EP2884892A1 - Procédé permettant de déterminer la distribution régionale d'une mesure en perfusion pulmonaire - Google Patents

Procédé permettant de déterminer la distribution régionale d'une mesure en perfusion pulmonaire

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Publication number
EP2884892A1
EP2884892A1 EP13750289.4A EP13750289A EP2884892A1 EP 2884892 A1 EP2884892 A1 EP 2884892A1 EP 13750289 A EP13750289 A EP 13750289A EP 2884892 A1 EP2884892 A1 EP 2884892A1
Authority
EP
European Patent Office
Prior art keywords
control
evaluation unit
perfusion
lung
bolus
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Withdrawn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
EP13750289.4A
Other languages
German (de)
English (en)
Inventor
Tim BAIER-LÖWENSTEIN
Yvo Gärber
Stefan Mersmann
Eckhard Teschner
Steffen Leonhardt
Robert Pikkemaat
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.)
Draegerwerk AG and Co KGaA
Original Assignee
Draeger Medical 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 Draeger Medical GmbH filed Critical Draeger Medical GmbH
Publication of EP2884892A1 publication Critical patent/EP2884892A1/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Withdrawn legal-status Critical Current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
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/053—Measuring electrical impedance or conductance of a portion of the body
    • A61B5/0536—Impedance imaging, e.g. by tomography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/026—Measuring blood flow
    • A61B5/0275—Measuring blood flow using tracers, e.g. dye dilution
    • A61B5/028—Measuring blood flow using tracers, e.g. dye dilution by thermo-dilution
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
    • A61B5/0813—Measurement of pulmonary parameters by tracers, e.g. radioactive tracers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/74—Details of notification to user or communication with user or patient ; user input means
    • A61B5/742—Details of notification to user or communication with user or patient ; user input means using visual displays
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/74—Details of notification to user or communication with user or patient ; user input means
    • A61B5/746—Alarms related to a physiological condition, e.g. details of setting alarm thresholds or avoiding false alarms
    • 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
    • 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
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142—Pressure infusion, e.g. using pumps
    • A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
    • A61M5/1452—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons
    • 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
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/172—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body electrical or electronic
    • A61M5/1723—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body electrical or electronic using feedback of body parameters, e.g. blood-sugar, pressure
    • 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
    • A61M2205/3368—Temperature
    • 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
    • A61M2205/35—Communication
    • A61M2205/3576—Communication with non implanted data transmission devices, e.g. using external transmitter or receiver

Definitions

  • the present invention relates to a device for loading ⁇ humor of the regional distribution of a measure of the lung perfusion in a sectional plane of the thorax of a patient with an electrical impedance tomography unit can be attached with a plurality of electrodes distributed around the circumference of the sectional plane of the thorax, and a control and evaluation unit connected to the plurality of electrodes, which is adapted to successively supply AC or AC voltage to each pair of electrodes and to receive voltage or current signals of the remaining electrodes as measurement signals and to reconstruct the impedance distribution in the sectional plane from the measurement signals; is provided with a supply means for intravenous delivery of a Leitdozensskontrastmit ⁇ means of, wherein the control and evaluation unit continues to be directed ⁇ , the changes of the impedance distribution due to the supply of conductivity contrast agent as a measure of Lun ⁇ genperfu sion in the cutting plane as a function of time.
  • Such a device is known from the article "Determination of lung perfusion by means of electrical impedance tomography", Henning Luepschen et al, Biomed Tech 2010;.. 55 (Suppl. 1), be ⁇ withdrawn
  • the apparatus comprises a Elektroimpedanztomographie- unit (EIT-unit) as they are widely used in techniktechni ⁇ 's applications.
  • EIT-unit has a plurality of electrodes distributed around the circumference of a sectional plane of the thorax are mounted.
  • a control and evaluation available which is connected to the Elekt ⁇ roden and which is adapted to successively supply AC or AC voltage to each pair of the plurality of electrodes and increase the resulting voltage or current signals of the other electrodes as measuring signals on ⁇ and from the measurement signals to reconstruct the impedance distribution in the cutting plane. More precisely, the impedance is not absolutely determined, but rather its change compared to a reference distribution.
  • Such an EIT unit is described, for example, in EP 2 228 009 A1.
  • a manually operated supply means eg, a syringe for intravenous supply of a conductivity contrast agent is present.
  • a conductivity contrast agent liquids can ⁇ used , whose conductivity differs significantly from that of blood.
  • the instantaneous values of the impedance can be displayed spatially resolved in a two-dimensional representation, the instantaneous values being represented by corresponding brightness values.
  • To Administration of a bolus of the conductivity contrast agent then displays, for example, first, the inflow of contrast agent into the right heart, where thereby exhibiting a correspondingly increased brightness in the image of the sectional plane of the thorax in the Be ⁇ reaching the right heart, after which the contrast medium, the right ventricle in the direction Lung leaves, causing the initially displayed with increased brightness right heart parts are darker again and the lungs brighter, after which the contrast ⁇ medium then flows back into the left heart, which then appears with ent ⁇ accordingly increased brightness on the display device.
  • a temporally varying representation of the instantaneous impedance value can also be displayed with spatial resolution, for example the maximum amplitude of the dilution curve or the integral value via the dilution curve; in the latter cases, a single spatially resolved representation of a measure of lung perfusion would then be generated for the administration of a bolus of the conductivity contrast agent.
  • the term "measure of lung perfusion" is used here to make it clear that the lung perfusion values do not have to be determined absolutely here, but only the relative proportions of the total perfusion can suffice.
  • the contrast agent When measuring lung perfusion with the aid of a conductivity contrast agent, the contrast agent must first be injected in order then to start the perfusion measurement on the EIT unit. This results in two problems in performing a measurement: a) based on the administration of the contrast agent, and b) based on the lung perfusion measurement.
  • a) based on the administration of the contrast agent In the transfer of the conductivity contrast agent has the Ge ⁇ speed at which the agent is administered under ⁇ To stands great influence on the accuracy of the measurement and the comparison of different measurements with one another. This is especially the case when the contrast agent is applied manually without detection of the exact volume and / or the exact time.
  • the administration of the contrast ⁇ takes place by means of manually and without technical supervision is not to be assumed that the in vivo concentration of the contrast medium is comparable for all measurements, and the possibility to quantify and comparability of EIT analysis is therefore not ensured.
  • the supply device for the conductivity contrast agent has a controllable metering device.
  • the control and evaluation unit and the metering device are connected to each other via a data connection and set up so that at least start and end time and amount of Ab ⁇ administration of a bolus of the conductivity contrast agent of the control and evaluation are available as parameters.
  • This, of course are also sets of parameters comprises arising by order ⁇ bill, such as start time, quantity and Injekti ⁇ ons horrus or start the timing, amount and duration of injection, etc ..
  • control and evaluation unit can be adapted to the control and evaluation unit, the controllable dosing a predetermined start time, a predetermined amount and a specified differently surrounded time course of the infusion of the conductive contrast medium as control parameters via the data link to- send.
  • the control and evaluation unit can only start the metering device and, as feedback from the metering device, receives the exact start time, the quantity and the time course of the infusion of the conductivity contrast agent.
  • the controllable metering device can be driven directly or indirectly via the control and evaluation unit also in third devices (eg, ventilator or patient monitor), wherein the metering device then concerning data starting time, administered amounts and time ⁇ union course of the bolus dose to the control and evaluation unit sends.
  • the data communication over the data connection can be implemented both wired and wireless.
  • control and evaluation unit is further configured to repeat the administration of the bolus of the conductivity contrast agent at predetermined time intervals and to display a trend representation representing the temporal development of the measure of lung perfusion as a function of time.
  • the delivery of the bolus can be manually triggered by operating a switch, wherein the actuation of the switch causes the Do ⁇ metering device for delivery of the bolus of the conductivity contrast ⁇ means, said metering device is started either by the control and evaluation unit, the pre give ⁇ nen Parameters (start, amount and time course of the bolus ⁇ task) are then known or directly without the interposition of the control and evaluation unit is started, the metering ⁇ device is adapted to the said parameters of bolus delivery then to the control and evaluation send.
  • the repeated actuation of the controllable metering device at predetermined time intervals from third devices can take place directly or indirectly via the control and evaluation unit.
  • control and evaluation unit is further adapted to the measure of the Perfu ⁇ sion spatially resolved via the pulmonary surface in the section plane through the thorax to bring two-dimensionally displayed.
  • control and evaluation unit is further adapted to determine the perfused area in the sectional plane and perfused FLAE ⁇ Chen, resulting respectively from the administration of a bolus of Conductive ⁇ keitskontraststoffs serving as trend display as function ⁇ on To show the time of the gifts of the boluses of the conductivity contrast medium.
  • perfused surfaces it is possible to define regions in which the measure for the perfusion lies above a predefined threshold value.
  • control and evaluation unit is further configured, in times without administration of conductivity contrast agent, from the impedance distributions of the sectional plane of the thorax to determine the regional distribution of the ventilator. tion and display it as a function of time. Procedures for determining the intratidal distribution of ventilation across the cross-section of the lung are described, for example, in EP 2 228 009 A1.
  • the metering device is provided with a temperature sensor for Leitdozensskontrastmit ⁇ tel or with a controllable by the control and evaluation unit for tempering the Leitdozensskontrastmit ⁇ tel.
  • the control and evaluation unit is to be ⁇ directed to determine from the determined or set by the tempering temperature of the Leitdozensskontrastmit ⁇ means of the cardiac output based on the Dilutionslicks and calibrate absolutely the measure of lung perfusion, due to the specific cardiac output.
  • an isotonic solution can be used for the calibration, the conductivity does not change and thus is not a conductivity contrast agent in the true sense.
  • the accuracy of measurement is increased, the comparability ver ⁇ different measurements as it is ensured that cyclic auto matic ⁇ measurements can be performed and the possibility of operator error is reduced by the user.
  • the administration of the contrast agent is carried out under conductivity defi ned ⁇ conditions such that the control and evaluation of the EIT-unit start time, volume and velocity are known to injection.
  • the control and evaluation unit triggers, either as a result of actuation of a switch or at predetermined time intervals automatically, or triggered by external third devices (such as the ventilator or patient monitor), the administration of a bolus of the conductivity ⁇ contrast agent with known parameters, wherein gleichzei ⁇ tig the EIT unit is caused to repeat measurements of the regional impedance distributions in the sectional plane of the thorax.
  • the dosing device sends data relating to start time, amount and time course of the delivery of a bolus to the control and evaluation unit, if the Dosiervorrich ⁇ device is prompted directly or by an external device for delivering a Bo ⁇ lus.
  • the timing of a perfusion measurement is precisely defined.
  • a defined volume of a conductivity contrast can be released at regular time intervals under defined conditions and a corresponding EIT measurement can be triggered by the EIT unit. This increases the accuracy of the measurement and ensures the comparability of different measurements.
  • a timer is integrated into the device, then cyclic, automatically performed measurements possible. The sources of error for a possible user error are reduced because the user can start a corresponding maneuver via a single switch pressure. The user therefore no longer has to inject the conductivity contrast agent as in the prior art, trigger the EIT measurement and possibly stop it. This makes such a device much easier to operate.
  • the defined administration of boluses allows a precise baseline for the EIT measurement to be determined by means of a modified Steward-Hamilton method.
  • the method can also be considered as a Steward-Hamilton method for EIT measurement.
  • ⁇ at not only the temperature of the injectate is measured son ⁇ countries the altered conductivity blood.
  • the results of the EIT measurements can be compared with each other, thus a trend over the heart-time volume and / or the lung perfusion can be calculated and displayed.
  • the calculation and display can take place both in the form of a regional representation, similar to an EIT ventilation image, but also as a single measured value (representation as a scalar).
  • V / Q ratio a trend in V / Q ratio can also be determined and displayed and used as a parameter for diagnosis and therapy.
  • V / Q ratio a trend in V / Q ratio can also be determined and displayed and used as a parameter for diagnosis and therapy.
  • the Bestim ⁇ tion of optimal ventilation parameters can be done in different ways. They can be determined either by a doctor or nursing staff, or they are determined by a wider ⁇ ren system (eg, an expert system) and proposed to the doctor or they are determined by another system (eg, an expert system) and automatically applied.
  • respirator e.g., expert system
  • respirator e.g., expert system
  • V / Q ratio the administration of drugs, based on a defined V / Q ratio can be optimized so that A possible ⁇ lichst optimum V / Q ratio is achieved.
  • alarms can be triggered with a correspondingly large shunt or dead space.
  • the alarm limits for triggering can either be entered by the user on the device or they can be generated automatically by means of appropriate clinical guidelines from another system (eg an expert system).
  • An alarm can also be triggered in the event of a corresponding change, that is to say as a function of the gradient of the observed measured value.
  • the symmetry operator calculates the symmetry in the tomograms and determines the symmetry between right and left half of the lung d is not simply placed in the middle of the picture, but it is automatically determined, for example, so that the center of gravity of the heart region is determined automatically. But it is also possible that the user has an appropriate sym- metric axis defined.
  • a score can be calculated. The smaller this score, the lower the symmetry between the two halves of the lung, the greater the probability for a Lurgierkran ⁇ effect.
  • the inverse of the symmetry operator the greater the inverse of the score, the greater the likelihood of lung disease.
  • control and evaluation unit is further adapted to areas of the lung in which the specific ventilation above a predetermined smoldering ⁇ lenhongs and the determined perfusion is below a further predetermined threshold value to identifi ⁇ for as a dead space and which in the illustrated sectional view Lungs to bring to the display.
  • control and evaluation unit is further configured to display lung areas in which the perfusion is above a predefined threshold value and the ventilation below a further predetermined threshold value as shunts for specific and in the sectional view of the lung.
  • control and evaluation unit can be further configured to display the time evolution of recognized shunts or dead spaces as a trend display over a period of time.
  • Fig. 1 shows a schematic block diagram of the invention shown SEN device
  • FIG. 2 shows by EIT certain changes of the impedance at three pixels in the sectional plane through the thorax after administration of a bolus of the conductivity concentrating agent
  • Fig. 3 shows a determined measure of the perfusion of the lung as a function of time as a trend representation
  • FIG. 4 shows the changes in the impedance at two pixels in the sectional plane through the thorax determined by EIT after administration of a bolus as a function of time
  • 5 to 13 show the development of the impedance distributions in the sectional plane through the thorax in the form of contour lines at successive times after administration of the bolus.
  • Fig. 1 the EIT unit with a control and evaluation ⁇ unit 2 connected to measuring cables 1 is shown.
  • the feed device 4 is a controllable metering device. Between the control and evaluation unit 2 and the feed device 4 is a two-way data link 3.
  • the dosing ⁇ device 4 is connected to a venous catheter 5 through which the conductivity contrast medium is injected.
  • the measurement ⁇ cables 1 connect the control and evaluation unit 2 with Elect ⁇ roden Ei, ... E N that are arranged annularly around the thorax.
  • the control and evaluation unit is provided with a excellenteinrich ⁇ device 6.
  • Both the supply device 4 and the control and evaluation unit 2 can via an external data ⁇ connection 8 with third devices, such as a ventilator including an expert system or monitoring monitor contained therein.
  • the control and evaluation unit causes the Dosiervor ⁇ direction to inject a bolus of 10 ml of 1 molar NaCl solution over a period of less than 2 seconds via a central venous catheter.
  • This bolus can be observed in the EIT image after about 3 seconds in the area of the heart for about 25 seconds and after about 6 seconds for about 20 seconds in the lungs, with the maximum of the bolus is observed after about 4 to 7 seconds , In FIG.
  • the impedance curves are exemplary after administration of a bolus at three points in the image plane of the thorax shown (in this case in the animal experiment, Jung ⁇ pig ca. 35kg), the curve in solid line corresponds to one picture element in the region of the heart that gepunk ⁇ ended curve one pixel in the right lung and the ge ⁇ dashed curve corresponds ent ⁇ a pixel in the left lung.
  • the bolus first reaches the heart and then the two lungs. In this case, it can be concluded from the delay of the two lung curves against each other already on a possible pathology in the lung.
  • the time difference between the two lung halves can be used to assess and indicate the severity of the pathophysiological manifestation.
  • the time difference of the curves of the right and left lungs is about 3 seconds. This time difference is determined from the time interval of the maxima of the two curves.
  • the measurement accuracy of the method is particularly high, since the bolus has a direct influence on the impedance of the blood and thus the EIT measurement di ⁇ rectly influenced.
  • shape of the dilution curves as in FIG. 2 reference is made to the article "The shape of indicator dilution curves used for cardiac output measurement in one", DM Band et al., The Journal of Physiology, 1997, January 1, 498 (US Pat.
  • Fig. 3 shows a measure of the perfusion of the lung, here the mean perfusion over the cutting plane through the thorax as a trend representation as a function of time over many hours. Egg- Such a trend view of lung perfusion can provide important clues to the patient's development and condition.
  • Fig. 4 shows the changes in the impedance at two pixels in the section plane through the thorax determined by EIT after administration of a bolus of the conductivity concentration medium as a function of time. At the times marked with circles, the impedance distributions in the sectional plane through the thorax in the form of contour lines are shown in FIGS. 5 to 14.
  • Fig. 5 shows graphs of lung perfusion resolved by EIT as height lines at time 0.025s (the bolus has not yet reached the heart and lungs) after bolus administration and 1.275s after bolus administration. At 1.275s you can see the bolus entering the heart region.
  • Figure 6 shows plots of lung perfusion EIT means resolved as contour lines at the time 2.525s 3.775s and after Bo ⁇ lusgabe. At 2,525s, you can see the bolus flow from the heart region into the right lung. In addition, the left lung is partially reached by the bolus. At 3.775s, you can see the bolus spreading further over the two halves of the lung.
  • Figure 7 shows graphs of lung perfusion resolved by EIT as height lines at time 5.025s and 6.275s after bolus delivery. At 5.025s, the bolus is completely dispersed and starts to drain at 6.275s.
  • Fig. 8 shows graphs of lung perfusion resolved by EIT as contour lines at time point 8,775s after bolus administration and 10,025s after bolus administration. The bolus flows out of the lungs through the heart.
  • Figures 9-13 show plots of lung perfusion resolved by EIT as contour lines between times 11.275s and 21.275s after bolus delivery.
  • the bolus flows out of the lungs through the heart.
  • one more heartbeat can be recognized by the extent of the contour lines in the heart region.

Abstract

L'invention concerne un dispositif permettant de déterminer la distribution régionale d'une mesure en perfusion pulmonaire. Ledit dispositif comprend : une unité de tomographie par impédance électrique munie d'électrodes (E1,... EN) qui peuvent être appliquées sur le thorax de manière répartie autour de la périphérie d'un plan d'intersection ; une unité de commande et d'évaluation (2) connectée aux électrodes et mise au point pour amener un courant alternatif ou une tension alternative successivement à chaque paire d'électrodes, et pour recevoir des signaux de tension ou de courant des autres électrodes sous forme de signaux de mesure et reconstruire la distribution de l'impédance dans le plan d'intersection à partir des signaux de mesure ; un dispositif d'amenée (4) pour l'amenée intraveineuse d'un agent de contraste de conductivité. L'unité de commande et d'évaluation (2) est par ailleurs mise au point pour afficher les changements de la distribution de l'impédance suite à l'amenée de l'agent de contraste de conductivité sous la forme d'une mesure pour la perfusion pulmonaire dans le plan d'intersection en temps que fonction du temps. Selon l'invention, le dispositif d'amenée (4) comporte un dispositif de dosage commandable ; et l'unité de commande et d'évaluation (2)) et le dispositif de dosage sont connectés l'un à l'autre par l'intermédiaire d'une liaison de données (3) et mis au point de telle manière qu'au moins l'heure de début et de fin et la quantité d'administration d'un bolus d'agent de contraste de conductivité sont fournies à l'unité de commande et d'évaluation (2).
EP13750289.4A 2012-08-20 2013-08-08 Procédé permettant de déterminer la distribution régionale d'une mesure en perfusion pulmonaire Withdrawn EP2884892A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102012214786.1A DE102012214786A1 (de) 2012-08-20 2012-08-20 Vorrichtung zur Bestimmung der regionalen Verteilung eines Maßes für die Lungenperfusion
PCT/EP2013/066633 WO2014029631A1 (fr) 2012-08-20 2013-08-08 Procédé permettant de déterminer la distribution régionale d'une mesure en perfusion pulmonaire

Publications (1)

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EP2884892A1 true EP2884892A1 (fr) 2015-06-24

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EP13750289.4A Withdrawn EP2884892A1 (fr) 2012-08-20 2013-08-08 Procédé permettant de déterminer la distribution régionale d'une mesure en perfusion pulmonaire

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US (1) US10064568B2 (fr)
EP (1) EP2884892A1 (fr)
CN (1) CN104582566B (fr)
BR (1) BR112015003159A2 (fr)
DE (1) DE102012214786A1 (fr)
WO (1) WO2014029631A1 (fr)

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US20150216443A1 (en) 2015-08-06
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US10064568B2 (en) 2018-09-04
DE102012214786A1 (de) 2014-05-15
WO2014029631A1 (fr) 2014-02-27
CN104582566B (zh) 2018-12-11

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