EP2252201A1 - Procédé et dispositif pour la mesure non invasive de paramètres dynamiques d interaction cardiopulmonaire - Google Patents

Procédé et dispositif pour la mesure non invasive de paramètres dynamiques d interaction cardiopulmonaire

Info

Publication number
EP2252201A1
EP2252201A1 EP09709639A EP09709639A EP2252201A1 EP 2252201 A1 EP2252201 A1 EP 2252201A1 EP 09709639 A EP09709639 A EP 09709639A EP 09709639 A EP09709639 A EP 09709639A EP 2252201 A1 EP2252201 A1 EP 2252201A1
Authority
EP
European Patent Office
Prior art keywords
pressure
cuff
volume
pulsatile
patient
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Withdrawn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
EP09709639A
Other languages
German (de)
English (en)
Inventor
Ulrich Pfeiffer
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.)
Philips Medizin Systeme Boeblingen GmbH
Original Assignee
UP Med 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 UP Med GmbH filed Critical UP Med GmbH
Publication of EP2252201A1 publication Critical patent/EP2252201A1/fr
Withdrawn legal-status Critical Current

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Classifications

    • 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
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/022—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers
    • A61B5/02233—Occluders specially adapted therefor
    • 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
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/02141—Details of apparatus construction, e.g. pump units or housings therefor, cuff pressurising systems, arrangements of fluid conduits or circuits
    • 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
    • A61B5/085—Measuring impedance of respiratory organs or lung elasticity

Definitions

  • the invention relates to a method and a device for the non-invasive measurement of dynamic heart-lung interaction parameters.
  • volumetric measures such as Volumes of the heart cavities or all of the volume in the chest (intrathoracic blood volume), although in principle better suited, but are also subject to various limitations.
  • the object of the present invention is therefore the detection of dynamic heart-lung interaction parameters (HLI) in a non-invasive manner.
  • HAI heart-lung interaction parameters
  • the object is achieved by a method for the non-invasive determination of in particular dynamic heart-lung interaction parameters (HLI) in a patient comprising the steps: applying a pressure cuff (20), adjusting the volume of the pressure cuff in the pulsatile region of the patient, measuring pulsatile signals the time, evaluating the measured pulsatile signals to determine the heart-lung interaction parameters (HLI).
  • HLI heart-lung interaction parameters
  • This method can be used to determine the dynamic heart-lung interaction parameters (HLI), such as PPV, SW, PEPV, and other heart-lung-derived derived variables, without the need for laborious cannulation of an arterial vessel. This allows these parameters to be determined non-invasively.
  • HAI heart-lung interaction parameters
  • This method is preferably used in a ventilated patient, in particular in a controlled ventilated patient.
  • these parameters can provide important information, as volume changes are created due to the pressure exerted on the lungs and indirectly on the patient's vessels and heart.
  • a pneumatic or hydraulic cuff is preferably used, with the aid of which the pulsatile arterial blood pressure fluctuations Similar to the known oscillometric blood pressure measurement on extremities of the body, such as arm or leg are detected.
  • a pressure cuff may preferably be filled with a fluid.
  • the pressure of this cuff is then adjusted by volume change.
  • filling material such as air, fluid, in particular liquid, etc.
  • the volume can be increased and thus the pressure exerted by the cuff on, for example, the upper arm can be increased.
  • discharging filler material the applied pressure can be lowered. So it is preferably also possible not to adjust the volume, but the pressure in the cuff so that by a compression of the respective body part an indirect coupling to the
  • the volume or pressure of the pressure cuff is adjusted so that the applied pressure is selected such that the cuff exerts the pressure between the systolic and the diastolic pressure in the pulsatile region of the patient.
  • the amplitude of the pulsatile signals is highest and thus most clearly detectable.
  • a device with a pneumatic or hydraulic cuff is used, with the aid of which the pulsatile arterial blood pressure fluctuations are detected similarly to the known oscillometric blood pressure measurement on extremities of the body.
  • the respiratory variation range of said parameters can be determined.
  • values for carrying out a pulse contour method are derived from the pulsatile signals.
  • the absolute blood pressure values are needed.
  • Pulse contour method it is possible to further improve the signal quality compared to the cuffs for oscillometric blood pressure measurement of the prior art, so that also a kind of noninvasive continuous blood pressure measurement is possible, including all other analysis options such. Pulse contour method.
  • the pulsatile signals it is also preferably possible to multiply the pulsatile signals by a factor or to use a correction function, in order thereby to reduce the occurring attenuation of the to compensate for arterial pressure signals.
  • This factor can be determined either empirically by statistical survey on a larger patient collective.
  • the factor of the attenuation can be calculated back from a direct invasive and simultaneous non-invasive measurement of the pulsatile signals and the evaluation of these signals. This factor can then be used in the following measurements non-invasive measurements to convert the measured pulsatile signals into the actual actual arterial values.
  • the attenuation that occurs between the arterial "true pressure" signal and the pressure signal in the cuff is essentially a function of the compressibility of the tissue, and this transfer function can be easily compensated for by a factor
  • the numerical compensation of this transfer function is a deconvolution
  • Transfer function (eg, resistance and capacitance in parallel), the parameters for transfer function for exact correction and recalculation to the "true intravascular pressure signal” preferably determine the following: In a first step using conventional oscillometric pressure measurement of the systolic and diastolic or mean arterial pressure In a second step, the mean pressure in the cuff is "clipped" at the pressure the maximum pulsatile signal quality is recorded (usually at mean arterial pressure).
  • the parameters of the transfer function are determined which lead to the "best fit" with the arterial model curve, whereby the systolic pressure value and the diastolic pressure value are predetermined by the previously obtained measured values. With sufficient signal quality, prior determination of these pressure values can be dispensed with, and these can be codetermined as free parameters in the iteration process.
  • the individual measured values are preferably combined into measured values which are to be assigned to a heartbeat.
  • an assignment to a respiratory cycle can also take place.
  • minimum and maximum of the individual blood pressure fluctuations per heartbeat can be determined and the fluctuations within a respiratory cycle can be determined. In this way it is possible to determine the desired heart-lung interaction parameters (HLI).
  • the oscillometric blood pressure measurement of the prior art is fundamentally based on the fact that in an externally applied pressure cuff the arterial blood vessels have variations in caliber, as long as the cuff pressure is less than the systolic and greater than the diastolic blood pressure. These caliber fluctuations of the arterial blood vessels in turn lead to pulsatile pressure fluctuations in the blood pressure cuff. At a cuff pressure greater than the systolic blood pressure, the arterial blood vessels are completely compressed throughout the cardiac cycle and thus there are no vascular caliber fluctuations and no pulsatile
  • the systolic and diastolic blood pressure values be predetermined as marginal values, and moreover the variation of these values based on the respiratory HLI.
  • the heart-lung interaction parameters include stroke volume variation (SW), pulse pressure variation (PPV) and / or pre-ejection phase variation (PEPV).
  • HLI may also be other derived variables based on cardiopulmonary interaction.
  • SW stroke volume variation
  • PV pulse pressure variation
  • PEPV pre-ejection phase variation
  • HLI may also be other derived variables based on cardiopulmonary interaction.
  • the respiratory fluctuation of the pulse wave velocity or the respiratory variation width of the pressure increase rate are conceivable.
  • a method is provided in which the measurement of the pulsatile signals via at least one
  • Breathing cycle of the patient takes place, preferably over at least three breathing cycles of the patient takes place.
  • the respiratory cycle is preferably determined from the temporal course of the pulsatile fluctuations.
  • the identification of a respiratory cycle but also over others
  • Measuring methods for example, from the thoracic electrical impedance signal that can be detected via the ECG electrodes, made.
  • Preferred further methods for determining the respiratory cycle are, for example, those described in EP 1 813 187 EP.
  • further advantageous evaluation options for the blood pressure data obtained according to the invention are given, to which reference is hereby made. For example, it is preferable to suppress an indication of the parameters such as PPV if, for example, there is arrhythmia or irregular breathing (not controlled ventilation).
  • the measuring period preferably comprises at least one respiratory cycle or breathing cycle, preferably several, more preferably three or more respiratory cycles. This can be achieved, for example, by keeping the pressure in the cuff within the pulsatile range for an extended period of time or draining it at a very slow rate. Preferably, for this purpose, a corresponding control of the volume in the cuff - and thus indirectly the applied pressure - provided.
  • the oscillometric blood pressure measurement in which essentially the mean pressure in the cuff is decisive at the time of the beginning of the pulsatility, at the time of the maximum fluctuations or at the time of the decrease in pulsatility, preference is given in the HLI method according to the present invention evaluated the pulsations themselves.
  • a method is provided in which the respiratory variation range of the heart-lung interaction parameters (HLI) is determined.
  • the maxima and the subsequent minima are determined (amplitude) - alternatively the minima and the subsequent maxima, i.
  • the blood pressure amplitude is determined from the systolic and the preceding diastolic pressure - and then determines the amplitude variation over the respiratory cycle as a measure of the pulse pressure variation.
  • the pulsatile pressure fluctuations in the cuff which are caused by the pulsatile caliber fluctuations of the blood vessels, considerably smaller than the pulsatile
  • HLI indices such as PPV and SW are relative measures (usually expressed in%) and the relative percentage variation of the signal fed into the cuff closely related to the respiratory variation of the HLI indices in the arterial blood vessel.
  • PEPV which, however, is the range of variation of a temporal dimension.
  • an electrocardiogram can additionally be used for the time recording of the beginning of the cardiac electrical activity.
  • the PEPV as HLI index can also be detected from the time difference between an electrocardiographic and a photoplethysmographic signal.
  • a method is provided in which the volume of the pressure cuff (20) set in the pulsatile region of the patient is kept substantially constant via the measurement of the pulsatile signals.
  • the volume of the pressure cuff according to the invention is substantially constant when the volume over a respiratory cycle not more than 10%, preferably not more than 5%, more preferably not more than 2% increases or decreases.
  • the volume can also be acted upon over this time of the measurement with a function with respect to a volume change to be selected - this can then be eliminated again during the evaluation. It is thus possible, for example, to constantly reduce the volume over the measurement and to calculate out the changes thus introduced into the measured amplitude again. If the changes remain within certain tolerances and the introduced errors sufficient are small, so they can also be disregarded in the evaluation.
  • a method is provided in which the volume of the pressure cuff (20) in the pulsatile region of the patient is adjusted so that the volume applied between the volume for determining the systolic blood pressure of the patient and the volume for determination the diastolic blood pressure of the patient is selected, preferably the mean of these two values.
  • the volume of the pressure cuff sufficiently emptied initially can preferably be supplied to a volume until the first pulsatile signals can be perceived - this then prevailing volume corresponds roughly to the diastolic pressure. If further volume is supplied, then there is a second time at which no more pulsatile signals can be measured - this corresponds to the systolic pressure.
  • These values can also be determined in the other direction, ie from an excessive pressure, it can be determined when a first pulsatile signal is received (systolic pressure) and when, with further volume reduction, no signal is received (diastolic pressure). Now, if a value between these two volumes applied at these times is used, then one is in the pulsatile range.
  • amplitudes are greater, the more one measures in the middle of this range, so preferably in the middle value between the two volumes. In this range, the maximum amplitude of the pulsatile signals can be expected and thus the best signals to be evaluated. It is also preferable to carry out the measurement in a range below the diastolic pressure. In this case, there are still caliber fluctuations and hydraulic coupling of the vessel to the external media, but non-linear effects that could result from temporary collapse of the vessel are avoided. With respect to the diastolic pressure, a particularly preferable range is 0.5 to the simple of the diastolic pressure, more preferably 0.6 to 0.95 times the diastolic pressure, particularly preferably 0.7 to
  • the range is above the Venous pressure, more preferably above 10 mmHg, more preferably above 20mmHG, more preferably above 30 mmHg.
  • the measurement is carried out in a range of 10 mmHg to 50 mmHg, preferably in a range of 20 mmHg to 45 mmHg, more preferably in a range of 25 mmHg to 40 mmHg.
  • a non-interfering pressure source is avoided for the above-described "dynamic" measurement during inflation and deflation, ie, the cuff is not directly filled by a pump with fluid or gas, but the cuff is supplied either from an external pressure source or one in the controller pressure tank of sufficient capacity, which in phases of non-measurement is again pressurized either externally or by an internal pump.
  • this mean value can preferably be maintained by readjustment, more preferably also in that the supply lines for the fluid or the air to the pressure cuff are closed so that a constant volume is applied in the cuff during the measurement, which does not change substantially during the measurement.
  • a device for the non-invasive determination of in particular dynamic heart-lung interaction parameters (HLI) in a (ventilated) patient comprising a pressure cuff (20) arranged for measuring the cuff pressure in the pulsatile range over at least one respiratory cycle the patient and a control device (10) for detecting the measured values of the pressure cuff (20) and for evaluating the measured pulsatile signals for determining the heart-lung interaction parameters (HLI).
  • HLI heart-lung interaction parameters
  • the preferred pneumatically or hydraulically operated pressure cuff is used as described above.
  • the measurement of the cuff pressure preferably takes place in the pulsatile range and supplies the corresponding pressure measurement values via a pressure sensor in the fluid (the fluid) or in the air of the cuff.
  • a controller takes over the storage and
  • a computing unit such as a microprocessor or a computer is preferably used.
  • a memory Preferably, at least one volatile memory is provided.
  • the measurement values of the pressure cuff are recorded via a pressure sensor in the filling medium of the cuff. These are determined over time.
  • the evaluation of the measured pulsatile signals preferably comprises the assignment of the signals over time to a heartbeat cycle as well as to a respiratory cycle.
  • the determination of the heart-lung interaction parameters can then be carried out by comparing the absolute and relative fluctuations.
  • a device in which an output device (15) is provided for outputting the determined heart-lung interaction parameter (HLI).
  • HHI heart-lung interaction parameter
  • the output device may be an indicator or a
  • Transfer device of the measured values or the evaluation of the determined heart-lung interaction parameter to another unit include. It is thus possible to display the value on a monitor and / or to pass it on to another device via an interface.
  • a device in which a volume control device (25) for controlling the volume in the pressure cuff (20) is provided.
  • the volume control device is a device via which the pressure cuff filling medium can be supplied or withdrawn.
  • An averaging can take place over several respiratory cycles.
  • the measurement period over which a pressure cuff on one extremity can be pressurized due to the impairment of blood flow is limited. However, it is possible to fear measuring without damage for several minutes. For longer measuring periods, it should be noted that a certain pressure loss in the cuff is recorded by pressing out of interstitial fluid, which is preferably compensated either by a corresponding control or by corresponding numerical methods.
  • Measures to improve the pressure measurement quality can preferably also be taken:
  • the outermost enclosure of the sleeve is preferably designed rigid. This will be the
  • the outer casing is rigid and the filling medium of the cuff incompressible. This leads to a complete coupling of the arterial vessels via the body tissue which is nearly incompressible in relation to the required measurement times (these are these, if the venous vessels are empty and there is no air between the arteries and the cuff, both of these are the case) , The pressure can still dodge laterally into the tissue.
  • a wider sleeve is selected, in particular a sleeve having a width of half the circumference of the sleeve, preferably the entire circumference of the sleeve, more preferably more than the circumference of the sleeve, in particular 1.3 to 1.5 times spanned circumference of the cuff.
  • the wider the cuff the less lateral pressure can escape.
  • the outer cover has a complete rigidity and not just a non-stretchable outer membrane.
  • a complete outer rigidity could be achieved with the same principle as in the stiffening of vacuum mattresses, ie with an outer chamber, with z. B. Mikrostyroporkugeln is filled, and is evacuated after application.
  • a fast external rigidity such as the use of ultra-fast 2-component systems for the outer layer of the cuff, which can cause a rigidity after activation.
  • the pulse wave propagation velocity can preferably also be measured.
  • the pulsation will begin primarily in the proximal cuffs, since the arterial vessels will not be opened to their full length in the event of a brief drop below the pressure. This can be used to identify the systolic blood pressure value.
  • the central portions may be actuated like a conventional oscillometric cuff to identify the systolic and diastolic (mean) blood pressure for calibration, and then to calibrate the full length measured signal.
  • the described embodiments of the cuff can be realized both in a reusable but also in a single-use disposable cuff which can be used in only one patient integrated into the place where the greatest pressure fluctuations are expected. This can also be achieved by a two-chamber disposable cuff where the gas volume in the outer chamber is varied accordingly, while in the inner fluid-filled lower compliance chamber which couples directly to the tissue to be compressed, the pressure measurement directly to the integrated preferably electronic Pressure transducer takes place.
  • NIBP non-invasive blood pressure
  • a pressure sensor for the measurement according to the invention can also be integrated in the additional valve.
  • the minimums and the maxima are determined after artifact detection.
  • the areas under the oscillatory fluctuations can also be evaluated, and here again their respiratory variation range.
  • the measured signals can be adapted to model curves, e.g. with linear or non-linear fitting procedures.
  • the sought sizes can then be derived from the parameters of the model curves.
  • the cuff with pressure sensor is placed on the upper arm of the patient.
  • the cuff is filled by means of a pump until the pressure fluctuations are maximum.
  • the pressure in the cuff is recorded every 10ms during a 30 second measurement interval. All in all 3000 pressure values.
  • a longer measurement interval e.g. 90 seconds, if a better signal is desired due to the limited signal-to-noise ratio at low respiratory tidal volumes. It is thus also longer averaging periods feasible, for example 1 - 2 minutes
  • the standard deviation is formed over a 2 second sliding window. At 10ms sampling interval, that is 200 pressure values.
  • S (t) standard deviation (P [t, t + 2s]). This is repeated for each sample t from zero to (30-2) seconds. This results in a list with 2800 standard deviations.
  • FIG. 3 shows a schematic view of a device for the non-invasive determination of cardiopulmonary interaction parameters according to an exemplary embodiment of the present invention.
  • Figure 1 shows a curve of the time course of the filling of a pressure cuff according to an embodiment of the present invention.
  • the pressure P is plotted against the time t.
  • the diastolic pressure level PD and the systolic pressure level PS are plotted.
  • a continuous line shows the pressure curve measured in the pressure cuff over the measurement - for easier orientation here points A to G are shown.
  • the deflated pressure cuff is placed on the upper arm of a patient and filled with fluid. This will be the one in the
  • Pressure cuff measured pressure increased.
  • the pressure reaches the level of the diastolic pressure PD applied to the upper arm and pulsatile signals are now recorded across the pressure sensor in the pressure cuff.
  • the volume in the pressure cuff is further increased and the pulsatile signals first become stronger and then weaker again.
  • the pressure reaches the level of systolic pressure PS exerted on the upper arm, and there are now no pulsatile signals across the pressure sensor in the pressure cuff.
  • the volume in the pressure cuff is raised a little to point C and then the volume in the cuff is drained.
  • pulsatile signals are again recorded for the first time, thus confirming the level of systolic pressure. This determines the systolic and diastolic levels. If there are any doubts on the diastolic level, it is possible to continue to drain the volume in the cuff until the pulsatile signals can no longer be recorded - then the diastolic level would be finally confirmed.
  • the volume in the cuff refilled to the extent that the level between the points E and F is reached again.
  • the values determined in this way are evaluated after artifact exclusion per heartbeat and per respiratory cycle, and the desired dynamic heart-lung interaction parameters, in particular the pulse-pressure variation PPV, are determined.
  • the volume in the cuff is now further vented, passing the point G indicating the achievement of the diastolic level PD.
  • the pressure cuff now no longer exerts any significant pressure on the upper arm and the body fluids displaced by the measurement can be reduced back into the tissue.
  • a second measurement can now be performed according to the same scheme.
  • Oscillations are improved and thus the measurements are performed more reliably, if the signals would be too weak by the applied pressure on the upper arm during a measuring cycle.
  • FIG. 2 shows a curve of the pulsatile measured values over at least one respiratory cycle.
  • the measured pulsatile pressure curve is shown together with an envelope curve.
  • MI is a denotes the minimum amplitude within a respiratory cycle
  • MA denotes the maximum values for the amplitude within the respiratory cycle
  • AZ represents an interval of a respiratory cycle.
  • the measurement is made at constant volume in the pressure cuff and shows the respiratory fluctuation of the pulsatile signals within the respiratory cycle.
  • MIl the minimum is indicated by MIl and the maximum by MAI, in a second respiratory cycle by MI2 and MA2, etc.
  • FIG. 3 shows a schematic view of a device for the non-invasive determination of cardiopulmonary interaction parameters according to an exemplary embodiment of the present invention.
  • a pressure cuff 20 is equipped with a volume control device 25.
  • the pressure cuff 20 preferably has an outer surface with low elasticity to minimize compliance during the measurement. This can be realized for example via a non-elastic band in the outer region of the pressure cuff 20.
  • a fluid can be supplied or withdrawn.
  • the pressure cuff 20 has a pressure sensor 21, which can detect the pressure prevailing in the pressure cuff.
  • the pressure cuff 20 or the pressure sensor 21 within the pressure cuff 20 is connected to a control device 10 via an electrical line.
  • the signals detected by the pressure sensor 21 can be transmitted to the control device 10.
  • an output device 15 is connected. If a measurement is to be carried out following the course according to FIG. 1, the pressure cuff 20 is filled with fluid via the volume control device 25. After passing point A from FIG. 1, pulsatile signals, which are transmitted to the control device 10, are detected via the pressure sensor 21. In this way, it is determined by the controller that the diastolic level has been reached. The volume is further increased and the measured pulsatile signals increase in intensity before decreasing again and then disappearing completely when the systolic level is reached.
  • the volume control device 25 now reduces the inflow of the fluid and subsequently drains the volume of fluid in the cuff 20 to the average between the volumes recorded at the diastolic and systolic levels. Now the point E in Figure 1 is reached. The volume is now kept constant by the volume control device 25, ie the supply of fluid into the cuff 20 is shut off. At this volume level, the measurement is now continued over several breathing cycles. Every second 50 to 200 measured values, preferably 100 measured values of the pressure sensor 21 are recorded and transmitted to the control device 10. There, the measured values are evaluated for heartbeat and respiratory cycle and the minima and maxima of the amplitudes within a respiratory cycle are determined.
  • the respiratory variation of the desired dynamic heart-lung interaction parameters in particular the pulse-pressure variation PPV, is determined.
  • the value thus determined is then displayed on the output device 15, in the present case a PPV of 9%.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Cardiology (AREA)
  • Vascular Medicine (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Surgery (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Physiology (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Physics & Mathematics (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Dentistry (AREA)
  • Ophthalmology & Optometry (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

Abstract

L'invention concerne un procédé et un dispositif pour la mesure non invasive de paramètres d'interaction cardiopulmonaire (ICP) chez un patient, le dispositif comprenant : une manchette à pression (20) conçue pour mesurer la pression de la manchette dans la zone pulsatile pendant au moins un cycle respiratoire du patient ; et une unité de commande (10) pour enregistrer les valeurs mesurées de la manchette à pression (20) et pour interpréter les signaux pulsatiles mesurés afin de déterminer les paramètres d'interaction cardiopulmonaire (ICP).
EP09709639A 2008-02-13 2009-02-13 Procédé et dispositif pour la mesure non invasive de paramètres dynamiques d interaction cardiopulmonaire Withdrawn EP2252201A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102008008840A DE102008008840A1 (de) 2008-02-13 2008-02-13 Verfahren und Vorrichtung zur nicht-invasiven Messung von dynamischen Herz-Lungen Interaktionsparametern
PCT/EP2009/001031 WO2009100927A1 (fr) 2008-02-13 2009-02-13 Procédé et dispositif pour la mesure non invasive de paramètres dynamiques d’interaction cardiopulmonaire

Publications (1)

Publication Number Publication Date
EP2252201A1 true EP2252201A1 (fr) 2010-11-24

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EP09709639A Withdrawn EP2252201A1 (fr) 2008-02-13 2009-02-13 Procédé et dispositif pour la mesure non invasive de paramètres dynamiques d interaction cardiopulmonaire

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Country Link
US (1) US20100324428A1 (fr)
EP (1) EP2252201A1 (fr)
JP (1) JP5337821B2 (fr)
DE (1) DE102008008840A1 (fr)
WO (1) WO2009100927A1 (fr)

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WO2009100927A1 (fr) 2009-08-20
JP2011511686A (ja) 2011-04-14
US20100324428A1 (en) 2010-12-23
DE102008008840A1 (de) 2009-09-24

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