WO1996037147A1 - Dispositif de controle du debit expiratoire maximal - Google Patents

Dispositif de controle du debit expiratoire maximal Download PDF

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Publication number
WO1996037147A1
WO1996037147A1 PCT/GB1996/001251 GB9601251W WO9637147A1 WO 1996037147 A1 WO1996037147 A1 WO 1996037147A1 GB 9601251 W GB9601251 W GB 9601251W WO 9637147 A1 WO9637147 A1 WO 9637147A1
Authority
WO
WIPO (PCT)
Prior art keywords
outlet
monitoring device
shells
shell
vent
Prior art date
Application number
PCT/GB1996/001251
Other languages
English (en)
Inventor
Pieter Rousseau Fourie
Original Assignee
Harwill Industries (Pty.) Limited
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 Harwill Industries (Pty.) Limited filed Critical Harwill Industries (Pty.) Limited
Priority to AU58266/96A priority Critical patent/AU697792B2/en
Priority to EP96919898A priority patent/EP0830080A1/fr
Priority to BR9608900-8A priority patent/BR9608900A/pt
Priority to JP8535507A priority patent/JPH11505741A/ja
Publication of WO1996037147A1 publication Critical patent/WO1996037147A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/41—Detecting, measuring or recording for evaluating the immune or lymphatic systems
    • A61B5/411—Detecting or monitoring allergy or intolerance reactions to an allergenic agent or substance
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
    • A61B5/087—Measuring breath flow
    • A61B5/0871—Peak expiratory flowmeters

Definitions

  • This invention relates to a flow monitoring device, notably a peak expiratory flow monitoring device.
  • Peak expiratory flow rate is a measure of lung function of a person which can be easily and accurately determined by several devices. Home monitoring of PEFR has gained acceptance as a means of monitoring the states of asthma. It can be monitored reliably by co-operative subjects without the help of technically skilled personnel and, since its original definition in 1959 (Wright BM, McKerrow CB: Maximum forced expiratory flow rate as a measure of ventilatory capacity - British Medicine, 2, 1041 - 1959) it has found wide application.
  • a number of portable PEFR measuring devices are presently available commercially. They vary in portability, graduation and cost and work, essentially, on two different principles. The first involves the displacement of a spring loaded piston, the total displacement of which depends on both the pressure arising from the generated flow and the area of a vent located behind the piston. The second class of devices utilises whistles or reeds that are normally threshold-activated in order to register PEFR.
  • the first class of devices includes well known devices such as the Wright Peak Flow Meter and the Vitalograph Pulmonary Monitor.
  • the devices of the second class include a peak flow whistle, a first prototype of which is described in Annals of Allergy, 47, August 1981 - 95 to 98 - Chiaramonte LT, Prabhu SL: Peak flow whistle: preliminary report - and a latter form of which is described in Annals of Allergy, 52 March 1984, 155 to 158 - Chiaramonte LT, Goldstein S, Rockwell W: Report of a newly redesigned peak flow whistle.
  • This device also forms the subject of USA Patent No.
  • the De Bono whistle consists of a plastics tube with a kettle-type whistle at one end.
  • a disposable cardboard mouthpiece fits over the other end and a leak hole is formed down one side of the tube, the size of the hole is adjusted by moving the mouthpiece.
  • a critical level of airflow through the whistle is needed to produce sound and the disposable mouthpiece is progressively withdrawn to increase the size of the leak hole thereby to require a progressively higher rate of airflow in order to produce a whistle.
  • This device suffers from the disadvantage that the whistle loses its intensity and sharpness at low flow rates. In addition, the flow of exhaust air and any expiratory wheezes produced by the subject tend to swamp or mimic the whistle.
  • the Edwards peak flow whistle utilises a threshold activated reed to register peak flow in that the reed sounds only at openings which are equal to or less than the peak flow of the subject.
  • the vent opening is determined by setting a rotatable closing plate, prior to use, at a known "critical" level of a predicted peak flow for the subject. The subject is then required to blow through the device, widening the opening with each successive expiratory effort until the whistle no longer sounds. The last position of the closing plate at which the whistle can just be heard gives the peak flow value.
  • a flow monitoring device comprises a signal generator that is adapted to generate a signal in dependence on the achievement of a predetermined volume flow rate of fluid across the signal generator, the signal generator being located in a fluid flow passage extending between an inlet and a vent outlet formed in a body, the size of the vent outlet being variable to vary the fluid flow resistance characteristics of the passage and the variation of the vent outlet being settable at a predetermined variation of the vent outlet size.
  • the size of the vent outlet is preferably incrementally variable and settable.
  • the sound generator is constituted by a reed located in an outlet formed in the body, the reed being threshold activated in that it is adapted to generate sound in dependence on the achievement of a predetermined volume flow rate of fluid across the reed and the flow rate of the fluid being predeterminable by the setting of the vent outlet.
  • the reed and vent outlets are preferably separate outlets formed in the body and the reed outlet may conveniently be shaped to expand outwardly to atmosphere in a horn-like shape, thereby substantially improving the signal to noise ratio of the device.
  • the static and dynamic flow thresholds of the sound generator or the reed are preferably close to one another in value, to minimise false positive sound generation due to impulse-like flow patterns, such as might occur during explosive as opposed to smooth expiratory flow through the device.
  • the dominant frequency of the sound generator is set to within the greatest area of human aural sensitivity, preferably between 800Hz and 2000Hz and conveniently at approximately 1000Hz.
  • the signal to noise ratio of the device can be improved yet further if the body is adapted to form a resonance chamber for the sound generator.
  • the body may be shaped in the form of a substantially bulbous resonance chamber.
  • the device may comprise a plurality of body shells that are interengageable to define the body, the outlet being formed in one body shell and another of the body shells being provided with an occluder for the outlet, the shells being movable relatively to one another for the occluder to occlude the outlet to a greater or lesser extent, depending on the relative positions of the shells thereby to vary the size of the vent outlet and the relatively movable shells being at least partially lockable to one another to set the vent outlet at a predetermined variation of the vent outlet size.
  • the body may comprise inlet and outlet body shells that are interengageable with one another in a plurality of positions in which the shells are rotated relatively to one another, the outlet shell being constituted by an external wall that encloses a resonance chamber formed with the vent opening and the inlet shell being constituted by a mouthpiece that extends into a cylindrical occluder that is adapted for location within the outlet shell and the upper edge of which is spirally shaped, the vent opening in the outlet shell extending axially long the length of the outlet shell and the occluder being adapted, when the shells are interengaged, to extend into the outlet shell to occlude the vent to a greater or lesser extent depending on the rotation of the shells relatively to one another.
  • the inlet and outlet body shells may conveniently be formed with complementary engagement formations by means of which the two shells can be clipped together, the engagement formations being constituted by an inwardly directed bead formed on an engagement end of an external wall of the outlet shell and an outwardly directed undercut groove formed on a flange extending peripherally about the exterior of the outlet shell, the bead and the engagement end of the inlet shell and the groove and the flange being dimensioned for the inlet and outlet shells to clip together with the bead engaging within the undercut groove.
  • the outlet may be defined by inwardly curved portions of the outer wall of the outlet shell, the flange on the inlet shell being formed with an engagement ring formed with outwardly directed notches that are shaped complementally to the base ends of the walls defining the vent outlet, the base ends of the curved walls being interengageable with the notches in the engagement ring, thereby to lock the inlet shell to the outlet shell in a predetermined rotational position.
  • the outwardly directed notches may conveniently be adapted to define relatively small increments of rotation.
  • the occluder may be provided with a stop formation that is positioned to catch against the curved walls at the maximum rotational positions of the inlet shell relatively to the outlet shell.
  • the device can be adapted for the bidirectional passage of fluids if the sound generator is adapted to generate sounds in either direction of flow across the sound generator.
  • a bi-directional reed would be an example of such a sound generator.
  • FIG. 1 an exploded perspective view of the monitoring device according to the invention, seen from the outlet end of the device;
  • Figure 2 is an exploded perspective view of the device of figure 1, seen from the inlet end of the device;
  • Figure 3 is a diagrammatic section on a line 3-3 in figure 2;
  • Figure 4 is an isometric view of the reed assembly of the monitoring device according to the invention.
  • Figure 5 is a diagrammatic section on a line 5-5 in figure 4;
  • Figure 6 is a diagrammatic section on a line 6-6 in figure 5;
  • Figure 7 is a side elevation (partly in section) of the device according to the invention.
  • Figure 8 is an end elevation (partly in section) of the device according to the invention.
  • the monitoring device of the invention is not a flow meter in the sense that it does not measure absolute flow through the device. Instead, it is a device intended to monitor the peak expiratory flow rate (PEFR) of a subject. This is done by monitoring the achievement or otherwise of a predetermined threshold PEFR by the subject. In this sense, the monitor of this invention is a threshold monitor in that it monitors the subject's achieved PEFR as compared to a diagnostic threshold.
  • PEFR peak expiratory flow rate
  • the predetermined PEFR is a diagnostic threshold that will depend on the treatment protocol prescribed for the subject after measurement of the subject's anticipated or predicted PEFR.
  • the monitor 10 of the invention can be seen to comprise a pair of interengageable shells 12, 14 and a sound generator constituted by a reed assembly 16.
  • the shell 12 is essentially an inlet shell and the shell 14 is an outlet shell that are joined together in the manner described below with reference to figures 7 and 8.
  • the subject breathes in as far as possible and then blows out or expires through the cylindrical tube constituting the mouthpiece 18 at the inlet end of the inlet shell 12.
  • the subject is normally instructed not to cough nor to allow explosive expiratory flow, such as spitting, coughing or interrupted flow resulting from tongue obstructions of the mouthpiece, but as will be seen below, the monitoring device 10 of the invention is designed to minimise the possible inaccuracies arising from such explosive expiratory flow.
  • the outlet shell 14 is constituted by an external wall 24 that encloses a resonance chamber 46 formed with a vent opening 26 that extends axially long the length of the outlet shell 14.
  • a central housing 22 for the reed assembly 16 extends axially within the resonance chamber 46.
  • the shells 12, 14 are intended for interconnection with one another (by means of interengaging clip formations which will be described in further detail below and the reed assembly 16 is intended for location within the horn-shaped housing 22.
  • the mouthpiece 18 extends into a cylindrical occluder 20, the upper edge of which is spirally cut.
  • the occluder 20 extends into the outlet shell 14 to occlude the vent 26 to a greater or lesser extent depending on the location of the upper edge of the occluder 20 relatively to the vent 26, which depends, in turn, on the relative degree of rotation of the shells 12, 14 relatively to one another.
  • the reed assembly can be seen to consists of a pair of baffle plates 28, 30 each occluding opposite halves of the ends of a tubular housing 32.
  • a reed bed 34 extends axially between the baffle plates 28, 30, the reed bed 34 being formed with an opening 36 within which a resiliently deformable reed 38 is set by the attachment of the fixed end 40 of the reed 38 into the reed bed 34.
  • the reed assembly 16 is non-linear (a linear whistle being one that will produce, for example, double the sound intensity for a doubling in the flow rate) , and the length, shape and mass of the reed is chosen so as to produce a sound within the frequency range that human hearing is most sensitive.
  • the reed 38 is adapted to produce sound with a pitch of approximately 1000Hz. While the reed 38 is non-linear, the device 10 can, in effect, be "linearised” by proper design of the spiral occluder.
  • the reed assembly 16 provides a clear and rapid onset of sound when its flow threshold is exceeded. in this regard it can be viewed as an analogue-to-digital device which is either "on” or “off” with nothing in between. To this end, the reed assembly 16 is manufactured to exacting tolerances to ensure minimum variation from unit to unit so that each reed 38 is activated at the same flow threshold. This eliminates the need to calibrate every monitoring device 10.
  • the reed 38 is shaped to ensure that the dynamic and static flow thresholds of the reed assembly 16 are close to one another to minimise erroneous sound generation due to large fluctuations in the flow, such as might occur during explosive as opposed to smooth expiratory flow through the device 10.
  • the reed assembly 16 is pressed into the housing 22 extending down the interior of the outlet shell 14, the outer shape of the reed assembly 16 and the inner shape of the housing 22 being complementally frusto-conical.
  • the inlet end of the reed assembly 16 is open to the interior of the inlet end 42 of the housing 22 and the outlet end of the reed assembly opens outwardly to atmosphere within the horn-shaped mouth 48 of the housing 22.
  • the horn-shaped mouth 48 enhances the audibility of the device 10 as does the outlet shell 14 which forms a resonance cavity 46 around the housing 22.
  • the inlet end 42 of the housing 22 is formed with a transversely extending barrier 44 (which can be seen more clearly in figure 2) .
  • the barrier 44 acts as a low pass filter and assists in preventing the reed 38 from being activated by the subject using explosive or impulse-like expiratory flow techniques in order to obtain an overly optimistic result of a test.
  • the inlet and outlet shells 12, 14 are formed with complementary engagement formations by means of which the two parts 12, 14 can be clipped together.
  • the engagement formations are constituted by an inwardly directed bead 54 formed on an engagement end 52 of the external wall 24 of the outlet shell 14 and an outwardly directed undercut groove 56 formed on a flange 58 extending peripherally about the exterior of the tubular mouthpiece 18.
  • the bead 54 and the engagement end 52 of the inlet shell 14 as well as the groove 56 and the flange 58 are dimensioned for the inlet and outlet shells 12, 14 to clip together with the bead 54 engaging within the undercut groove 56.
  • vent aperture 26 are defined by inwardly curved portions 50 of the outer wall 24 of the outlet shell 14.
  • the vent walls 50 are curved and aerodynamically shaped to minimise noise resulting from air escaping from the vent 26.
  • the flange 58 is formed with a notched engagement ring 60, the outwardly directed notches of which are shaped complementally to the base ends 62 of the curved in walls 50 defining the vent 26.
  • the practitioner will be required to align the base ends 62 of the curved walls 50.1, 50.2 with the notches in the engagement ring 60, thereby to lock the inlet shell 12 to the outlet shell 14 in a predetermined rotational position.
  • the combination of the groove 56 and flange 58 engagement of the body shells 12, 14 with the notched engagement ring 60 and the base ends 62 of the walls 50 results in positive locking of the body shells 12, 14 that the subject will alter only with difficulty.
  • the spiral occluder 20 is locked in a particular position relatively to the vent 26, thereby to determine the effective vent opening.
  • the vent opening will be determined by the treatment protocol.
  • the advantage of the notched engagement ring 60 is that it permits the adjustment of the monitoring device 10 of the invention in small increments.
  • the occluder 20 is provided with a stop formation 64 that is positioned to catch against the curved walls 50 at the maximum rotational positions of the inlet shell 12 relatively to the outlet shell 14.
  • the stop 64 will catch inside the curved wall 50.1 in the maximum "closed” position of the monitoring device 10, in which position the spirally cut upper surface 20.1 of the occluder is as close to the upper extremity of the vent 26 as rotation of the inlet shell 12 relatively to the outlet shell 14 will allow.
  • the stop 64 will catch inside the curved wall 50.2 in the maximum "open” position of the monitoring device 10, in which position the spirally cut upper surface 20.1 of the occluder is as close to the lower extremity of the vent 26 as relative rotation of the shells 12, 14 will allow.
  • the clinician will determine the subject's diagnostic threshold whereupon the clinician will assemble the device 10 or instruct the subject in the assembly of the device 10, by engagement of the inlet and outlet shells 10, 12, to one another with the occluder 20 located in the position determined by the subject's treatment protocol.
  • appropriate markings may be made on one or more of the occluder 20, the flange 58 and the outlet shell 14.
  • matching markings can be moulded into the outer wall of the occluder 20 and on one or both of the curved vent walls 50.
  • such markings can be moulded into the outer surface of the wall 24 of the outlet shell 14 and the facing surface of the flange 58.
  • the appropriate markings will than have to be matched up in accordance with the treatment protocol.
  • the markings may take the form of flow rate values.
  • the subject is required merely to implement the home monitoring regime - the subject will be told when flow should be measured and how the monitoring device is to be used.
  • the dominant frequency of the reed 38 is well within the most sensitive auditory range of human hearing and it has a relatively high signal to noise ratio as a result of the round surfaces of the device, the large resonance chamber and the horn-shaped housing for the reed assembly 16. To improve the signal to noise ratio even further, the subject will be encouraged to turn the vent opening downwardly away from the ear during use.
  • the outer wall 24 of the outlet shell 14 can be formed with grip formations to facilitate such a grip and also to minimise the risk of the subject accidentally occluding the vent 26 by hand.
  • the device 10 can be predesigned for use by children or adults.
  • the size of the vent 26 can be predetermined to permit peak flows of up to 4501.min "1
  • the size of the vent can be predetermined to permit peak flows of up to 8001.min *1 .
  • the invention thus also provides a method for monitoring the peak exhalation flow rate of a subject using a device of the invention, which method is characterised in that the subject exhales into the inlet of a device in which the aperture of the vent outlet has been pre- set to correspond with the predicted value of the peak exhalation flow rate which the subject should achieve, for example by the clinician setting the relative rotational positions of the two inlet and outlet shells; and the subject monitors whether the signal generating device is actuated, indicating that the subject has achieved the predicted peak exhalation flow rate, or whether the signal generating device has not been actuated, indicating that the subject has failed to achieve the predicted peak exhalation flow rate and that remedial action, for example to take medication or to visit the clinician, is required.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Surgery (AREA)
  • Public Health (AREA)
  • Animal Behavior & Ethology (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • General Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Veterinary Medicine (AREA)
  • Molecular Biology (AREA)
  • Vascular Medicine (AREA)
  • Immunology (AREA)
  • Pulmonology (AREA)
  • Physiology (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Measuring Volume Flow (AREA)
  • Catching Or Destruction (AREA)
  • Indicating Or Recording The Presence, Absence, Or Direction Of Movement (AREA)
  • Measurement Of Radiation (AREA)
  • Investigating, Analyzing Materials By Fluorescence Or Luminescence (AREA)

Abstract

Il existe des dispositifs portables de contrôle du débit expiratoire maximal utilisant des sifflets ou des anches à fonctionnement par seuil, conçus pour enregister le débit expiratoire maximal. La présente invention concerne un dispositif de contrôle du débit expiratoire maximal doté d'une anche à fonctionnement par seuil (16) située dans un orifice de sortie formé dans un corps. Ce corps comprend un boîtier entrée et un boîtier sortie (12, 14) qui peuvent s'enclencher l'un dans l'autre dans plusieurs positions de rotation l'un par rapport à l'autre. Une ouverture de ventilation (26) s'étend axialement le long du boîtier de sortie (14). Le boîtier d'entrée (12) comprend un embout (18) qui pénètre dans un dispositif de fermeture cylindrique (20) dont la tranche supérieure (20.1) est en forme de spirale. Lorsque les boîtiers sont enclenchés l'un dans l'autre, le dispositif de fermeture (20) pénètre dans le boîtier de sortie pour fermer plus ou moins la ventilation, en fonction de la position de rotation (12, 14), ce qui permet d'augmenter ou de réduire le débit de l'air passant à travers l'anche (16). Les boîtiers (12, 14) peuvent être bloqués l'un à l'autre de sorte que la taille de l'orifice de sortie de ventilation soit modifiée, normalement conformément à un protocole de traitement déterminé à l'avance.
PCT/GB1996/001251 1995-05-25 1996-05-24 Dispositif de controle du debit expiratoire maximal WO1996037147A1 (fr)

Priority Applications (4)

Application Number Priority Date Filing Date Title
AU58266/96A AU697792B2 (en) 1995-05-25 1996-05-24 Peak flow monitoring device
EP96919898A EP0830080A1 (fr) 1995-05-25 1996-05-24 Dispositif de controle du debit expiratoire maximal
BR9608900-8A BR9608900A (pt) 1995-05-25 1996-05-24 Dispositivo de monitoramento de fluxo de pico
JP8535507A JPH11505741A (ja) 1995-05-25 1996-05-24 ピーク流量監視装置

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
ZA95/4263 1995-05-25
ZA954263 1995-05-25
ZA95/9506 1995-11-09
ZA959506 1995-11-09

Publications (1)

Publication Number Publication Date
WO1996037147A1 true WO1996037147A1 (fr) 1996-11-28

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Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/GB1996/001251 WO1996037147A1 (fr) 1995-05-25 1996-05-24 Dispositif de controle du debit expiratoire maximal

Country Status (8)

Country Link
EP (1) EP0830080A1 (fr)
JP (1) JPH11505741A (fr)
AU (1) AU697792B2 (fr)
BR (1) BR9608900A (fr)
CA (1) CA2221998A1 (fr)
HU (1) HUP9802668A3 (fr)
PL (1) PL323501A1 (fr)
WO (1) WO1996037147A1 (fr)

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1998048694A1 (fr) * 1997-04-29 1998-11-05 Harwill Industries (Pty.) Ltd. Dispositif servant a controler un debit de pointe
GB2325410A (en) * 1997-05-21 1998-11-25 James William Carlyle Respiratory muscle training device
WO1999042033A1 (fr) * 1998-02-17 1999-08-26 Glaxo Group Limited Dispositif pour mesurer la force d'inspiration
WO2000004531A1 (fr) * 1998-07-17 2000-01-27 Harwill Industries (Pty) Ltd. Anche produisant des sons
EP2283773A1 (fr) * 2009-08-10 2011-02-16 Koninklijke Philips Electronics N.V. Traitement d'un signal de respiration
EP3050513A1 (fr) 2015-01-27 2016-08-03 Royal College of Art Contrôle de débit expiratoire

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB1018387A (en) * 1963-07-20 1966-01-26 Edward Francis De Bono A device for testing lung function
US4421120A (en) * 1981-03-02 1983-12-20 Biotrine Corporation Peak respiratory flow monitor
US5357975A (en) * 1991-02-28 1994-10-25 Isoraw S.A. Device for measuring the flow-volume of pulmonary air

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB1018387A (en) * 1963-07-20 1966-01-26 Edward Francis De Bono A device for testing lung function
US4421120A (en) * 1981-03-02 1983-12-20 Biotrine Corporation Peak respiratory flow monitor
US5357975A (en) * 1991-02-28 1994-10-25 Isoraw S.A. Device for measuring the flow-volume of pulmonary air

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1998048694A1 (fr) * 1997-04-29 1998-11-05 Harwill Industries (Pty.) Ltd. Dispositif servant a controler un debit de pointe
GB2325410A (en) * 1997-05-21 1998-11-25 James William Carlyle Respiratory muscle training device
WO1999042033A1 (fr) * 1998-02-17 1999-08-26 Glaxo Group Limited Dispositif pour mesurer la force d'inspiration
AU747255B2 (en) * 1998-02-17 2002-05-09 Glaxo Group Limited Device for measuring inspiratory strength
US6450969B1 (en) 1998-02-17 2002-09-17 Smithkline Beecham Corporation Device for measuring inspiratory strength
US6986745B2 (en) 1998-02-17 2006-01-17 Smithkline Beecham Corp. Device for measuring inspiratory strength
WO2000004531A1 (fr) * 1998-07-17 2000-01-27 Harwill Industries (Pty) Ltd. Anche produisant des sons
EP2283773A1 (fr) * 2009-08-10 2011-02-16 Koninklijke Philips Electronics N.V. Traitement d'un signal de respiration
EP3050513A1 (fr) 2015-01-27 2016-08-03 Royal College of Art Contrôle de débit expiratoire

Also Published As

Publication number Publication date
AU697792B2 (en) 1998-10-15
EP0830080A1 (fr) 1998-03-25
HUP9802668A2 (hu) 1999-03-29
CA2221998A1 (fr) 1996-11-28
AU5826696A (en) 1996-12-11
PL323501A1 (en) 1998-03-30
MX9709084A (es) 1998-10-31
JPH11505741A (ja) 1999-05-25
HUP9802668A3 (en) 1999-05-28
BR9608900A (pt) 1999-12-14

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