WO2024252002A1 - Détermination de type de capteur d'écoulement - Google Patents

Détermination de type de capteur d'écoulement Download PDF

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Publication number
WO2024252002A1
WO2024252002A1 PCT/EP2024/065826 EP2024065826W WO2024252002A1 WO 2024252002 A1 WO2024252002 A1 WO 2024252002A1 EP 2024065826 W EP2024065826 W EP 2024065826W WO 2024252002 A1 WO2024252002 A1 WO 2024252002A1
Authority
WO
WIPO (PCT)
Prior art keywords
flow sensor
gas flow
respiratory gas
identification resistor
flow
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.)
Ceased
Application number
PCT/EP2024/065826
Other languages
English (en)
Inventor
Frede JENSEN
Edmund O'keeffe
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.)
EUROPLAZ TECHNOLOGIES Ltd
Original Assignee
EUROPLAZ TECHNOLOGIES Ltd
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 EUROPLAZ TECHNOLOGIES Ltd filed Critical EUROPLAZ TECHNOLOGIES Ltd
Priority to EP24732588.9A priority Critical patent/EP4723951A1/fr
Publication of WO2024252002A1 publication Critical patent/WO2024252002A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
    • G01F1/00—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow
    • G01F1/68—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by using thermal effects
    • G01F1/684—Structural arrangements; Mounting of elements, e.g. in relation to fluid flow
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
    • G01F1/00—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow
    • G01F1/68—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by using thermal effects
    • G01F1/696—Circuits therefor, e.g. constant-current flow meters
    • G01F1/6965—Circuits therefor, e.g. constant-current flow meters comprising means to store calibration data for flow signal calculation or correction
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Measuring devices for evaluating the respiratory organs
    • A61B5/087—Measuring breath flow
    • A61B5/0878—Measuring breath flow using temperature sensing means
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
    • G01F1/00—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow
    • G01F1/68—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by using thermal effects
    • G01F1/684—Structural arrangements; Mounting of elements, e.g. in relation to fluid flow
    • G01F1/6842—Structural arrangements; Mounting of elements, e.g. in relation to fluid flow with means for influencing the fluid flow
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
    • G01F1/00—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow
    • G01F1/68—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by using thermal effects
    • G01F1/696—Circuits therefor, e.g. constant-current flow meters
    • 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
    • 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
    • A61B2562/085—Sensors provided with means for identification, e.g. barcodes or memory chips combined with means for recording calibration data
    • 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
    • A61B2562/22—Arrangements of medical sensors with cables or leads; Connectors or couplings specifically adapted for medical sensors
    • A61B2562/225—Connectors or couplings
    • A61B2562/226—Connectors or couplings comprising means for identifying the connector, e.g. to prevent incorrect connection to socket
    • 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
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
    • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
    • A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
    • A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical

Definitions

  • the present invention relates to a respiratory gas flow sensor and to a respiratory gas flow sensor system for measuring gas flow rates to and from the lung of a patient during respiratory care.
  • the present invention is concerned with the automatic determination of a flow sensor type to reduce the likelihood of operator error.
  • thermo-resistive sensing element refers to the thermo-resistive flow sensor member which effects the measurement function.
  • Tidal volume is the volume of air inhaled and exhaled at each breath.
  • Deadspace is a volumetric space in the flow sensor and associated tube connectors from which gas does not reach the patient’s alveoli during inhalation and/or which buffers carbon dioxide rich gas from reaching the exhaust channel during exhalation.
  • Operation of the flow sensor relies upon the principle that the electrical response of the sensing element is exponentially proportional to gas velocity.
  • signal conditioning and arithmetic and algorithmic processing is applied in i converting the analogue gas velocity measurement into a digital representation of a directional volumetric flow rate. This conversion is a function of the cross-sectional area of the flow channel within the sensor body and gas density factors.
  • the relationship between flow rate and time is used to derive the tidal breath volume (the volume of air inhaled and exhaled at each breath).
  • the rate of respiratory flow change is further used to detect the onset of breath in spontaneous breathing patients and initiates ventilator synchronisation.
  • Neonatal patients require sensors in which the flow channel has a minimised deadspace to avoid rebreathing of exhaled gas causing harmful levels of blood carbon dioxide.
  • Such a smaller flow channel presents a higher flow resistance, which can prevent full elastic recoil in the lungs of larger and adult patients, resulting in an incomplete exhalation between breaths. This causes an abnormal retention of air within the lungs, known as gas trapping.
  • Sensors intended for neonatal, paediatric and adult patients are therefore designed with different flow channel dimensions.
  • a flow sensor may incorporate a sidestream port upstream from the flow sensing elements, such as described in patent US 9999741 (Jensen); or a flow sensor may alternatively combine with a sidestream port adapter that is placed downstream from the flow sensing element.
  • a ventilator usually incorporates an algorithm for compensating the respiratory tidal flow measurement for the lost sampling gas.
  • a typical sampling gas rate of 50 ml/min requires 50% compensation in calculating the tidal breath volume. The determination of the most appropriate sensor type for a specific patient is thus vital.
  • the respiratory gas flow sensor is a respiratory gas flow rate sensor. This may be mass flow rate and/or volumetric flow rate.
  • a respiratory gas flow sensor having a flow channel formed therein, the sensor comprising: a thermo-resistive sensing element located in the flow channel; an identification resistor electrically coupled to the sensing element; and an electrical interface to facilitate electrical connection to a controller arranged to determine the identification resistor value and thereby identify the flow sensor type.
  • the electrical interface is preferably a socket or an electronic cable connector providing connectivity to a host device.
  • the host device may be a ventilator or a respiratory function monitor device.
  • the flow channel is a gas flow channel for the respiratory gas.
  • the thermo- resistive sensing element senses flow rate of respiratory gases passing along the flow channel.
  • a respiratory gas flow sensor system comprising: a gas flow sensor as described herein having: a flow channel formed therein; a thermo-resistive sensing element located in the flow channel and an identification resistor electrically coupled to the sensing element; and a controller electrically connected to the gas flow sensor and arranged to determine the identification resistor value and thereby identify the flow sensor type.
  • the present invention provides advancements in safety and authentication of equipment for use on a patient in a medical context.
  • patient refers to a human or an animal.
  • the controller determines the flow sensor type automatically so that the operator does not need to manually select the flow sensor’s patient type and/or type of combination device arrangement. This minimises the risk of unmitigated selection errors.
  • the sensor of the present invention is configured for connection to a controller which is remote therefrom.
  • the controller may comprise an electronic driver/electronic circuit incorporating an identification resistor value detector. This arrangement enables the resistor value to be determined externally from the flow sensor. Since flow sensors are generally disposable, by providing the controller externally therefrom, the ingress of electronic components into the clinical waste stream is minimised. Furthermore, the provision of a controller distinct from the flow sensor allows a range of signal conversion functions to be pre-programmed externally from the connected sensor. In this way, the controller may be configured with the appropriate software to identify a range of different flow rate sensors.
  • the flow channel defines a flow path extending between a first end, configured to connect to a supply of gas, and a second end, configured to couple to a patient airway interface.
  • the flow channel may ideally be a substantially straight passageway. This can help to minimise turbulence and improve flow characteristics.
  • the flow channel may be tubular and usually is of a generally circular cross section, although it may have a different cross-sectional shape.
  • the identification resistor may be electrically coupled to either the current inflow or the current outflow ends of the two or more thermo-resistive sensing elements.
  • the identification resistor is connected to the current inflow end of a first or first group of thermo-resistive sensing elements and the current outflow end of a second or second group of thermo-resistive sensing elements within said flow sensor.
  • thermo-resistive sensing elements may comprise a wire, a flat bar or a film.
  • the thermo-resistive sensing elements may be arranged perpendicularly across and/or substantially centrally within the flow path.
  • the sensing elements are energised in accordance with principles for constant temperature anemometry or constant current anemometry or constant power anemometry.
  • the gas flow sensor system further comprises an electric cable electrically connecting the gas flow sensor to the controller.
  • the cable may be up to 2m in length.
  • the controller of the gas flow sensor system may comprise an amplifier for determining the identification resistor value.
  • the amplifier may be a high impedance differential amplifier.
  • the controller includes a Wheatstone Bridge to convert the resistance into a voltage differential and the high impedance differential amplifier amplifies that voltage difference.
  • the controller of the gas flow sensor system may comprise switches and may be configured to control the state of the switches to determine the identification resistor value.
  • the resistive value of the identification resistor is greater than one Kilo Ohm. Depending upon the configuration of the flow sensor, this may prevent the identification resistor from interfering with the normal measurement operation of the gas flow sensor.
  • the identification resistor is ideally provided in the senor in a location distinct from the sensing element.
  • the identification resistor is ideally not located in the gas flow path.
  • the identification resistor may be in a part of the sensor external to the gas flow path. Among other advantages location outside the flow path ensures the gas flow is not disrupted.
  • the gas flow sensor may define a port leading to the flow channel. That port may be a side port.
  • the identification resistor is housed within the port or within an insert located in the port so as to electrically connect to the sensing elements, yet preferably to be outside the gas flow path.
  • the identification resistor may be provided in an aperture, and that aperture may be in the insert.
  • the insert may also carry the sensing element(s).
  • the flow sensor may further comprise a cap, arranged to seal the resistor.
  • the cap may comprise a compressible elastomeric cap.
  • the seal provided by the cap may be configured to prevent the ingress of moisture to the resistor.
  • the respiratory gas flow sensor system of the present invention is preferably able to discriminate between more than fifty different sensor types and enables respiratory care ventilators and respiratory function monitors automatically to receive the correct tidal flow conversion and/or correction, without requiring any intervention from the human operator. It further enables host ventilators and monitors to detect sensors that are not clinically validated or otherwise unqualified for their specific application. This is an improvement over the prior art by preventing selection errors or incompatibility and thereby protecting the patient from potential sources of harm.
  • Figure 1 is a schematic view of a patient being ventilated by a ventilator set up including the flow sensor of the present invention and illustrates separation between the flow sensor and the controller which is remote therefrom;
  • Figure 2 is a block schematic diagram of a first example electronic system that encompasses a flow sensor type identification
  • Figure 3 is a block schematic diagram of a second example electronic system that encompasses a flow sensor type identification
  • Figure 4 is a block schematic diagram illustrating possible alternative arrangements for coupling the identification resistor to a pair of thermo-resistive sensing elements
  • Figure 5 shows a detailed components and construction view of a flow sensor embodiment incorporating an identification resistor
  • Figure 6 illustrates a range of three flow sensor variants with differing operating characteristics while sharing identical cable connectors for connecting to a common electronic driver.
  • FIG. 1 there is shown a typical arrangement for clinical application where a ventilator 51 distal to the patient delivers respiratory gas through a ventilator breathing system 52.
  • the ventilator breathing system connects to the flow sensor 30 via a manifold, often referred to as a Y-piece 53.
  • the flow sensor is connected to an endotracheal tube 54 inserted into the patient’s lung 60.
  • the flow sensor 30 is connected via an electric cable 6 that is up to 2m in length to an electronic driver and detector unit 40 located inside (or associated with) the distal ventilator 51 .
  • the arrangement may have 2 operating phases. In the first phase, the flow sensor electronic driver 40 inside the ventilator 51 measures and identifies the flow sensor type. This process takes a few milliseconds to perform. In the second phase, normal flow measurement operation commences, where the electronic driver 40 inside the ventilator 51 applies the conversion algorithm and arithmetic that is specific to the identified flow sensor type.
  • FIG. 2 there is shown an electronic system including an identification resistor 33 incorporated into a flow sensor 30.
  • the system receives electrical power 3,4 and has a digital data bus interface 50 connecting to a host device, which may be a ventilator or respiratory function monitor.
  • a microprocessor 5 shown in both the right-hand and left-hand side of Figure 2 is a single combined component (explained by dotted line).
  • the thermo- resistive sensing element 31 and the three resistors 11 , 13 and 14 form a Wheatstone bridge 1.
  • a typical operating value of the thermo-resistive sensing element 31 and resistors 11 , 13, 14 are in the regions of 4 Ohm, 8 Ohm, 3kOhm and 5kOhm respectively.
  • the proportional integral amplifier 15 servo-controls transistor 10 to affect an electrical current that maintains the thermo-resistive sensing element 31 at an elevated constant temperature and resistance.
  • a digitally programmable variable resistor 12 calibrates the bridge 1 to a target operating temperature.
  • the mid-point value of the variable resistor 12 is typically equal to the value of resistor 11 , to enable the calibration function straddling the 4/8 Ohm ratio of the low resistance bridge 1 leg.
  • Gas flow across the thermo-resistive sensing element 31 causes a rise in the driving current, which is measurable as a voltage change in the output from signal conditioning amplifier 16.
  • the analogue domain voltage of this signal represents the gas flow velocity and is digitised by the microcontroller’s 5 analogue-to-digital converter.
  • thermo-resistive sensing element 32 The system is mirrored with bridge 2 driving a second thermo-resistive sensing element 32. Variants of this conventional design may use additional heated or colder thermo-resistive elements, such as for gas temperature compensation.
  • the identification resistor 33 is inserted into the flow sensor 30 and is electrically connected between a pair of thermo-resistive sensing elements 31 , 32.
  • FIG. 3 shows an alternative example electronic system for measuring the value of identification resistor 33.
  • Electronic components 17, 18, 27 and 28 are switches, such as milli-Ohm resistance MOSFET transistors or Solid State Relays or electro-mechanical Reed Relays.
  • the four switches 17, 18, 27, 28 are kept in a low resistance state during normal flow measurement operation.
  • switch 17 is kept at low resistance while switches 18, 27 and 28 are switched to high resistance or open circuit
  • the voltage on the input to the signal conditioner 16 and the microprocessor’s 5 analogue-to-digital converter is defined by the value of identification resistor 33 divided by the values of bypass resistors 19 and 29.
  • the identity test can be reversed by setting switch 17 to high resistance and switch 18 to low resistance and then measuring the value from the mirrored signal conditioner 26.
  • bypass resistors 19, 29 are each 10 kOhm.
  • Such high resistive values significantly reduce the current flow through the Wheatstone bridges 1 , 2 during the identification procedure.
  • a logic high output from the microprocessor 5 to the proportional integral amplifier 15 assures transistor 10 fully conducts the low current.
  • labelling the output from amplifier 16 as ADC1 and the output from amplifier 26 as ADC2 the identification resistor 33 value is found to be equal to 10000 x (ADC2 - ADC1 )/ADC1.
  • the identification resistor 33 may in this embodiment be specified in the range from 3 kOhm to 80 kOhm and reliably enable the system identifying more than fifty different sensor variants.
  • Figures 2 and 3 illustrates the servo-controller operating the principle of voltage feedback Constant Temperature Anemometry. Variant thermo-resistive sensing principles exists. Constant Current Anemometry is also well-know, for example, although it is less commonly used. Constant Current Anemometry maintains a target current through the thermo-resistive sensing elements 31 ,32 and permits varying temperatures. Constant Power Anemometry is mixed variant, in which a multiplier of voltage and current across the thermo-resistive sensing elements 31 ,32 is servocontrolled to be maintained constant. The flow sensor identification principle described for Figures 2 and 3 may equally be applied to such alternative variant thermo-resistive sensing principles. In all instances, the microcontroller 5 applies the type relevant conversion and correction to determine the volumetric flow rate and to output its digital value via a serial or parallel data bus interface 50 to a host device.
  • Figure 4 illustrates alternative electrical coupling points of the identification resistor 33 to the thermo-resistive sensing elements 31 and 32 within the flow sensor 30.
  • the identification method is practically insensitive to the alternative arrangements 3A, 3B and 3C and flexibly allows for the identification resistor 33 be connected to either the current inflow or the current outflow ends of the thermo-resistive sensing elements 31 , 32.
  • FIG. 5 illustrates an exploded view of an example embodiment of the identification resistor 33 about to be inserted into a typical respiratory flow sensor 30.
  • the identification resistor 33 is a surface mount size 0805 resistor chip.
  • the carrying insert 37 features a side aperture that extends into the exposed connector pins 34, 35. Once the insert 37 is guided and snapped into a port on the flow sensor body 30 a lightly compressed elastomeric cap (or bung) 36 pushes the identification resistor 33 into a forced interference contact with the connector pins 34, 35 which are in electrical contact with the thermo-resistive sensing elements 31 , 32. The compression effect further deforms the elastomeric cap 36 to cause it to lightly spread in height and width and create a moisture seal against the insert’s 37 cavity walls.
  • FIG. 6 illustrates a range of respiratory flow sensors 30A, 30B, 30C that all differ in dimensions or combination device port connectivity, while sharing the identical electronic cable connector 38 (as in Figure 5) and system controller (electronic driver), as illustrated by Figure 2 and or 3.
  • Flow sensor 30A may often be used in combination with a sidestream capnometry adapter (not shown) that draws a sampling gas downstream from the flow sensing element and therefore requires the tidal flow measurement be compensated for the lost respiratory gas.
  • Flow sensor 30B incorporates a sidestream sampling port that is upstream from the flow sensing element, which eliminates the need for a correction factor and produces a net smaller dead space by also eliminating the additional sidestream adapter (not shown).
  • Flow sensor 30C is a paediatric sensor enabling higher flow rates. Each flow sensor type is differentiated by each their own unique identification resistor value 33A, 33B, 33C.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Fluid Mechanics (AREA)
  • General Physics & Mathematics (AREA)
  • Biomedical Technology (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Physiology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Pulmonology (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

L'invention concerne un capteur d'écoulement de gaz respiratoire (30) comportant un canal d'écoulement de gaz, le capteur comprenant : un élément de détection thermorésistant (31) situé dans le canal d'écoulement pour détecter un écoulement ; une résistance d'identification (33) couplée électriquement à l'élément de détection ; et une interface électrique (38) pour faciliter la connexion électrique du capteur d'écoulement à un dispositif de commande conçu pour déterminer la valeur de résistance d'identification et identifier ainsi le type de capteur d'écoulement. L'invention concerne également un système de détection d'écoulement de gaz respiratoire comprenant : un capteur d'écoulement de gaz (30) comme susmentionné ; et un dispositif de commande électronique (40) connecté électriquement au capteur d'écoulement de gaz et conçu pour déterminer la valeur de résistance d'identification et identifier ainsi le type de capteur d'écoulement.
PCT/EP2024/065826 2023-06-09 2024-06-07 Détermination de type de capteur d'écoulement Ceased WO2024252002A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP24732588.9A EP4723951A1 (fr) 2023-06-09 2024-06-07 Détermination de type de capteur d'écoulement

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
GB2308650.7A GB2630810A (en) 2023-06-09 2023-06-09 Flow sensor type determination
GB2308650.7 2023-06-09

Publications (1)

Publication Number Publication Date
WO2024252002A1 true WO2024252002A1 (fr) 2024-12-12

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PCT/EP2024/065826 Ceased WO2024252002A1 (fr) 2023-06-09 2024-06-07 Détermination de type de capteur d'écoulement

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GB (1) GB2630810A (fr)
WO (1) WO2024252002A1 (fr)

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB1512290A (en) 1975-11-24 1978-06-01 Agar J Instrumentation Ltd Method and apparatus for determining fluid flow rate and/or for exercising a control in dependence thereon
US4363238A (en) 1979-08-16 1982-12-14 Franz Willam Device for measuring the breath of patients
US5069066A (en) 1990-05-10 1991-12-03 Djorup Robert Sonny Constant temperature anemometer
DE4020522A1 (de) * 1990-06-28 1992-01-09 Fresenius Ag Medizinisches geraetesystem
US20010039833A1 (en) * 2000-05-13 2001-11-15 Dieter Engel Respiratory flow sensor
EP1950535A1 (fr) 2006-08-07 2008-07-30 General Electric Company Procédé et système de compensation dynamique de capteur de flux bidirectionnel au cours d'une thérapie respiratoire
US9999741B2 (en) 2011-12-08 2018-06-19 Europlaz Technologies Limited Respiratory gas flow sensor with sampling port
US20220370742A1 (en) * 2012-04-05 2022-11-24 Fisher & Paykel Healthcare Limited Breathing assistance apparatus with serviceability features

Family Cites Families (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6190326B1 (en) * 1999-04-23 2001-02-20 Medtrac Technologies, Inc. Method and apparatus for obtaining patient respiratory data
CN103143099B (zh) * 2004-08-20 2018-04-20 菲舍尔和佩克尔保健有限公司 用于测量供应给患者的气体的特性的装置
DE202006021019U1 (de) * 2005-03-01 2011-11-08 Resmed Ltd. Erkennungssystem für eine Vorrichtung, die einem Patienten ein atembares Gas zuführt

Patent Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB1512290A (en) 1975-11-24 1978-06-01 Agar J Instrumentation Ltd Method and apparatus for determining fluid flow rate and/or for exercising a control in dependence thereon
US4363238A (en) 1979-08-16 1982-12-14 Franz Willam Device for measuring the breath of patients
US5069066A (en) 1990-05-10 1991-12-03 Djorup Robert Sonny Constant temperature anemometer
DE4020522A1 (de) * 1990-06-28 1992-01-09 Fresenius Ag Medizinisches geraetesystem
US20010039833A1 (en) * 2000-05-13 2001-11-15 Dieter Engel Respiratory flow sensor
EP1950535A1 (fr) 2006-08-07 2008-07-30 General Electric Company Procédé et système de compensation dynamique de capteur de flux bidirectionnel au cours d'une thérapie respiratoire
US9999741B2 (en) 2011-12-08 2018-06-19 Europlaz Technologies Limited Respiratory gas flow sensor with sampling port
US20220370742A1 (en) * 2012-04-05 2022-11-24 Fisher & Paykel Healthcare Limited Breathing assistance apparatus with serviceability features

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GB202308650D0 (en) 2023-07-26
GB2630810A (en) 2024-12-11
EP4723951A1 (fr) 2026-04-15

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