EP0566710A1 - Procede et dispositif medico-techniques de mesure de l'irrigation sanguine d'organes - Google Patents

Procede et dispositif medico-techniques de mesure de l'irrigation sanguine d'organes

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Publication number
EP0566710A1
EP0566710A1 EP92919928A EP92919928A EP0566710A1 EP 0566710 A1 EP0566710 A1 EP 0566710A1 EP 92919928 A EP92919928 A EP 92919928A EP 92919928 A EP92919928 A EP 92919928A EP 0566710 A1 EP0566710 A1 EP 0566710A1
Authority
EP
European Patent Office
Prior art keywords
measuring
coding
probe
electrode
measurement
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Withdrawn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
EP92919928A
Other languages
German (de)
English (en)
Inventor
Hans BÄR
Eduard Dr. Hirsbrunner
Daniel Flückiger
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.)
Individual
Original Assignee
Individual
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 Individual filed Critical Individual
Publication of EP0566710A1 publication Critical patent/EP0566710A1/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14542—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring blood gases
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1468—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means
    • A61B5/1473—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means invasive, e.g. introduced into the body by a catheter
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1495—Calibrating or testing of in-vivo probes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/6848—Needles
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0209—Special features of electrodes classified in A61B5/24, A61B5/25, A61B5/283, A61B5/291, A61B5/296, A61B5/053
    • A61B2562/0215—Silver or silver chloride containing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/04—Arrangements of multiple sensors of the same type
    • A61B2562/043—Arrangements of multiple sensors of the same type in a linear array
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/08—Sensors provided with means for identification, e.g. barcodes or memory chips

Definitions

  • the present invention relates to a method for measuring the blood flow to an organ, in particular a human tissue, using the hydrogen washout method, and to suitable means for carrying out this method.
  • the blood of the test subject is enriched with hydrogen and used as an electrolyte which forms a galvanic element with two electrodes inserted into the tissue to be examined.
  • the electrical voltage of this element is determined, among other things, by the concentration of hydrogen in the blood.
  • the hydrogen is introduced into the blood with the breathing air or by injection. As soon as the voltage between the electrodes has reached a certain limit, the supply of hydrogen is interrupted and the decrease in the voltage as a function of time is observed.
  • the steepness of the measurement curve of this function is a measure of the blood flow to the tissue, in which the blood enriched with hydrogen is removed and replaced by blood free of hydrogen.
  • the theoretical basis of this method in particular the calculation of the potentials of the electrodes as a function of the hydrogen ion concentration using the serious equation and the Determination of the blood flow to a tissue volume from the decrease in the concentration of hydrogen in the blood using the diffusion laws are described in detail, for example, by K.Auckland et al in Circulation Research, Volume XV, 1964, pages 164ff.
  • a device with which for the first time the blood circulation of tissue can be used according to the advantageous hydrogen washing-out method without the measuring current which is physiologically questionable for humans is used described for example in EP patent application No. 0 452 276.
  • a plurality of probes are introduced into the tissue at a plurality of spatially separated locations.
  • several measuring devices are required today and an undesirably large amount of effort is required to achieve usable results.
  • This spatial measurement is particularly difficult for long-term measurements due to the repeated insertion of new probes and the adjustment of these newly inserted probes.
  • the insertion of new probes at predetermined locations of an organ to be examined requires an undesirably high expenditure on equipment and can only be carried out by appropriately trained doctors.
  • the object of the present invention is therefore to create a method for measuring the blood flow using the hydrogen washout method, which overcomes the known disadvantages and in particular enables reproducible long-term measurements with several probes and high security against manipulation.
  • the method according to the invention provides for the use of interchangeable probes of any kind or connecting elements or other medical-technical utensils which are inseparably provided with codes,
  • age and type for example, in order to be able to monitor their correct connection in the assembled, that is to say application-ready, condition. to be able to operate them from a single measuring device and / or therapy device, respectively. to enable an additional anterograde and / or posterodrade function control and monitoring.
  • the advantages achieved by the invention lie essentially in increasing the functional and thus patient safety, in particular by checking all contacts and functions between the measuring device and the arbitrarily arranged probes, medical-technical instruments or utensils, in the possibility of long-term measurements with increased measuring accuracy and the multi-dimensional display of measured values, as well as in quality assurance and in the variety of applications made possible by the modular design.
  • the probes and / or the connection elements can return stored or measured information. report on. This operating method also allows special functions of the probes to be controlled in a targeted manner.
  • a measuring device in this case also a control device, which is suitable for performing the method according to the invention has at least the features listed in the present claim 4.
  • the measuring electrode and the reference electrode essentially consist of metals whose chemical natural potentials are close to one another. Both the measuring electrode as well as the reference electrode are connected to the inputs of an operational amplifier via appropriate feed lines to form the difference of their potentials.
  • the measuring electrode, the reference electrode and the neutral electrode and their leads have a shield against external interference fields.
  • the shields of the measuring and reference electrodes and their leads are connected to the neutral electrode via the positive input of a voltage amplifier circuit and the negative input of this voltage amplifier circuit is connected to the one to form the mean value the potentials of the measuring and reference electrodes, connected between the leads of these electrodes connected voltage dividers.
  • the measuring device is preferably equipped with an electronic multiplexer, with which the voltage applied to the individual sensors is scanned in succession, for example 5 times per second.
  • this device Since the measuring part of the device is electrically isolated from the other parts of the device, this device makes it possible to carry out the hydrogen washout method for determining the blood flow in a reproducible manner with physiologically acceptable current strengths.
  • FIG. 1 a flow chart with the essentials of the invention
  • FIG. 3 a circuit diagram of the analog or measuring part of a measuring device suitable for carrying out the method
  • FIG. 4 a detailed circuit diagram of the analog or measuring part of a measuring device suitable for carrying out the method
  • FIGS 5a - 5q connecting pieces, connecting elements or
  • FIGS. 6a-6o probes as are suitable for carrying out the method according to the invention
  • FIG. 7 a possible measuring arrangement for carrying out the method according to the invention.
  • step a To measure the spatial blood circulation distribution of a human organ, several detachable, individually coded probes are implanted spatially distributed in a tissue to be examined in step a). This step is usually done by an experienced doctor.
  • step b the individual probes now implanted are connected via coded connecting elements to a measuring device for determining the blood flow rate using the hydrogen washout method. Thanks to the present method, this second step can also be carried out by trained auxiliary personnel.
  • step c the individual coding values of the probes, connecting elements and possibly other medical utensils are read and checked by the measuring device.
  • the measuring device displays a corresponding error message F. If the control performed by the measuring device does not lead to an error message, the measured value acquisition unit is released for signal acquisition at the measuring electrodes. Simultaneously with the measurement d), the measured values are stored together with the associated coding values, displayed or fed to the evaluation A.
  • the probes can be left in the tissue and method step c) in regular intervals are repeated. After a desired duration, a further measurement can preferably be carried out using the hydrogen washout method. The measured values of the individual measurements are then subjected to an evaluation A.
  • the block diagram shown in FIG. 2 shows a power supply unit 100 which is connected to a supply 200, which supply has a potential lock of at least 4 kW and supplies an analog part 300 with the necessary voltage.
  • the probes A and B are connected to the analog part 300.
  • the likewise electrically isolated output of the analog part 300 is connected to a digital part 400.
  • catheter-like probes are implanted, through the cannulas of which the electrodes required for the desired measurement are inserted, preferably with a needle.
  • the electrodes required for the desired measurement are inserted, preferably with a needle.
  • they can be removed and / or replaced after a series of measurements has taken place or, by successively extending the needle, contaminated electrodes can always be used for the measurement.
  • This flowchart can also be used for other measurement and therapy techniques, e.g. 0 ⁇ -, pH, glucose, potassium, temperature, blood pressure, intracranial pressure measurements, as well as medicinal infusion devices are taken over.
  • FIG. 3 shows the measuring part of a measuring device suitable for carrying out the method.
  • Essential to the invention is the measurement value acquisition unit 46, which is connected to a probe connector 52.
  • the fixed resistor 54 forms one together with the grounded coding resistor 49 Voltage divider whose value is recognized by the measured value acquisition unit 46.
  • the measuring electrode 11 shielded against external interference potentials is connected via a feed line 12 to a first impedance converter 14, the output of which is connected to the negative input of a measuring amplifier 13.
  • a shielded 27 reference electrode 15 is connected via a feed line 17 to a second impedance converter 16, the output of which is connected to the positive input of the measuring amplifier 13 via a resistor which can be regulated for zero adjustment.
  • the measuring device which is preferably used for the method according to the invention also has a driving neutral electrode 29 with which opposing fields are actively coupled in to the measuring region in order to compensate for external interference fields.
  • the mean value from the voltage divider 31 of all signals is kept at zero volts by changing the common mass.
  • the mass feedback via the two inverting amplifiers 28, respectively.
  • a PI controller is high-resistance, for example via a 100 kOhm resistor.
  • the supply line 24 for the interference voltages is connected to the shields 25, 27.
  • the output of the differential amplifier 13 is connected to an A / D converter 46 via a low-pass filter.
  • the block 46 shown in FIG. 3 detects six signals and has a 10-byte resolution (1024 bytes).
  • the A ⁇ capitaung on the digital side is effected by a micro- • processor 41 via a data bus 51 having at least four leads which are connected via optical coupler 47 to the A / D converter 46th
  • a suitable transmitter 48 is provided for the supply.
  • the free analog inputs 33, 50 can be further signals such as eg record pH value, temperature or codes.
  • the processor Via the four digital lines 51, the processor can transmit signals into the analog part simply and with the same connections. The transmission is serial and can be expanded as required. This gives you the option, for example, of controlling the current for H_ generation, switching over the measuring range or changing OFFSET and amplification during signal detection.
  • the digital part mainly consists of the processor 41, the program of which is stored in an EPROM of the memory 42. In addition, a timer and an 8 to 32 kbyte RAM memory are provided, the operation of which is secured by a built-in battery.
  • the voltage of the probes is measured five times a second.
  • the current value is calculated from this and shown in the display.
  • the signal of the probe coding is read and stored in the non-volatile memory and made available for evaluation.
  • the mean value of the exponential regression is preferably calculated from five to ten measured values in order to further eliminate measurement value disturbances.
  • FIG. 4 shows the circuit diagram of the analog or measuring part for two coded probes in detail.
  • the probes are connected to the device with a multi-pin plug connector made of plastic and a highly flexible and shielded probe cable.
  • Each of these parts has a special coding that can be recognized by the device.
  • Figures 5a - 5q show different embodiments for connectors and connecting elements respectively.
  • Final elements as are required for the execution of the method according to the invention.
  • Such and other connecting pieces and connecting elements are generally known in medical technology and, according to the invention, are provided with an electronically recognizable coding, i.e. If necessary, include at least one shielded electrical line with a corresponding contact point for establishing an electrical connection between an independent or integrated in the measuring device code reading unit and the coding element, which e.g. are formed from a resistance element, a microchip or other electronic components with de inable value or condition.
  • FIGS. 6a-6o show examples of probes and, in particular, electrode carriers as can be used for carrying out the method according to the invention. Since practically an unrestricted area of application in medicine is possible, the probes also have a variety of shapes and properties. The following list is therefore limited to only a few basic types, which of course can be easily adapted to the corresponding needs in their design.
  • each electrode is. each measuring and or therapy head is individually managed. This embodiment makes it possible to place the individual electrodes locally independently. This results in three individual electrode carriers with the associated electrode materials.
  • the electrodes are combined in one probe. With this embodiment, all electrodes are placed in the same place. The result is only a single probe with the associated electrode materials.
  • This special embodiment even allows the sensitive measuring electrodes to be exposed only for the desired measurement and then to be pulled back into the protective cover.
  • several electrodes are combined in one probe. A three-dimensional measurement is possible with this embodiment. The result is only a single probe with the associated electrode materials.
  • the electrodes can be used all possible forms, such as are already as membrane- covered Electrodes, implantierb 'are electrodes for W, 0 or bioelectric signals, adhesive electrodes-surface-electrodes, Ei ⁇ wegelektrode ⁇ , Stechelelektroden, brush electrodes, disk microelectrodes, thin film electrodes, 3D electrodes are known.
  • ultrasound probes or catheters such as, for example, venous catheters, central venous catheters, arterial catheters, cardiac catheters, balloon catheters, lung catheters, shunt measuring catheters, stenosis measuring catheters, liver catheters, port-a-cath catheters, intracranial pressure catheters, drainage catheters, kidneys / urine catheters , Probe catheter (for temperature, blood pressure, H_, 0_, etc.) or in biopsy and puncture instruments, as also shown in FIGS. 5o-5q and 6a-6e.
  • the carrier materials used are preferably polyamide, p + type silicone, n type silicone, silicone rubbers, Kapton (polyi ide), Pyrex, Teflon, Tri-Mil insulated silver wire, Dacro ⁇ -mesh matrix, carbo ⁇ , polyethylene, polyethylene glycol, polyurethane , borosilicate, epoxy resin, Hysol epoxy, epoxylite, cyanoacrylate, stainless steel, silastic, parylene-N, polystyrene, polyepichlorohydrin, cellulose acetate membrane, PVC membrane.
  • the probes resp. Therapy heads can also carry transistors or other sensors as well as controllable valves.
  • a probe detection is integrated in all probes used in connection with the blood flow meter. This coding has the advantage that the device automatically recognizes the respective probe type, whereby a probe-specific and measurement-specific software can be loaded. Defective or third-party products which lead to error measurements can also be identified
  • the probe can select a defined filter value in the measuring device.
  • Various circuitry implementations are possible in the coding.
  • coding with resistance a defined voltage potential being generated with this resistance, which potential is fed to the microprocessor via A / Q converter.
  • the software processes the corresponding signal and automatically selects the associated parameters.
  • coding with AS1C customer-specific IC
  • AS1C customer-specific IC
  • the microprocessor processes this signal and then also selects the associated parameters.
  • Can the coding of the corresponding reader resp. -Device parts are not decrypted, an alarm signal can be triggered.
  • These codes are also integrated in the catheters etc., which ensures that the probe type is clearly assigned.
  • the device (measuring and / or application and / or control device is capable of clearly recognizing the specifically coded electrode, micropipette, catheter connecting element and / or measuring therapy head and can only be compatible with them and therefore function properly.
  • the coding can give the appropriately programmed basic device, for example, the following information: make of the electrode, type of electrode, function of the electrode, functionality of the electrode, functional state of the electrode, location of the electrode, age of the electrode, section resp. Sector identification on the electrode resp. Catheter, electrode-specific baseline. With an active coding element, there is even the possibility of coding the measurement signal itself.
  • a part of the measuring electronics can also be integrated in miniaturized form into the respective probe and in particular at its measuring tip.
  • the coding element can have a preamplifier, control and control function and is a component of the measuring and / or application probe, micropipette, catheter, connecting element and / or measuring therapy head.
  • the coding element lies in the distance between the measuring tip and the device and can be attached or attached directly to the probe, the micropipette or the catheter etc. is integrated into it. It can also be part of the Forwarding or a corresponding screw, plug or bayonet connection to the device. It is understood that the coding element can also be part of the sheath or sheath of the electrode, the micropipette or the catheter etc. and has a direct connection with the electrode function, the micropipette function or the catheter function, i.e. Control functions for the respective use takes over.
  • the advantages of the coding lie in quality assurance, patient safety and the reproducibility of the measurements, in particular the long-term measurements.
  • material properties can be determined by the coding, the localization of the electrodes, micropipettes or catheters etc. can be made clear can be defined, a basis for coordinate capability with multidimensional measured value resp.
  • the display of the measurement object, the electrode-specific measurement range can be automatically determined, an electrolysis or Stimulation current limitation (organ or function-specific fuse) can be implemented and electrode-specific calibration values can be recorded. Regardless of this, the coding of medical-technical utensils opens up further advantageous uses of the aids according to the invention.
  • the coded connectors can be used to check and monitor the lines of conventional H_ explosimeters for correct closure.
  • the measuring device according to the invention can be combined with other devices, such as devices for infusing liquids and medications.
  • the measuring electrodes can also be used as sensors for measuring the concentration of applied medicaments, for example vitamin C complexes, or for monitoring the pH value, the glucose value, the potassium value, etc. can.
  • the measuring arrangement shown in FIG. 7 shows a patient 500 who is connected to a hydrogen container 502 via an encoded mask 501.
  • An infusion bottle 503 is connected to an infusion needle 504 with corresponding connection elements.
  • Measuring probes 506 and an operating instrument 507 are also connected to the Measuring device 508 connected.
  • Implanted probes 505 are provided with an electromagnetic, readable coding. All the utensils and instruments used are also provided with a code 510.
  • probes with a plurality of electrodes are preferably used, which electrodes are lifted out of a protective sleeve or covering for the measurement.
  • This covering can consist of a resorbable material.
  • the probes are provided with means with which the electrodes can be sanded bright before each measurement. It is understood that this method and its means can also be used in technical and industrial areas.
  • the probes are connected to the measuring device via five-pole electrical lines. In order not for each of the coded used
  • IC bus circuit an RS 485 or a
  • ASB bus system can be used, or the supply voltage for the active coding elements or a signal processor TSS 400, which is commercially available today, can be clocked in order to send the measurement data during sleep mode of the supply voltage via the same conductors.
  • a PAL'S programmable logic array
  • PAL'S programmable logic array
  • the coding elements can integrate a microprocessor. This has recently made it possible to manage data transmission in the form of a logical ring, described below as "Tokenring-H_".
  • the token ring H_ is passed on from active subscribers to active subscribers in a numerically increasing subscriber address sequence with a token telegram.
  • the participant with the highest address is an exception; it returns a tolken to the central unit (which has the lowest address) to close the logical ring.
  • an active participant receives a token telegram addressed to him from his predecessor, then he can use the token and process message cycles.
  • Its predecessor determined on the basis of the entries in the list of active stations (LAS), which was generated according to P0WER-0N in the list Tolken phase and which is continuously updated later when a Tolken telegram is received. If the token sender is not the registered predecessor, the addressee must first assume that an error has occurred and ignores the tolken.
  • a request status is received during LAS generation, then it must acknowledge with the status "not ready for the ring". All other telegrams are not processed in the list token state, ie neither acknowledged nor answered. If the software recognizes its own address when capturing the active participants in two token telegrams in the source address, it must assume that a participant with the same address is already in the ring. It must then go into the off-line state and submit a report to the management (central unit).
  • the software assumes the ClaimToken-State state after the ListenToken-State or Active-State state if its TimeOut has expired, if no bus activity has been detected for a certain time and it must be assumed that the token has been lost. In this state, an attempt is made to reinitialize the logical ring or to start an initialization.
  • the central unit is therefore always able to Check the active number of participants using the list of active stations (LAS) and immediately trigger an alarm if there is a change.
  • the number of participants (hose, connector, probe, etc.) is also not limited to a specific number, and the individual participants can be interconnected in any order. It follows from this that only one processor type with the same software is always used for each conceivable connection, which of course considerably simplifies the manufacturing process.
  • the individual components are then only loaded with some component-specific data. This data is stored in the EEPROM area of the processor and could be changed at any time if necessary.
  • a possible need for change is a change in parameters based on empirical determinations.
  • the central unit of the measuring device is thus able to check the active codes at any time.
  • the number of medical technology components used is not a software-related restriction subject and can be switched in any order, that is not specified and combination, without the software having to be adjusted or changed. In this way, not only can basic data of the individual medical-technical components be recorded, but expiration data, for example of stored blood, can be stored and evaluated.
  • the above measurement and control method can also work in multiplex mode or for control purposes for medical manipulations, e.g. periodic tissue removal, medication applications etc. is suitable.

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  • Life Sciences & Earth Sciences (AREA)
  • Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Biomedical Technology (AREA)
  • Medical Informatics (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • General Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Optics & Photonics (AREA)
  • Chemical & Material Sciences (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • General Chemical & Material Sciences (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Measuring And Recording Apparatus For Diagnosis (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

Abstract

Un dispositif de mesure concerne un patient (500) relié au moyen d'un masque codé (501) à une bouteille d'hydrogène (502). Une bouteille de transfusion (503) est reliée à une aiguille de transfusion (504) par des éléments correspondants de liaison. Des sondes de mesure (506), ainsi qu'un instrument chirurgical (507), sont eux aussi reliés à l'appareil de mesure par des éléments de liaison pourvus de raccords correspondants. Des sondes implantées (505) sont pourvues d'un code lisible par des moyens électromagnétiques. Tous les outils et instruments utilisés sont également pourvus d'un code (510).
EP92919928A 1991-09-26 1992-09-25 Procede et dispositif medico-techniques de mesure de l'irrigation sanguine d'organes Withdrawn EP0566710A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
CH286091 1991-09-26
CH2860/91 1991-09-26

Publications (1)

Publication Number Publication Date
EP0566710A1 true EP0566710A1 (fr) 1993-10-27

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EP92919928A Withdrawn EP0566710A1 (fr) 1991-09-26 1992-09-25 Procede et dispositif medico-techniques de mesure de l'irrigation sanguine d'organes

Country Status (8)

Country Link
US (1) US5830129A (fr)
EP (1) EP0566710A1 (fr)
JP (1) JPH06507815A (fr)
AU (2) AU667055B2 (fr)
CA (1) CA2096836A1 (fr)
FI (1) FI932354A (fr)
NO (1) NO931879D0 (fr)
WO (1) WO1993005700A1 (fr)

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US20040215235A1 (en) 1999-11-16 2004-10-28 Barrx, Inc. Methods and systems for determining physiologic characteristics for treatment of the esophagus
US20060095032A1 (en) 1999-11-16 2006-05-04 Jerome Jackson Methods and systems for determining physiologic characteristics for treatment of the esophagus
WO2001035846A1 (fr) 1999-11-16 2001-05-25 Ganz Robert A Systeme et procede de traitement de tissus anormaux dans l'oesophage humain
DE10155886B4 (de) * 2001-11-14 2006-07-13 Endress + Hauser Conducta Gesellschaft für Mess- und Regeltechnik mbH + Co. KG Automatisierbare Mess-, Reinigungs-und/oder Kalibriereinrichtung für Elektroden zur Messung von ph-Werten oder Redoxpotentialen
US20030225334A1 (en) * 2002-01-31 2003-12-04 Christopher Hicks Sensor identification method and system
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US5830129A (en) 1998-11-03
WO1993005700A1 (fr) 1993-04-01
NO931879D0 (no) 1993-05-24
FI932354A0 (fi) 1993-05-24
CA2096836A1 (fr) 1993-03-27
FI932354A (fi) 1993-05-24
AU667055B2 (en) 1996-03-07
JPH06507815A (ja) 1994-09-08
AU4220596A (en) 1996-06-06
AU2589892A (en) 1993-04-27

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