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WO2025188871A1 - Compliance de système respiratoire non invasif - Google Patents

Compliance de système respiratoire non invasif

Info

Publication number
WO2025188871A1
WO2025188871A1 PCT/US2025/018537 US2025018537W WO2025188871A1 WO 2025188871 A1 WO2025188871 A1 WO 2025188871A1 US 2025018537 W US2025018537 W US 2025018537W WO 2025188871 A1 WO2025188871 A1 WO 2025188871A1
Authority
WO
WIPO (PCT)
Prior art keywords
user
sensor data
breathing cycle
airflow
applied pressure
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.)
Pending
Application number
PCT/US2025/018537
Other languages
English (en)
Other versions
WO2025188871A8 (fr
Inventor
Girish Nair
Edward Castillo
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.)
University of Texas at Austin
Corewell Health William Beaumont University Hospital
Original Assignee
William Beaumont Hospital
University of Texas at Austin
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 William Beaumont Hospital, University of Texas at Austin filed Critical William Beaumont Hospital
Publication of WO2025188871A1 publication Critical patent/WO2025188871A1/fr
Publication of WO2025188871A8 publication Critical patent/WO2025188871A8/fr
Pending legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Classifications

    • 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
    • A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes operated by electrical means
    • A61M16/022—Control means therefor
    • A61M16/024—Control means therefor including calculation means, e.g. using a processor
    • 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
    • A61B5/085—Measuring impedance of respiratory organs or lung elasticity
    • 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
    • A61B5/0816—Measuring devices for examining respiratory frequency
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Measuring devices for evaluating the respiratory organs
    • A61B5/087—Measuring breath flow
    • A61B5/0871—Peak expiratory flowmeters
    • 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
    • A61B5/091—Measuring volume of inspired or expired gases, e.g. to determine lung capacity
    • 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
    • A61B5/097—Devices for facilitating collection of breath or for directing breath into or through measuring devices
    • 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
    • A61M16/0057—Pumps therefor
    • A61M16/0066—Blowers or centrifugal pumps
    • 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
    • A61M16/04—Tracheal tubes
    • A61M16/0488—Mouthpieces; Means for guiding, securing or introducing the tubes
    • A61M16/049—Mouthpieces
    • 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
    • A61M16/0833—T- or Y-type connectors, e.g. Y-piece
    • 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
    • A61M16/20—Valves specially adapted to medical respiratory devices
    • A61M16/208—Non-controlled one-way valves, e.g. exhalation, check, pop-off non-rebreathing valves
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes
    • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
    • A61M2016/0027—Accessories therefor, e.g. sensors, vibrators, negative pressure pressure meter
    • 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
    • A61M2205/3331—Pressure; Flow
    • 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
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3334—Measuring or controlling the flow rate
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/35—Communication
    • A61M2205/3546—Range
    • A61M2205/3553—Range remote, e.g. between patient's home and doctor's office
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/35—Communication
    • A61M2205/3576—Communication with non implanted data transmission devices, e.g. using external transmitter or receiver
    • A61M2205/3592—Communication with non implanted data transmission devices, e.g. using external transmitter or receiver using telemetric means, e.g. radio or optical transmission
    • 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
    • A61M2205/50—General characteristics of the apparatus with microprocessors or computers
    • A61M2205/502—User interfaces, e.g. screens or keyboards
    • 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
    • A61M2205/50—General characteristics of the apparatus with microprocessors or computers
    • A61M2205/52—General characteristics of the apparatus with microprocessors or computers with memories providing a history of measured variating parameters of apparatus or patient
    • 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
    • A61M2205/82—Internal energy supply devices
    • A61M2205/8206—Internal energy supply devices battery-operated
    • 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
    • A61M2230/46—Resistance or compliance of the lungs

Definitions

  • Abnormal LC can be used as an early indicator of lung disease and regular measurement can track disease progression.
  • traditional methods of LC measurement are prohibitively invasive for use as a routine monitoring tool.
  • typical LC measurement techniques require invasive monitoring, such as intra-pleural measurement or esophageal manometry, and are not routinely calculated unless the patient is mechanically ventilated.
  • SUMMARY [0004] One aspect of the disclosure provides a computer-implemented method that when executed on data processing hardware causes the data processing hardware to perform operations. The operations include, during a measuring period, generating first sensor data representative of a breathing cycle of a user under a first applied pressure and second sensor data representative of the breathing cycle of the user under a second applied pressure.
  • the operations include determining a change in lung volume of the user during the breathing cycle under the first applied pressure as compared to the breathing cycle under the second applied pressure. Based on the change in lung volume, the first applied pressure, and the second applied pressure, the operations include determining a lung compliance (LC) value for the user.
  • determining the change in lung volume includes 1 59382415.1 Attorney Docket No: 5475-563152 determining a first lung volume of the user during the breathing cycle under the first applied pressure based on the first sensor data and determining a second lung volume of the user during the breathing cycle under the second applied pressure based on the second sensor data.
  • the first lung volume and the second lung volume are both determined for a common phase of the breathing cycle of the user.
  • the common phase of the breathing cycle of the user is one of an end-inspiration phase and an end- expiration phase.
  • a first flow rate function is derived from the first sensor data and a second flow rate function is derived from the second sensor data.
  • the first lung volume is determined based on an inflection point along the first flow rate function.
  • the second lung volume is determined based on an inflection point along the second flow rate function.
  • the first sensor data and the second sensor data both include measured airflow volume rates during the breathing cycle.
  • the first sensor data and the second sensor data both include measured airflow pressure during the breathing cycle.
  • the user interfaces with a measurement device to create a closed system that includes the measurement device and the respiratory system of the user.
  • the measurement device generates the first sensor data and the second sensor data as the user executes the breathing cycle.
  • the measurement device generates the first applied pressure and the second applied pressure.
  • the measurement device includes an airflow source, an air conduit that receives pressurized airflow from the airflow source, a mouthpiece configured to interface with the user to provide fluid communication between the air conduit and the user to deliver pressurized airflow to the user and to receive exhaled airflow from the user, and at least one sensor in fluid communication with the air conduit and configured to generate the first sensor data and the second sensor data.
  • processing of the first sensor data and the second sensor data is performed at electronic circuitry of the measurement device.
  • the operations further include transmitting the LC value to at least one of a mobile device of the user and a remote sever associated with a healthcare provider.
  • Another aspect of the disclosure provides a system.
  • the system includes memory hardware storing instructions that, when executed on data processing hardware in communication with the memory hardware, cause the data processing hardware to perform 2 59382415.1 Attorney Docket No: 5475-563152 operations.
  • the operations include during a measuring period, generating first sensor data representative of a breathing cycle of a user under a first applied pressure and second sensor data representative of the breathing cycle of the user under a second applied pressure. Based on the first sensor data and the second sensor data, the operations include determining a change in lung volume of the user during the breathing cycle under the first applied pressure as compared to the breathing cycle under the second applied pressure. Based on the change in lung volume, the first applied pressure, and the second applied pressure, the operations include determining a lung compliance (LC) value for the user.
  • LC lung compliance
  • determining the change in lung volume includes determining a first lung volume of the user during the breathing cycle under the first applied pressure based on the first sensor data and determining a second lung volume of the user during the breathing cycle under the second applied pressure based on the second sensor data.
  • the first lung volume and the second lung volume are both determined for a common phase of the breathing cycle of the user.
  • the common phase of the breathing cycle of the user is one of an end-inspiration phase and an end-expiration phase.
  • a first flow rate function is derived from the first sensor data and a second flow rate function is derived from the second sensor data.
  • the first lung volume is determined based on an inflection point along the first flow rate function.
  • the second lung volume is determined based on an inflection point along the second flow rate function.
  • the first sensor data and the second sensor data both include measured airflow volume rates during the breathing cycle.
  • the first sensor data and the second sensor data both include measured airflow pressure during the breathing cycle.
  • the user interfaces with a measurement device to create a closed system that includes the measurement device and the respiratory system of the user.
  • the measurement device generates the first sensor data and the second sensor data as the user executes the breathing cycle.
  • the measurement device generates the first applied pressure and the second applied pressure.
  • the measurement device includes an airflow source, an air conduit that receives pressurized airflow from the airflow source, a mouthpiece configured to interface with the user to provide fluid communication between the air conduit and the user to deliver pressurized airflow to the user and to receive exhaled airflow from the user, and at least one sensor in fluid 3 59382415.1 Attorney Docket No: 5475-563152 communication with the air conduit and configured to generate the first sensor data and the second sensor data.
  • processing of the first sensor data and the second sensor data is performed at electronic circuitry of the measurement device.
  • the operations further include transmitting the LC value to at least one of a mobile device of the user and a remote sever associated with a healthcare provider.
  • the measurement device includes an airflow source configured to generate pressurized airflow.
  • An air conduit is configured to receive the pressurized airflow from the airflow source.
  • a mouthpiece is configured to interface with a user to provide fluid communication between the air conduit and the user to deliver pressurized airflow to the user and to receive exhaled airflow from the user.
  • At least one sensor is in fluid communication with the air conduit and configured to generate sensor data representative of a breathing cycle of the user.
  • the measurement device includes memory hardware storing instructions that, when executed on data processing hardware in communication with the memory hardware, cause the data processing hardware to perform operations.
  • the operations include generating via the at least one sensor first sensor data representative of the breathing cycle of the user under a first applied pressure generated by the airflow source and second sensor data representative of the breathing cycle of the user under a second applied pressure generated by the airflow source. Based on the first sensor data and the second sensor data, the operations include determining a change in lung volume of the user during the breathing cycle under the first applied pressure as compared to the breathing cycle under the second applied pressure. Based on the change in lung volume, the first applied pressure, and the second applied pressure, the operations include determining a lung compliance (LC) value for the user.
  • This aspect may include one or more of the following optional features.
  • determining the change in lung volume includes determining a first lung volume of the user during the breathing cycle under the first applied pressure based on the first sensor data and determining a second lung volume of the user during the breathing cycle under the second applied pressure based on the second sensor data.
  • a first flow rate function is derived from the first sensor data and a second flow rate function is derived from the second sensor data. The first lung volume is determined based on an inflection point along the first flow rate function and the second lung volume is determined based on an inflection point along the second flow rate function.
  • the at least one sensor includes a first sensor configured to measure an airflow pressure at a first end of the air conduit and a second sensor configured to measure an airflow pressure at a second end of the air conduit.
  • the second end of the air conduit is closer to the mouthpiece than the first end of the air conduit and the first end of the air conduit is closer to the airflow source than the second end of the air conduit.
  • operation of the airflow source is regulated based on the airflow pressure measured by the first sensor.
  • the measurement device is configured to transmit the LC value to at least one of a mobile device of the user and a remote server associated with a healthcare provider.
  • FIG. 1 is a schematic view of a measurement device that generates sensor data representative of respiratory function of a user to determine lung compliance (LC) for the user.
  • FIG. 2A is a schematic view of another measurement device that generates sensor data representative of respiratory function of the user to determine LC for the user.
  • FIG. 2B is a plan view of the measurement device of FIG. 2A.
  • FIG. 3A is a schematic showing stages of a breathing cycle of the user.
  • FIG. 3A is a schematic showing stages of a breathing cycle of the user.
  • FIG. 3B is a graph of lung volumes during the breathing cycle of the user.
  • FIG. 4A is a graph showing example lung volumes of the user during breathing cycles under different applied pressures.
  • FIG. 4B is a graph showing example lung volumes of the user at maximum inhalation and maximum exhalation under different applied pressures.
  • FIG. 5A is a graph showing example LC values determined for users with different health conditions.
  • FIG. 5B is a graph showing example LC values determined for users with a health condition initially and after six months.
  • FIG. 6 is a graph showing example pressure measurements used to regulate a pressurized airflow source of the measurement device.
  • FIG.7 is a schematic view of a user device in communication with the measurement device and operable to display a graphical user interface based on data collected by the measurement device.
  • FIG. 8 is a flow diagram of an example method of determining LC values for the user.
  • FIG. 9 is a flow diagram of another example method of determining LC values for the user.
  • FIG.10 is a schematic view of an example computing device operable to implement the measurement device and/or user device.
  • Like reference symbols in the various drawings indicate like elements.
  • Lung compliance (LC) for a patient may be calculated as the ratio of the change in lung volume to the change in trans-pulmonary pressure, where the trans-pulmonary pressure is the relative pressure between the alveoli compared to the intra-pleural space.
  • LC Lung compliance
  • static and dynamic There are two types of LC, static and dynamic.
  • Static LC is the change in volume for a specific applied pressure, such as when there is no flow in the airway at peak inspiration or end expiration.
  • Dynamic LC is the compliance of the lung at any given time during tidal breathing (i.e., normal respiration with a relatively constant rate and inspiratory/expiratory or tidal volumes).
  • Normal static LC may be 328 ⁇ 102 mL/cmH2O and normal dynamic LC may be 285 ⁇ 105 mL/cmH2O.
  • Abnormal LC can be used as an early indicator of lung disease and measurements can track disease progression.
  • methods for measuring LC require physically invasive procedures and/or use of advanced medical imaging. These methods can be impractical for routine monitoring and thus result in infrequent and unreliable tracking of disease progression.
  • a system and method for non-invasive measurement of static and dynamic LC that does not rely on medical imaging allows for easier and more frequent implementation, leading to more routine monitoring of disease progression and quicker treatment response, especially in patients with diseases affecting respiratory function such as chronic obstructive pulmonary disease (COPD), interstitial lung disease (ILD), radiation-induced pneumonitis (RP), asthma, pneumonia, muscular dystrophy, polio, myasthenia gravis, Guillain-Barre syndrome and pulmonary fibrosis.
  • COPD chronic obstructive pulmonary disease
  • ILD interstitial lung disease
  • RP radiation-induced pneumonitis
  • asthma asthma
  • pneumonia muscular dystrophy
  • polio myasthenia gravis
  • Guillain-Barre syndrome Guillain-Barre syndrome
  • pulmonary fibrosis pulmonary fibrosis
  • an LC measurement system 100 includes a measurement device 102 that generates sensor data representative of breathing cycles of a user 10 during a breathing exercise or measuring period and a control module 104 that processes the sensor data to determine LC of the user 10.
  • the measurement device 102 may generate sensor data representative of airflow rate and tidal volume at various air source pressures during discrete respiratory phases (e.g., 10 phases of a breathing cycle) or continuously throughout the measuring period.
  • the measurement device 102 provides a closed system that applies specific positive pressures to inhaled airflows while regulating tidal airflow to measure changes in lung volume throughout phases of inhalation and exhalation by the user 10 and to determine LC of the user 10.
  • the measurement device 102 includes an air chamber 106 that holds a volume of air and a breathing interface 108, such as a mouthpiece, nasal mask or full face mask, configured to deliver and receive an airflow between the user 10 and the air chamber 106.
  • the mouthpiece 108 may be configured to form a sealed connection between the measurement device 102 and the airway of the user 10, such as via a compression or cushioned seal against the user’s face and around their mouth and/or nose, to create a closed loop between the user’s respiratory system and the measurement device 102.
  • a pressure adapter 110 connected to the chamber 106 pressurizes the volume of air and the airflow is routed between the chamber 106 and the mouthpiece 108 via an airflow regulator 112 to control and/or measure the rate of airflow provided to and received from the user 10.
  • a spirometer 114 is in communication with the mouthpiece 108 and the air chamber 106 for measuring a volume of airflow or airflow rate delivered to the user 10 during inhalation and/or a volume of airflow or airflow rate received from the user 10 during exhalation.
  • the measurement device 102 such as during a breathing exercise or measuring period
  • the user 10 inhales airflow from the air chamber 106 through the mouthpiece 108 and exhales airflow into the air chamber 106 through the mouthpiece 108.
  • Pressure of the airflow is adjusted via operation of the pressure adapter 110 while the airflow regulator 112 controls and/or measures the rate of airflow between the measurement device 102 and the user 10.
  • the spirometer 114 generates sensor data representative of the volume of airflow or airflow rate exiting the chamber 106 (and thus inhaled by the user 10) and entering the chamber 106 (and thus exhaled by the user 10) across breathing cycles of the user 10 during the measuring period.
  • the measurement device 102 is in communication with the control 7 59382415.1 Attorney Docket No: 5475-563152 module 104 during operation, such as for transmitting instructions to adjust the pressure and/or rate of inhaled airflow and for transmitting sensor data captured during the measuring period.
  • the control module 104 includes data processing hardware 1010 (FIG. 10) and memory hardware 1020 (FIG.10) in communication with the data processing hardware 1010.
  • the memory hardware 1020 stores instructions that, when executed on the data processing hardware 1010, cause the data processing hardware 1010 to perform operations.
  • the control module 104 stores instructions for determining LC of the user 10 based on sensor data from the measurement device 102.
  • the control module 104 is in communication with the measurement device 102 (e.g., wireless communication and/or wired communication) for receiving the sensor data from the measurement device 102.
  • the control module 104 may be accommodated by electronic circuitry and associated software at the measurement device 102 and/or the control module 104 may be accommodated by a remote device 12 in communication with the measurement device 102.
  • the remote device 12 may comprise a mobile device of the user 10, such as a cell phone, laptop, tablet or smart watch, or a remote server, such as a remote server associated with a healthcare provider (e.g., the user’s doctor or a health system associated with the user’s doctor).
  • a healthcare provider e.g., the user’s doctor or a health system associated with the user’s doctor.
  • the measurement device 102 may pair with the mobile device 12 of the user 10 for in-home use.
  • the measurement device may be configured to generate controlled levels of positive pressure for determining airflow rates and lung volumes of the user based on pressure differential of airflow between the user and the pressurized air source.
  • another measurement device 202 is configured to generate sensor data representative of breathing cycles of the user 10 during breathing exercises and communicate the sensor data to the control module 104 (e.g., at the user device 12). As discussed further below, the measurement device 202 may generate sensor data representative of pressure within the measurement device 202 between the user 10 and the pressurized air source.
  • the measurement device 102 includes a conduit or tube 206 that extends between a breathing interface 208 and a pressure adapter 210.
  • the pressure adapter 210 includes an airflow source 212, such as an electric fan blower, that is configured to direct incoming or inhaled airflow 14 toward the user 10 at a known or controlled pressure.
  • the pressure adapter 210 further includes an outlet 214, such as a passive vent or active vent with another electric fan blower, configured to receive outgoing or exhaled airflow 16 from the user 10.
  • the airflow source 212 may be configured to provide the inhaled airflow 14 at controlled pressures between 8 59382415.1 Attorney Docket No: 5475-563152 about 0 cmH2O and 15 cmH2O, such as between about 5 cmH2O and 15 cmH2O.
  • the pressure adapter 210 includes or is in communication with an onboard control module 216, such as an ARDUINO TM Uno board or integrated printed circuit board (PCB), for controlling the airflow source 212 and/or communicating with the user device 12 (e.g., to transfer captured sensor data to the user device 12 and receive instructions from the user device 12).
  • an onboard control module 216 such as an ARDUINO TM Uno board or integrated printed circuit board (PCB)
  • PCB printed circuit board
  • Operation of the airflow source 212 may be controlled based on pressure of the inhaled airflow 14 measured at the first pressure sensor 218 (e.g., a first pressure measurement taken at the outlet of the fan blower 212).
  • the control module 216 may control the fan speed of the airflow source 212 through pulse-width modulation and thus regulate the positive pressure generated based on the pressure measured between the pressure adapter 210 and the user 10 at the first pressure sensor 218.
  • the second pressure sensor 220 may measure the pressure of the airway of the user 10 (e.g., a second pressure measurement taken at or near the mouthpiece 208). During inspiration, the pressure measured at the first pressure sensor 218 is greater than the pressure measured at the second pressure sensor 220.
  • the conduit 206 is a shared or common limb for the inhaled airflow 14 and the exhaled airflow 16.
  • a first mechanically regulated valve 222 is disposed between the airflow source 212 and the conduit 206 and a second mechanically regulated valve 224 is disposed between the outlet 214 and the conduit 206 to ensure that the pressure readings at the first pressure sensor 218 and the second pressure sensor 220 are not affected by airflow going in opposite directions.
  • the airflow source 212 During use of the measurement device 202 (such as during a breathing exercise or measuring period), the airflow source 212 generates positive pressure and the user 10 inhales the airflow 14 through the mouthpiece 208 and exhales the airflow 16 to the outlet 214 through the mouthpiece 208.
  • the measurement device 202 may be powered and controlled via wired connection to the user device 12 (or the measurement device 202 may be independently powered, such as via battery power, and controlled via wireless connection to the user device 12). Pressure of the inhaled airflow 14 may be adjusted via an input device (e.g., a knob or button) at the measurement device 202 or via control signals from the user device 12 and/or control module 104.
  • an input device e.g., a knob or button
  • a display device such as an LCD display device, at the measurement 9 59382415.1 Attorney Docket No: 5475-563152 device 202 or user device 12 may show the applied pressure during the breathing exercise.
  • the first pressure sensor 218 and the second pressure sensor 220 generate sensor data representative respectively of the applied pressure of the inhaled airflow 14 and the pressure of the exhaled airflow 16. This sensor data may be transferred to the user device 12 and/or the control module 104 for LC determination and recording.
  • Physiological characteristics between changes in lung volume and distending pressure are non-linear. During inhalation, as the volume of the lung increases, the elastic elements within the lung approach maximum distension.
  • volume changes are different in each respiratory phase while volume plateaus at maximum inhalation and exhalation. Adjusting the distending pressure affects volume changes over the respiratory cycle differently in patients with lung abnormalities.
  • Performing repeated measurements with the measurement device 102, 202 and deriving differential equations via processing at the control module 104 of sensor data captured by the measurement device 102, 202 controls for factors that affect distension beyond the distending pressure, such as resistance of the airway and chest wall compliance.
  • the system 100 may process data captured by the measurement device 102, 202 during a measuring period where the user 10 performs one or more breathing cycles and the measurement device 102, 202 applies specific positive pressures to the inhaled airflow and regulates tidal airflow to determine changes in lung volume V based on changes in transpulmonary pressure p throughout phases of the breathing cycle (e.g., 10 phases of inhalation and exhalation) to determine the respiratory system compliance.
  • the spirometer 114 may generate sensor data representative of the rate of airflow delivered to the user 10 during inhalation phases of the breathing cycle and representative of rate of airflow received from the user 10 during exhalation phases of the breathing cycle.
  • sensor data is generated representative of the pressure of airflow inhaled and exhaled by the user 10 and 10 59382415.1
  • P1 sensor 218, P2 represents pressure measured at the resistance to flow through the measurement device 202.
  • the resistance to flow is determined based on the viscosity of air ⁇ (e.g., 16.64 x 10 -6 m 2 /s), the length l of the conduit 206, and the radius r of the conduit 206.
  • ⁇ e.g. 16.64 x 10 -6 m 2 /s
  • the length l of the conduit 206 e.g. 16.64 x 10 -6 m 2 /s
  • r radius of the conduit 206.
  • the pressure p would be defined with respect to time t according to instructions from the control module 104, which may be a predetermined set of instructions or based on a user input.
  • the patient-specific constant V 0 represents the lung volume V at exhale during free breathing without positive pressure.
  • the function B(t, p(t)) indicates the lung volume contribution induced by breathing and R(p(t)) represents the lung volume induced by positive pressure.
  • V(t 1 ) and V(t 2 ) may be derived from the flow rate Q using equation (2) above.
  • Static LC may be determined based on changes in lung volume V between different applied pressures p at the same state or phase of the breathing cycle (i.e., which may be the same time t in different measurement periods or portions of the measuring period).
  • Dynamic LC may be 11 59382415.1 Attorney Docket No: 5475-563152 determined based on changes in lung volume V at different times t under the same applied pressure p (i.e., which may be different times t in the same measuring period).
  • Numerically calculating lung compliance LC(t) requires recovering volume V(t) from the airflow rate data acquired with the measurement device 102, 202.
  • tn is used to determine the airflow rate function Q(t).
  • lung volumes V(t) correspond to pressures p(t) applied by the measurement device 102, 202 during the measuring period (such as multiple pressures each applied for one or more breathing cycles) and LC curves may be generated based on the determined volumes V(t) and known pressures p(t).
  • the measurement device 102, 202 may generate the applied pressures p(t1), p(t2) during the measuring period, and the measurement device 102, 202 may gradually increase the applied pressure p between p(t1) and p(t2) such that data may be gathered for incremental applied pressures p(t) throughout the breathing cycle. This may result in a smoother airflow rate function Q(t) and more accurate LC determination.
  • the airway pressure Pairway (e.g., the pressure P2 measured at the second pressure sensor 220) is equivalent to an alveolar pressure P alv of the user 10 only during the resting phase of the breathing cycle 300 (i.e., at end-inspiration or end-expiration) (FIG. 3A).
  • the complete volume curve 302 may be generated during tidal breathing using equation (6), such that inflection points on the curve 302 may represent lung volume V at end-inspiration or end-expiration (FIG.3B). For example, the inflection points may be determined based on where the first derivative of the volume curve 302 is equal to zero.
  • the volumes V at end-inspiration and end-expiration may be used as V(t 1 ) and V(t 2 ) in equation (4).
  • the LC may be determined in a time period with tidal respiration by dividing the changes in volume V at end-inhalation and the applied pressures p by the number of breath cycles 300 during the time period.
  • continuous positive pressure p is controlled (e.g., between 5 cmH2O and 15 cmH2O) and pressure p is measured via the measurement device 102, 202 to determine the airway pressure P airway of the user 10.
  • the static LC of the user 10 may be determined using the changes in volume V and pressure p between end-inspiration and end-expiration in one breathing cycle 300. Because the measurement device 102, 202 in combination with the respiratory system of the user 10 is a closed system, the measurements of changes in lung volume V may be accomplished via monitoring the changes in airflow within the system. The system 100 may determine static LC for the user 10 with an error rate less than five percent. [0057] As shown in the graph 400 of FIG.
  • alveolar volume V(t) changes during tidal breathing (from inhalation (Phase 80 in FIG. 4A) to exhalation (Phase 50 in FIG. 4A)) in response to changes in pressure p(t) based on distensibility LC(t).
  • FIG.4A shows determined volumes V(t) under pressures p(t) of 5 cmH2O and 10 cmH2O, where more dramatic differences in volume V(t) between pressures p(t) are experienced at Phase 40 (prior to max inhalation) and Phase 60 (after max inhalation) than at Phase 50 (max inhalation) and Phase 80 (max exhalation).
  • a longitudinal correlation of decreased lung volume V(t) and LC(t) may indicate progression of disease. That is, the measurement device 102, 202 may be used to monitor static and dynamic LC for the user 10 over time.
  • the measurement device 102, 202 may prompt the user 10 to participate in measuring periods at regular or irregular intervals, such as monthly, weekly, daily, or multiple times per day.
  • Use of the measurement device 102, 202 by the user 10 to determine LC may require a breathing exercise of five minutes or less, one minute or less, and may require the user 10 to perform as little as one complete breathing cycle.
  • LC measurements generated under similar conditions e.g., pressures p and phase of the breathing cycle
  • the system 100 may determine disease progression or improvement.
  • the graph 500 represents LC measurements determined for patients with different health conditions using the numerical methods described herein at end- inhalation under pressures of 5 cmH2O and 10 cmH2O.
  • the graph 500 includes a first box plot 500a representative of LC measurements for patients with COPD, a second box plot 500b representative of LC measurements for patients with ILD, and a third box plot 500c representative of LC measurements for patients with lung nodules.
  • the patients with lung nodules may be considered healthy as lung nodules do not affect LC.
  • the median LC of the third box plot 500c is greater than the median LC of the first box plot 500a in most cases and almost two times the median LC of the second box plot 500b.
  • the graph 502 represents LC measurements determined for patients with idiopathic pulmonary fibrosis (IPF) (a type of ILD that causes irreversible lung scarring) using the numerical methods described herein at end-inhalation under pressures of 5 cmH2O and 10 cmH2O.
  • the graph 502 includes a first box plot 502a representative of initial LC measurements and a second box plot 502b representative of LC measurements taken after six months. As shown, a significant difference was observed between the first box plot 502a and the second box plot 502b (a one-sided p-value of 0.0058), demonstrating that the numerical methods described herein may feasibly monitor the IPF progression.
  • the control module 104 may store instructions for performing a measuring period.
  • the control module 104 may operate the measurement device 102, 202 (e.g., 14 59382415.1 Attorney Docket No: 5475-563152 the pressure adapter 110 or the airflow source 212) to apply a first pressure for a period of time.
  • the period of time may be a preset period of time or based on a number of breathing cycles the user 10 performs under the first pressure.
  • Sensor data captured by the measurement device 102, 202 may be processed to determine flow rate and/or lung volumes for the user 10 during at least one breathing cycle under the first pressure.
  • the control module 104 may operate the measurement device 102, 202 to apply a different second pressure and capture sensor data representative of at least one breathing cycle under the second pressure.
  • the control module 104 may cycle through a plurality of different pressures to capture sensor data representative of a suitable number of breathing cycles at the various pressures.
  • the captured flow rate and/or air pressure data may be further processed to determine static and/or dynamic LC values for the user 10.
  • the measurement device 102, 202 may be configured to self-regulate the applied pressure p during the measuring period, such as via proportional-integral-derivative (PID) control, to accurately control the positive pressure p applied to the user 10 and ensure reliable LC measurements.
  • FIG. 6 includes a graph 600 where the line 602 represents pressure measurements at the first pressure sensor 218 of the measurement device 202 (and thus an input that controls operation of the airflow source 212) during a measuring period at 10 cmH2O.
  • a first portion 602a of the line 602 represents use where the mouthpiece 208 is blocked (causing a peak in the line 602) and then completely released (causing the trough in the line 602).
  • the airflow source 212 quickly regulated the applied pressure p toward 10 cmH 2 O.
  • a second portion 602b of the line 602 represents use where the user 10 is breathing normally and the airflow source 212 maintains the pressure p at or near 10 cmH2O.
  • the system 100 may be configured to communicate LC data to the user 10 and/or a healthcare professional associated with the user 10.
  • the measurement device 102, 202 may be associated with a software application or mobile app configured to operate on the mobile device 12 of the user 10 (FIG. 7).
  • the mobile device 12 is operable to display a graphical user interface (GUI) 700 to illustrate data collected by the measurement device 102, 202.
  • GUI graphical user interface
  • the GUI 700 may include a measuring period display 702 representative of airflow data captured during a single measuring period (e.g., a most recent measuring period).
  • the measuring period display 702 may show the measured volume and/or airflow under different pressures at corresponding respiratory phases over the 15 59382415.1 Attorney Docket No: 5475-563152 measuring period.
  • the measuring period display 702 may show a determined LC (static and/or dynamic LC) for the user 10 during the measuring period.
  • the GUI 700 may include a historical measuring period display 704 representative of airflow data captured during one or more previous measuring periods (e.g., as stored in data storage 1020).
  • the GUI 700 may include a comparison display 706 representative of improvements or losses in LC and/or lung volume capacity between measuring periods.
  • the GUI 700 may further include an input or interface 708 for communicating information related to recent measuring period data, historical measuring period data and/or a comparison of data from the mobile device 12.
  • interaction of the user 10 with the communication interface 708 may cause the mobile device 12 to transmit data to a healthcare professional associated with the user 12.
  • the mobile application may cause transmission of the data to the healthcare professional based on a condition, such as based on determination of a threshold loss in LC or lung volume capacity.
  • the system may measure airflow rate and/or air pressure differentials during inspiration and expiration. Using advanced computational methods, the system directly assesses distensibility of the lung and characterizes lung stiffness.
  • the system can be monitored daily at home, such as using a mobile device interface, to relay valuable information to a healthcare team regarding disease progression and treatment response, especially in patients with pulmonary fibrosis.
  • the system and measurement device for determining lung compliance may utilize characteristics of the systems, calculations, and methods described in U.S. Pub. No. US-2021- 0345906, which is hereby incorporated herein by reference in its entirety.
  • FIG. 8 provides a flowchart of an exemplary arrangement of operations for a method 800 of determining LC values for the user 10.
  • the data processing hardware 1010 of the control module may execute instructions stored on the memory storage 1020 to cause the data processing hardware 1010 to perform the operations for the method 800.
  • the method 800 includes, during a measuring period, generating first sensor data representative of a breathing cycle of the user 10 under a first applied pressure and second sensor data representative of the breathing cycle of the user 10 under a second applied pressure.
  • a change in lung volume of the user 10 during the breathing cycle under the first applied 16 59382415.1 Attorney Docket No: 5475-563152 pressure as compared to the breathing cycle under the second applied pressure may be determined based on the first sensor data and the second sensor data.
  • the method 800 may include determining a first lung volume of the user 10 during the breathing cycle under the first applied pressure based on the first sensor data.
  • the method 800 may include determining a second lung volume of the user 10 during the breathing cycle under the second applied pressure based on the second sensor data.
  • the change in lung volume may be determined based on the determined first lung volume and the determined second lung volume.
  • the method 800 includes determining a LC value for the user 10 based on the change in lung volume, the first applied pressure, and the second applied pressure.
  • FIG. 9 provides a flowchart of another exemplary arrangement of operations for a method 900 of determining LC values for the user 10.
  • the data processing hardware 1010 of the control module may execute instructions stored on the memory storage 1020 to cause the data processing hardware 1010 to perform the operations for the method 900.
  • the method 900 includes, during a measuring period, generating sensor data representative of the pressure P 1 at the first pressure sensor 218 and the pressure P 2 at the second pressure sensor 220 of the measurement device 202.
  • the method 900 includes determining the flow rate function Q(t) for the breathing cycle of the user 10 during the measuring period.
  • the method 900 includes generating a volume curve based on the flow rate function Q(t).
  • the method 900 includes determining a change in volume ⁇ V for the breathing cycle of the user 10 during the measuring period based on the flow rate curve.
  • FIG. 10 is schematic view of an example computing device 1000 that may be used to implement the systems and methods described in this document.
  • the computing device 1000 is intended to represent various forms of digital computers, such as laptops, desktops, workstations, personal digital assistants, servers, blade servers, mainframes, and other appropriate computers.
  • the components shown here, their connections and relationships, and their functions, are meant to be exemplary only, and are not meant to limit implementations of the inventions described and/or claimed in this document.
  • the computing device 1000 includes a processor 1010, memory 1020, a storage device 1030, a high-speed interface/controller 1040 connecting to the memory 1020 and high- 17 59382415.1 Attorney Docket No: 5475-563152 speed expansion ports 1050, and a low speed interface/controller 1060 connecting to a low speed bus 1070 and a storage device 1030.
  • Each of the components 1010, 1020, 1030, 1040, 1050, and 1060 are interconnected using various busses, and may be mounted on a common motherboard or in other manners as appropriate.
  • the processor 1010 can process instructions for execution within the computing device 1000, including instructions stored in the memory 1020 or on the storage device 1030 to display graphical information for a graphical user interface (GUI) on an external input/output device, such as display 1080 coupled to high speed interface 1040.
  • GUI graphical user interface
  • multiple processors and/or multiple buses may be used, as appropriate, along with multiple memories and types of memory.
  • multiple computing devices 1000 may be connected, with each device providing portions of the necessary operations (e.g., as a server bank, a group of blade servers, or a multi-processor system).
  • the memory 1020 stores information non-transitorily within the computing device 1000.
  • the memory 1020 may be a computer-readable medium, a volatile memory unit(s), or non-volatile memory unit(s).
  • the non-transitory memory 1020 may be physical devices used to store programs (e.g., sequences of instructions) or data (e.g., program state information) on a temporary or permanent basis for use by the computing device 1000.
  • Examples of non- volatile memory include, but are not limited to, flash memory and read-only memory (ROM) / programmable read-only memory (PROM) / erasable programmable read-only memory (EPROM) / electronically erasable programmable read-only memory (EEPROM) (e.g., typically used for firmware, such as boot programs).
  • the storage device 1030 is capable of providing mass storage for the computing device 1000.
  • the storage device 1030 is a computer-readable medium.
  • the storage device 1030 may be a floppy disk device, a hard disk device, an optical disk device, or a tape device, a flash memory or other similar solid state memory device, or an array of devices, including devices in a storage area network or other configurations.
  • a computer program product is tangibly embodied in an information carrier.
  • the computer program product contains instructions that, when executed, perform one or more methods, such as those described above. 18 59382415.1 Attorney Docket No: 5475-563152
  • the information carrier is a computer- or machine-readable medium, such as the memory 1020, the storage device 1030, or memory on processor 1010.
  • the high speed controller 1040 manages bandwidth-intensive operations for the computing device 1000, while the low speed controller 1060 manages lower bandwidth- intensive operations. Such allocation of duties is exemplary only.
  • the high-speed controller 1040 is coupled to the memory 1020, the display 1080 (e.g., through a graphics processor or accelerator), and to the high-speed expansion ports 1050, which may accept various expansion cards (not shown).
  • the low-speed controller 1060 is coupled to the storage device 1030 and a low-speed expansion port 1090.
  • the low-speed expansion port 1090 which may include various communication ports (e.g., USB, Bluetooth, Ethernet, wireless Ethernet), may be coupled to one or more input/output devices, such as a keyboard, a pointing device, a scanner, or a networking device such as a switch or router, e.g., through a network adapter.
  • the computing device 1000 may be implemented in a number of different forms, as shown in the figure. For example, it may be implemented as a standard server 1000a or multiple times in a group of such servers 1000a, as a laptop computer 1000b, or as part of a rack server system 1000c.
  • Various implementations of the systems and techniques described herein can be realized in digital electronic and/or optical circuitry, integrated circuitry, specially designed ASICs (application specific integrated circuits), computer hardware, firmware, software, and/or combinations thereof.
  • ASICs application specific integrated circuits
  • These various implementations can include implementation in one or more computer programs that are executable and/or interpretable on a programmable system including at least one programmable processor, which may be special or general purpose, coupled to receive data and instructions from, and to transmit data and instructions to, a storage system, at least one input device, and at least one output device.
  • machine-readable signal refers to any signal used to provide machine instructions and/or data to a programmable processor.
  • the processes and logic flows described in this specification can be performed by one or more programmable processors executing one or more computer programs to perform functions by operating on input data and generating output.
  • the processes and logic flows can also be performed by special purpose logic circuitry, e.g., an FPGA (field programmable gate array) or an ASIC (application specific integrated circuit).
  • processors suitable for the execution of a computer program include, by way of example, both general and special purpose microprocessors, and any one or more processors of any kind of digital computer.
  • a processor will receive instructions and data from a read only memory or a random access memory or both.
  • the essential elements of a computer are a processor for performing instructions and one or more memory devices for storing instructions and data.
  • a computer will also include, or be operatively coupled to receive data from or transfer data to, or both, one or more mass storage devices for storing data, e.g., magnetic, magneto optical disks, or optical disks.
  • mass storage devices for storing data, e.g., magnetic, magneto optical disks, or optical disks.
  • Computer readable media suitable for storing computer program instructions and data include all forms of non- volatile memory, media and memory devices, including by way of example semiconductor memory devices, e.g., EPROM, EEPROM, and flash memory devices; magnetic disks, e.g., internal hard disks or removable disks; magneto optical disks; and CD ROM and DVD-ROM disks.
  • processors and the memory can be supplemented by, or incorporated in, special purpose logic circuitry.
  • a display device e.g., a CRT (cathode ray tube), LCD (liquid crystal display) monitor, or touch screen for displaying information to the user and optionally a keyboard and a pointing device, e.g., a mouse or a trackball, by which the user can provide input to the computer.
  • a display device e.g., a CRT (cathode ray tube), LCD (liquid crystal display) monitor, or touch screen for displaying information to the user and optionally a keyboard and a pointing device, e.g., a mouse or a trackball, by which the user can provide input to the computer.
  • a keyboard and a pointing device e.g., a mouse or a trackball
  • a computer can interact with a user by sending documents to and receiving documents from a device that is used by the user; for example, by sending web pages to a web browser on a user's client device in response to requests received from the web browser.
  • first, second, third, etc. may be used herein to describe various elements, components, regions, layers and/or sections. These elements, components, regions, layers and/or sections should not be limited by these terms. These terms may be only used to distinguish one element, component, region, layer or section from another region, layer or section. Terms such as “first,” “second,” and other numerical terms do not imply a sequence or order unless clearly indicated by the context. Thus, a first element, component, region, layer or section discussed below could be termed a second element, component, region, layer or section without departing from the teachings of the example configurations. [0082] A number of implementations have been described. Nevertheless, it will be understood that various modifications may be made without departing from the spirit and scope of the disclosure. Accordingly, other implementations are within the scope of the following claims. 21 59382415.1

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Abstract

Un procédé selon l'invention consiste, pendant une période de mesure, à générer des premières données de capteur représentatives d'un cycle respiratoire d'un utilisateur sous une première pression appliquée et des secondes données de capteur représentatives du cycle respiratoire de l'utilisateur sous une seconde pression appliquée. Sur la base des premières données de capteur, le procédé consiste à déterminer un premier volume pulmonaire de l'utilisateur pendant le cycle respiratoire sous la première pression appliquée. Sur la base des secondes données de capteur, le procédé consiste à déterminer un second volume pulmonaire de l'utilisateur pendant le cycle respiratoire sous la seconde pression appliquée. Sur la base du premier volume pulmonaire déterminé, de la première pression appliquée, du second volume pulmonaire déterminé et de la seconde pression appliquée, le procédé consiste à déterminer une valeur de compliance pulmonaire (LC) pour l'utilisateur.
PCT/US2025/018537 2024-03-06 2025-03-05 Compliance de système respiratoire non invasif Pending WO2025188871A1 (fr)

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Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4031885A (en) * 1975-10-15 1977-06-28 Puritan-Bennett Corporation Method and apparatus for determining patient lung pressure, compliance and resistance
US20100286548A1 (en) * 2007-07-26 2010-11-11 Avi Lazar System and Methods for the Measurement of Lung Volumes
US20160089509A1 (en) * 2013-05-08 2016-03-31 Koninklijke Philips N.V. Pressure support system for breath stacking therapy
US20220362505A1 (en) * 2013-10-30 2022-11-17 ResMed Pty Ltd Control for pressure of a patient interface
US20230083767A1 (en) * 2016-11-02 2023-03-16 Fisher & Paykel Healthcare Limited Method of driving a form of respiratory therapy

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4031885A (en) * 1975-10-15 1977-06-28 Puritan-Bennett Corporation Method and apparatus for determining patient lung pressure, compliance and resistance
US20100286548A1 (en) * 2007-07-26 2010-11-11 Avi Lazar System and Methods for the Measurement of Lung Volumes
US20160089509A1 (en) * 2013-05-08 2016-03-31 Koninklijke Philips N.V. Pressure support system for breath stacking therapy
US20220362505A1 (en) * 2013-10-30 2022-11-17 ResMed Pty Ltd Control for pressure of a patient interface
US20230083767A1 (en) * 2016-11-02 2023-03-16 Fisher & Paykel Healthcare Limited Method of driving a form of respiratory therapy

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