US20060178592A1 - System and method for controlling the flow of exhaled breath during analysis - Google Patents

System and method for controlling the flow of exhaled breath during analysis Download PDF

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Publication number
US20060178592A1
US20060178592A1 US11/053,047 US5304705A US2006178592A1 US 20060178592 A1 US20060178592 A1 US 20060178592A1 US 5304705 A US5304705 A US 5304705A US 2006178592 A1 US2006178592 A1 US 2006178592A1
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United States
Prior art keywords
side stream
stream
exhaled breath
flow rate
pump
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.)
Abandoned
Application number
US11/053,047
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English (en)
Inventor
Kevin Nason
Jonathan Fay
Bryan Flaherty
Bhairavi Parikh
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.)
Niox AB
Apieron Biosystems Corp
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Apieron Biosystems Corp
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 Apieron Biosystems Corp filed Critical Apieron Biosystems Corp
Priority to US11/053,047 priority Critical patent/US20060178592A1/en
Priority to US11/348,943 priority patent/US8932230B2/en
Priority to AT06720372T priority patent/ATE518479T1/de
Priority to AU2006212828A priority patent/AU2006212828B2/en
Priority to JP2007554301A priority patent/JP2008530532A/ja
Priority to PCT/US2006/004150 priority patent/WO2006086323A1/en
Priority to CA 2596452 priority patent/CA2596452C/en
Priority to EP20060720372 priority patent/EP1850748B1/en
Assigned to APERON BIOSYSTEMS CORP. reassignment APERON BIOSYSTEMS CORP. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: FAY, JONATHAN, FLAHERTY, BRYAN, NASON, KEVIN, PARIKH, BHARAVI
Publication of US20060178592A1 publication Critical patent/US20060178592A1/en
Priority to NO20074073A priority patent/NO20074073L/no
Assigned to SILICON VALLEY BANK reassignment SILICON VALLEY BANK SECURITY AGREEMENT Assignors: APIERON, INC.
Assigned to AEROCRINE AB reassignment AEROCRINE AB ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: APIERON, INC., F/K/A APERON BIOSYSTEMS CORP., BY AND THROUGH ITS CHAPTER 7 TRUSTEE, JANINA M. ELDER
Assigned to APIERON, INC. F/K/A APERON BIOSYSTEMS CORP. reassignment APIERON, INC. F/K/A APERON BIOSYSTEMS CORP. RELEASE BY SECURED PARTY (SEE DOCUMENT FOR DETAILS). Assignors: SILICON VALLEY BANK
Priority to JP2012204513A priority patent/JP5491598B2/ja
Priority to US14/592,974 priority patent/US9919123B2/en
Priority to US15/899,582 priority patent/US20180243523A1/en
Abandoned legal-status Critical Current

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    • 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
    • A61M16/0841—Joints or connectors for sampling
    • A61M16/085—Gas sampling
    • 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
    • A61B5/0803—Recording apparatus specially adapted therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Measuring devices for evaluating the respiratory organs
    • A61B5/082—Evaluation by breath analysis, e.g. determination of the chemical composition of exhaled breath
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Measuring devices for evaluating the respiratory organs
    • A61B5/097—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
    • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
    • 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
    • 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
    • A61M16/06—Respiratory or anaesthetic masks
    • 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
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
    • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
    • G01N33/483—Physical analysis of biological material
    • G01N33/497—Physical analysis of biological material of gaseous biological material, e.g. breath
    • 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

Definitions

  • This invention relates to systems and methods for the analysis of exhaled breath.
  • nitric oxide (NO) concentration in exhaled breath can indicate a change in the level of inflammation in the airway of a patient with asthma, indicating an increase in the likelihood of an asthmatic attack.
  • Excessive carbon monoxide (CO) can indicate hemolytic jaundice, and high levels of hydrogen can indicate carbohydrate malabsorption.
  • a trace gas breath analyzer must make some provision for changes in the flow rate of breath from the patient.
  • the clinician or device simply provided feedback to the patient, indicating that the flow rate should be higher or lower.
  • An alternative system alters flow resistance in response to changes in flow rate, thereby attempting to maintain a constant flow rate. See U.S. Pat. No. 6,733,463 (“Moilanen System”).
  • the Moilanen system is somewhat complex and requires a relatively high number of components, since it depends on a relatively complicated feedback control for operation.
  • the present invention is a system and method for controlling the flow of a gaseous sample in an exhaled breath analysis system.
  • This invention can be used with systems that quantify a number of analytes, including but not limited to trace gas constituents such as NO.
  • the present invention has a number of different embodiments, but the common element is the use of a pump or pumps to affect and control the flow rate of the exhaled breath.
  • a pump or pumps to affect and control the flow rate of the exhaled breath.
  • Two specific embodiments are described, but the scope of the present patent should be determined by its claims, and should not be limited to these two particular embodiments.
  • FIG. 1 is a circuit diagram of a “single pump” embodiment of the present invention.
  • FIG. 2 is a circuit diagram of a “dual pump” embodiment of the present invention.
  • FIG. 3 is a circuit diagram of a “dual pump” embodiment in the side and stream and primary stream have separate exhaust points.
  • the present invention is a system and method for controlling the flow of a sample gas in an exhaled breath analysis system. Two embodiments are described in this patent: a single pump embodiment and a dual pump embodiment.
  • This invention may be used with sensors that have sensing elements that change in response to an analyte in a gaseous sample. Examples of sensing systems and devices that could be used with present invention are provided in U.S. patent applications Ser. Nos. 10/767,709, 10/334,625, and 10/659,408, the disclosures of which are incorporated by reference herein as if set out in full.
  • the breath analysis begins with the user exhaling into a blow tube 10 .
  • Other means of capturing a flow of exhaled breath can be used, such as a mask, etc. See FIG. 1 .
  • the breath would be captured from the mouth, and the device would typically allow an entire breath stream to flow through it, with a portion being captured for analysis.
  • the breath then travels to a pressure sensor 50 that monitors the pressure within the user's mouth.
  • the pressure sensor 50 should have an operating range appropriate to breath pressure requirements, and in one embodiment this range is 5 to 20 cm H 2 O.
  • the pressure sensor 50 is used as feedback for the patient, so that the patient maintains pressure in the desired range of 5 to 20 cm H 2 O.
  • this threshold is 5 cm H 2 O, which represents the pressure necessary to close the velum.
  • the upper end of the range, 20 cm H 2 O is selected because pressures above that threshold can cause discomfort in some patients.
  • the breath then travels through an optional first resistance means 60 .
  • the first resistance means 60 may be set to ensure a constant flow rate of 50 cc/sec from the patient.
  • the two resistance means cause the pressure in the patient's mouth to increase, thereby causing the velum to close.
  • the first resistance means 60 may be a fixed orifice, and in one embodiment this fixed orifice has a round aperture of approximately 0.11 cm diameter. Other conventional resistance means could be used instead of or in addition to the fixed orifice.
  • “resistance means” or “resistor” shall refer to a structure that creates resistance. This first resistance means 60 is not necessary, but may help to “tune” the system to the pump specifications.
  • the circuit splits into two streams: a primary stream 20 and a side stream 22 . See FIG. 1 .
  • the primary stream 20 contains a second resistance means 70 that produces a resistance R p .
  • this resistance means 70 may be able to produce a variable resistance, as described below.
  • the second resistance means 70 may be a motor-controlled needle valve, a solenoid controlled needle valve (as used in mass flow controllers), a manual needle valve, a fixed resistance orifice, or any other means of producing the desired resistance.
  • the side stream 22 contains a side stream valve 24 that controls whether this stream is open or closed.
  • the side stream valve 24 may be a solenoid valve or other appropriate open/close valve.
  • the side stream valve 24 opens, and while the side stream is open, the breath flow moves in parallel through the two streams.
  • the side stream 22 is open for the period of time between 7-10 seconds after exhalation into the blow tube begins. Thus, in this embodiment, for the first seven seconds, all the exhaled breath passes through the primary stream 22 , then through the pump 40 , and then is vented into the ambient atmosphere.
  • the side stream 22 contains a sensor 30 .
  • the sensor 30 creates its own resistance, Rs.
  • Other components, including a carbon dioxide scrubber, may also be placed in the side stream 22 .
  • the inlet and outlet of the sensor 30 may have check valves 32 , 34 to prevent leakage. See FIG. 1 . Thus, for the period of time when the breath is passing through the side stream, it is passing over the sensor 30 .
  • the primary stream 20 has a second resistance means 70 that varies its resistance to ensure a total flow rate of 50 cc/sec (or other desired rate) from the patient throughout the entire exhalation.
  • the resistance from the second resistance means 70 will be referred to as “Rp,” where the p stands for pump.
  • the resistance from the sensor (Rs) and the other components of the side stream 22 has a constant value, but in this embodiment, Rp has a variable value.
  • the values Rp 1 and Rp 2 are chosen so that the sum of the flow rates through the primary stream 20 and the side stream 22 is equal to the flow rate through the primary stream 20 when the side stream 22 is closed.
  • the resistance from the other components in the circuit such as Rs and the first resistance means 60 ) must be taken into account, and the pump voltage must also be considered.
  • the value of Rp may change as described below: Side Stream Valve Closed Side Stream Valve Open ⁇ P 32 cm H2O 32 cm H2O R1 0.4 cm H2O/mL/s 0.4 cm H2O/mL/s Rp1 0.24 cm H2O/mL/s Not applicable Rp2 Not applicable 0.29 cm H2O/mL/s Rs infinite 1.5 cm H2O/mL/s i 50 mL/s 50 mL/s
  • ⁇ P stands for the change in pressure across the pump
  • R 1 is the resistance from the first resistance means
  • Rp 1 and Rp 2 are the resistances from the second resistance means 70 when the side stream valve 24 is closed and open, respectively
  • Rs is the resistance from the sensor 30
  • i is the total flow through the system and from the patient's mouth.
  • Rp 1 and Rp 2 are chosen so that a constant flow rate of 50 ml/s is maintained throughout exhalation.
  • the second resistance means 70 may be a solenoid needle valve (as used in mass flow controllers), or a motor-controlled needle valve, or a pinch tube valve, or any other suitable resistor that can change its resistance.
  • the following table illustrates certain values in the system when the voltage of the pump is varied: Side Stream Valve Closed Side Stream Valve Open ⁇ P 34.3 cm H2O 32 cm H2O R1 0.4 cm H2O/mL/s 0.4 cm H2O/mL/s Rp 0.29 cm H2O/mL/s 0.29 cm H2O/mL/s Rs infinite 1.5 cm H2O/mL/s i 50 mL/s 50 mL/s 50 mL/s
  • ⁇ P stands for the change in pressure across the pump
  • R 1 is the resistance from the first resistance means
  • Rp 1 is the resistance from the second resistance means 70
  • Rs is the resistance from the sensor 30
  • i is the total flow through the system and from the patient's mouth.
  • both the primary stream 20 and the side stream 22 terminate at the same exhaust point.
  • the first pump 40 is downstream from the joinder of side stream 22 and the primary stream 20 , so that it can control the overall flow of the system, and not each stream individually. See FIG. 1 .
  • the pump 40 would be the model UNMP50 from KNF Neuberger, Inc., which has a free-flow capacity of 66.7 ml/s, a maximum vacuum of 400 mbar (407 cmH2O), and a maximum continuous pressure of 0.5 bar (510 cmH2O).
  • the first pump 40 which is placed downstream from the sensor 30 , draws breath at a constant flow rate.
  • the first pump 40 is resistant enough to inlet pressure to maintain a substantially constant flow rate despite changes in the subject's mouth pressure across the range of interest for this application, namely 5-20 cmH2O.
  • the pump model described above has the ability to maintain a flow rate within a wide pressure range that is appropriate for the chosen application.
  • the pump could be closed-loop controlled using the pressure sensor 50 as feedback.
  • the acceptable range would be between 5 cm H 2 O and 20 cm H 2 O.
  • the lower figure represents the minimum pressure required to close the velum, and the higher figure represents a pressure above which users may experience discomfort.
  • the present system avoids the possibility that output from the pump 40 would contaminate the sensor 30 .
  • both pumps would typically be placed downstream from the sensor 30 .
  • the pump or pumps it is also possible for the pump or pumps to be placed upstream from the sensor 30 .
  • the system has two pumps: a first pump 40 (as described above), and a second pump 80 . See FIG. 2 .
  • the second pump 80 may be advantageous because Rs may not be constant across systems but may vary from device to device. Also, Rs may be change as part of a design change to the sensor. With the second pump 80 , independent flow rates can be established for the primary stream 20 and the side stream 22 . As shown in FIG. 2 , the second pump 80 may be on the side stream 22 , downstream from the sensor 30 , although it could be placed in another location on the side stream 22 . It may be advantageous for the second pump to be placed downstream from sensor 30 so that materials from the pump do not interfere with the gas analysis.
  • the second pump 80 may be used to control flow to control flow into the side stream 22 .
  • side stream 22 and the primary stream 20 may not rejoin, but instead may vent through separate exhaust points. See FIG. 3 .
  • the present system uses a side stream 22 to direct breath flow through the sensor 30 .
  • a side stream 22 allows analysis of a relatively small breath sample, which in turn allows the creation of a smaller, more conveniently-sized sensing device.
  • use of a side stream 22 allows the division of a 50 ml/s exhaled breath stream into a 8.0 ml/s side stream 22 and a 42.0 ml/s primary stream 20 .
  • the smaller side stream 22 can be used to supply exhaled breath to a smaller sensor 30 than would be necessary if the entire breath stream were analyzed.
  • the side stream 22 is opened only after a period of time, such as 7 seconds after exhalation begins, to allow concentration of the exhaled analyte to stabilize. Breath will then flow into the side stream 22 and sensor 30 for a fixed period of time, such as 3 seconds.
  • the side stream 22 can be closed to allow the sensor enough time to interact with the exhaled breath.
  • the sensor 30 will “incubate” a sample of stopped exhaled breath for a period of time. In one embodiment, this “incubation” period or analysis period would be approximately 1 minute. After the incubation period, the sensor 30 would then be analyzed to determine concentration of the analyte.
  • the present invention allows the use of sensors that have response times that are too slow to analyze a moving stream of breath.
  • the present invention allows the sensor 30 to receive multiple cycles of exhaled breath before the flow is stopped. For instance, if the sensor 30 has a volume of 5.0 ml, and if the side stream 22 provides 8.0 ml/s of exhaled breath to the sensor for 3 seconds, then approximately 24.0 ml of breath will have passed through the sensor before the final 5.0 ml is trapped. This represents three complete cycles through the sensor before analysis begins, thereby completely flushing the sensor of whatever gas was inside the sensor before capturing the breath.
  • the “stopped flow” aspect of the present invention provides a number of advantages. By stopping the flow of breath through the sensor during analysis, the present invention creates a stable analytical environment, with no changes in pressure or flow during the entire analysis period. Changes in pressure or flow could create artifacts that interfere with analysis.
  • a stopped flow system can also accommodate slow sensors that detect trace gases. By stopping the flow, the system creates a stable testing environment that can be maintained for a much longer period than is possible for a flowing system. In one embodiment, the analysis period is approximately one minute, although much longer periods are also possible.
  • the present system can be used for analysis of many different analytes in exhaled breath, including trace gases like NO.
  • trace gas includes gases with concentrations below 1 part per million.
  • the system can be used in a conjunction with a sensor consisting of cytochrome-c in a sol-gel to measure NO.

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US11/053,047 2005-02-07 2005-02-07 System and method for controlling the flow of exhaled breath during analysis Abandoned US20060178592A1 (en)

Priority Applications (12)

Application Number Priority Date Filing Date Title
US11/053,047 US20060178592A1 (en) 2005-02-07 2005-02-07 System and method for controlling the flow of exhaled breath during analysis
CA 2596452 CA2596452C (en) 2005-02-07 2006-02-06 Controlling flow of exhaled breath during analysis
EP20060720372 EP1850748B1 (en) 2005-02-07 2006-02-06 Controlling flow of exhaled breath during analysis
AT06720372T ATE518479T1 (de) 2005-02-07 2006-02-06 Ausatemstromsteuerung während der analyse
AU2006212828A AU2006212828B2 (en) 2005-02-07 2006-02-06 Controlling flow of exhaled breath during analysis
JP2007554301A JP2008530532A (ja) 2005-02-07 2006-02-06 分析中の呼気の流れ制御
PCT/US2006/004150 WO2006086323A1 (en) 2005-02-07 2006-02-06 Controlling flow of exhaled breath during analysis
US11/348,943 US8932230B2 (en) 2005-02-07 2006-02-06 Controlling flow of exhaled breath during analysis
NO20074073A NO20074073L (no) 2005-02-07 2007-08-07 Styring av flyten ved utpust under en analyse
JP2012204513A JP5491598B2 (ja) 2005-02-07 2012-09-18 分析中の呼気の流れ制御
US14/592,974 US9919123B2 (en) 2005-02-07 2015-01-09 Controlling flow of exhaled breath during analysis
US15/899,582 US20180243523A1 (en) 2005-02-07 2018-02-20 Controlling flow of exhaled breath during analysis

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Application Number Priority Date Filing Date Title
US11/053,047 US20060178592A1 (en) 2005-02-07 2005-02-07 System and method for controlling the flow of exhaled breath during analysis

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US11/348,943 Continuation-In-Part US8932230B2 (en) 2005-02-07 2006-02-06 Controlling flow of exhaled breath during analysis

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US11/053,047 Abandoned US20060178592A1 (en) 2005-02-07 2005-02-07 System and method for controlling the flow of exhaled breath during analysis
US11/348,943 Active 2032-02-07 US8932230B2 (en) 2005-02-07 2006-02-06 Controlling flow of exhaled breath during analysis
US14/592,974 Active 2026-01-14 US9919123B2 (en) 2005-02-07 2015-01-09 Controlling flow of exhaled breath during analysis
US15/899,582 Abandoned US20180243523A1 (en) 2005-02-07 2018-02-20 Controlling flow of exhaled breath during analysis

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US11/348,943 Active 2032-02-07 US8932230B2 (en) 2005-02-07 2006-02-06 Controlling flow of exhaled breath during analysis
US14/592,974 Active 2026-01-14 US9919123B2 (en) 2005-02-07 2015-01-09 Controlling flow of exhaled breath during analysis
US15/899,582 Abandoned US20180243523A1 (en) 2005-02-07 2018-02-20 Controlling flow of exhaled breath during analysis

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US (4) US20060178592A1 (enExample)
EP (1) EP1850748B1 (enExample)
JP (2) JP2008530532A (enExample)
AT (1) ATE518479T1 (enExample)
AU (1) AU2006212828B2 (enExample)
CA (1) CA2596452C (enExample)
NO (1) NO20074073L (enExample)
WO (1) WO2006086323A1 (enExample)

Cited By (15)

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US20100031730A1 (en) * 2006-11-09 2010-02-11 UNIVERSITEIT TWENTE a University Device for measuring the ammonia content in a gas mixture
US20110077545A1 (en) * 2008-06-05 2011-03-31 Filt Lungen- Und Thoraxdiagnostik Gmbh Portable pneumotachograph for measuring components of an expiration volume
US20110208081A1 (en) * 2007-09-07 2011-08-25 Smith Trevor Apparatus and method
US20140228699A1 (en) * 2013-02-12 2014-08-14 Capnia, Inc. Sampling and storage registry device for breath gas analysis
US20140358019A1 (en) * 2011-12-22 2014-12-04 Aerocrine Ab Method and device for measuring a component in exhaled breath
US20160174875A1 (en) * 2013-08-08 2016-06-23 Siemens Aktiengesellschaft Assembly for the Extraction of Respiratory Gas Samples
US20180078719A1 (en) * 2014-04-11 2018-03-22 Fisher & Paykel Healthcare Limited Gas therapy system
IL256761A (en) * 2015-07-10 2018-04-30 Lantz Jean Sebastien Device for tracheobronchial-air stimulation
US10034621B2 (en) 2011-12-21 2018-07-31 Capnia, Inc. Collection and analysis of a volume of exhaled gas with compensation for the frequency of a breathing parameter
US20180243523A1 (en) * 2005-02-07 2018-08-30 Circassia Ab Controlling flow of exhaled breath during analysis
US20190046074A1 (en) * 2016-02-03 2019-02-14 Cognita Labs, LLC Forced oscillation technique based lung function testing
US10499819B2 (en) 2013-01-08 2019-12-10 Capnia, Inc. Breath selection for analysis
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US20180243523A1 (en) 2018-08-30

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