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WO2024141878A1 - Dispositif pour système d'assistance respiratoire - Google Patents

Dispositif pour système d'assistance respiratoire Download PDF

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Publication number
WO2024141878A1
WO2024141878A1 PCT/IB2023/063055 IB2023063055W WO2024141878A1 WO 2024141878 A1 WO2024141878 A1 WO 2024141878A1 IB 2023063055 W IB2023063055 W IB 2023063055W WO 2024141878 A1 WO2024141878 A1 WO 2024141878A1
Authority
WO
WIPO (PCT)
Prior art keywords
gases
patient
channel
respiratory apparatus
coupling
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/IB2023/063055
Other languages
English (en)
Inventor
Craig Karl White
Sam James TULLETT
Taylor James EDWARDS
Graeme Matthew SMITH
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.)
Fisher and Paykel Healthcare Ltd
Original Assignee
Fisher and Paykel Healthcare 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 Fisher and Paykel Healthcare Ltd filed Critical Fisher and Paykel Healthcare Ltd
Publication of WO2024141878A1 publication Critical patent/WO2024141878A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • 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
    • A61M16/06—Respiratory or anaesthetic masks
    • A—HUMAN NECESSITIES
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    • A61M15/00—Inhalators
    • A61M15/08—Inhaling devices inserted into the nose
    • A—HUMAN NECESSITIES
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    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
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    • A—HUMAN NECESSITIES
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    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
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    • A61M16/1005—Preparation of respiratory gases or vapours with O2 features or with parameter measurement
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    • A61M16/12—Preparation of respiratory gases or vapours by mixing different gases
    • A61M16/122—Preparation of respiratory gases or vapours by mixing different gases with dilution
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    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
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    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
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    • A61M2205/02—General characteristics of the apparatus characterised by a particular materials
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    • A61M2209/00—Ancillary equipment
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Definitions

  • the present disclosure relates to a device for use in a system for providing respiratory support to a patient.
  • the system includes a first respiratory apparatus and a second respiratory apparatus. It also relates particularly but not exclusively to a system and method for providing respiratory support using the device, and a kit for a system for providing respiratory support to a patient.
  • Patients may lose respiratory function during anaesthesia, or sedation, or more generally during certain medical procedures.
  • a patient Prior to a medical procedure, a patient may be pre-oxygenated by a medical professional to provide a reservoir of oxygen saturation. Pre-oxygenation and CO2 flushing/washout may be carried out with high flow respiratory support via a nasal cannula or other patient interface.
  • High flow systems may be present in the operating theatre for use during anaesthetic or sedation procedures, or other medical procedures.
  • High flow respiratory support has been found effective in meeting or exceeding the patient’s normal inspiratory demand, to increase oxygenation of the patient, reduce the work of breathing or perform Transnasal Humidified Rapid-Insufflation Ventilatory Exchange (THRIVE).
  • TRRIVE Transnasal Humidified Rapid-Insufflation Ventilatory Exchange
  • the device is configured to receive a flow of breathing gases from the first respiratory apparatus and to deliver the flow of breathing gases to the second respiratory apparatus.
  • the first respiratory apparatus may provide an inspiratory flow path through which a flow of breathing gases is directed into the patient’s airway during delivery of the first respiratory support and/or the second respiratory support to the patient.
  • the inlet of the device may be couplable with the first respiratory apparatus to enable fluid communication with the inspiratory flow path.
  • the inlet of the device may be configured to sealingly couple with the first respiratory apparatus.
  • the first respiratory apparatus may also provide an expiratory flow path through which a flow of expired gases from the patient is received during delivery of the first respiratory support to the patient.
  • the device may be couplable with the first respiratory apparatus such that the expiratory flow path is isolated from the fluid pathway of the device.
  • the first respiratory apparatus may further include an expiratory conduit for passage of the flow of expired gases received from the patient.
  • the inspiratory conduit and the expiratory conduit are coaxial.
  • the first respiratory apparatus may further include a mechanism for blocking the expiratory flow path upon coupling of the device with the first respiratory apparatus.
  • the mechanism may include a plunger that releasably seals the expiratory conduit from flow communication with the fluid pathway of the device, and wherein the device is configured to engage with the plunger to seal the expiratory flow conduit when coupled with the first respiratory apparatus.
  • the first respiratory apparatus further includes a filter in the inspiratory conduit and/or the expiratory conduit.
  • the second respiratory apparatus may include a second patient interface for providing a non-sealing interface with the patient’s airway.
  • the second patient interface may include a nasal cannula.
  • the system further includes a controller configured to operate in the following modes of operation: a first mode in which the first respiratory support is delivered to the patient by the first respiratory apparatus; and a second mode in which the second respiratory support is delivered to the patient by the first respiratory apparatus and the second respiratory apparatus being coupled together.
  • the system further includes at least one flow source operable by the controller to provide a flow of breathing gases at a pre-determined flow rate for delivery of the first respiratory support and/or the second respiratory support to the patient.
  • the first respiratory apparatus may include the at least one flow source operable by the controller for delivery of the first respiratory support and the second respiratory support to the patient.
  • the first respiratory support delivered to the patient may include the flow of breathing gases having one or more anaesthetic agents.
  • the pre-determined flow rate of the breathing gases may be less than or equal to about 15 L/min.
  • the first respiratory apparatus is configurable in gas flow communication with: a gas delivery apparatus receiving a supply of gas including NO, 02 and air, the gas delivery apparatus including: a gas mixing element for combining NO, 02 and/or air in a proportion required for operation of the system by the controller in the first mode and/or the second mode; and a gas outlet supplying gas from the gas delivery apparatus to the first respiratory apparatus.
  • the system is configured to measure a resistance to flow associated with the first respiratory apparatus and/or the second respiratory apparatus when in use with the patient.
  • the system may be configured to detect that the resistance to flow corresponds with one of: the first respiratory apparatus and/or the second respiratory apparatus in use with the patient; or coupling of the first respiratory apparatus and the second respiratory apparatus together via the device.
  • the controller may be configured to change the operating mode of the system based on the detected resistance to flow.
  • the controller may be configured to change the operating mode from the first mode to the second mode.
  • the first respiratory apparatus may include a first patient interface for providing a sealing interface with the patient’s airway.
  • the first patient interface may include a sealing mask or an endotracheal tube.
  • the first respiratory apparatus further includes an inspiratory conduit for passage of the flow of breathing gases to the patient’s airway during delivery of the first respiratory support and/or the second respiratory support, and wherein the inspiratory conduit is in fluid communication with the first patient interface.
  • the first respiratory apparatus may also provide an expiratory flow path through which a flow of expired gases from the patient is received during delivery of the first respiratory support to the patient.
  • the first respiratory apparatus further includes an expiratory conduit for passage of the flow of expired gases received from the patient.
  • the inspiratory conduit and the expiratory conduit are coaxial.
  • the second respiratory apparatus may include a second patient interface for providing a non-sealing interface with the patient’s airway.
  • the second patient interface may include a nasal cannula.
  • the kit further includes a connector configured to couple with the inspiratory conduit, the expiratory conduit and the first patient interface. [0061] In some embodiments, the kit further includes a coaxial tube including the inspiratory conduit and the expiratory conduit.
  • the first respiratory apparatus may further include a filter in the inspiratory conduit and/or the expiratory conduit.
  • the present disclosure provides a device for use in a system for providing respiratory support to a patient, the system including: a first respiratory apparatus for delivering a first respiratory support to the patient; and a second respiratory apparatus for delivering a second respiratory support to the patient; wherein the first respiratory apparatus comprises or is in fluid communication with a gases coupling comprising a first channel and at least a second channel; wherein the device is configured to couple the first respiratory apparatus and the second respiratory apparatus together in order to provide the second respiratory support to the patient; and wherein the device is configured to permit a flow of gases from the first channel to the second respiratory apparatus while preventing fluid communication between the at least second channel and the second respiratory apparatus.
  • the body portion is configured to couplingly receive at least a portion of the gases coupling.
  • the device is configured to couple only with the first channel.
  • the device comprises a body portion defining a through channel for flow of gases from the first channel to a conduit, wherein a proximal end portion of the conduit is receivable with in at least part of the through channel and to form a substantial seal therewith.
  • the through channel may be configured to receive the conduit concentrically.
  • the through channel may be configured to receive the conduit through an outlet end of the through channel.
  • the through channel is configured to receive, via an inlet end of the through channel, at least a portion of the gases coupling defining the first channel.
  • the through channel comprises an inlet opening configured to guide alignment of the through channel and the first channel during connection of the device and the gases coupling.
  • the conduit is substantially permanently affixed to the device.
  • the conduit may be affixed to the device by e.g. crimping or welding.
  • the first respiratory apparatus further includes an inspiratory conduit for passage of the flow of breathing gases into the patient’s airway during delivery of a first respiratory support and/or a second respiratory support, and wherein the inspiratory conduit is in fluid communication with the patient interface.
  • An inlet end of the device may be configured to sealingly couple with the inspiratory conduit.
  • the inlet end of the device may include at least one sealing surface for sealingly engaging with a wall of the inspiratory conduit.
  • the present disclosure provides a gases coupling comprising a first channel and a second channel and configured to connect with a device comprising a body portion having a through channel for receiving a flow of gases from the first channel of the gases coupling while substantially preventing gases flow between the through channel and at least the second channel of the gases coupling.
  • Figure 1 A is a schematic diagram showing components of an anaesthesia machine.
  • Figure 8 is sectional view showing a first respiratory apparatus including a dual lumen tube having an inspiratory conduit and an expiratory conduit with respective filters, where the inspiratory conduit is coupled with a sealing mask, and a device having an inlet is sealingly coupled with the inspiratory conduit, according to some embodiments of the disclosure.
  • Figure 9 is a sectional view showing a first respiratory apparatus including another dual lumen tube having an inspiratory conduit and an expiratory conduit with respective filters, where both conduits are coupled with the sealing mask, and a device having an inlet which is sealingly coupled with the inspiratory conduit, according to some embodiments of the disclosure.
  • Figure 10 is a sectional view showing a first respiratory apparatus including another dual lumen tube having an inspiratory conduit and an expiratory conduit with a central filter, where the inspiratory conduit is coupled with a sealing mask and the expiratory conduit is releasably sealed via a plunger mechanism upon coupling of a device, according to some embodiments of the disclosure.
  • Figure 13A is an isometric view of another example of a device for enabling/disabling flow channels;
  • Figure 13B is a sectional view of Figure 13A;
  • Figure 13C is an exploded view of the device in Figure 13A;
  • Figure 13D is a sectional view of Figure 13C.
  • Figure 15A is an isometric view of another example of a device for enabling/disabling flow channels which is another variation of the example in Figure 13A;
  • Figure 15B is a sectional view of Figure 15A;
  • Figure 15C is an exploded view of the device in Figure 15A;
  • Figure 15D is a sectional view of Figure 15C.
  • Figure 16A is an isometric view of another example of a device for enabling/disabling flow channels which is variation of the example in Figure 15A;
  • Figure 16B is a sectional view of Figure 16A;
  • Figure 16C is an exploded view of the device in Figure 16A;
  • Figure 16D is a sectional view of Figure 16C.
  • Figure 17A is an isometric view of another example of a device for enabling/disabling flow channels which is another variation of the example in Figure 12A;
  • Figure 17B is a side sectional view of the device in Figure 17A;
  • Figure 17C is an exploded view of the device in Figure 17A;
  • Figure 17D is a sectional view of Figure 17C.
  • Figure 18A is an isometric view of another example of a device for enabling/disabling flow channels which is another variation of the example in Figure 12A;
  • Figure 18B is a sectional view of the device in Figure 18A;
  • Figure 18C is an exploded view of the device in Figure 18A;
  • Figure 18D is a sectional view of Figure 18C.
  • Figure 19A is an isometric view of yet another example of a device for enabling/disabling flow channels;
  • Figure 19B is a side sectional view of the device in Figure 19A;
  • Figure 19C is an exploded view of the device in Figure 19A;
  • Figure 19D is a sectional view of Figure 19C;
  • Figure 19E shows an enlarged portion of the device in Figure 19D.
  • Figure 21 is a flow chart showing additional steps in the method of Figure 20 in relation to delivering respiratory support to the patient, according to some embodiments of the disclosure.
  • Figure 22 is a flow chart showing additional steps in the method of Figure 20 in relation to mode selection of the system by a controller, according to some embodiments of the disclosure.
  • Figure 23 is a schematic diagram of a kit for a system for providing respiratory support to a patient, according to some embodiments of the disclosure. Detailed
  • Figure 1 A is a schematic diagram showing components of an anaesthesia machine 10, which is configurable to receive a gas supply 1060 for delivering a respiratory support to a patient 300 through piped connections known in the art.
  • the gas supply 1060 may include one or more of an anaesthetic gas (e.g. nitric oxide (NO)), oxygen (O2) and air supply.
  • the air supply may be ambient air.
  • Flow meters may be incorporated into the gas supply 1060, or placed upstream of the anaesthesia machine 10, or incorporated into it, to control the flow of gases through the machine. Flow meters may be manually controlled and/or precision controlled by a controller of the anaesthesia machine.
  • a breathing circuit delivers gases to the patient 300 and returns expired gases to rebreathing components 140.
  • the breathing circuit may include corrugated tubing, valves and one or more patient interfaces for directing gases into the patient’s airway and removing expired gases.
  • the breathing circuit is simplified and denoted as including (but not limited to) inspiratory conduit 1 10 and first patient interface 120 which directs gas into the airway 310 of patient 300 and expiratory conduit 130 which collects expired gases.
  • first patient interface 120 may be a sealing interface such as a sealing mask or endotracheal tube and may be configured to direct expired gases from the patient 300 to an expiratory flow path 130 which returns the expired gases to rebreathing components 140 of the anaesthesia machine 10.
  • the inspiratory and expiratory conduits may be connected to the patient interface by a wye piece connector.
  • One or more vaporizers 150 convert volatile anaesthetics such as isoflurane and sevoflurane from liquid to vapour, and control introduction of these agents into the breathing circuit in accurately controlled concentration and dosages as required by the user, typically an anaesthetist clinician. Vaporizers 150 may be manually controlled and/or precision controlled by a controller of the respiratory apparatus. In some embodiments, vaporizers 150 feed into the rebreathing components 140.
  • a ventilation system which ventilates patient 300 during induction and after administration of anaesthetic agents to achieve ongoing anaesthesia.
  • a manual ventilation bag 142 may be used during induction (dot-dash lines inside rebreathing components 140) when volatiles are being delivered and prior to the patient being intubated.
  • the compliance of the ventilation bag 142 enables the patient to breathe in and out a fixed volume of gas through a sealing first patient interface 120 in the form of a face mask.
  • the ventilation mode changes from manual to mechanical, effectively isolating the manual ventilation bag 142 and associated pressure relief valve 143 from the rebreathing components 140 so that ventilation occurs via a mechanical system (dash lines inside rebreathing components 140).
  • Rebreathing components 140 provide a gas recirculation system in which exhaled gases from the patient are treated as they flow around the circuit and are then re-inhaled. This provides advantages by reusing oxygen and volatiles that are present in the expired gas flow from the patient, reducing costs as well as the presence of anaesthetic agents in the atmosphere.
  • Expired gases in the rebreathing components 140 are passed through CO2 absorber 141 which may include a canister containing soda lime (or another CO2 absorbing substance).
  • the soda lime (a mixture of NaOH & Ca(OH)2) acts as a CO2 scrubber to remove CO2 before gases in the rebreathing components 140 re-enter the inspiratory conduit 1 10.
  • gases from pressure relief valves 143, 146 are directed via an exhaust (not shown) to an external scavenger system 144 which filters and collects anaesthetic gases from the gas flow.
  • FIG. 1 B is a schematic diagram of a ventilator 20 which may be used in an ICU.
  • Ventilator 20 ventilates a patient with gases from gas supply 1060 and often with active humidification by humidifier 420 which is configured to heat and humidify gases delivered to the patient’s airway 310. While humidifier 420 is shown as part of a ventilator 20 in Fig 1 B, this need not be the case.
  • Gases from ventilator 20 may be humidified by a humidifier provided separately from the ventilator, humidifying gases from the ventilator before they reach first patient interface 120
  • a ventilator 20 can support the patient’s own breathing (breath triggering) or replaces it by delivering respiratory gases to a patient that are controlled to replicate ‘normal’ inhalation and exhalation breathing phases.
  • Mechanical ventilator 184 may include a flow modulator and/or blower, and controls the pressure, volume and breathing rate of breathing gases delivered through inspiratory conduit 110 which is delivered to the patient by a sealing first patient interface 120.
  • the sealing first patient interface may be invasive (e.g. endotracheal tube or laryngeal mask airway (LMA)) or non-invasive (e.g. sealing face mask). Exhaled gases leave the patient via the first patient interface and expiratory conduit 130 where they are treated e.g. by filter 182 and released to atmosphere.
  • expired gases exit through a vent or exhaust ports in the patient interface 120 or the expiratory conduit enables expired gases to exit to atmosphere without returning to the ventilator apparatus 20.
  • FIG. 2 is a schematic diagram of components of a high flow system 30 which is configurable to receive from a gas supply 1060 for delivering high flow respiratory support to a patient 300.
  • the gas supply 1060 may be one or more of an anaesthetic gas (e.g. nitric oxide (NO)), oxygen (02) or air supply, preferably an 02 and/or air supply.
  • the air supply may be ambient air.
  • High flow system 30 has a flow modulator 250 configured to generate gas flows that are passed through a humidifier 420 which is configured to heat and humidify gas flows generated by the flow modulator 250.
  • the flow modulator 250 may comprise a gas supply 1060 as described below.
  • the humidified high gas flow is delivered to the patient 300 by a second inspiratory conduit 210 and a second patient interface 220 (e.g. a non-sealing patient interface).
  • the second patient interface 220 may be a nasal cannula, which directs the high flow of breathing gases into the patient’s airway 310 through one or both nares.
  • An optional filter 230 may be provided between the inspiratory conduit 210 and the second patient interface 220 so that components of the breathing circuit upstream from the filter can be reused without risk of contamination by any inadvertently captured expired gases by the second patient interface 220.
  • the flow modulator 250 is configured to provide gases to the patient through high flow system 30.
  • the flow modulator comprises a gas generation means, for example a blower adapted to receive gases from the environment outside of the high flow system 30 and propel them through the high flow system 30.
  • the flow modulator 250 may comprise a source available from a hospital gas outlet or wall supply (e.g. oxygen or air), or one or more containers of compressed air and/or another gas and one or more valve arrangements adapted to control the rate at which gases leave the one or more containers.
  • the flow modulator 250 may comprise an oxygen concentrator.
  • high flow means, without limitation, any gas flow with a flow rate that is higher than usual/normal, such as higher than the normal inspiration flow rate of a healthy patient, or higher than some other threshold flow rate that is relevant to the context. It may be provided by a non-sealing respiratory system with substantial leak, for example happening at the entrance of the patient’s airways. It can also be provided with humidification to improve patient comfort, compliance and safety.
  • “High flow” can mean any gas flow with a flow rate higher than some other threshold flow rate that is relevant to the context - for example, where providing a gas flow to a patient at a flow rate to meet inspiratory demand, that flow rate might be deemed “high flow” as it is higher than a nominal flow rate that might have otherwise been provided. “High flow” is therefore context dependent, and what constitutes “high flow” depends on many factors such as the health state of the patient, type of procedure/therapy/support being provided, the nature of the patient (big, small, adult child) and the like. A person skilled in the art would appreciate, in a particular context what constitutes “high flow”. But, without limitation, some indicative values of high flow can be as follows.
  • high flow delivery of gases to a patient is at a flow rate of about 5 or 10 LPM to about 150 LPM, or about 10 LPM to about 120 LPM, or about 15 LPM to about 95 LPM, or about 20 LPM to about 100 LPM, or about 20 LPM to about 70 LPM, or about 25 LPM to about 85 LPM, or about 30 LPM to about 80 LPM, or about 35 LPM to about 75 LPM, or about 40 LPM to about 70 LPM, or about 45 LPM to about 65 LPM, or about 50 LPM to about 60 LPM.
  • a flow rate of gases supplied by embodiments of the systems disclosed may comprise, but is not limited to, flows of at least about 5, 10, 15, 20, 30, 40, 50, 60, 70, 80, 90, 100, 110, 120, 130, 140, 150 LPM, or more, and useful ranges may be selected to be any of these values (for example, about 20 LPM to about 100 LPM, about 15 LPM to about 70 LPM, about 20 LPM to about 70 LPM, about 40 LPM to about 70 LPM, about 40 LPM to about 80 LPM, about 50 LPM to about 80 LPM, about 60 LPM to about 80 LPM, about 70 LPM to about 100 LPM, about 70 LPM to about 80 LPM).
  • ‘high flow’ or ‘high flow respiratory support may refer to the delivery of gases to a patient at a flow rate of between about 5 or 10 LPM and about 100 LPM, or between about 15 LPM and about 95 LPM, or between about 20 LPM and about 100 LPM, or between about 25 LPM and about 85 LPM, or between about 30 LPM and about 80 LPM, or between about 35 LPM and about 75 LPM, or between about 40 LPM and about 70 LPM, or between about 45 LPM and about 65 LPM, or between about 50 LPM and about 60 LPM.
  • Gases delivered may comprise a percentage of oxygen. In some configurations, the percentage of oxygen in the gases delivered may be about 15% to about 100%, 20% to about 100%, or about 30% to about 100%, or about 40% to about 100%, or about 50% to about 100%, or about 60% to about 100%, or about 70% to about 100%, or about 80% to about 100%, or about 90% to about 100%, or about 100%, or 100%.
  • Flow rates for “High flow” for premature/infants/paediatrics can be different.
  • the flow rate can be set to about 0.4 LPM/kg to about 8 LPM/kg with a minimum of about 0.5 LPM and a maximum of about 25 LPM.
  • For patients under 2 kg maximum flow is set to 8 LPM.
  • High flow may be used as a means to promote gas exchange and/or respiratory support through the delivery of oxygen and/or other gases, and through the removal of CO2 from the patient’s airways.
  • High flow may be particularly useful prior to, during or after a medical procedure.
  • Further advantages of high gas flow can include that the high gas flow increases pressure in the airways of the patient, thereby providing patency support that opens airways, the trachea, lungs/alveolar and bronchioles. The opening of these structures enhances oxygenation, and to some extent assists in removal of CO2.
  • the increased pressure can also keep structures such as the larynx from blocking the view of the vocal chords during intubation.
  • the high gas flow can also prevent airways from drying out, mitigating mucociliary damage, and reducing risk of laryngospasms and risks associated with airway drying such as nose bleeding, aspiration (as a result of nose bleeding), and airway obstruction, swelling and bleeding.
  • subject and patient are used interchangeably.
  • a subject or patient may refer to a human or an animal subject or patient.
  • FIG. 3 illustrates components in a system 1000 for providing respiratory support to a patient 300 according to a preferred embodiment of the disclosure.
  • the system 1000 includes a first respiratory apparatus 100 for delivering a first respiratory support to the patient 300 and a second respiratory apparatus 200 for delivering a second respiratory support to the patient 300.
  • the first respiratory apparatus 100 and the second respiratory apparatus 200 may each be independently couplable with an airway 310 of the patient 300 (see also Figures 4a, 4b and 5).
  • the first respiratory apparatus 100 and the second respiratory apparatus 200 are couplable together via a device 500 in order to deliver the second respiratory support to the patient 300.
  • the components of the first respiratory apparatus 100 and the second respiratory apparatus 200 as described in embodiments of the disclosure having similar numbering to the components of the anaesthesia machine 10, ventilator 20 and high flow system 30 are intended to refer to the same components.
  • the description of those components in relation to the anaesthesia machine 10, ventilator 20 and high flow system 30 is considered to be applicable to the first respiratory apparatus 100 and the second respiratory apparatus 200, according to some embodiments of the disclosure.
  • the arrows in Figure 3 illustrate the direction of gas flow in the system 1000.
  • the device 500 may be configured to receive a flow of breathing gases from the first respiratory apparatus 100 and to deliver the flow of breathing gases to the second respiratory apparatus 200.
  • a first respiratory support including a flow of breathing gases may be provided to the patient 300.
  • the first respiratory apparatus 100 is an anaesthesia machine, having componentry similar to the anaesthesia machine 10 of Figure 1 A
  • a flow of breathing gases optionally including anaesthetic agents, may be provided to the patient 300.
  • the first respiratory support is only delivered to the patient 300 when the first respiratory apparatus 100 is uncoupled from the device 500.
  • the first respiratory apparatus 100 may include the flow source 1030.
  • the system 1000 may only include a single flow source 1030 which provides a flow of breathing gases suitable for delivery of the first respiratory support and the second respiratory support. That is, the single flow source 1030 may be included in the first respiratory apparatus 100 and may be configured to provide a flow of breathing gases suitable for delivery of the first respiratory support, such as anaesthetic ventilation, optionally with anaesthetic agents, and for delivery of the second respiratory support, such as high flow respiratory support.
  • the system 1000 may include multiple flow sources, for example located in one or more of the first respiratory apparatus 100, the device 500 and the second respiratory apparatus 200, for providing the flow of breathing gases suitable for delivery of the first respiratory support and/or the second respiratory support.
  • the first respiratory apparatus 100 and the second respiratory apparatus 200 are independently couplable with the device or adapter 500, they can each include independent flow sources, or alternatively, the second respiratory apparatus 200 may only include the breathing circuit solely for use by coupling with the adapter 500.
  • the first respiratory apparatus 100 may include one or more rebreathing components 140 coupled with the expiratory conduit 130 which enable expired gases to be returned to the inspiratory flow path (not shown in Figure 4A and 4B). That is, the first respiratory apparatus 100 may be a closed system including a return path that re-uses the expired gases from the patient 300, with similar components to the anaesthesia machine 10 as shown in Figure 1 A.
  • the device 500 includes an inlet 510 for coupling with the first respiratory apparatus 100, an outlet 520 for coupling with the second respiratory apparatus 200, and a fluid pathway 530 defined between the inlet 510 and the outlet 520 to enable fluid communication from the first respiratory apparatus 100 to the second respiratory apparatus 200 when coupled with the device 500 as shown in Figure 4B.
  • the flow of breathing gases provided by the first respiratory apparatus 100 pass through the inspiratory conduit 110 and mask 120 and into the device 500 through the inlet 510.
  • the breathing gases flow through the device 500 via the fluid pathway 530 and are delivered to the second respiratory apparatus 200 via the device outlet 520.
  • the second respiratory apparatus 200 includes at least an inspiratory conduit 210 and a second patient interface 220 for delivering the second respiratory support to the patient 300.
  • the second respiratory apparatus 200 need not include the humidifier 420 as shown in Figure 5 as the humidification function may be provided by the first respiratory apparatus 100 being couplable or including a humidifier 420 or the device 500 including a humidifier 420 (not shown).
  • the system 1000 may be operable in two modes of operation.
  • the first mode as illustrated in Figure 4A may include delivering the first respiratory support to the patient 300 using the first respiratory apparatus 100.
  • the second mode as illustrated in Figure 4B may include delivering the second respiratory support to the patient 300 using the first respiratory apparatus 100 and the second respiratory apparatus 200 being coupled together via the device 500.
  • the system 1000 may include a controller 1010 as shown in Figures 4A and 4B configured to operate the system 1000 in the first and second modes.
  • the controller 1010 may include a microcontroller for operating the system 1000.
  • the controller or microcontroller 1010 may form part of the first respiratory apparatus 100 or may be located externally although at least in electronic communication with the first respiratory apparatus 100.
  • the controller 1010 may also be in electronic communication with one or more sensors 1050 of the system 1000 as shown in Figures 4A and 4B, which will be described in more detail. [0184] The controller 1010 may also be configured to operate at least one flow source 1030 of the system 1000.
  • the flow source 1030 may form part of the first respiratory apparatus 100 as shown in Figures 4A and 4B.
  • the system 1000 may include only one flow source 1030 located in the first respiratory apparatus 100 for providing a flow of breathing gases in the first and/or second modes. However, this is not limiting and the system 1000 may include a flow source 1030 located externally but fluidly couplable with the first respiratory apparatus 100 for providing a flow of breathing gases. Additionally/alternati vely, one or more flow sources may be included in the first respiratory apparatus 100, the device 500 and the second respiratory apparatus 200.
  • the controller 1010 may be in electronic communication with the flow source 1030 to control operation of the system 1000.
  • the system 1000 may also be configured to detect that the resistance to flow corresponds with: (1 ) the first respiratory apparatus 100 in use with the patient 300, (2) the first respiratory apparatus 100 and the second respiratory apparatus 200 in use with the patient 300, and (3) coupling of the first respiratory apparatus 100 and the second respiratory apparatus 200 together via the device 500 (see also method flow chart in Figure 22).
  • the controller 1010 may be configured to change the operating mode (i.e., between the first mode and the second mode), based on the detected resistance to flow.
  • the device 500 may be couplable with the first respiratory apparatus such that the expiratory flow path is isolated from the fluid pathway 530 of the device 500.
  • the engagement of the device inlet 510 and the connector 600 may be such that the expiratory flow path is isolated from the fluid pathway 530 of the device 500.
  • walls 514 of the inlet channel 516 may prevent fluid communication of the fluid pathway 530 with the expiratory conduit 130 as shown in Figure 7. This effectively isolates the expiratory conduit 130 from fluid pathway 530 of the device 500, and thus the expiratory flow path.
  • the spring 136 deforms or compresses and the plunger 134 seals the expiratory conduit 130. This enables fluid communication with the inspiratory flow path to the exclusion of the expiratory flow path.
  • the force applied due to the member 540 is removed and the spring 136 returns to its original position either due to being resiliently deformable or through gravity, and the seal due to the plunger 134 is released thereby opening the expiratory conduit 130.
  • the plunger 134 and the member 540 may be integral with the device or adapter 500 such that the expiratory conduit 130 contacts or engages with the plunger 145/member 540 to compress the plunger 134 and seal the expiratory conduit 130.
  • Figures 12A to 19E illustrate embodiments of a device 500 for use in a system 1000 for providing respiratory support to a patient 300.
  • the device of these embodiments may be considered a variation of the device of Figure 8 which is couplable with a dual lumen conduit.
  • system 1000 comprises a first respiratory apparatus 100 which provides a first respiratory support and a second respiratory apparatus 200 which provides a second respiratory support.
  • the device 500 is configured to couple the first respiratory apparatus 100 and the second respiratory apparatus 200 together in order to deliver the second respiratory support to the patient 300 via a patient interface.
  • the second channel is configured to receive expiratory gases from the patient and the first respiratory apparatus 100 may determine and/or respond to characteristics of expired gases received via the second channel.
  • the first respiratory apparatus 100 may be operated with the second channel in fluid communication with the first channel such that first respiratory apparatus may determine and/or respond to characteristics of gases provided to the patient from the first channel.
  • the first respiratory apparatus 100 may comprise a mechanism to deploy an intervention when a gas parameter from the sensing flow path in the second channel exceeds a predetermined threshold.
  • An intervention may comprise, for example, presenting via a user interface of the first respiratory apparatus 100 a visible and/or audible alert that enables a user to check operation of the apparatus and patient safety.
  • the intervention may comprise a tactile alert, such as by vibration of a wearable device that is in operative communication with the first respiratory apparatus.
  • an intervention may comprise limiting gas pressure provided to the patient.
  • the second respiratory apparatus 200 may include one or more sensing and/or active components which provide functionality in response to pre-defined gas characteristics, as an alternative or additional to the sensing capability of the second channel of the first respiratory apparatus 100. Furthermore, the second respiratory apparatus 200 may also comprise a mechanism to automatically deploy an intervention when a gas parameter of gases in the second respiratory apparatus exceed a predetermined threshold.
  • An intervention may comprise, for example, presenting on a display of the second respiratory apparatus 200 a visible and/or audible alert that enables a user to check operation of the apparatus and patient safety. Alternatively or additionally the intervention may comprise a tactile alert, for example vibration of a wearable device that is in operative communication with the second respiratory apparatus 200.
  • an intervention may comprise limiting gas pressure provided to the patient.
  • One or both of the first respiratory support and the second respiratory support may comprise high flow respiratory support as disclosed elsewhere herein.
  • High flow respiratory support may comprise gas flows in a flow rate range of e.g. about 20 LPM to about 100 LPM.
  • Figures 12A to 19E show examples of a device 500 having a body portion 550 that is couplable with a gases coupling 111.
  • Body portion 550 has a through channel 530 for receiving a flow of gases from a first channel 113 of the gases coupling 111 while substantially preventing gases flow between the through channel and at least a second channel 115 of the gases coupling. While the examples provided show a gases coupling 111 having only a first channel 113 and a second channel 115, it is to be understood that the scope of the present disclosure contemplates a gases coupling having plurality of channels which are in addition to the first channel and the second channel and which are prevented from making fluid communication with the through channel when the device is coupled with the gases coupling.
  • the gases coupling 111 may comprise a medical gases outlet of the first respiratory apparatus.
  • the gases coupling 111 may comprise a medical gases connector which may be coupled with the medical gases outlet of the first respiratory apparatus 100 e.g. via a conduit or directly.
  • the sectional views of the first to seventh examples that follow best illustrate the first flow channel 113 and the second flow channel 115 of the gases coupling 111 which may be regarded as a dual lumen coupling.
  • the two channels of the coupling 111 may be concentric although that need not be the case.
  • the second channel 115 is an outer channel.
  • Through channel 530 is configured to sealingly couple with gases coupling 111 in a manner that permits fluid communication between the first channel 113 and the through channel.
  • the device 500 comprises at least one sealing mechanism 512 to substantially prevent leak of gases flowing between the first channel 113 and the through channel 530. By preventing leak of gases, the sealing mechanism substantially prevents those gases from entering the second channel 1 15. Thus, connection of the device 500 to the gases coupling 111 can achieve a desired effect of preventing fluid communication with the second channel 115. This may be desirable to disable one or more features associated with the second channel, such as sensing of gas characteristics as described above.
  • the gases coupling 111 comprises a tapered shaft 117 providing the first channel 113 which protrudes past the end of the portion defining the second channel 115.
  • the tapered portion may be smooth or textured, and/or comprise barbs as are common in medical gases couplings.
  • the first channel 113 is provided by a protruding shaft 117, upon attachment of the device 500 to the gases coupling 111 the shaft enters the through channel 530.
  • the device may operate with a gases coupling 111 in which the first channel 113 does not protrude past the portion that defines the second channel 115.
  • the full length of the shaft 117 need not be tapered, and that only the end portion may comprise a taper. In some examples, the shaft 117 need not be tapered at all.
  • the device 500 may be applied over the gases coupling 111 such that substantially all of the gases coupling 111 is received within the body portion 550.
  • the gases coupling 111 is a medical gases outlet of the first respiratory apparatus 100
  • the device 500 may be applied to the first respiratory apparatus 100 over the gases coupling 111 so that it sits in abutment with part of the gases coupling 111 or part of the first respiratory apparatus housing.
  • the engagement between the gases coupling 111 and the device 500 may be substantially rigid such that, for example, there is little axial movement of the device when in use.
  • part of the gases coupling 111 need not be received within the device 500, and the device need not sit in abutment with any part of the gases coupling or the housing of the first respiratory apparatus 100 when in use.
  • part of the gases coupling 111 may be situated outside the inlet end 510 of the device when in use.
  • part of the device 500 at the inlet end 510 may comprise a plug that is received within the second channel 115 of the gases coupling 111 to stabilise the device when in use.
  • FIG. 12A is an isometric view of the device 500 attached to the coupling 111 with a sectional view of the same in Figure 12B.
  • Figure 12C is an exploded view of the device in Figure 12B with a sectional view of the same in Figure 12D.
  • the at least one sealing mechanism 512 may be an annular gasket, such as an o-ring as shown in Figures 12B and 13B, in order to provide a seal between the through channel 530 and the external wall of the part of the gases coupling 111 defining the first channel 113. It is contemplated that only one of these annular gaskets may be required however providing more than one gasket can provide redundancy in the sealing mechanism.
  • FIG. 15A to 15D show a gasket in the form of a rod seal (or u-seal)
  • Figures 16A to 16D which show a new sealing mechanism comprising a rod seal portion with a flanged gasket portion
  • Figures 17A to 17D which show a sealing mechanism comprising an elongate gasket. Any manner of sealing mechanism between the through channel 530 and the first channel 113 is contemplated to minimise or reduce leakage of gases flowing between the first channel 113 and the through channel 530.
  • the device comprises at least one annular recess 532 for accommodating the sealing mechanism such as o-ring 512.
  • One, or more than one of the recesses 532 may receive a gasket or sealing mechanism 512.
  • a single o-ring gasket is shown in each recess 532 however it is to be understood that an adequate seal may be provided when only one or two of the annular recesses 532 contain a sealing mechanism 512. In such an example, any recess not cooperating with a sealing mechanism can be omitted from the design.
  • FIG. 12B and 12D illustrate the contact surfaces between the sealing mechanism 512, the gases coupling 111 and inner wall 531 defining part of the through channel 530.
  • the sealing mechanism 512 prevents gases flowing in the through channel 530 from entering the second channel 115 of the gases coupling 111 , thereby disabling any functionality associated with the second channel.
  • sleeve 560 may be configured to engage with a notch 116 on the gases coupling 111.
  • sleeve 560 may have a protrusion 566 which cooperates with the notch 116 to provide a further level of safety by reducing risk of accidental removal of the device from the gases coupling 111 when high flow rates and potentially high pressures are generated within the device 500 when in use.
  • the sleeve 560 may comprise or be manufactured from a material having characteristics that permit deformation while the sleeve is applied over the part of the gases coupling 111 that enables engagement with the notch 116 and recovery once the protrusion 566 is engaged with the notch.
  • Such materials may be softer than the material of the gases outlet which in many cases, may be Aluminium.
  • An example of one suitable material for the sleeve portion 560 is Polyoxymethylene although other materials with suitable characteristics are contemplated and within the scope of this disclosure.
  • the connector 570 and the body portion 550 may be couplable by one or more of a friction fit, threaded coupling, or bayonet coupling.
  • a friction fit coupling it may be desirable for the connector 570 to be manufactured from a material that has certain properties which facilitate connection and reconnection with the body portion.
  • the coefficient of friction between the connector 570 and the body portion 550, and between the sleeve 560 and the body portion 550 is greater than about 0.1 , such as greater than about 0.2 or about 0.4 to limit the risk of the one or more of the connector, the body portion and the coupling separating during use.
  • FIG. 14A is an isometric view of the device attached to the coupling 111 with a sectional view of the same in Figure 14B.
  • Figure 14C is an exploded view of the device in Figure 14A with a sectional view of the same in Figure 14D.
  • the third example is a variation of the second example of Figures 13A to 13D.
  • a modified coupling arrangement is provided between the body portion 550 and the connector 570 in which the inlet end 572 of the connector is received inside the outlet end 520 of the body portion 550.
  • the connector 570 may regarded as a plug and the body portion 550 into which it is inserted may be regarded as a socket.
  • the sealing mechanism 512 has been omitted from the body portion 550 and the conduit 110 has been omitted from the connector 570 in Figures 14A to 14D.
  • FIG. 15A is an isometric view of the device attached to the coupling 111 with a sectional view of the same in Figure 15B.
  • Figure 15C is an exploded view of the device in Figure 15A with a sectional view of the same in Figure 15D.
  • the fourth example is a further variation of the second example of Figures 13A to 13D.
  • the sealing mechanism 512 comprises a rod seal (or a u-seal) instead of an o-ring although it is to be understood that a rod seal may be provided in addition to one or more o-rings in some examples.
  • the feature of the rod-seal 512 is emphasised in the sectional views of Figures 15B and 15D by shading.
  • Advantages of a sealing mechanism comprising a rod seal may include more robust sealing when the device is subjected to axial movement or bending forces, and/or improved sealing against higher pressures when compared with an o-ring, and/or reduced risk of dislodgement from the body portion 550 compared with an o-ring.
  • FIG. 17A is an isometric view of the device attached to the coupling 111.
  • Figure 17B is a side sectional view of the device in Figure 17A.
  • Figure 17C is an exploded view of the device in Figure 17A with a sectional view of the same in Figure 17D.
  • the sixth example is a variation of the first example of Figures 12A to 12D.
  • the sealing mechanism comprises an elongate gasket 512 which seals along a length of the through channel 530.
  • the sealing surface may extend along substantially the entire length of the shaft 117, or it may extend along only part of it.
  • the body portion 550 is configured to couple only with the protruding shaft 117 defining part of the first channel 113 of the gases coupling 111 .
  • a gap may exist between the device 500 and part of the gases coupling 111 defining the second channel 115, best shown in Figure 17B. Since the second channel 115 is open to ambient room gas in this arrangement, it is unlikely to receive gas flows having characteristics that activate sensing features associated with the second channel as discussed above.
  • annular recess 118 is provided in the shaft 117 to accommodate the sealing mechanism 512 which prevents fluid communication between gases in the through channel 530 and the second channel 115 of the gases coupling 111.
  • the gasket 512 may be tensioned to seal onto the shaft 117 which may in some examples provide better retention of the o-ring when the body portion 550 is connected and disconnected with the gases coupling 111.
  • an arrangement wherein an annular recess 1 18 is provided in the shaft 117 to accommodate the sealing mechanism or gasket 512 may be incorporated into any one of the first to sixth examples, as an alternative or in addition to the sealing arrangement discussed in relation to those examples wherein an annular recess 532 is provided in the body portion 550.
  • the coupling between the device 500 and the gases coupling 111 may comprise a friction fit as shown.
  • the coefficient of friction between the gases coupling 111 and the body portion 550 is greater than about 0.1 , such as greater than about 0.2 or about 0.4 to limit the risk of the body portion and the gases coupling separating during use.
  • the body portion 550 comprises a material such as PEEK
  • the gases coupling 111 comprises a material such as Aluminium or stainless steel.
  • the coupling between the device 500 and the gases coupling 111 may comprise e.g. a threaded coupling or a bayonet coupling as would be appreciated by one of skill in the art.
  • the inlet opening may comprise an internal taper 522 configured to guide alignment of the protruding shaft 1 17 of the gases coupling 11 1 which comprises an external taper.
  • the proximal end 1 10a of the conduit 1 10 may include an internal taper that aligns with the internal taper 522 of the inlet opening of body portion 550.
  • the through channel 530 may further comprise a recess 534 proximal to the inlet end 510 to accommodate expansion of at least part of the conduit 1 10 when the protruding shaft 1 17 of the gases coupling 1 11 defining the first channel 1 13 is inserted into the conduit while inside the body portion 550.
  • the device 500 in Figures 19A to 19E may be repeatedly connected and disconnected with the gases coupling 11 1.
  • the large sealing area provided by the conduit 1 10 and the shaft 1 17 also assist with stabilising the connection which may or may not (as shown) sit in abutment with part of the gases coupling 1 1 1 or part of a housing of the first respiratory apparatus 100.
  • FIG. 20 is a flow chart showing steps in a method 1100 for providing respiratory support to a patient 300, according to some embodiments of the disclosure.
  • the method 1 100 includes in a first step 1 1 10 providing a system 1000 for providing respiratory support to the patient 300.
  • the system 1000 includes a first respiratory apparatus 100 for delivering a first respiratory support to the patient 300 in a first mode, and a second respiratory apparatus for delivering a second respiratory support to the patient 300 in a second mode.
  • the first respiratory apparatus 100 and the second respiratory apparatus 200 are independently couplable with an airway 310 of the patient 300.
  • the method 1 100 includes a second step 1 120 of coupling the first respiratory apparatus 100 with a device 500 to enable operation of the system in the second mode, and a third step 1 130 of delivering the second respiratory support to the patient 300 in the second mode.
  • the method 1100 may include the step of sealingly engaging the device inlet 510 with a wall 610 of the connector 600 coupled with the inspiratory conduit 110 as shown in Figure 7. In other embodiments, the method 1100 may include the step of sealingly engaging the device inlet 510 with a wall of the inspiratory conduit 110.
  • the method 1100 may include the step of coupling the first respiratory apparatus 100 with the device 500 such that the expiratory flow path is isolated from the fluid pathway 530 of the device 500.
  • the engagement of the device inlet 510 and the connector 600 may be such that the expiratory flow path is isolated from the fluid pathway 530 of the device 500.
  • walls 514 of the inlet channel 516 may prevent fluid communication with the expiratory conduit 130 as shown in Figure 7. This effectively isolates the expiratory conduit 130 from fluid pathway 530 of the device 500, and thus the expiratory flow path.
  • the first respiratory apparatus 100 includes a dual lumen tube 170, however in this case the inspiratory conduit 1 10 and the expiratory conduit 130 are in a side-by-side arrangement.
  • the method 1 100 may include the step of coupling the inlet 510 of the device 500 with the inspiratory conduit 1 10 of the dual lumen conduit 170 to enable fluid communication with the inspiratory flow path and fluid pathway 530 of the device 500.
  • the embodiment of Figure 10 includes the first respiratory apparatus 100 having a coaxial dual lumen tube 170, and also a mechanism for blocking the expiratory flow path upon coupling of the device 500.
  • the method 1 100 may include the step of coupling the device 500 with the first respiratory device 100 such that the mechanism is configured to block the expiratory flow path.
  • the mechanism may include a plunger 134 that releasably seals the expiratory conduit 130 from flow communication with the fluid pathway 530 of the adapter 500.
  • the method 1 100 may include the step of engaging the device 500 with the plunger 134 as shown in Figure 10 to seal the expiratory conduit 130.
  • the plunger 134 is located in a tube within the central filter 174 and may include a seal 134 to prevent filter bypass.
  • a spring 136 may be connected to the plunger 134 which is deformable, such as by a member 540 upon coupling of the device 500 with the first respiratory apparatus 100.
  • the method 1 100 may include the step of coupling the device 500 with the first respiratory apparatus 100 such that the spring 136 deforms or compresses and the plunger 134 seals the expiratory conduit 130.
  • the method 1 100 may also include the step of decoupling the device 500 from the first respiratory apparatus 100 such that the force applied due to the member 540 is removed, the spring 136 returns to its original position, and the seal due to the plunger 134 is released, thereby opening the expiratory conduit 130.
  • the device 500 may already be coupled with the second respiratory apparatus 200. Otherwise, the clinician or user may perform an optional step 1 122 of coupling the second respiratory apparatus 200 with the outlet 520 of the device 500.
  • the second respiratory apparatus 200 may include at least the inspiratory conduit 210 and second patient interface 220.
  • the inspiratory conduit 210 may be coupled with the device outlet 520 and in fluid communication with the second patient interface 220.
  • the method 1100 may then include an optional step 1124 of positioning the second patient interface 220 on the patient 300. In some embodiments, step 1124 may be performed prior to step 1122 such that the second patient interface 220 is already coupled with the patient’s airway 310 prior to coupling of the second respiratory apparatus 200 with the device 500.
  • Figure 22 is a flow chart showing additional steps in the method 1100 of Figure 20 in relation to mode selection by a controller 1010 of the system 1000, according to some embodiments of the disclosure.
  • the controller 1010 may be configured to operate a sensor 1050 of the system 1000 in order to perform step 1160 to measure a resistance to flow associated with the first respiratory apparatus and/or the second respiratory apparatus when in use with the patient.
  • the controller 1010 may operate the sensor 1050 as previously described in relation to Figures 4A and 4B.
  • the controller 1010 may also be configured to detect that the resistance to flow corresponds with at step 1162 the first respiratory apparatus 100 in use, at step 1164 the second respiratory apparatus 200 in use, and at step 1166 coupling of the first respiratory apparatus 100 and/or the second respiratory apparatus 200 together with the device 500.
  • the method 1100 includes the step 1140 of the controller 1010 operating the system 1000 in the first mode (e.g., as per Figure 4A). This may include the step 1114 of the controller 1010 operating the flow source 1030 to deliver a flow of breathing gases at a pre-determined flow rate (ideally of equal or less than 15 L/min), a pre-determined pressure, and/or a pre-determined volume, optionally with one or more anaesthetic agents. That is, the first respiratory support provided may be suitable for anaesthetic ventilation, with or without the use of anaesthetic agents.
  • the recess comprises a chamfer configured to guide alignment of the proximal end of the conduit in the through channel upon removal of the gases coupling from the device.
  • the through channel comprises a stepped portion configured to guide alignment of the conduit within the through channel after removal of the gases coupling from the device.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Pulmonology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Emergency Medicine (AREA)
  • Otolaryngology (AREA)
  • Bioinformatics & Cheminformatics (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

L'invention concerne un dispositif destiné à être utilisé dans un système pour fournir une assistance respiratoire à un patient. Le système inclut un premier appareil respiratoire pour administrer une première assistance respiratoire au patient, et un second appareil respiratoire pour administrer une seconde assistance respiratoire au patient. Le premier appareil respiratoire et le second appareil respiratoire peuvent chacun être couplés indépendamment à une voie aérienne du patient. Le dispositif est configuré pour coupler ensemble le premier appareil respiratoire et le second appareil respiratoire afin de délivrer la seconde assistance respiratoire au patient. L'invention concerne également un système et un procédé pour fournir une assistance respiratoire à un patient par l'utilisation d'un dispositif. L'invention concerne également un kit pour un système destiné à fournir une assistance respiratoire à un patient qui comprend le dispositif. L'invention concerne également un dispositif comprenant une partie corps pouvant être couplée à un raccord de gaz et définissant un canal traversant pour recevoir un flux de gaz depuis un premier canal du raccord de gaz tout en empêchant sensiblement un écoulement de gaz entre le canal traversant et au moins un second canal du raccord de gaz.
PCT/IB2023/063055 2022-12-29 2023-12-20 Dispositif pour système d'assistance respiratoire Ceased WO2024141878A1 (fr)

Applications Claiming Priority (2)

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US202263477667P 2022-12-29 2022-12-29
US63/477,667 2022-12-29

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Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2018083313A2 (fr) * 2016-11-04 2018-05-11 Viomedex Limited Dispositif d'administration de thérapie
US20200360637A1 (en) * 2015-03-31 2020-11-19 Fisher & Paykel Healthcare Limited User interface and system for supplying gases to an airway
WO2022137143A1 (fr) * 2020-12-23 2022-06-30 Fisher & Paykel Healthcare Limited Intégration et commutation de mode pour appareil respiratoire

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20200360637A1 (en) * 2015-03-31 2020-11-19 Fisher & Paykel Healthcare Limited User interface and system for supplying gases to an airway
WO2018083313A2 (fr) * 2016-11-04 2018-05-11 Viomedex Limited Dispositif d'administration de thérapie
WO2022137143A1 (fr) * 2020-12-23 2022-06-30 Fisher & Paykel Healthcare Limited Intégration et commutation de mode pour appareil respiratoire

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