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WO2024083892A1 - Composant d'émission de rayonnement pour la détection optique à compensation de température d'une teneur en oxygène d'un fluide - Google Patents

Composant d'émission de rayonnement pour la détection optique à compensation de température d'une teneur en oxygène d'un fluide Download PDF

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Publication number
WO2024083892A1
WO2024083892A1 PCT/EP2023/078946 EP2023078946W WO2024083892A1 WO 2024083892 A1 WO2024083892 A1 WO 2024083892A1 EP 2023078946 W EP2023078946 W EP 2023078946W WO 2024083892 A1 WO2024083892 A1 WO 2024083892A1
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WO
WIPO (PCT)
Prior art keywords
radiation
luminophore
emission component
contact surface
base body
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/EP2023/078946
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German (de)
English (en)
Inventor
Eva-Maria GRETHER
Philipp Baur
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.)
Hamilton Medical AG
Original Assignee
Hamilton Medical AG
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 Hamilton Medical AG filed Critical Hamilton Medical AG
Priority to EP23790668.0A priority Critical patent/EP4605730A1/fr
Publication of WO2024083892A1 publication Critical patent/WO2024083892A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/75—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated
    • G01N21/77—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0071—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by measuring fluorescence emission
    • 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
    • A61B5/082—Evaluation by breath analysis, e.g. determination of the chemical composition of exhaled breath
    • 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
    • A61B5/083—Measuring rate of metabolism by using breath test, e.g. measuring rate of oxygen consumption
    • A61B5/0833—Measuring rate of oxygen consumption
    • 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
    • A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
    • A61M16/0816—Joints or connectors
    • 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
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/1005—Preparation of respiratory gases or vapours with O2 features or with parameter measurement
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/6428—Measuring fluorescence of fluorescent products of reactions or of fluorochrome labelled reactive substances, e.g. measuring quenching effects, using measuring "optrodes"
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/645—Specially adapted constructive features of fluorimeters
    • 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
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/1005—Preparation of respiratory gases or vapours with O2 features or with parameter measurement
    • A61M2016/102—Measuring a parameter of the content of the delivered gas
    • A61M2016/1025—Measuring a parameter of the content of the delivered gas the O2 concentration
    • 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
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/1005—Preparation of respiratory gases or vapours with O2 features or with parameter measurement
    • A61M2016/102—Measuring a parameter of the content of the delivered gas
    • A61M2016/103—Measuring a parameter of the content of the delivered gas the CO2 concentration
    • 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
    • A61M2205/3306—Optical measuring means
    • 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
    • A61M2205/3372—Temperature compensation
    • 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
    • A61M2230/00—Measuring parameters of the user
    • A61M2230/40—Respiratory characteristics
    • A61M2230/43—Composition of exhalation
    • A61M2230/432—Composition of exhalation partial CO2 pressure (P-CO2)
    • 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
    • A61M2230/00—Measuring parameters of the user
    • A61M2230/40—Respiratory characteristics
    • A61M2230/43—Composition of exhalation
    • A61M2230/435—Composition of exhalation partial O2 pressure (P-O2)
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/6428—Measuring fluorescence of fluorescent products of reactions or of fluorochrome labelled reactive substances, e.g. measuring quenching effects, using measuring "optrodes"
    • G01N2021/6432—Quenching
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/6428—Measuring fluorescence of fluorescent products of reactions or of fluorochrome labelled reactive substances, e.g. measuring quenching effects, using measuring "optrodes"
    • G01N2021/6434—Optrodes
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/62—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light
    • G01N21/63—Systems in which the material investigated is excited whereby it emits light or causes a change in wavelength of the incident light optically excited
    • G01N21/64—Fluorescence; Phosphorescence
    • G01N21/645—Specially adapted constructive features of fluorimeters
    • G01N2021/6482—Sample cells, cuvettes
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/75—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated
    • G01N21/77—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator
    • G01N2021/775—Indicator and selective membrane
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/75—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated
    • G01N21/77—Systems in which material is subjected to a chemical reaction, the progress or the result of the reaction being investigated by observing the effect on a chemical indicator
    • G01N2021/7769—Measurement method of reaction-produced change in sensor
    • G01N2021/7786—Fluorescence
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
    • G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
    • G01N21/35—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light
    • G01N21/3504—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light for analysing gases, e.g. multi-gas analysis
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2201/00—Features of devices classified in G01N21/00
    • G01N2201/02—Mechanical
    • G01N2201/022—Casings
    • G01N2201/0228—Moulded parts
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2201/00—Features of devices classified in G01N21/00
    • G01N2201/12—Circuits of general importance; Signal processing
    • G01N2201/121—Correction signals
    • G01N2201/1211—Correction signals for temperature

Definitions

  • Radiation emission component for temperature-compensated optical detection of the oxygen content of a fluid
  • the present invention relates to a radiation-emitting component for temperature-compensated optical detection of an oxygen content of a fluid, wherein the radiation-emitting component comprises a contact surface wettable by the fluid and a coupling surface different from the contact surface for coupling to a radiation-sensitive sensor arrangement.
  • the radiation-emitting component has a region containing a luminophore.
  • a luminophore in the region containing the luminophore can be excited by irradiation with a first electromagnetic radiation of a first wavelength to emit a second electromagnetic radiation of a second wavelength different from the first wavelength.
  • the excited emission behavior of the luminophore in the region containing the luminophore depends on an oxygen partial pressure in a fluid contacting the contact surface.
  • the luminophore can be reached by oxygen in a first section of the contact surface. Its emission of excited radiation can be extinguished by contact of the luminophore with oxygen molecules in a manner known per se.
  • the radiation-emitting component further comprises a temperature-detecting region that emits infrared radiation.
  • the temperature-detecting region is offset relative to the luminophore-containing region in a reference direction along the contact surface.
  • the radiation emission component has, in the section in which the temperature detection area is arranged, a base body with a recess extending towards the contact surface.
  • the recess is covered by a base comprising a base layer body.
  • a surface of the base layer body facing away from the recess forms a second section of the contact surface that is different from the first section.
  • Such a radiation emission component is known as a layered body from WO 2018/- 166847 A1.
  • the base layered body is preferably made of thermally highly conductive metal, in particular aluminum.
  • the known base layered body made of metal foil is glued to the front side of the base body on the side facing the measuring fluid during operation in such a way that it covers a recess that passes through the base body.
  • the metal foil, i.e. the base layered body can be coated with a black lacquer on its side facing the recess in order to achieve a higher emissivity in the relevant wavelength range than would be the case with the bare metal surface.
  • Such radiation emission components are preferably arranged to measure the oxygen content of respiratory gas in ventilation lines of ventilation devices for artificial ventilation of patients, for example in a measuring cuvette through which respiratory gas flows, which can be coupled to a radiation-sensitive sensor arrangement for radiation exchange.
  • the measuring fluid is then a measuring gas, namely the respiratory gas.
  • the known "quenching" of the luminophore used by the radiation emission component to detect the oxygen content in the respiratory gas of a ventilated patient depends on the temperature of the luminophore in addition to the oxygen partial pressure of the respiratory gas.
  • the temperature detection area is arranged with the specified spatial offset from the luminophore-containing area, the infrared radiation emitted by the area is a measure of its temperature.
  • the temperature of the bottom or the temperature of the free surface pointing towards the recess is Surface of the base approximately equal to the temperature of the luminophore in the luminophore-containing area. Due to the base, which covers the recess, the recess is designed like a blind hole.
  • a temperature corresponding sufficiently precisely to the temperature of the luminophore can be detected spatially away from the luminophore, so that the two radiation detections, once in the luminophore-containing area and once again in the temperature detection area, do not interfere with each other.
  • the manufacture of the known radiation emission component is complex, since the metal foil, possibly after coating, has to be glued to the base body of the temperature detection area, which is usually made of plastic.
  • This bonding process is not only laborious in its process due to the application of adhesive and positioning of the components to be bonded together relative to one another, trouble-free curing of the adhesive, etc., but also requires the use of specially adapted adhesives, since aluminum foils in particular cannot be bonded easily.
  • Either metal foils require pretreatment, for example by applying a primer as an adhesion promoter layer, or a special adhesive must be selected which can permanently bond a metal foil to the base body.
  • the base body and the bottom layer body each comprise plastic material, wherein the base body and the bottom layer body are connected to one another in one piece by means of their respective plastic materials.
  • the one-piece connection is clearly a particularly secure connection.
  • plastic material generally has a lower thermal conductivity than the metal foil known from the state of the art.
  • this disadvantage of the base can be compensated for by making the base sufficiently thin between its contact surface that can be wetted by the measuring fluid and its free surface opposite the recess that emits infrared radiation.
  • the contact surface of the radiation emitting component is wettable by fluid, which basically indicates that the contact surface of the radiation emitting component is an exposed surface thereof. This ensures wettability by the measuring fluid to be detected.
  • the coupling surface of the radiation-emitting component is also an exposed surface. It is spatially arranged or formed at a different location than the contact surface and is therefore different from the contact surface.
  • the coupling surface is an exposed surface of the base body opposite the contact surface along a path or axis of the depth of the recess. In this case, the recess extends like a blind hole from a surface of the base body opposite the contact surface, which is usually free, to the contact surface.
  • the coupling surface serves to couple the radiation-sensing element. sitive sensor arrangement.
  • the first electromagnetic radiation for radiative excitation of the luminophore in the luminophore-containing region can preferably be introduced into the base body through the coupling surface.
  • the second electromagnetic radiation emitted by the luminophore also preferably exits the base body through the coupling surface.
  • infrared radiation emanating from the coupling surface is detected by an infrared sensor of the radiation-sensitive sensor arrangement.
  • the infrared radiation emitted from the bottom of the recess in the temperature detection area is emitted in a different direction than the second electromagnetic radiation in the luminophore-containing area, i.e. for the coupling surface to have differently oriented areas in the luminophore-containing area and in the temperature detection area.
  • the coupling surface of the radiation emission component is uniformly oriented across the luminophore-containing area and the temperature detection area, on the one hand to form the coupling surface with the smallest possible surface area and/or installation space requirement and on the other hand to facilitate coupling of the radiation-sensitive sensor arrangement.
  • the plastic material of the base body and the plastic material of the base layer body are fused together in some areas.
  • This first possible embodiment allows a great deal of design freedom in the design of the base layer body in particular, but requires an additional work step in the production of the radiation emission component with the joining process for fusing the base body and the base layer body.
  • the base body and the base layer body can be formed monolithically from the same plastic material in one piece.
  • the base layer body manufactured in one piece with the base body can be manufactured without difficulty with a thickness in the range of between 200 pm and 300 pm.
  • a so-called injection-compression molding process can be used for thicknesses in the range of 100 pm to 200 pm, in which a blank close to the final shape is first injection-molded and the base area of the recess and thus the base layer body is reshaped in a second molding process while still in the injection mold using a slider used as an embossing stamp.
  • the layer thicknesses that can be achieved by injection molding alone or by injection-compression molding depend on the respective process and the plastic material used. In the thickness range of 80 to 120 pm, depending on the plastic material to be molded, there is certainly a certain choice of producing the base area in one piece with the base body using one or the other process. This one-piece, monolithic production of the base body and base layer body achieves the most permanent and firmest connection between the bodies mentioned.
  • the base layer body is preferably made of 100% plastic material.
  • the plastic material can be plastic filled with a filling material, such as particles and/or fibers, in order to increase its strength, such as tensile strength and bending strength.
  • the filling material can, but does not have to, consist of plastic or include plastic.
  • the plastic material can alternatively be unfilled plastic, which is advantageous in terms of spatial The most homogeneous material properties of the temperature detection section are preferred.
  • an optically transparent base layer body can be achieved using an unfilled plastic, which is generally not possible with filled plastic.
  • the plastic is preferably a thermoplastic, regardless of whether it is used as a matrix plastic of a filled plastic material or as an unfilled plastic.
  • the bottom layer body can be designed as a plastic film, particularly if it is manufactured separately from the base body and is joined to it in one piece by a welding process.
  • the plastic film can be formed from several layers, in particular plastic material layers.
  • the plastic film can thus have a temperature information layer with a particularly advantageously low degree of transmission in the infrared wavelength range relevant for the planned infrared temperature measurement.
  • the temperature information layer can have an external connecting layer on its side facing the base body or the recess, which can be particularly well melted into the plastic of the base body, in particular by welding or sealing.
  • the connecting layer can be thinner than the temperature information layer.
  • the bottom layer body forms the above-mentioned second section of the contact surface and thus an exposed surface facing away from the recess in the base body in order to form the temperature detection area as simply as possible, a surface of the temperature information layer can form the second section of the contact surface.
  • the first and second sections of the contact surface are arranged offset from one another in a reference direction along the contact surface, for example in the longitudinal direction of the radiation-emitting component.
  • the first and second sections of the contact surface can additionally or alternatively be arranged offset relative to one another in the reference direction parallel to the contact surface.
  • the soil layer body preferably comprises only one type of Plastic.
  • This type of plastic can be styrene, polyester, polyolefin, etc., to name just a few examples.
  • the base body also preferably comprises only one type of plastic. As a rule, different plastics of the same type are compatible with each other and can be joined together in one piece by melting.
  • the base layer body and preferably also the base body, particularly preferably comprises only one plastic.
  • This plastic is preferably the same plastic for both components consisting of the base body and the base layer body, particularly in the case of a one-piece monolithic design.
  • This plastic is preferably the plastic methyl methacrylate acrylonitrile butadiene styrene (MABS), which has already proven itself in applications for medical devices.
  • the base layer body is particularly preferably a single-layer body with only a single layer, such as is available from injection molding or injection compression molding.
  • a separate base layer body for example designed as a film, can also be a single-layer body.
  • the base layer body in addition to the simplification achieved by using preferably only a single plastic, there is also further simplification achieved by forming the base layer body in only a single layer.
  • this does not exclude the possibility of subsequently applying one or more coatings to the soil layer body, for example in order to adapt the emission behaviour and/or the absorption behaviour of the soil to the planned application of detecting the emitted infrared radiation.
  • a coating subsequently applied viscously to a previously produced soil layer body and then cured and/or dried is part of the soil, but not part of the soil layer body.
  • the bottom layer body is preferably thinner than the base body surrounding the recess.
  • the bottom layer body or the base of the temperature detection area can have a thickness in the range of 50 pm to 300 pm.
  • the base body is at least 500 pm, preferably at least 1 mm, particularly preferably several millimeters thick to provide sufficient rigidity and strength.
  • the thickness of the radiation emitting component in the temperature detection area is preferably measured along the direction of the depth extension of the recess.
  • the section of the coupling surface through which the first electromagnetic radiation is introduced into the base body and/or the second electromagnetic radiation exits therefrom forms a first section of the coupling surface.
  • the first electromagnetic radiation is introduced and the second electromagnetic radiation, but no infrared radiation, is detected at this first section of the coupling surface.
  • the exposed surface of the base facing the recess and opposite the second section of the contact surface forms a second section of the coupling surface.
  • the second section of the coupling surface is arranged offset in a direction along the coupling surface, in particular parallel to the coupling surface, relative to the first section of the coupling surface in order to avoid mutual interference in the detection of infrared radiation on the one hand and in the emission of the first electromagnetic radiation and the detection of the second electromagnetic radiation on the other hand.
  • At the second section of the coupling surface preferably only the infrared radiation emitted by the second section is detected, but no radiation to or from the luminophore-containing area.
  • the second section of the coupling surface is offset in a direction in the direction of the depth of the recess relative to the first section of the coupling surface.
  • the direction of the depth extension of the recess corresponds to the thickness direction of the base body.
  • the coupling surface and the contact surface are parallel to one another.
  • the first sections of the contact surface and the coupling surface are opposite one another in the thickness direction of the base body.
  • the second sections of the contact surface and the coupling surface are opposite one another in the thickness direction of the base body, in particular the bottom of the recess.
  • the second section of the coupling surface is also arranged offset in the reference direction relative to the first section of the coupling surface.
  • a plastic material of the bottom layer body that is advantageous for temperature detection by infrared radiation emission preferably has a transmittance of not more than 20% for infrared radiation in a wavelength range from 5500 nm to 14000 nm.
  • the entire thickness range of the bottom layer body between its opposite outer surfaces is formed from the plastic material with the low transmittance of 20% or less.
  • the plastic material of the base layer body has a transmittance of no more than 5% for infrared radiation in the wavelength range.
  • the above-mentioned plastic MABS has the advantageously low transmittance of no more than 5% in the wavelength range. This ensures that it is not infrared radiation emitted by the measuring gas or measuring fluid beyond the contact surface that reaches an infrared sensor, but infrared radiation actually emitted by the base layer body. In this way, incorrect measurements can be avoided in which the temperature of the measuring fluid takes the place of the temperature of the base layer body or the second section of the coupling surface.
  • the plastic material of the base layer body can directly form the surface of the base facing the recess.
  • the surface of an injection-molded or injection-compressed base layer body or a film surface of a base layer body designed as a film can form the surface facing the recess or the second section of the coupling surface.
  • an additional coating to adapt the radiation behavior of the soil to the measurement conditions is advantageously not required.
  • the base layer body can have a coating on its surface facing away from the contact surface and/or on its surface facing the contact surface or forming a section of the contact surface.
  • a coating is required, its arrangement on the surface facing away from the contact surface is preferred, since this points directly to an infrared sensor arranged on the side of the coupling surface and can preferably only be opposite this with an air gap in between.
  • This coating is preferably subsequently applied to the base layer body.
  • the coating is preferably selected such that the base has an absorption level of at least 95% and/or an emission level of at least 95% in the direction of the recess in the wavelength range from 5500 nm to 14000 nm.
  • the coating is preferably made of a material which has an absorption level of at least 95% and/or an emission level of at least 95%.
  • Such a coating is available, for example, as a deep black coating from ACM COATINGS GmbH, Rudelsburgpromenade 20c, in 06628 Naumburg - Bad Kosen (DE).
  • the temperature detection area in particular the soil, particularly preferably the soil layer body, is preferably free of luminophore.
  • the radiation emission component can have a luminophore base body.
  • the luminophore base body can carry an oxygen-permeable film.
  • a first surface of the film preferably forms the first section of the contact surface of the radiation emission component.
  • the luminophore is also preferably arranged between a second surface of the semi-permeable film, which is opposite the first surface, and the luminophore base body.
  • the luminophore is basically accessible to oxygen to extinguish the excited radiation, but is nevertheless protected from the influence of the measuring fluid wetting the contact surface.
  • the luminophore is basically a surface of the luminophore base body, it is preferred for manufacturing reasons if the luminophore is arranged in the film or on the surface of the film facing the luminophore base body.
  • One material for producing an oxygen-permeable film that can serve as a substrate for a luminophore layer is, for example, polyvinylidene fluoride.
  • the luminophore itself forms the first section of the contact surface and is directly wettable by the measuring fluid.
  • this design is not preferred.
  • the surface of the oxygen-permeable film forming the first section of the contact surface can be arranged flush with the second section of the contact surface.
  • the surface of the oxygen-permeable film forming the first section of the contact surface can be offset in the direction of the depth extension, and thus preferably also in the thickness direction of the luminophore base body, with respect to the second section of the contact surface, by an amount approximately equal to the thickness of the film.
  • the thickness of a luminophore layer carried by the oxygen-permeable film can also contribute to the amount of the offset.
  • the luminophore base body preferably has a transmittance of at least 80% for radiation in a first wavelength range from 450 to 480 nm and in a second wavelength range from 730 to 1100 nm. Preferably of at least 90%, particularly preferably of at least 95%.
  • the above-mentioned plastic MABS also has the desired high transmittances in the latter wavelength ranges.
  • the luminophore base body is therefore preferably made of MABS.
  • the base body of the temperature detection area and the luminophore base body can be considered to produce the base body of the temperature detection area and the luminophore base body separately and to join or assemble them to form a base body of the radiation emission component.
  • the base body and the luminophore base body are formed in one piece and monolithically as a radiation emission component base body.
  • the base body and the luminophore base body each form a section of this radiation emission component base body.
  • the section of the base body and the section of the luminophore base body are preferably arranged offset from one another in the reference direction.
  • both the luminophore base body and the base layer body can preferably be made from the thermoplastic MABS and since the base body of the temperature detection area and the base layer body are more preferably made integrally connected to one another, the base body of the temperature detection area is preferably also made from MABS. Consequently, in a particularly preferred embodiment, the radiation emission component base body and the base layer body integrally connected to it are made from MABS, even more preferably by injection molding or injection compression molding.
  • the reference direction is preferably the longitudinal direction of the radiation-emitting component.
  • the radiation-emitting component has its largest dimension among the Cartesian coordinate directions mentioned and thus offers sufficient space for the formation of the temperature detection area on the one hand and the luminophore-containing area on the other side by side.
  • the present invention relates in an advantageous development to a measuring cuvette with a radiation emission component as described and developed above.
  • the measuring cuvette has a gas space with a receiving volume for receiving a measuring gas as the measuring fluid.
  • the contact surface forms a wall of the gas space which delimits the receiving volume and is exposed to the receiving volume.
  • at least a section of the coupling surface is located towards the outside environment of the Measuring cuvette.
  • the first and second regions of the coupling surface on the measuring cuvette preferably point in identical directions.
  • at least the first region of the coupling surface is flat.
  • the second region of the coupling surface is preferably flat and particularly preferably parallel to the first region of the coupling surface, although due to the recess it is arranged offset relative to the first region in the direction of the depth of the recess.
  • At least one boundary wall of the gas space has a window that is permeable to radiation in the infrared wavelength range.
  • the proportion of carbon dioxide in the breathing gas can thus be determined using infrared spectroscopy based on the absorption behavior of carbon dioxide in the breathing gas.
  • the at least one boundary wall with the IR-permeable window is a different boundary wall than the wall or contact surface formed by the radiation-emitting component.
  • the boundary wall having the IR-permeable window has a surface normal on its inner surface wetted by the measuring gas, which forms an angle of 80 to 100°, preferably 90°, with the surface normal of the contact surface.
  • the measuring cuvette is designed to irradiate the gas space with infrared radiation in order to measure the carbon dioxide content of the measuring gas, so that two boundary walls opposite each other across the gas space each have a window made of material permeable to radiation in the infrared wavelength range.
  • the gas space is filled with the measuring gas and that the measuring gas is measured after filling.
  • the preferred application of the measuring cuvette is the measuring of respiratory gas as the measuring gas, namely during its supply to the patient and/or its discharge from the patient.
  • the gas space can therefore preferably be flowed through by measuring gas along one flow direction, preferably along two opposite flow directions.
  • the measuring cuvette preferably forms part of a ventilation line in order to supply inspiratory breathing gas to a patient and to remove expiratory breathing gas.
  • the radiation emission component can therefore be located in the flow direction between two connection formations, each of the connection formations being designed to connect a line carrying measuring gas.
  • the measuring cuvette is not limited to applications in ventilation lines, although this is preferred.
  • the present invention relates to a sensor device comprising a measuring cuvette as described and developed above, and further comprising a radiation-sensitive sensor arrangement with a sensor housing.
  • the sensor housing accommodates at least: a radiation source for emitting the first electromagnetic radiation, a first radiation sensor for detecting the second electromagnetic radiation and at least one infrared sensor for detecting infrared radiation in a wavelength range for which the bottom of the temperature detection area has a transmittance of no more than 20%, preferably no more than 10%, particularly preferably no more than 5%.
  • the sensor housing which can preferably be reused for subsequent measuring tasks after completion of a measuring task, can be detachably attached to a section of the measuring cuvette having the radiation emission component.
  • the sensor housing can preferably be pushed astride the section of the measuring cuvette having the radiation emission component and can be removed from it.
  • the sensor housing can also preferably be secured to the measuring cuvette in the coupled state by means of an overridable catch or a detachable lock.
  • Fig. 1 is a longitudinal sectional view through a first embodiment of a radiation emitting component of the present application
  • Fig. 2 is a perspective view of a second embodiment of a radiation emitting device of the present application
  • Fig. 3 is a perspective view of a measuring cuvette with a radiation emission component of the present application
  • Fig. 4 is a front view of the measuring cuvette of Fig. 3 against the longitudinal direction L,
  • Fig. 5 is a cross-sectional view of the measuring cuvette of Figures 3 and 4, wherein the offset cutting plane oriented orthogonally to the longitudinal direction L runs through the gas space of the measuring cuvette and through the recess in the temperature detection area of the radiation emission component,
  • Fig. 6 is a perspective view of a radiation-sensitive sensor arrangement for detachable coupling with the measuring cuvette of Figures 3 to 5, and
  • Fig. 7 is a bottom view of the radiation-sensitive sensor arrangement of Figure 6.
  • a first embodiment of a radiation emission component according to the invention is generally designated 10.
  • the radiation emission component 10 comprises a radiation emission component base body 12 made of MABS and manufactured in one piece by injection molding.
  • a Cartesian coordinate system consisting of pairs of mutually orthogonal coordinate directions: longitudinal direction L, width direction B and thickness direction D, is indicated in the figures showing a radiation-emitting component in order to make clear the respective orientation of the radiation-emitting component in the figure in question.
  • the radiation emission component 10 has a luminophore-containing region 14 and a temperature detection region 16, which are arranged offset relative to one another in the longitudinal direction L as a reference direction.
  • the radiation emission component 10 has a contact surface 18 that can be wetted by a fluid to be measured, in particular gas, during operation of the radiation emission component 10.
  • a section of the contact surface 18 located in the luminophore-containing region 14 forms a first section 20 of the contact surface 18.
  • a section of the contact surface 18 located in the temperature detection region 16 forms a second section 22 of the contact surface 18.
  • the radiation-emitting component 10 Arranged at a distance from the contact surface 18 in the thickness direction D or opposite thereto, the radiation-emitting component 10 has a coupling surface 24 which serves for the temporary detachable coupling with a radiation-sensitive sensor arrangement (see, for example, the radiation-sensitive sensor arrangement 80 in Figures 6 and 7) in order to transmit radiation information from the radiation-emitting component 10 to the radiation-sensitive sensor arrangement and to transmit an excitation radiation, which is referred to in the introduction to the description as first electromagnetic radiation, to the luminophore in the luminophore-containing region 14 in order to excite it to emit a second electromagnetic radiation whose wavelength is different from that of the excitation radiation.
  • a radiation-sensitive sensor arrangement see, for example, the radiation-sensitive sensor arrangement 80 in Figures 6 and 7
  • a section of the coupling surface 24 located in the luminophore-containing region 14 forms a first section 26 of the coupling surface 24 and a section of the coupling surface 24 located in the temperature detection region 16 forms a second section 28 of the coupling surface 24.
  • the luminophore-containing region 14 is defined by the arrangement of the luminophore.
  • An oxygen-permeable film 30 made of polyvinylidene fluoride is integrally connected to a luminophore base body 32 in the luminophore-containing region 14, for example by ultrasonic welding.
  • the luminophore base body 32 forms a section of the radiation emission component base body 12.
  • the luminophore base body 32 is formed by injection molding in one piece and monolithically with a base body 34 of the temperature detection area 16.
  • the base body 34 also forms a section of the radiation emission component base body 12.
  • the film 30 forms the first section 20 of the contact surface 18 with the free surface 31 on its side facing away from the luminophore base body 32 and has a thin layer 36 with the luminophore on its opposite surface 33, indicated by close dotting.
  • the luminophore is thus arranged between the luminophore base body 32 and the film 30 and is protected from external influences.
  • the film 30 made of polyvinylidene fluoride is permeable to oxygen, so that oxygen molecules can reach the luminophore in the layer 36 in the luminophore-containing region 14 via the contact surface 18 or via the first section 20 thereof and can influence its radiation behavior by extinguishing it in a manner known per se.
  • the amount of oxygen molecules reaching the luminophore per unit of time is proportional to the partial pressure of oxygen in the measuring fluid MF wetting the contact surface 18 or the first section 20 thereof.
  • the measuring fluid MF is symbolized in the representation as a point cloud with a thinner point density than that of layer 36.
  • the temperature detection area 16 is characterized by a blind hole-like recess 38.
  • the recess 38 extends from a free surface 25 of the radiation emission component base body 12 or the base body 34, which is opposite the contact surface 25 in the thickness direction D, along an axis 40 of the depth extension to the contact surface 18.
  • the surface 25 forms a common flat surface with the second section 26 of the coupling surface 24.
  • the recess 38 is covered by a base 42, which in the embodiment shown is formed by a base layer body 44 formed in one piece with the base body 34 during injection molding.
  • the base layer body 44 thus formed exclusively from MABS, forms the second section of the contact surface 18 with its free surface 45 facing away from the recess 38 and forms with its opposite free surface 47 pointing towards the recess 38, the second portion of the coupling surface 24.
  • the bottom layer body 44 Due to its construction from MABS, the bottom layer body 44 is virtually impermeable in the wavelength range of 5,500 to 14,000 nm relevant for infrared temperature detection, or has a transmittance of less than 5%. In the embodiment shown, the bottom layer body 44 has a thickness of approximately 200 pm to 240 pm.
  • the base layer body 44 Due to its one-piece, monolithic design together with the base body 34 or with the radiation emission component base body 12, it is arranged on the base body 34 with high strength and is connected to it. In the embodiment shown, detachment of the base layer body 44 from the base body 34 is only conceivable by deliberate destruction of the temperature detection area 16 of the radiation emission component 10. This requires a considerable amount of force, which significantly exceeds the forces that occur during normal operation. At the same time, the base layer body 44 can be manufactured very advantageously in a single operation together with the base body 34 and the radiation emission component base body 12.
  • the film 30 has a similar thickness to the base layer body 44 and, as a plastic, has a similar heat capacity and a similar thermal conductivity, so that when the contact surface 18 is wetted with measuring fluid, the luminophore layer 36 on the surface 33 of the film 30 opposite the first section 20 of the contact surface 18 and the second section 28 of the coupling surface 24 have approximately the same temperature. This applies advantageously both in the quasi-stationary state and in a transient view, for example when the temperature of the measuring fluid changes at the contact surface 18 and the measuring fluid transfers this temperature change to the contact surface 18.
  • the first section 20 and the second section 22 of the contact surface 18 are not only offset from one another in the longitudinal direction L as a possible reference direction, but also in a direction parallel to the contact surface 18.
  • Reference direction RD wherein the reference direction RD in the illustrated embodiment has its largest dimensional component in the longitudinal direction L.
  • a recess 46 is formed in the luminophore base body 32, in which the film 30 is preferably received such that the first section 20 and the second section 22 of the contact surface 18 are arranged flush and lie in a common plane.
  • the surface 27 of the radiation emission base body 12 facing the measuring fluid MF has a jump in the transition to the recess 46.
  • Figure 2 shows a perspective view of a second embodiment of a radiation-emitting component according to the invention.
  • Components and component sections that are identical and have the same function as in the first embodiment shown in Figure 1 are provided with the same reference numerals in Figure 2, but increased by the number 100.
  • the film 130 with the luminophore layer 136 is attached to the flat, crack- and kink-free surface 127 of the radiation emission component base body 112 by ultrasonic welding.
  • the surface 127 in the region of the temperature detection region 116 forms part of the second section 122 of the contact surface 118.
  • the first section 120 of the contact surface 118 is offset with respect to the second section 122 by the thickness of the film 130 and by the essentially negligible thickness of the luminophore layer 136 in the thickness direction D, i.e. in the direction of the axis 140 of the depth extension of the recess 138.
  • a measuring cuvette 50 with the radiation emission component 10 is shown in perspective. Instead of the radiation emission component 10, which is chosen merely as an example, the measuring cuvette 50 could also have the radiation emission component 110.
  • the measuring cuvette comprises a cuvette housing 52, of which the radiation emission component 10 forms a part.
  • the remaining cuvette housing 54 without the radiation emission component 10 is also made predominantly or completely from MABS by weight and is preferably manufactured using an injection molding process.
  • the IR-permeable windows 72 and 74 and their frame parts 77 and 78 are also preferably manufactured using an injection molding process. Because the materials are identical, the part of the remaining cuvette housing 54 produced using injection molding can simply be molded onto the radiation emission component 10 to form the cuvette housing 52 without any further joining measures.
  • the cuvette housing 52 can be flowed through bidirectionally along the flow path 56, which is preferably designed to be straight in the example shown.
  • the cuvette housing 52 is designed for use in a ventilation line. It has a distal connection formation 58 and a proximal connection formation 60, to each of which further sections of the ventilation line can be connected. In the intended installation position, a ventilation line section connected to the proximal connection formation 60 leads to the ventilated patient and a ventilation line section connected to the distal connection formation 58 leads to the ventilation device.
  • a coupling section 62 with a coupling formation 64 is formed, which can be detachably coupled to the radiation-sensitive sensor arrangement 80 shown in Figures 6 and 7.
  • the radiation-sensitive sensor arrangement 80 can be pushed astride the coupling section 62 along the arrow K1 and pulled off the coupling section 62 in the opposite direction along the arrow K2.
  • a coupling structure 66 tapering from the proximal to the distal end on the lower side of the coupling section 62 in the direction of the arrow K1 prevents coupling of an incorrectly oriented sensor arrangement 80 and also allows a releasable locking of the sensor arrangement 80 to the coupling section 62.
  • the distal connection formation 58 ends at a wall 59 which is oriented substantially orthogonally to the flow path 56 and which separates the connection formation 58 from the coupling section 62.
  • the coupling section 62 ends in a wall 61, from which the proximal connection formation 60 extends away from the coupling section 62.
  • the radiation emission component 10 forms a ceiling section of the coupling section 62.
  • Side walls 68 and 70 oriented transversely, preferably orthogonally, to the ceiling section each have a side window 72 or 74 that is permeable to infrared radiation in order to be able to shine infrared radiation through a gas space 76 located inside the coupling section 62.
  • the observer of Figure 4 looks along the flow path 56 from the distal longitudinal end of the measuring cuvette 50 into the gas space 76 of the same.
  • the gas space 76 has a receiving volume 76a in which the measuring gas MF can be received, also as a flowing measuring gas MF.
  • Figure 5 shows a cross section through the measuring cuvette 50 along a bent cutting plane, with a first plane section which extends orthogonally to the flow path 56 in the area of the radiation emission component 10 through its recess 38, and with a second plane section parallel to the first, which extends from the second section 22 of the contact surface through the centers of the circular side windows 72 and 74.
  • the viewer of Figure 5 looks from the cutting surface in the direction of the distal connection formation 58.
  • the side windows 72 and 74 are connected to frames 77 and 78, respectively, which are integrally formed with the rest of the cuvette housing 54 by injection molding.
  • the contact surface 18 of the radiation emission component 10 forms a wall of the gas space 76, which limits its receiving volume 76a at the top.
  • Figures 6 and 7 show a radiation-sensitive sensor arrangement 80 that can be detachably coupled to the measuring cuvette 50, more precisely to its coupling section 62.
  • Figure 6 shows a perspective view of the sensor arrangement 80
  • Figure 7 shows a bottom view of the same.
  • the sensor arrangement 80 comprises a sensor housing 82 with a through-opening 84 surrounded by the sensor housing 82 on three sides, in which the coupling formation 62 of the measuring cuvette 50 is located when the sensor arrangement 80 is coupled to the measuring cuvette 50.
  • an electrical line 85 is connected to the sensor housing 82, which electrical line 85 supplies electrical functional units accommodated in the sensor housing 82 with electrical current and also delivers control signals to the functional units and transmits detection signals from the functional units to a higher-level control device or evaluation device.
  • a sensor unit 86 cooperating with the luminophore-containing region 14 of the radiation emission component 10 of the measuring cuvette 50 can be seen as such a functional unit.
  • This sensor unit 86 comprises a radiation source 86a, which is designed to emit a first electromagnetic radiation as excitation radiation.
  • the sensor unit 86 further comprises a radiation sensor 86b, which is designed to detect an excited second electromagnetic radiation emitted by the luminophore-containing region 14 in response to this excitation.
  • an infrared sensor 88 which is designed to detect infrared radiation emitted by the second section 28 of the coupling surface 24.
  • the sensor unit 86 and the infrared sensor are accommodated in a housing section 87 bridging the through-opening and, when coupled to the measuring cuvette 50, are located directly opposite the coupling surface 24 of the radiation emission component 10.
  • an infrared radiation source 92 is accommodated as a third such functional unit, which emits infrared radiation across the width of the through-opening 84 to the sensor housing area 94 opposite the sensor housing area 90 and located on the other side of the through-opening 84, where a second infrared sensor 96 is accommodated as a fourth such functional unit.
  • the second infrared sensor 96 detects the infrared radiation emitted by the infrared radiation source 92 after passing through the two side windows 72 and 74 and through the gas space 76. This enables an infrared spectroscopic quantitative detection of the carbon dioxide content of a gas flowing through the gas space 76.

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Abstract

La présente invention concerne un composant d'émission de rayonnement (10) pour la détection optique à compensation de température d'une teneur en oxygène d'un fluide (MF), le composant d'émission de rayonnement (10) comprenant une surface de contact (18) pouvant être mouillée par le fluide (MF), et une surface de couplage (24) différente de la surface de contact (18), le composant d'émission de rayonnement (10) ayant une région contenant un luminophore (14), le luminophore étant accessible par l'oxygène dans une première partie (20) de la surface de contact (18) pour sa désactivation, le composant d'émission de rayonnement (10) ayant une région de détection de température (16) disposée de manière décalée le long de la surface de contact (18) par rapport à la région contenant un luminophore (14), et le composant d'émission de rayonnement (10) ayant, dans la région de détection de température (16), un corps principal (34) ayant une découpe (38) s'étendant vers la surface de contact (18), la découpe (38) étant recouverte par une base (42) comprenant un corps de couche de base (44 ; 144), une surface du corps de couche de base (44) faisant face à l'opposé de la découpe (38) formant une seconde partie (22) de la surface de contact (18). Selon l'invention, le corps principal (34) et le corps de couche de base (44) comprennent chacun une matière plastique, le corps principal (34) et le corps de couche de base (44) étant reliés l'un à l'autre d'un seul tenant au moyen de leurs matières plastiques respectives.
PCT/EP2023/078946 2022-10-19 2023-10-18 Composant d'émission de rayonnement pour la détection optique à compensation de température d'une teneur en oxygène d'un fluide Ceased WO2024083892A1 (fr)

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Application Number Priority Date Filing Date Title
EP23790668.0A EP4605730A1 (fr) 2022-10-19 2023-10-18 Composant d'émission de rayonnement pour la détection optique à compensation de température d'une teneur en oxygène d'un fluide

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DE102022127603.1A DE102022127603A1 (de) 2022-10-19 2022-10-19 Strahlungsemissionsbauteil zur temperaturkompensierten optischen Erfassung eines Sauerstoffgehalts eines Fluids
DE102022127603.1 2022-10-19

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WO2024083892A1 true WO2024083892A1 (fr) 2024-04-25

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Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20160187258A1 (en) * 2014-12-30 2016-06-30 New York University Systems and methods for oxygen sensing
WO2018166847A1 (fr) 2017-03-13 2018-09-20 Hamilton Medical Ag Dispositif pour la détection optique compensée en température d'une teneur en oxygène d'un fluide
DE102018129838A1 (de) * 2018-11-26 2020-05-28 Hamilton Medical Ag Von Atemgas durchströmbare Messvorrichtung zur Messung von Gasbestandteilen des Atemgases

Family Cites Families (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5793044A (en) * 1995-11-09 1998-08-11 Ntc Technology, Inc. Infrared radiation detector units and methods of assembling transducers in which said units are incorporated
DE19548922A1 (de) * 1995-12-27 1997-07-03 Max Planck Gesellschaft Optische Temperatursensoren und Optroden mit optischer Temperaturkompensation
US6095986A (en) * 1998-07-28 2000-08-01 Square One Technology, Inc. Disposable anti-fog airway adapter
DE19913783C1 (de) * 1999-03-26 2000-03-09 Draeger Sicherheitstech Gmbh Atemalkohol-Meßgerät mit einem im Probenahmekanal angeordneten Temperaturfühler
US6888101B2 (en) * 2001-05-31 2005-05-03 Respironics, Inc. Heater for optical gas sensors, gas sensors including the heater, and methods
US7569395B2 (en) * 2006-03-13 2009-08-04 Cryovac, Inc. Method and apparatus for measuring oxygen concentration
DE102006052999B4 (de) * 2006-11-10 2014-11-06 Dräger Medical GmbH Messgasküvette für die Konzentrationsmessung von Gasbestandteilen und Verfahren zur Herstellung einer Messgasküvette
US8312878B2 (en) * 2006-12-04 2012-11-20 Ric Investments, Llc Compensation of volumetric errors in a gas monitoring system
DE102009038237A1 (de) * 2009-08-20 2011-03-03 Siemens Aktiengesellschaft Probenentnahmesystem für ein Gerät zur Atemgasanalyse
US20130023782A1 (en) * 2011-07-18 2013-01-24 General Electric Company Gas sensor, analyzer and method for measuring oxygen concentration of a respiratory gas
DE102013006546B4 (de) * 2013-04-16 2020-08-06 Dräger Safety AG & Co. KGaA Messvorrichtung, Reaktionsträger und Messverfahren
GB2533806B (en) * 2014-12-31 2017-02-08 Gen Electric Airway adapter and method for molding the airway adapter
US20170348047A1 (en) * 2016-06-06 2017-12-07 Buffalo Filter Llc Sensor systems for use in connection with medical procedures
DE102020112557A1 (de) * 2020-05-08 2021-11-11 Hamilton Medical Ag Beatmungsvorrichtung, welche zur Ermittlung einer funktionellen Beeinträchtigung ihrer O2-Sensoranordnung ausgebildet ist

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20160187258A1 (en) * 2014-12-30 2016-06-30 New York University Systems and methods for oxygen sensing
WO2018166847A1 (fr) 2017-03-13 2018-09-20 Hamilton Medical Ag Dispositif pour la détection optique compensée en température d'une teneur en oxygène d'un fluide
DE102018129838A1 (de) * 2018-11-26 2020-05-28 Hamilton Medical Ag Von Atemgas durchströmbare Messvorrichtung zur Messung von Gasbestandteilen des Atemgases

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