WO1994013204A1 - Injecteur de gaz - Google Patents

Injecteur de gaz Download PDF

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Publication number
WO1994013204A1
WO1994013204A1 PCT/EP1993/003401 EP9303401W WO9413204A1 WO 1994013204 A1 WO1994013204 A1 WO 1994013204A1 EP 9303401 W EP9303401 W EP 9303401W WO 9413204 A1 WO9413204 A1 WO 9413204A1
Authority
WO
WIPO (PCT)
Prior art keywords
gas
valve
pressure
catheter
gas outlet
Prior art date
Application number
PCT/EP1993/003401
Other languages
German (de)
English (en)
Inventor
Wolfgang Kloess
Martin Zwaan
Original Assignee
Wolfgang Kloess
Martin Zwaan
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 Wolfgang Kloess, Martin Zwaan filed Critical Wolfgang Kloess
Priority to EP94902669A priority Critical patent/EP0671894A1/fr
Publication of WO1994013204A1 publication Critical patent/WO1994013204A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/48—Diagnostic techniques
    • A61B6/481—Diagnostic techniques involving the use of contrast agents
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/50—Clinical applications
    • A61B6/504—Clinical applications involving diagnosis of blood vessels, e.g. by angiography
    • 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
    • A61M13/00—Insufflators for therapeutic or disinfectant purposes, i.e. devices for blowing a gas, powder or vapour into the body
    • A61M13/003—Blowing gases other than for carrying powders, e.g. for inflating, dilating or rinsing
    • 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
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/007—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests for contrast media
    • 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
    • A61M2202/00—Special media to be introduced, removed or treated
    • A61M2202/02—Gases
    • A61M2202/0225—Carbon oxides, e.g. Carbon dioxide
    • 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
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3344—Measuring or controlling pressure at the body treatment site

Definitions

  • the invention relates to a device for introducing gaseous media into a liquid-filled vessel system, with a pressure source for the gaseous medium, a metering valve for adjusting the gas flow, a gas outlet which can be connected to the vessel system and a sensor arranged between the metering valve and gas outlet for detecting the pressure, mass flow or Volume flow of the gaseous medium, a control variable for the metering valve being able to be derived from the output signal of the sensor.
  • Such a gas injector is used, for example, in angiography.
  • Angiography is the X-ray imaging of blood vessels with the aid of a contrast agent introduced into the bloodstream.
  • positive contrast agents which increase the radiation absorption
  • negative contrast agents which reduce the radiation absorption are known in radiology to improve the recognizability of anatomical structures.
  • iodine-containing liquids are usually used as positive contrast agents.
  • a considerable part (approx. 13% for ionic and 3% for non-ionic contrast agents) of the angiographed patients has allergic reactions to contrast agents, which can lead to serious and even fatal incidents.
  • a servo valve with a downstream metering resistor is used to regulate the gas flow.
  • a servo valve is a directional valve usually constructed as a longitudinal slide or rotary slide valve. Exemplary embodiments are described in the journal "Oil hydraulics and pneumatics" 35 (1991), pp. 43-47. Such servo valves, which can be adjusted by an electric motor, have a relatively complicated structure and also require a signal feedback of the travel path covered, i.e. A separate position transducer, which generates a corresponding signal, is required to determine the current control state of the servo valve.
  • Servo valves also require relatively high working pressures, the desired low gas pressures corresponding to the pressure prevailing in the blood vessel cannot be given off directly, so that a downstream throttling resistance is required which has to be changed every time after use of this known injector for hygienic reasons.
  • the invention has for its object to provide a device of the type mentioned, which does not have the disadvantages mentioned or to a lesser extent and which is simple and inexpensive to manufacture.
  • the invention solves this problem in that the metering valve is designed as a proportional valve.
  • a proportional valve in the sense of the invention is any poppet valve whose opening cross-section is proportional to the (usually electrical) manipulated variable and in which no signal feedback of the valve path is required to determine the current actuating state of the valve, since the respective actuating state (opening cross-section) of the Proportional valve can be derived directly from the supplied (electrical) manipulated variable.
  • Such a proportional valve is considerably less expensive than the servo valve used in the prior art.
  • a proportional valve can release the gaseous medium directly with the relatively low excess pressure required for introduction into a blood vessel; an additional metering or throttling resistance as in DE-B 38 02 128 is not necessary.
  • small gas volume flows about 5-40 ml / s, depending on the vessel size) can also be metered precisely and flutter-free against the pulsating blood pressure.
  • US-A-5 094260 describes a so-called "proportional valve", which, however, is actually not a proportional valve in the sense of the present invention, but rather a conventional servo valve, which means an actuator is set. Its operating principle corresponds to the valve used in DE-B 3802 128.
  • a particularly serious disadvantage of these servo valves, particularly in medical technology, is that such electromotive operated valves remain open in the last set position in the event of a power failure, while the proportional valve used according to the invention closes automatically in the event of a power failure. So it offers a much higher inherent security.
  • DSA digital subtraction angiography
  • the control loop containing the sensor and the proportional valve is expediently designed to regulate the gas volume flow. It has been shown that the gas volume flow is the essential parameter influencing the quality of the angiogram, so that the controllability and Reproducibility of this parameter is particularly important.
  • the sensor arranged between the proportional valve and the gas outlet can be designed directly for measuring the volume flow or mass flow. As a rule, however, this sensor is a pressure sensor, which then measures the pressure prevailing at the outlet of the proportional valve.
  • the pressure at the proportional valve on the inlet side is the known outlet pressure of the pressure source.
  • the pressure drop via the proportional valve, the opening cross section of which is known in each case, can then be used to calculate and regulate the gas volume flow resulting on the output side of the proportional valve.
  • the primary pressure prevailing on the outlet side of the pressure source is also monitored without an additional pressure sensor being required. If a certain gas pressure at the outlet side of the proportional valve is no longer reached with a certain opening cross section of the proportional valve, this indicates a pressure drop in the pressure source, for example an empty gas bottle. The injector can then switch off automatically and trigger an alarm signal.
  • the control loop for regulating the gas volume flow can be subjected to correction factors corresponding to the compressibility of the gas used and the flow resistance of the gas outlet used. These correction factors can be taken, for example, from a database and fed to the control loop as a control variable. This ensures that the gas is actually released into the vascular system at the desired pressure and volume flow.
  • a temperature control device for the gaseous medium is advantageously provided. It can be designed, for example, as a temperature control chamber upstream of the proportional valve with electrical heating devices.
  • the proportional valve itself can also be provided with heating elements to heat the gaseous medium or to prevent the heated medium from cooling. In this way, the medium can be warmed to body temperature (37 ° C.) before being introduced into the blood vessel system, so that the vascular spasms (spastic occlusion of the blood vessel) that otherwise occur when liquid or gaseous media are injected into blood vessels are avoided.
  • temperature sensors can be provided in the temperature control chamber and / or between the proportional valve and the gas outlet. The cooling of the gas by pipe flows can be neglected given the small diameters and lengths of the gas outlets used.
  • the device according to the invention expediently has an adjustable maximum narrow limit for the gas introduced into the vascular system. This limitation prevents the body from being fed carelessly with an impermissibly high amount of carbon dioxide.
  • the gas outlet is generally designed as a catheter that can be inserted into the vascular system.
  • the connection point already mentioned above between the gas outlet and the vascular system is then the catheter tip from which the gas is released into the area of the vascular system to be angiographed. Since carbon dioxide has a low viscosity, even small blood vessels can be angiographed using appropriately thin catheters.
  • an additional switching valve is arranged between the proportional valve and the gas outlet.
  • “between” means that the switching valve is arranged in the flow direction of the gas between the proportional valve and the gas outlet.
  • the term “between” is also to be understood in this sense in the remaining claims.
  • “Switching valve” is to be understood as a valve that can be switched back and forth between the two states “closed” and “open”.
  • Such an additional switching valve makes it possible to pneumatically separate the gas outlet from the rest of the injector.
  • the device can be immediately separated from the vascular system in the event of malfunctions, on the other hand it can be prevented, for example, that blood rises back into the injector when the catheter is inserted and contaminates it.
  • An additional pressure sensor is advantageously provided between the switching valve and the gas outlet. After inserting the catheter, this sensor measures the blood pressure in the vascular system. Thus, even when the switching valve is still closed, the pressure against which the gas must be introduced into the vascular system is already known. Even before the switching valve is opened, the pressure prevailing at the proportional valve on the output side can therefore be adjusted accordingly, so that on the one hand no blood flows back into the injector when the switching valve is opened and on the other hand no carbon dioxide with excessive pressure is released into the vascular system .
  • This additional pressure sensor thus serves to measure the back pressure prevailing in the vascular system and to adjust the injection parameters accordingly before the start of the injection process.
  • a filter can also be arranged between the switching valve and the gas outlet.
  • a filter is expediently designed as a microfilter with a mesh structure of about 0.2 ⁇ m pore size. On the one hand, it serves as a very fine filter for the gas to be introduced into the vascular system and, on the other hand, as a reservoir with hydrophobic properties (impermeable to blood) which, for example in the event of malfunctions of the device, initially collects blood flowing back before it can enter the injector. It is possible here to use microfilters that are commonly used in anesthesia machines and that are changed after each use.
  • the filter can also be provided with a hydrophobic membrane as a gas-liquid barrier. In this way, it is prevented that liquid (blood) flows from the patient into the gas channels of the injector. The mutual contamination of both the patient and the device according to the invention is prevented.
  • a check valve and / or a liquid detector can additionally be arranged between the switching valve and the gas outlet as additional safeguards against the backlash of blood into the injector.
  • the check valve prevents backflow from occurring at all.
  • the liquid detector triggers an alarm when liquid flows back to it, closes the switching valve and shuts down the injector.
  • a foot switch can be provided to trigger the gas injection, so that the operating doctor has his hands free for other activities.
  • all parts of the device according to the invention that come into contact with the gaseous medium are heat and chemical resistant. They can then be sterilized by heating to temperatures around 65 ° C. and / or fumigation, for example with ethylene oxide or formaldehyde.
  • angioscopy Another method for examining blood vessels is angioscopy.
  • an angioscope endoscope
  • a camera or comparable optical device is inserted at the tip into the blood vessel to be examined.
  • the section of the vessel to be angioscoped must be rinsed free with an optically transparent medium. In the prior art, this is usually done with a physiological salt solution.
  • This liquid must be applied via a catheter at a relatively high pressure so that the blood is completely washed away and the corresponding section of the vessel is visible to the angioscope. This leads to turbulence in the interior of the vessel, which in turn can damage the inner walls of the vessel. Since large amounts of irrigation fluid (between 120 - 1100 ml / min) must also be injected, the heart may become overloaded.
  • the catheter has at least two lumens and that a lumen is connected to an inflatable balloon that surrounds the outer circumference of the catheter.
  • a lumen is connected to an inflatable balloon that surrounds the outer circumference of the catheter.
  • the balloon should be inflated with a pressure which is sufficient to largely block the undesirable flow of blood, but which is also not so great that damage to the inner walls of the vessel occurs. It is therefore expedient if the catheter lumen connected to the balloon is connected to the pressure source for the gaseous medium via a second proportional valve. In this way, the balloon can be inflated with a predetermined, defined pressure.
  • a pressure sensor is also arranged between the second proportional valve and the balloon, so that it can be reliably determined whether the balloon pressure required to block the blood vessel has been reached.
  • the balloon can first be inflated with a predetermined gas pressure and then the gas introduction into the vascular system can be triggered with an adjustable time delay.
  • the angioscope is introduced into the vessel through the same catheter lumen through which the CO 2 is also introduced into the vessel.
  • This is possible because modern angioscopes have an outer diameter of only 0.5 mm.
  • the narrowing of the cross-section of this catheter lumen through the angioscope can, however, lead to the pressure drop across this catheter lumen increasing in a manner which is hardly calculable.
  • the angioscope at the catheter outlet can be made to flutter by the gas flow or pressed against the vessel wall, so that no satisfactory angioscopic images are produced. It is therefore advantageous if the catheter has a separate, additional lumen for inserting an angioscope (endoscope).
  • a catheter for use as a gas outlet of a device described above has at least three lumens.
  • the gas flow through the angioscope then no longer occurs.
  • the lumen for inflating the balloon and the lumen for introducing the carbon dioxide into the vascular system have a diameter of approximately 0.4 mm
  • the lumen for inserting the angioscope has a diameter of approximately 1 mm.
  • Advantageous materials for such a catheter are PVC, polyurethane or polyethylene.
  • Figure 1 is a schematic representation of the gas injector.
  • Fig. 3 shows schematically a Vierlu igen catheter
  • FIG. 4 shows the catheter from FIG. 3 in cross section
  • FIG. 5 is an exploded view of the microfilter used behind the outlet of the switching valve.
  • the gas injector has a carbon dioxide bottle 1 as a pressure source, which is connected via a pressure reducing valve 2 and a microfilter 3 to a manually operated emergency shutdown valve 4.
  • a pressure reducing valve 2 By actuating this valve 4, the pressure source 1 is separated from the gas injector in emergencies.
  • An electrically operated input valve 5 then follows, with which the pressure source can also be separated from the gas injector. In emergency situations recognized by the automatic control of the gas injector, this input valve 5 serves as an emergency shutdown valve.
  • the pressure prevailing on the outlet side of the inlet valve 5 is monitored by a pressure sensor 5a, and pressure switches and sensors 6 are also provided for limit pressure detection of the permissible minimum and maximum pressures, which can be, for example, 3 or 5 bar.
  • the temperature control chamber 7 On the output side of the input valve 5, the temperature control chamber 7 is connected with an electrical heating device in which the gas is heated to the desired temperature, generally the body temperature of 37 ° C. This temperature is monitored by means of the temperature sensor 7a.
  • the proportional valves 8 and 11 are connected in parallel on the output side of this temperature control chamber 7.
  • Each of these proportional valves 8, 11 has a pressure sensor 8a, 11a on the output side, which detects the respective output pressure of the proportional valve and converts it into an electrical signal, which is then used again as Controlled variable for controlling the proportional valve is fed back.
  • the proportional valves 8, 11 are actuated electromagnetically and are explained in more detail below.
  • the temperature of the gas on the outlet side of the proportional valve 8 is monitored by means of the temperature sensor 10.
  • the pressure sensor 12 monitors the pressure on the output side of the proportional valve 11; in addition, for safety reasons, a limit pressure switch 18 is provided, which emits an alarm signal when a permissible maximum pressure (for example between 1 and 3 bar) is overwritten.
  • the pressure on the output side of the proportional valve 8 is monitored by a pressure sensor 9, and in addition a limit pressure switch 13 is also provided, which emits an alarm signal when a permissible maximum pressure is exceeded.
  • switching valves 14, 19 On the output side of the proportional valves 8, 11 there are electromagnetically actuated switching valves 14, 19, each of which is assigned a pressure sensor 16, 20 which, in the closed state of these switching valves 14, 19, measures the pressure present on the output side thereof.
  • An additional vent valve 15, designed as a 3/2-way valve, is provided behind the switching valve 14, by means of which the inflated balloon 24 can be vented.
  • a temperature sensor 17 for monitoring the gas temperature is provided downstream of the switching valve 19.
  • Microfilters 21, 22 connect to the output side of the vent valve 15 and the switching valve 19, the structure of which is explained in more detail below.
  • the outlet of the switching valve 19 feeds the lumen 23b of a catheter 23 via this microfilter 22. This lumen 23b is open at the catheter tip 25 and serves to introduce C0 2 into the blood vessel 26.
  • the switching valve 14 is on the outlet side via the vent valve 15 and the microfilter 21 is connected to the lumen 23a of the catheter 23, via which the balloon 24 can be inflated.
  • a control unit 27 is provided for monitoring all functions of the gas injector and for controlling the valves. For safety reasons, this control unit 27 has a microprocessor control with double redundancy.
  • microfilters 21, 22 The structure of the microfilters 21, 22 is explained in more detail in FIG. 5.
  • O-rings 56, 53 are inserted into the filter housing 57 and the screw cover 52, respectively.
  • a steel grid 54 also serves as the actual filter elements a mesh size of 5 ⁇ m and a hydrophobic membrane 55 with a pore size of 0.2 ⁇ m.
  • This filter disk or membrane 55 is hydrophobic and does not allow liquids such as blood to penetrate. It therefore represents a gas-liquid barrier.
  • the microfilters are connected to the gas line system via Luer lock connections 58, 59.
  • the valve housing 31 has a pressure inlet 28, a pressure outlet 29 and a vent outlet 30.
  • the valve housing 31 has a pressure inlet 28, a pressure outlet 29 and a vent outlet 30.
  • the magnetic device 35 which is only schematically indicated in the drawing, actuates the control piston 37 via a piston rod 36, which, in the idle state, rests sealingly on an axial surface of the main piston 32.
  • Main piston 32 and control piston 37 are designed as essentially cylindrical hollow bodies.
  • the control piston 37 has openings on its axial surface facing the magnetic device 35, which connect its interior to the ventilation opening 30.
  • the magnet device 35 pulls the control piston 37 in the opposite direction to the arrow A in FIG. 2 to such an extent that it lifts off the axial surface of the main piston 32 and thus the pressure outlet 29 with its inner cavity and thus also connects to the vent outlet 30.
  • the function of the injector is described below using the example of a gas injection with a previous balloon blockage of the blood vessel. The following injection parameters are entered into the control unit 27 or are already stored in it:
  • Catheter type volume, flow resistance, number of lumens, catheter with or without balloon
  • the catheter 23 is inserted into the blood vessel to be examined. Its two lumens 23a and 23b are connected to the corresponding connections of the injector. It must be ensured that the entire gas-carrying system no longer contains any foreign gases other than carbon dioxide, since otherwise air boluses could occur. For example, the catheter 23 can be rinsed with physiological saline for this purpose. Instead, an automatic flushing of the entire dead spaces of the gas injector, which can still contain ambient air, can be provided with C0 2 .
  • the control unit 27 now opens the input valve 5.
  • the outlet pressure of the proportional valve 8 is now set so that it corresponds to the desired filling pressure of the balloon 24. It is monitored by the pressure sensor 8a.
  • the output pressure of the proportional valve 11 (monitored by the pressure sensor 11a) is set such that it is somewhat higher than the blood pressure in the blood vessel 26 measured by the pressure sensor 20. The amount by which it is set higher than this blood pressure is determined on the one hand by the pressure drop taking place in the catheter and on the other hand by the desired volume flow with which the CO 2 is to be injected into the blood vessel 26.
  • the switching valve 14 is now opened and connects the output of the Proportional valve 8 with the lumen 23a of the catheter 23 and thus with the balloon 24.
  • This balloon is now inflated with the desired pressure and blocks the blood vessel 26.
  • the switching valve 14 can be closed again, the pressure transducer 16 then monitors the balloon pressure.
  • the switching valve 19 opens and connects the outlet of the proportional valve 11 to the lumen 23b of the catheter 23.
  • C0 ? can now flow into the blood vessel 26 from the catheter tip 25.
  • the volume flow of the inflowing carbon dioxide is regulated if necessary by adjusting the proportional valve 11 and kept constant over the desired period of time.
  • the gas volume flow at the outlet 25 of the catheter 23 is calculated from the following parameters:
  • the balloon 24 can be vented again via the corresponding vent outlet of the additional switching valve 15.
  • the gas injection is ended by closing the switching valve 19.
  • the gas is heated in the temperature chamber 7 and by means of the heating elements 8b, 11b provided in the proportional valves 8, 11, the monitoring or regulation of the desired temperature is carried out by means of the thermal sensors 7a, 10, 17.
  • the in addition to the pressure sensors 8a, 11a, pressure sensors 9, 12 monitor the pressure prevailing on the output side at the proportional valves 8, 11 and thus offer increased security against malfunctions.
  • connection 39 is above the lumen or Channel 49 (diameter 0.33 mm) in connection with the latex balloon 44 arranged near the patient end of the catheter. This latex balloon can thus be inflated by introducing gas into the connection 39.
  • Connection 40 is used to insert the angioscope and is connected to the angioscopy channel 48 (diameter 1 mm).
  • Connection 41 is connected to an additional working channel 50 (diameter 0.66 mm), which is used for aspiration or as an instrument channel.
  • Connection 42 is connected to the gas channel 51 (diameter 0.33 mm) through which the carbon dioxide is introduced into the vessel.
  • the channels 48, 50 and 51 are open towards the end of the catheter on the patient side, which is indicated in FIG. 3 by the reference symbols 45, 46 and 47.
  • the channel integrator or channel separator 43 brings together the four connections 39-42 and connects them to the respective lumens of the catheter.
  • the embodiment of the catheter shown has a length of 1.3 m and an outer diameter of 2.1 mm.
  • the latex balloon 44 is dimensioned so that it can block vessels up to a maximum inside diameter of 25mm.

Abstract

Un injecteur de gaz utilisé pour introduire un gaz dans un système de vaisseaux remplis de liquide comprend, en tant que source de pression, une bouteille de gaz carbonique (1) reliée aux entrées des soupapes proportionnelles (8, 11). Le gaz carbonique peut être introduit dans le vaisseau sanguin (26) par l'intermédiaire de la soupape proportionnelle (8) et le cathéter à flux volumique réglable. En outre, le vaisseau sanguin peut être bloqué par le ballon (24) qui peut être gonflé par l'intermédiaire de la soupape proportionnelle (8) et du passage (23a) du cathéter (23).
PCT/EP1993/003401 1992-12-04 1993-12-03 Injecteur de gaz WO1994013204A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP94902669A EP0671894A1 (fr) 1992-12-04 1993-12-03 Injecteur de gaz

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DEG9216558.3U 1992-12-04
DE9216558U DE9216558U1 (de) 1992-12-04 1992-12-04 Gasinjektor

Publications (1)

Publication Number Publication Date
WO1994013204A1 true WO1994013204A1 (fr) 1994-06-23

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Application Number Title Priority Date Filing Date
PCT/EP1993/003401 WO1994013204A1 (fr) 1992-12-04 1993-12-03 Injecteur de gaz

Country Status (3)

Country Link
EP (1) EP0671894A1 (fr)
DE (1) DE9216558U1 (fr)
WO (1) WO1994013204A1 (fr)

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US6106497A (en) * 1997-01-31 2000-08-22 Medical Instrument Development Laboratories System and method for preventing an air embolism in a surgical procedure
EP1074221A2 (fr) * 1999-08-04 2001-02-07 Grupo Grifols, S.A. Appareil pour l angiographie avec injection de CO2
EP1074222A2 (fr) * 1999-08-04 2001-02-07 Grupo Grifols, S.A. Dispositif d' injection de CO2 pour angiographie
FR2856306A1 (fr) * 2003-06-17 2004-12-24 Sedat Appareil medical de distribution d'au moins un fluide
WO2007090253A1 (fr) * 2006-02-08 2007-08-16 De Sa Roriz Paraguassu Dispositif electronique de regulation de la perfusion de dioxyde de carbone gazeux de qualite medicale
WO2008028723A1 (fr) * 2006-07-24 2008-03-13 Wolfgang Herrmann Systeme de dosage d'ozone ou d'un melange ozone/oxygene
US11602320B2 (en) 2019-05-29 2023-03-14 Siemens Healthcare Gmbh Method for creating a three-dimensional digital subtraction angiography image and a C-arm X-ray device

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DE102009037765B4 (de) * 2009-08-17 2011-12-29 Gottfried Hesse Verfahren und Vorrichtung zur Herstellung eines Gasgemisches
DE202010005131U1 (de) * 2010-04-09 2011-08-30 Jakob Hoiss Vorrichtung zum Befüllen eines Spritzenkörpers mit einem Gasgemisch zum anschließenden Injizieren eines Gemisches aus dem Gasgemisch und einem Medikament in den menschlichen oder tierischen Körper
DE102019207921B4 (de) * 2019-05-29 2022-08-11 Siemens Healthcare Gmbh Verfahren zur Erstellung eines 3D DSA-Bildes und C-Bogen Röntgengerät

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4030495A (en) * 1975-11-07 1977-06-21 Baxter Travenol Laboratories, Inc. Twin check valve pump system having fail-safe characteristic
US4332254A (en) * 1980-11-17 1982-06-01 Advanced Catheter Systems, Inc. System for filling and inflating and deflating a vascular dilating cathether assembly
WO1987000759A1 (fr) * 1985-07-29 1987-02-12 Minnesota Mining And Manufacturing Company Systeme d'irrigation
EP0316593A1 (fr) * 1987-11-17 1989-05-24 Richard Wolf GmbH Dispositif d'insufflation pour les interventions endoscopiques
DE3802128A1 (de) * 1988-01-26 1989-08-03 Backe Wolfgang Dosiervorrichtung fuer ein gasfoermiges medium
US5006109A (en) * 1989-09-12 1991-04-09 Donald D. Douglas Method and device for controlling pressure, volumetric flow rate and temperature during gas insuffication procedures
FR2663231A1 (fr) * 1990-06-15 1991-12-20 Walz Elektronik Gmbh Insufflateur.
US5094260A (en) * 1990-10-26 1992-03-10 Alcon Surgical, Inc. Proportional valve and pressure control system

Patent Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4030495A (en) * 1975-11-07 1977-06-21 Baxter Travenol Laboratories, Inc. Twin check valve pump system having fail-safe characteristic
US4332254A (en) * 1980-11-17 1982-06-01 Advanced Catheter Systems, Inc. System for filling and inflating and deflating a vascular dilating cathether assembly
WO1987000759A1 (fr) * 1985-07-29 1987-02-12 Minnesota Mining And Manufacturing Company Systeme d'irrigation
EP0316593A1 (fr) * 1987-11-17 1989-05-24 Richard Wolf GmbH Dispositif d'insufflation pour les interventions endoscopiques
DE3802128A1 (de) * 1988-01-26 1989-08-03 Backe Wolfgang Dosiervorrichtung fuer ein gasfoermiges medium
US5006109A (en) * 1989-09-12 1991-04-09 Donald D. Douglas Method and device for controlling pressure, volumetric flow rate and temperature during gas insuffication procedures
FR2663231A1 (fr) * 1990-06-15 1991-12-20 Walz Elektronik Gmbh Insufflateur.
US5094260A (en) * 1990-10-26 1992-03-10 Alcon Surgical, Inc. Proportional valve and pressure control system

Cited By (13)

* Cited by examiner, † Cited by third party
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US6106497A (en) * 1997-01-31 2000-08-22 Medical Instrument Development Laboratories System and method for preventing an air embolism in a surgical procedure
ES2162573A1 (es) * 1999-08-04 2001-12-16 Grifols Grupo Sa Aparato de angiografia por inyeccion de co2.
EP1074222A2 (fr) * 1999-08-04 2001-02-07 Grupo Grifols, S.A. Dispositif d' injection de CO2 pour angiographie
EP1074222A3 (fr) * 1999-08-04 2001-10-24 Grupo Grifols, S.A. Dispositif d' injection de CO2 pour angiographie
EP1074221A3 (fr) * 1999-08-04 2001-10-24 Grupo Grifols, S.A. Appareil pour l angiographie avec injection de CO2
ES2161618A1 (es) * 1999-08-04 2001-12-01 Grifols Grupo Sa Dispositivo para la inyeccion de co2 para angiografia.
EP1074221A2 (fr) * 1999-08-04 2001-02-07 Grupo Grifols, S.A. Appareil pour l angiographie avec injection de CO2
US6503226B1 (en) 1999-08-04 2003-01-07 Grupo Grifols, S.A. Apparatus for angiography by the injection of CO2
FR2856306A1 (fr) * 2003-06-17 2004-12-24 Sedat Appareil medical de distribution d'au moins un fluide
US7762983B2 (en) 2003-06-17 2010-07-27 Sedat Medical device for distributing at least one fluid
WO2007090253A1 (fr) * 2006-02-08 2007-08-16 De Sa Roriz Paraguassu Dispositif electronique de regulation de la perfusion de dioxyde de carbone gazeux de qualite medicale
WO2008028723A1 (fr) * 2006-07-24 2008-03-13 Wolfgang Herrmann Systeme de dosage d'ozone ou d'un melange ozone/oxygene
US11602320B2 (en) 2019-05-29 2023-03-14 Siemens Healthcare Gmbh Method for creating a three-dimensional digital subtraction angiography image and a C-arm X-ray device

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DE9216558U1 (de) 1994-03-31

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