as the stand by left ventricle.
  • the Pumping unit performs the full right ventricle pumping action with one of the balloons collapsed and the other balloon filling to occupy the entire space [110] at the time of systole.
  • Pumping unit [2] performs the full left ventricle pumping action with one of the balloons inside collapsed and the other balloon filling to occupy the entire space [110] at the time of systole.
  • Pumping unit [1] When a leak is detected in Pumping unit [1] the Pumping unit [1] is automatically totally deactivated. Pumping unit [3] is automatically activated to serve as the functional right ventricle. If a leak is detected in Pumping unit [2] that pumping unit is deactivated and Pumping unit [4] is activated to serve as the left ventricle entirely.
  • a solvent as for example ethanol for the hardening chemical gelatin and hydroxyapatite combination can be pumped into the space [109] of the faulty pumping unit via the Inter outer shell layer entry port of Pumping unit to dissolve the compound and suck it out.
  • the outer shell [105] of the faulty pumping unit becomes flaccid.
  • the coupling /uncoupling tube joint corresponding to the faulty pumping unit is uncoupled by a special surgical instrument inserted through a keyhole opening in the chest wall.
  • the faulty pumping unit can then be extracted out of the keyhole opening in the chest wall.
  • a new pumping unit is then inserted through the keyhole opening. At all times during the procedure the artificial heart continues to function.

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Cardiology (AREA)
  • Biomedical Technology (AREA)
  • Anesthesiology (AREA)
  • Mechanical Engineering (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Vascular Medicine (AREA)
  • External Artificial Organs (AREA)

Abstract

La présente invention concerne un cœur artificiel pouvant être réparé en cours de fonctionnement en vue de l'auto-obturation d'une petite fuite en cours d'utilisation, ledit coeur artificiel ayant une estimation en temps réel de l'amplitude de la fuite En outre dans le cas de fuites plus importantes qui ne parviennent pas à être auto-obturées, le système désactive automatiquement la sous-unité défaillante du cœur artificiel et commute sur une sous-unité d'attente du cœur artificiel. La sous-unité désactivée peut être convertie en une forme molle et amovible par micromanipulation chirurgicale tandis que la circulation sanguine est maintenue par l'unité d'attente qui est activée. La sous-unité retirée peut être remplacée, par micromanipulation chirurgicale, par une nouvelle sous-unité. L'auto-réparation et la réparation par intervention tandis que le cœur artificiel est en fonctionnement garantissent au cœur artificiel une propriété de fonctionnement continu.
PCT/IN2016/000100 2015-04-20 2016-04-18 Cœur artificiel pouvant être réparé en cours de fonctionnement Ceased WO2016170543A1 (fr)

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IN1101DE2015 2015-04-20
IN1101/DEL//2015 2015-04-20

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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2024245790A1 (fr) * 2023-05-30 2024-12-05 AdjuCor GmbH Dispositif d'assistance cardiaque comprenant une unité extensible

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB1307135A (en) * 1970-09-16 1973-02-14 Cutter Lab Artificial ventricle heart assist device and heart assembly
US4173796A (en) 1977-12-09 1979-11-13 University Of Utah Total artificial hearts and cardiac assist devices powered and controlled by reversible electrohydraulic energy converters
FR2585249A1 (fr) * 1985-07-26 1987-01-30 Biomasys Sa Coeur artificiel heterotopique : prothese cardiaque monobloc pour assistance biventriculaire implantable dans l'hemi-thorax droit
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US5135539A (en) 1988-01-14 1992-08-04 Etablissement Public: Universite Pierre Et Marie Curie Quick-connect, totally implantable cardiac prosthesis with floating membranes and removable sensitive elements
US20040054251A1 (en) * 2002-09-18 2004-03-18 Liotta Domingo Santo Corporal implantation device for assisting blood and heart ventricular circulation
GB2483422A (en) 2009-07-10 2012-03-07 Sujoy Kumar Guha Replaceable artificial-heart implantable by keyhole surgery
US8636638B2 (en) 2009-04-16 2014-01-28 Bivacor Pty Ltd Heart pump controller

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Publication number Priority date Publication date Assignee Title
GB1307135A (en) * 1970-09-16 1973-02-14 Cutter Lab Artificial ventricle heart assist device and heart assembly
US4173796A (en) 1977-12-09 1979-11-13 University Of Utah Total artificial hearts and cardiac assist devices powered and controlled by reversible electrohydraulic energy converters
FR2585249A1 (fr) * 1985-07-26 1987-01-30 Biomasys Sa Coeur artificiel heterotopique : prothese cardiaque monobloc pour assistance biventriculaire implantable dans l'hemi-thorax droit
US5135539A (en) 1988-01-14 1992-08-04 Etablissement Public: Universite Pierre Et Marie Curie Quick-connect, totally implantable cardiac prosthesis with floating membranes and removable sensitive elements
US4981484A (en) 1988-08-15 1991-01-01 Holfert John W Modified elliptical artificial heart
US20040054251A1 (en) * 2002-09-18 2004-03-18 Liotta Domingo Santo Corporal implantation device for assisting blood and heart ventricular circulation
US8636638B2 (en) 2009-04-16 2014-01-28 Bivacor Pty Ltd Heart pump controller
GB2483422A (en) 2009-07-10 2012-03-07 Sujoy Kumar Guha Replaceable artificial-heart implantable by keyhole surgery

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WO2024245790A1 (fr) * 2023-05-30 2024-12-05 AdjuCor GmbH Dispositif d'assistance cardiaque comprenant une unité extensible

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