EP1896095A1 - Systeme de circulation extracorporelle, en particulier pour un coeur-poumon artificiel multifonction et pour reduire les risques d'embolie gazeuse - Google Patents

Systeme de circulation extracorporelle, en particulier pour un coeur-poumon artificiel multifonction et pour reduire les risques d'embolie gazeuse

Info

Publication number
EP1896095A1
EP1896095A1 EP06754417A EP06754417A EP1896095A1 EP 1896095 A1 EP1896095 A1 EP 1896095A1 EP 06754417 A EP06754417 A EP 06754417A EP 06754417 A EP06754417 A EP 06754417A EP 1896095 A1 EP1896095 A1 EP 1896095A1
Authority
EP
European Patent Office
Prior art keywords
reservoir
blood
ecc
circulation system
venous
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.)
Withdrawn
Application number
EP06754417A
Other languages
German (de)
English (en)
Inventor
Kai Liebing
Thorsten Wahlers
Mirko Kaluza
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Maquet Cardiopulmonary GmbH
Original Assignee
Maquet Cardiopulmonary GmbH
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Maquet Cardiopulmonary GmbH filed Critical Maquet Cardiopulmonary GmbH
Publication of EP1896095A1 publication Critical patent/EP1896095A1/fr
Withdrawn legal-status Critical Current

Links

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
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3627—Degassing devices; Buffer reservoirs; Drip chambers; Blood filters
    • 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
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3627—Degassing devices; Buffer reservoirs; Drip chambers; Blood filters
    • A61M1/3632—Combined venous-cardiotomy reservoirs
    • 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
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3624—Level detectors; Level control
    • 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
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3379—Masses, volumes, levels of fluids in reservoirs, flow rates
    • A61M2205/3386—Low level detectors

Definitions

  • Extracorporeal circulation system especially for multifunctional cardiopulmonary bypass and to minimize air embolisms
  • the invention relates to an extracorporeal circulation system (ECC system) with a reservoir, in particular a venous cardiotomy reservoir for blood and / or priming solution, and preferably with means for defoaming and filtering of the blood, as in a heart-lung bypass Application finds.
  • ECC system extracorporeal circulation system
  • Such an ECC system is used, inter alia, to remove blood, for example, from the right atrium of the heart and to feed it back into the arterial blood circulation of the patient via the EKZ system.
  • the function of the heart and / or the lungs should be partially or completely artificially replaced in this way.
  • ECC Extracorporeal membrane oxygenation in adult patients
  • HLM cardiopulmonary bypass
  • the basic system of a heart-lung machine used today consists of an oxygenator (mainly membrane oxygenator), which subjects the patient's venous blood to gas exchange, and a blood pump that pumps blood through the oxygenator via a perfusion cannula into the vasculature (predominantly back to the aorta ascendens) of the patient (H. Weitkemper, D. Troitzsch, W. Böttcher, R. Körfer: Elements and Functional Principle of a Heart-Lung Machine, Extracorporeal Circulation in Theory and Practice, Published by Rudolf J. Tschaut, Pabst Science Publishers , 2005, p. 258).
  • an oxygenator mainly membrane oxygenator
  • a blood pump that pumps blood through the oxygenator via a perfusion cannula into the vasculature (predominantly back to the aorta ascendens) of the patient
  • these perfusion systems are commonly divided into open ECC systems, closed-circuit ECC systems, and minimized ECC systems, with each system finding its specific use.
  • the advantage of the open ECC system is that even large air bubbles in the venous tubing line, in particular through the open hard shell reservoir, are for the most part automatically eliminated.
  • This system is useful, for example, for heart valve surgery in which the heart cavities are opened and there is thus a particularly high risk of air entering the heart-lung machine via the venous catheters.
  • a disadvantage is the constant blood-air contact in the venous hard shell reservoir, even if no air enters the venous line, as well as the high dilution of the blood with the priming solution in the reservoir.
  • a relatively high level level of blood and / or priming solution in the hard shell reservoir is necessary so that the blood pump does not suck in air, especially with a high pump flow.
  • the blood collected from the reservoir and diluted with priming solution is then transported by the pump into the so-called artificial lung of the heart-lung machine, the oxygenator, and then further into the patient's arterial vasculature. It is pumped only as much blood as is passively drained via gravity, which sometimes, however, is not always sufficient for a good circulation of the patient.
  • the return flow of venous blood can be improved, with a negative pressure of - 40 mmHg to a maximum of - 75 mmHg completely sufficient and stronger negative pressure differences are to be avoided.
  • a soft bag reservoir is used instead of a venous rigid hard shell reservoir, which easily collapses when the blood pump aspirates more volume than is drained passively by gravity from the patient's venous vasculature (H. Frerichs: Schlauchsysteme Extracorporeal Circulation in Theory and Practice, ed. Rudolf J. Tschaut, Pabst Science Publishers, 2005, p. 289). It is particularly advantageous that no or hardly any blood-air contact takes place in the closed ECC system. The disadvantage, however, is that air bubbles in the venous tubing line are not automatically eliminated in the closed reservoir.
  • a venous reservoir is usually dispensed with or a hard shell reservoir or soft-tissue reservoir is located, manually completely disconnected, in the bypass of the venous line and is used to fill the minimized EKZ system with priming solution or for manual volume dispensing.
  • a venous reservoir often only the venous system of the patient is used, which requires a fundamentally more elaborate and adapted anesthesia, volume and perfusion management than in the previously described ECC systems.
  • the drainage of the venous blood is not passive by gravity, but actively by the arterial blood pump. This involves considerable dangers (air embolisms), which must be taken into account.
  • the venous cannulation site should be completely airtight sealed by a Mersileneband around the right atrium.
  • a newly introduced on the market in June 2005 minimized ECC system (ROCSAFE, company prospectus Terumo®), for example, automatically detects the detection of air bubbles reduces the speed of the blood pump and the venous line is disconnected, resulting in a blood circulation shutdown. Then the macro bubbles are sucked off. Subsequently, the clamp is opened again manually and the rotational speed of the rotary blood pump is increased. If the next bubble with more than 0.5 ml volume is detected, the process is repeated. The electronic clamp closes the venous line again, resulting in cardiac arrest again for several seconds.
  • a regular air aspiration can mean for the patient with activated automatic clamp that continuous stops of the blood circulation take place.
  • Minimized ECC systems are used, for example, in the context of cardiopulmonary resuscitation in the intensive care unit (or as an ECMO in respiratory failure) or in an aortocoronary bypass operation, if the heart cavities are not opened and the risk of air entering the venous line appears low.
  • a disadvantage of these minimized ECC systems is that in most cases there is no adequate negative pressure limitation in the venous line and no automatic volume compensation.
  • Centrifugal and diagonal pumps can generate up to - 600 mmHg negative pressure (eg DeltaStream®, Medos AG), depending on the hydraulic capacity.
  • the invention is therefore based on the object to provide a universally applicable extracorporeal circulation system, in particular for an artificial heart-lung bypass, which benefits (for example, minimal dilution and minimal foreign surface contact of the blood) of a minimized ECC system uses, but if necessary also multifunctional and, above all, without the need for a blood circulation stop and with such risks and dangers for the patient as quickly as possible and without the use of mechanical and cost-intensive ECC conversion, make use of the option of other open and / or closed ECC systems which have a minimized ECC system (especially a minimized ECC system without automatic vacuum and volume compensation) can not offer.
  • a special reservoir in particular a venous cardiotomy reservoir, which consists of a lower, dimensionally stable part body and of a flexible part body arranged thereon. Due to its dimensional stability, the lower partial body has the ability to integrate or additionally attach one or more level sensors or means for receiving the same, for example adhesive elements, without changing their position or even losing their position with a change in the capacity of the reservoir.
  • the body located above it is designed to be flexible and shows by its shape (for example as a bellows) and / or by its material properties and / or additional means, such as positive or non-positive elements, such as suspensions, the desire to expand and its capacity Increase priming solution and / or blood uptake.
  • one or more means for selectively opening the same to the atmosphere are preferably provided in the upper region of the reservoir. These means can be realized for example by sealing plugs, clamping hoses or other ventilation elements.
  • a multifunctional usable reservoir was created in which the capacity is flexibly adjustable and which is suitable for minimized, closed and open ECC systems.
  • the advantages of a minimized ECC system with the advantages of, in particular, minimal blood thinning and a lower blood foreign surface contact can be utilized. Only by manual or automatic transfer of terminals or by opening and closing of system components, so without additional effort to constructively change (retrofitting) or to replace the ECC system and without the known risks to the patient and risks, such as the Air embolism, one and the same device with the proposed reservoir can be used universally if necessary with the option of other open and / or closed ECC systems, which can not offer the said minimized ECC system.
  • Such a universally usable ECC system can advantageously be used multifunctionally, for example, for mobile emergency aid and clinical use under the options of all known open, closed or minimized ECC systems.
  • it can be fully assembled and filled with priming solution as a mobile rescue perfusion system (minimized ECC system, often erroneously referred to as ECMO) for emergency use.
  • ECMO mobile rescue perfusion system
  • the same ECC system can, for example, for a planned bypass or heart valve operation optionally as a minimized ECC system with automatic vacuum and volume compensation, as closed ECC system or be used as an open ECC system.
  • a planned bypass or heart valve operation optionally as a minimized ECC system with automatic vacuum and volume compensation, as closed ECC system or be used as an open ECC system.
  • the emergency patient connected to the minimized ECC system can be transported to the operating room and the emergency operation can take place immediately, without it being absolutely necessary to use another heart-lung machine.
  • FIG. 1 shows a schematic diagram of the open ECC system known per se
  • FIG. 1 shows the schematic structure of a known open ECC system.
  • the blood coming from the patient passes passively via a venous line 1 from the heart 2 into an open hard shell reservoir 3.
  • the driving pressure here is the central venous pressure and the hydrostatic pressure resulting from the height difference between the heart 2 and the open hard shell reservoir 3 ,
  • a blood pump 4 sucks the volume contained in the hard shell reservoir 3 and pumps it into the artificial lung, the oxygenator 5 with integrated heat exchanger. From there, the oxygen-rich blood passes through an arterial filter 6 back into the vascular system of the patient.
  • Fig. 2 shows the schematic structure of a known closed ECC system.
  • the blood coming from the patient passively passes through the venous line 1 from the heart 2 into a closed soft-pouch reservoir 7.
  • the driving pressure here is also the central venous pressure and the hydrostatic resulting from the height difference between the heart 2 and the closed soft-pouch reservoir 7 Print.
  • the blood pump 4 sucks the volume contained in the soft-bag reservoir 7 and pumps it into the artificial lung, the oxygenator 5 with integrated heat exchanger. From there, the oxygen-rich blood passes through the arterial filter 6 back into the vascular system of the patient.
  • FIG. 3 shows the schematic structure of a minimized ECC system known per se.
  • This ECC system is not only closed and there is thus no unfavorable blood-to-air contact for the patient, but also the priming solution, the hemodilution (blood dilution) and the blood contact with the foreign surface have been minimized.
  • the patient's venous blood is actively aspirated directly from the blood pump 4, which may experience brief excessive negative pressure fluctuations, and pumps it into the artificial lung, the oxygenator 5 with integrated Heat exchanger. From there, the oxygen-rich blood passes via an arterial line 11 directly back into the vascular system of the patient.
  • FIG. 4 shows, for one possible application, the schematic structure of a universally usable ECC system with the proposed multifunctional reservoir using the example of an aortocoronary bypass operation on a cardioplegically immobilized heart.
  • the multifunctional ECC system (referred to as '& ECC system') is primarily used as a minimized ECC system with automatic negative pressure and volume compensation.
  • a bypass 13 is to be sewn.
  • the heart 2 is shown schematically in FIG. 4 with its right atrium 14, its left atrium 15, its right ventricle 16 and its left ventricle 17.
  • the moderately stenosed coronary artery 12 leads from the aorta 18 (shown aortic valve with ascending aorta) to the capillary bed 19 of the heart 2.
  • the aorta 18 is closed by an aortic clamp 20.
  • a cannula 21 In the clamped aortic root is a cannula 21 through which as a so-called vent (ventricular discharge sucker) a small amount of blood can be sucked.
  • the negative pressure is limited by a one-way valve to about - 100 mmHg and the opening of this small cannula 21 is largely closed by the collapsed aortic inner wall. If the Ventsaugung further amplified, the one-way valve opens even more towards the atmosphere to keep the negative pressure in the cannula 21 constant. As a result, even more air is added to the extracted blood, so that this patient's blood must then be defoamed when reused.
  • a rotary blood pump 39 does not receive enough blood via a venous two-stage catheter 24 and a high negative pressure difference results. It is assumed that this strong negative pressure can be transmitted in an attenuated form to the left heart and the root of the aorta 18 (here are more extensive research on all described ECC systems, in particular a study of said situational negative pressure and via the cardiac air aspiration, in the Friedrich- Schiller University Jena).
  • the oxygenated by the heart-lung machine blood is pumped through a flow sensor 28 and through an arterial cannula 29 back into the aorta 18 of the patient.
  • a flow sensor 28 For the sake of completeness and for better understanding are in Fig. 4 also from the patient pulmonary valve 30 with pulmonary trunk, the capillary bed 31 of the lung, the Vv. Pulmonales 32, the tricuspid valve 33 in the right heart, the mitral valve 34 in the left heart and the sinus coronarius 35 and the vena obliqua atrii sinistri 36 greatly simplified.
  • a three-way cock 37 and a preferably 1.2 mm or even better 1.5 mm button cannula 38 is to improve the visual conditions for the surgeon and to minimize air embolisms about 0.5 to 3.0 l / min of carbon dioxide on the coronary anastomosis attention should be paid to sufficient moisture and greater changes in myocardial pH.
  • variable speed rotary blood pump 39 actively aspirates and pumps blood primarily from the right atrium 14 and vena cava 22, 23 via the two-stage catheter 24, venous tubing line 40, venous air bubble detector 41, venous restriction 42, air bubble trap 43, and pressure transducer 44 into the oxygenator 5. Subsequently, the oxygen-enriched blood passes via an arterial tube line 45, via an arterial bubble detector 46, via the flow sensor 28 and via the arterial cannula 29 into the clamped aorta 18.
  • a flexible reservoir 48 is located in the venous shunt, was completely emptied of priming solution by autologous priming at the beginning of the ECC, but has not yet fully unfolded and is closed to the atmosphere.
  • the pressure transducer 44 measured negative pressure in the venous line 40 is at full flow, for example - 40 mmHg. If the negative pressure z. B. by volume deficiency due to bleeding (and excretion via the kidneys) on, it opens at about - 70 mmHg a one-way valve 47 and it is briefly drawn volume from the reservoir 48.
  • the reservoir 48 as a vacuum reservoir is primarily filled with priming solution, is used for automatic vacuum and volume compensation and is in the shunt of the venous line 40. It turns on only as described, in the emergence of excessive negative pressure automatically and otherwise takes on the artificial circulation not part. If only a small and slow volume compensation is desired, the venous shunt tubing at the one-way valve 47 may be partially disengaged. If during the entire ECC time the negative pressure is in the desired normal range and no volume had to be automatically substituted, the priming solution from the reservoir 48 is discarded.
  • the reservoir 48 consists in this case of a vertical transparent bellows 56 in the central region and a transparent dimensionally stable part body 57 in the lower region to which an adhesive member for receiving the level sensor 55, for example, an ultrasonic sensor has been attached and which down to a reservoir Outlet 58 tapers.
  • the effort of the reservoir 48 to expand can be reinforced by springs 59 and inhibited by springs 60. This increases or decreases the negative pressure in the reservoir or the negative pressure difference required for the rotary blood pump 39 for aspirating blood and / or priming solution from the reservoir 48.
  • the extent of the reservoir 48 and thus the maximum filling volume can be limited by a barrier 61 or the contraction by a barrier 62.
  • Limiting contraction may be useful, for example, if the reservoir 48 is operated as a closed reservoir and there is some air in it.
  • teat blood from the operating field or priming solution can be introduced via connections 63.
  • This volume may be introduced via filters and defoamers and, for example, by opening the sealing plug 52 in the underlying part of the reservoir 48 or especially for the purpose of processing the teat blood through an opening 64 (which can simultaneously represent a said opening to the atmosphere) sucked off again.
  • a clamp 65 to a reservoir inlet 66 (indicated by a clamp 65 ')
  • the automatic clamp 49 is opened, the arterial blood and / or the priming solution can flow from the reservoir 48 directly into the venous tubing line 40.
  • the blood and / or priming solution could be opened and closed by airway elimination terminals 67, 67 'via an arterial filter branch 68 having an arterial filter 69 and a one-way valve 70 are headed. Also, the blood and / or the priming solution could flow back into the reservoir 48 by opening the automatic clamp 49 and corresponding opening / closing of the clamps 65 and 65 '.

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

Abstract

L'invention concerne un système de circulation extracorporelle, en particulier pour un coeur-poumon artificiel multifonction et pour réduire les risques d'embolie gazeuse. L'objectif de l'invention est de créer un système multifonction de circulation extracorporelle (CEC) pour un coeur-poumon artificiel qui bénéficie des avantages d'un système CEC simplifié tout en pouvant être utilisé en permanence, en cas de besoin, de façon universelle et avec un risque réduit comme un autre système CEC fermé ou ouvert. Par ailleurs, une compensation automatique de vide et de volume doit être possible en cas d'utilisation comme système CEC simplifié. Le système selon l'invention se caractérise en ce qu'il comprend un réservoir spécial (48), en particulier un réservoir veineux de cardiotomie destiné à contenir du sang et/ou une solution d'amorçage, ce réservoir étant constitué d'une partie inférieure indéformable (57) dans laquelle peut être intégré un capteur de niveau (55) et d'une partie souple (56) située sur la partie inférieure, cette partie souple étant destinée à augmenter la capacité du réservoir. Le système selon l'invention peut être utilisé comme système de circulation artificielle pour des patients avec un coeur-poumon artificiel.
EP06754417A 2005-06-21 2006-06-16 Systeme de circulation extracorporelle, en particulier pour un coeur-poumon artificiel multifonction et pour reduire les risques d'embolie gazeuse Withdrawn EP1896095A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102005029682A DE102005029682A1 (de) 2005-06-21 2005-06-21 Extrakorporales Zirkulationssystem, insbesondere für einen multifunktionalen Herz-Lungen-Bypass und zur Minimierung von Luftembolien
PCT/EP2006/005816 WO2006136343A1 (fr) 2005-06-21 2006-06-16 Systeme de circulation extracorporelle, en particulier pour un coeur-poumon artificiel multifonction et pour reduire les risques d'embolie gazeuse

Publications (1)

Publication Number Publication Date
EP1896095A1 true EP1896095A1 (fr) 2008-03-12

Family

ID=36952881

Family Applications (1)

Application Number Title Priority Date Filing Date
EP06754417A Withdrawn EP1896095A1 (fr) 2005-06-21 2006-06-16 Systeme de circulation extracorporelle, en particulier pour un coeur-poumon artificiel multifonction et pour reduire les risques d'embolie gazeuse

Country Status (5)

Country Link
US (1) US20090275875A1 (fr)
EP (1) EP1896095A1 (fr)
CH (1) CH699261B1 (fr)
DE (1) DE102005029682A1 (fr)
WO (1) WO2006136343A1 (fr)

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DE502004007297D1 (de) * 2004-11-24 2008-07-10 Lifebridge Medizintechnik Ag Vorrichtung zur Bereitstellung eines extrakorporalen Blutkreislaufs
DE102007037755A1 (de) * 2007-08-09 2009-02-12 Rheinisch-Westfälische Technische Hochschule Aachen Herz-Lungen-Maschine
EP2246080B1 (fr) 2007-10-12 2016-02-10 DEKA Products Limited Partnership Système de circulation sanguine extracorporel
US9247729B2 (en) * 2009-05-29 2016-02-02 Institut Georges Lopez Systems and methods for preserving a human organ for transplantation
DE102009026592B4 (de) 2009-05-29 2014-08-28 Sorin Group Deutschland Gmbh Vorrichtung zur Festlegung des venösen Zuflusses zu einem Blutreservoir eines extrakorporalen Blutkreislaufs
DE102009027195A1 (de) 2009-06-25 2010-12-30 Sorin Group Deutschland Gmbh Vorrichtung zur Förderung von Blut in einem extrakorporalen Kreislauf
DE102010049536A1 (de) 2010-10-26 2012-05-10 Universitätsklinikum Jena Universelles künstliches Blutkreislaufsystem
EP2543402B1 (fr) 2011-07-08 2020-12-23 Qura S.R.L Dispositif d'utilisation médicale pour collecter et transporter le sang, produits dérivés et/ou fluides complétants, et circuit extracorporel comprenant le dispositif
EP2754458B1 (fr) 2011-07-12 2017-02-01 Sorin Group Italia S.r.l. Réservoir de sang à double chambre
US9327066B2 (en) * 2013-03-13 2016-05-03 Keith Samolyk CPB system with dual function blood reservoir
WO2015173611A1 (fr) 2014-05-16 2015-11-19 Sorin Group Italia S.R.L. Réservoir de sang à mesure de volume de fluide basée sur un capteur de pression

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US3907504A (en) * 1973-04-06 1975-09-23 Gen Electric Blood oxygenation system including automatic means for stabilizing the flow rate of blood therethrough
DE3218561C2 (de) * 1982-05-17 1988-08-18 Günter H. Dr.-Ing. 8035 Gauting Marx Gerät zur Aufnahme und Reinfusion von Blut
IT1260685B (it) * 1993-09-29 1996-04-22 Sorin Biomedica Spa Dispositivo per il contenimento di sangue
EP0766974B1 (fr) * 1995-10-03 2006-09-06 Terumo Kabushiki Kaisha Réservoir de sang, instrument et appareil pour fournir du sang
EP1053760A3 (fr) * 1999-05-21 2001-08-16 Medtronic, Inc. Réservoir à paroi souple
US6322546B1 (en) * 1999-10-28 2001-11-27 Jostra Bentley Inc. Fluid control conduit
US20030135152A1 (en) * 2000-09-27 2003-07-17 Kollar Kevin J. Disposable cartridge for a blood perfusion system

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Also Published As

Publication number Publication date
CH699261B1 (de) 2010-02-15
DE102005029682A1 (de) 2006-12-28
WO2006136343A1 (fr) 2006-12-28
US20090275875A1 (en) 2009-11-05

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