+

WO1997018003A1 - Dispositif de detection de debit respiratoire cible - Google Patents

Dispositif de detection de debit respiratoire cible Download PDF

Info

Publication number
WO1997018003A1
WO1997018003A1 PCT/US1996/018042 US9618042W WO9718003A1 WO 1997018003 A1 WO1997018003 A1 WO 1997018003A1 US 9618042 W US9618042 W US 9618042W WO 9718003 A1 WO9718003 A1 WO 9718003A1
Authority
WO
WIPO (PCT)
Prior art keywords
negative pressure
pressure sensor
flow rate
air flow
target
Prior art date
Application number
PCT/US1996/018042
Other languages
English (en)
Inventor
Warren J. Warwick
Leland G. Hansen
Original Assignee
Regents Of The University Of Minnesota
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 Regents Of The University Of Minnesota filed Critical Regents Of The University Of Minnesota
Priority to AU77260/96A priority Critical patent/AU7726096A/en
Publication of WO1997018003A1 publication Critical patent/WO1997018003A1/fr

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
    • A61M15/00—Inhalators
    • 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
    • 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
    • A61M16/0006—Accessories therefor, e.g. sensors, vibrators, negative pressure with means for creating vibrations in patients' airways
    • 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
    • A61M16/0051—Devices for influencing the respiratory system of patients by gas treatment, e.g. ventilators; Tracheal tubes with alarm 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
    • A61M16/021—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
    • 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
    • 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
    • A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
    • A61M16/0816—Joints or connectors
    • A61M16/0841—Joints or connectors for sampling
    • A61M16/0858—Pressure sampling ports
    • 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
    • A61M16/0866—Passive resistors 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
    • A61M16/0057—Pumps therefor
    • A61M16/0063—Compressors
    • 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
    • A61M2016/0015—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors
    • A61M2016/0018—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical
    • A61M2016/0021—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical with a proportional output signal, e.g. from a thermistor
    • 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
    • A61M2016/003—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter
    • A61M2016/0033—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical
    • A61M2016/0039—Accessories therefor, e.g. sensors, vibrators, negative pressure with a flowmeter electrical in the inspiratory circuit

Definitions

  • the present invention relates generally to a flow system that detects target flow rates in a patient's respiratory cycle, and more particularly, to a system in which one or more preselected target flow rates are detected using flow restrictors.
  • Various types of medical treatments that depend on the respiratory cycle of a patient are used for persons suffering from respiratory diseases, or persons who are indisposed or unconscious.
  • These medical treatments include, for example, aerosol generators, chest compressors, respirators, and ventilators.
  • aerosol therapy is widely used due to its recognized clinical advantages over intravenous or oral drug therapy. The advantages include: higher therapeutic effect with a given dose of drug, fewer side effects, and more rapid action ofthe drug.
  • Some drugs designed to treat airway dysfunction and parenchymal disease are more effective when delivered by an aerosol.
  • One requirement of effective aerosol therapy is to deposit the aerosols at the appropriate site of the respiratory tract. The flow rate at which an aerosol is inhaled influences the site of aerosol deposition in the lungs ofthe patient.
  • aerosol generators should ideally be activated within target minimum and maximum respiratory flow rates to achieve the optimum therapeutic effect.
  • variable flow rate sensors to trigger a nebulization stream. These devices are expensive, often requiring processing ofthe output from the sensor to an analogue comparator circuit or to digital electronics. Some of these devices attach the variable flow rate sensors directly to the mouthpiece used by the patient, adding to the weight ofthe unit and the possibility of damage due to mishandling. Additionally, the sensitivity of some of these devices is such that an increased respiratory flow rate is required, that in practice cannot always be achieved especially by children and indisposed persons. Chest compressor devices used to loosen and eliminate mucus from the lungs, such as high frequency chest compressors (HFCC), are another example of medical treatments that are dependant on the respiratory cycle of a patient.
  • HFCC high frequency chest compressors
  • the degree of airway obstruction due to mucus in the lungs affects the site of aerosol deposition in aerosol therapy. Clearance of mucus from the respiratory tract in healthy individuals is accomplished primarily through air flow and ciliary transport, accompanied with sighing and coughing. Failure of these natural systems result in accumulation of mucus which must be removed to reduce the build-up and the risk of infection. Treatment involves aerosol therapy to obtain bronchial drainage in combination with daily pounding on the chest wall to loosen mucus for expectoration.
  • Some HFCC systems rely on a patient hand held control to activate HFCC during the patient's respiratory cycle. Although activation of HFCC is often found to be most effective during a particular portion ofthe respiratory cycle, it is difficult using present HFCC systems for the patient to identify that particular portion ofthe respiratory cycle in order to activate HFCC precisely.
  • the present invention is directed to an air flow system for detecting one or more target flow rates in a respiratory cycle of a subject.
  • the target flow rates may be used for controlling various medical treatments.
  • a signal generated when a target flow rate is reached may be used for administering aerosols during inhalation, activation of HFCC therapy during exhalation, or to control various other medical treatments.
  • the air flow system allows for selection of a narrow flow rate range for administering aerosols during inhalation to target particular areas in the respiratory tree as major deposition sites for the aerosols.
  • the air flow system ofthe present invention is activated by detecting a negative pressure condition in an opening of a flow restrictor.
  • Target flow rates are preselected and thereby quantified by using a restrictor opening of a particular size. When a low or minimum flow rate is required, a small restrictor opening is used while a higher or maximum flow rate requires a larger opening.
  • the system in effect, operates as a switch to activate various medical treatments by using predetermined target air flow rates, which are a function ofthe size of the opening of the flow restrictors.
  • the air flow system includes a patient mouthpiece and at least a first interchangeable flow restrictor.
  • the first flow restrictor has a first chamber fluidly coupled to a first air flow resistance opening and the patient mouthpiece.
  • the first air flow resistance opening has a first cross sectional area less than the cross sectional area ofthe first chamber.
  • a first sampling port is located proximate the first chamber in fluid communication with a first negative pressure sensor so that a first target flow rate generates a negative pressure condition in the first chamber that activates the first negative pressure sensor.
  • the target flow rate is a function of the first cross sectional area.
  • One or more additional interchangeable air flow restrictors may be releasably attached to the distal end of the first flow restrictor to detect other target flow rates.
  • additional flow restrictors may be inte ⁇ osed between the first air flow restrictor and the mouthpiece.
  • the cross sectional areas are generally in the range of about 6 to 130 mm 2 .
  • the sampling ports are preferably fluidly connected to the sensors by tubes so that the mouthpiece can be remote from the sensors.
  • the cross sectional area of the flow restrictor connected to the mouthpiece is preferably less than the cross sectional areas of subsequent flow restrictors.
  • the first target flow rate is generally a minimum target flow rate and the second target flow rate is a maximum target flow rate.
  • the present invention is also directed to controlling a medical treatment in response to target respiration flow rates.
  • a medical device may be activated or deactivated in response to the activation or deactivation of one or more negative pressure sensors.
  • the medical device may include an aerosol generator fluidly connected to the mouthpiece that is activated in response to activation of the first negative pressure sensor.
  • the medical treatments may be deactivated in response to activation ofthe second negative pressure sensor.
  • the activation of the second negative pressure sensor may signal an alarm.
  • the medical device may include a high frequency chest compression device activated at the end ofthe inspiration cycle. In an alternate embodiment, a high frequency chest compressor may be used in combination with the aerosol generator.
  • a ventilator may also be activated in response activation or deactivation of one of the negative pressure sensors.
  • Figure 1 is a schematic illustration of an exemplary system for controlling an aerosol generator and/or a high frequency chest compressor as a function of target respiratory flow rates;
  • Figure 2 A illustrates an exploded, cross-sectional view of two exemplary flow restrictors for detecting target respiratory flow rates
  • Figure 2B illustrates an exploded cross-sectional view of three exemplary flow restrictors for detecting target respiratory flow rates
  • Figure 3 is a schematic illustration of an exemplary system for controlling a generic medical treatment as a function of target respiratory flow rates
  • Figure 4 is a graph of an oscillatory curve representing an exemplary patient's respiratory cycle
  • Figure 5 is a graph illustrating respiratory flow rates as a function of cross-sectional areas of openings in flow restrictors.
  • FIG. 1 is a schematic illustration of an exemplary air flow system 10 for controlling an aerosol generator 12 as a function of a minimum and a maximum target respiratory flow rate.
  • the aerosol generator 12 is fluidly connected to a T- tube 14.
  • the T-tube 14 has an opening 16 for a mouth piece at one end and a minimum flow restrictor 20 at the other end.
  • a maximum flow restrictor 18 is fluidly connected to the opposite or distal end ofthe minimum flow restrictor 20.
  • the minimum flow restrictor 20 has a one degree tapered opening 22 sized for frictional engagement with one end of the T- tube 14 (see Figure 1).
  • a negative pressure sensing port 26 At base 24 ofthe opening 22 is a negative pressure sensing port 26.
  • a tube 28 is pressure-fit into the port 26.
  • the tube 28 is preferably pe ⁇ endicular to the direction ofthe air stream "S" and protrudes slightly above the inside surface of the opening 22.
  • the protrusion ofthe tube 28 serves as a stop for the connection with the T-tube 14 (see Figure 1).
  • the opposite end 30 ofthe minimum flow restrictor 20 has an external one degree taper for frictional engagement with the maximum flow restrictor 18.
  • the minimum flow restrictor 20 has an air flow resistance opening 32 with a cross-sectional area "A : .”
  • the cross sectional area "A 2 " of the minimum flow resistance opening 32 is determined by the target minimum flow rate, as will be discussed below.
  • One end ofthe maximum flow restrictor 18 has an opening 34 with a one degree internal taper sized for frictional engagement with the opposite end 30 of the minimum flow restrictor 20.
  • a negative pressure sensing port 36 is located at base 35 of the opening 34.
  • a tube 38 is pressure-fit into the port 36.
  • the tube 38 is preferably perpendicular to the direction ofthe air stream "S" and protrudes slightly above the inside surface of the opening 34.
  • the protrusion ofthe tube 38 serves as a stop for the connection with the minimum flow restrictor 20. (see Figure 1).
  • the opposite end ofthe maximum flow restrictor 18 has an opposite end 40 with a similar diameter and taper as the opening 22 so that it may optionally be attached to another flow restrictor (see Figure 2B).
  • the maximum flow restrictor 18 has an air flow resistance opening 42 having a cross-sectional area "A,.”
  • the cross sectional area "A,” ofthe maximum flow resistance opening is determined by the target maximum flow rate, as will be discussed below.
  • the openings 22 and 34 preferably have the same or similar inside diameter and the opposite ends 30 and 40 preferably have the same outside diameter so that the flow restrictors are interchangeable. In the preferred embodiment, only the air flow resistance openings 32, 42 ofthe flow restrictors
  • a chamber 23 is formed within the flow restrictor 20 adjacent to the tube 28 and a chamber 25 is also formed in the flow restrictor 18 adj cent to the tube 38 of the flow restrictor 20, so that a venturi effect is created in the chambers 23 and 25.
  • the air flow rate increases until it is first restricted by the air flow resistance opening 32.
  • the air flow rate in the air flow resistance opening 32 reaches a particular level, a negative pressure condition is created in the chamber 23 that is transmitted to sensor 50 through tubes 28 and 54.
  • the air flow is next restricted by the air flow resistance opening 42 in the flow restrictor 18.
  • the negative pressure sensors 50, 52 each include a relay wired in the open position.
  • a negative pressure sensor/relay combination suitable for use in the present invention is available from World Magnetics of Traverse City, MI under model number PSF100A/5RF100B. It will be understood that in embodiments utilizing more than two air flow restrictors, additional sensors may be added to the air flow system 10 without departing from the scope ofthe present invention.
  • the tubes 54, 56 are constructed from a 2.54 mm ID (0.1 inch) clear, vinyl tubing. Consequently, the present air flow system 10 requires no electrical connections to be attached to the patient's hand-held aerosol generator 12.
  • the sensors 50, 52 are calibrated to trigger when subjected to a negative pressure condition equivalent to 124.5 Pa
  • a two-way solenoid 60 directs compress air from a compress air source 62 to the atmosphere through a vent 64.
  • a patient's inhalation flow rate is above a target minimum flow rate, the pressure in the chamber 23 drops.
  • the relay in the negative pressure sensor 50 closes.
  • the closed relay 50 provides electric power from power supply 58 to activate the two-way solenoid 60.
  • the compressed air is redirected by the activated solenoid 60 through hose 66 to the aerosol generator 12.
  • the relay in the negative pressure sensor 50 will remain closed until the inhalation flow rated drops below the minimum target flow rate.
  • a 1 OOV AC two-way solenoid suitable for use in the present invention is available from Grainger of Arden Hills, MN under model number 74514-01 15.
  • the pressure in the chamber 25 drops. That pressure drop is communicated to the sensor 52 through the tube 56, causing the relay in the sensor 52 to close and an alarm 70 to be activated.
  • the alarm generally signals the patient to slow the inhalation flow rate.
  • the signal from the alarm 70 stops.
  • the alarm 70 is a 9 volt battery wired to a Piezo signal generator.
  • a relay wired to provide electrical power to the ultrasonic nebulizer is substituted for the solenoid 60.
  • the sensor 52 may be wired to deactivate the solenoid 60 when the target maximum flow rate is achieved.
  • a high frequency chest compressor 90 may be used in combination with the aerosol generator 12. When a patient's inhalation flow rate is above a target minimum flow rate, the aerosol generator 12 is activated and remains so until the inhalation air flow drops below the minimum target flow rate. The high frequency chest compressor 90 is deactivated by double-throw relay 92 during the inhalation cycle.
  • the double-throw relay 92 activates the high frequency chest compressor 90.
  • a high frequency chest compression device suitable for use in the present invention is disclosed in U.S. Patent Nos. 5,056,505 and 4,838,263, which are hereby inco ⁇ orated by reference.
  • Figure 2B is an exemplary configuration of three interchangeable flow restrictors 70, 72, 74 with air flow resistance openings 76, 78, 80 having progressively smaller cross sectional areas A 3 A 4 A, along airstream "S".
  • the flow restrictors 70, 72, 74 may be "nested” in the order shown in Figure 2B, or alternatively, rearranged in a different order. Openings 79, 81, 82 are sized so that any ofthe flow restrictors 70, 72, 74 may be attached to the T-tubes (see Figures 1 and 3).
  • the tubes 84, 86, 88 are fluidly attached to negative pressure sensors (not shown), as previously discussed herein.
  • the flow restrictors 70, 72, 74 detect maximum, intermediate and minimum target flow rates, respectively. It will be understood that the number of flow restrictors may increase or decrease depending upon the particular application.
  • FIG 3 is a schematic illustration of an exemplary air flow system 10' for controlling a medical treatment 90 as a function of minimum and maximum target respiratory flow rates.
  • Breathing tube 14' has an opening 16' for a mouth piece at one end and a minimum flow restrictor 20' at the other end.
  • the minimum flow restrictor 20' has an air flow resistance opening 32'.
  • a maximum flow restrictor 18' is fluidly connected to the opposite or distal end ofthe minimum flow restrictor 20'.
  • the maximum flow restrictor 18' has an air flow resistance opening 42'.
  • the flow restrictors 18', 20' are fluidly coupled to a pair of negative pressure sensors 50', 52' via a pair of tubes 54', 56', as discussed in Figure 1.
  • a relay in the sensor 50' close and triggers relay 92' to activate or deactivate medical treatment 90'.
  • the relay in sensor 52' closes and activates alarm 70'.
  • the alarm generally signals the patient to slow the inhalation flow rate.
  • the signal from the alarm 70' stops.
  • activation ofthe sensor 52' may trigger the relay 92' to activate or deactivate the medical treatment 90'.
  • the flow restrictors 18, 18' and 20, 20' as shown in Figures 1 and 3, are preferably constructed using delrin, although a variety of plastic materials approved for medical use would be suitable for this pu ⁇ ose. For example, disposable, low-cost plastic would be suitable and would eliminate the need for sterilization.
  • the medical treatments include, for example, a high frequency chest compression device, such as discussed above, a ventilator or a respirator. It will be understood that the present air flow system may be used with any medical treatment that is dependent on the respiratory cycle ofthe patient.
  • Figure 4 depicts an oscillatory curve 100 representing an exemplary respiratory cycle of a patient.
  • the air flow rate is zero.
  • the flow rate initially increases and then tapers off to zero 104 at the end of the inhalation cycle.
  • the present air flow system 10. 10' detects target air flow rate 106, 108, 1 10, 1 12 generated during inhalation. When the inhalation air flow exceeds the minimum target flow rate 106, the sensor 50, 50' are activated, and remain activated until the flow rate drops below the minimum target flow rate at 112.
  • the sensors 52, 52' are activated, and remain activated until the flow rate drops below the maximum target flow rate at 1 10. None of the negative pressure sensors are activated during the exhalation cycle 101.
  • the cross sectional areas "A" ofthe flow resistance openings 32, 32' and 42, 42' are determined by the target flow rate.
  • Figure 5 depicts a range of target flow rate values as a function of the cross-sectional area of flow resistance openings for the negative pressure sensors calibrated to trigger when exposed to a negative pressure condition equivalent to 124.5 Pa (0.5 inches of water).
  • Air flow was measured using a calibrated manostat flow meter calibrated at 20 °C +/- 2% for eleven different flow restrictors.
  • Cross-sectional areas that were tested ranged from 7.94 mm 2 to 103.9 mm 2 (0.0123 in 2 to 0.161 1 in 2 ) corresponding flow rate values ranged from 4 to 60 1/min.
  • the correlation coefficient comparing the cross sectional area of each flow restrictor and flow rate value was 0.99.
  • the minimum flow restrictors are made 1.1 in (27.94 mm) in length with an outer diameter of 1.25 in (31.75 mm).
  • the end ofthe minimum flow restrictor that frictionally engages with the end ofthe breathing tube or T-tube is 0.5 in (12.7 mm) long and has a one degree tapered opening that is 0.5 in (12.7 mm) deep, with a 0.85 in (21.59 mm) minimum inner diameter at the base.
  • the negative pressure sensing port is located 0.1 in (2.54 mm) from the base.
  • a one inch long stainless steel hypo tube is pressure-fit into the port pe ⁇ endicular to the air stream "S".
  • the opposite end of the minimum flow restrictor that frictionally engages with the maximum flow restrictor is 0.5 in (12.7 mm) long and has a one degree external tapered opening, with a maximum diameter of 0.86 in (21.84 mm).
  • the maximum flow restrictor is also 1.1 in (27.94 mm) in length with an outer diameter of 1.25 in (31.75 mm).
  • the end ofthe maximum flow restrictor that frictionally engages with the opposite end of the minimum flow restrictor is 0.5 in (12.7 mm) long and has a one degree internal tapered opening with a maximum outside diameter of 0.85 in (21.59 mm).
  • the negative pressure sensing port is located 0.1 in (2.54 mm) from the base.
  • a one inch long stainless steel hypo tube is pressure-fit into the port.
  • the tube is preferably pe ⁇ endicular to the direction ofthe air stream and protrudes slightly above the inside surface ofthe opening to serve as a stop for the connection with the minimum flow restrictor (see Figure 1 ).
  • the opposite end ofthe maximum flow restrictor has an opening with a similar diameter and taper as the opening on the minimum flow restrictor that engages with the breathing tube.
  • EXAMPLE 2 To determine the efficiency ofthe air flow system 10 at reducing the loss of nebulized aerosol, water vapor samples were captured on fresh CaSO 4 (Dryrite) granules and weighed. Samples were collected from three groups: (1) normal breathing with no aerosol, (2) normal breathing with aerosol without the air flow system 10, and (3) normal breathing with aerosol using the air flow system 10. A 1 in (25.4 mm) inner diameter tube was loaded with 20 grams of CaSO 4 granules. The tube and CaS0 4 were then weighed. A one way valve allowed only exhaled air to pass through the CaS0 4 granules.
  • the efficiency of aerosol delivery to the patient was determined by comparing the amount of aerosol produced over the test period to the amount lost to the environment.
  • the output of the nebulizer water vapor was determined by measuring and weighing the amount of water vapor trapped after operating for ten seconds through the water vapor trap described above. The procedure was repeated six times.
  • the efficiency of controlled and uncontrolled aerosol delivery to patients was estimated by calculating the amount of aerosol produced by each method based on the time the nebulizer was active during the five breath cycle. That amount was then compared to the amount of loss to the environment over that period.
  • the mean weight of water vapor added from five breaths of normal breathing with no aerosol was 0.13 +/- 0.02 gm; for normal breathing with uncontrolled aerosol (i.e., without the air flow system) 0.32 +/- 0.06 gm; and for normal breathing with a controlled aerosol using the present air flow system 0.17 +/- 0.04 gm.
  • the difference between the amount of water vapor added by normal breathing and normal breathing with a controlled aerosol generator was
  • the efficiency of deliver ⁇ ' to the patient was determined by comparing the amount of aerosol produced over the test time period to the amount lost to the environment.
  • the controller delivered aerosol for a mean time of 3.8 seconds +/- 0.18 per breath. Delivery efficiency was calculated by multiplying total time aerosol was delivered during the five breath cycle by 0.006 gm (output per second of the aerosol generator) to determine the total aerosol produced. This amount minus the amount lost to the environment is the amount delivered to the patient.
  • the controlled aerosol generator delivered aerosol to the patient at an efficiency rate of 64%.
  • the uncontrolled aerosol five breath cycle had a mean total activation time of 43 seconds +/- 2.5 seconds.
  • the mean total activation time multiplied by 0.006 gm represents the number of grams of aerosol produced. That number minus the quantity lost to the environment is the amount of aerosol delivered to the patient.
  • the uncontrolled aerosol generator delivered aerosol to the patient at an efficiency rate of 27%.

Landscapes

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

Abstract

L'invention a trait à un dispositif à flux d'air (10) permettant la détection de débits cibles en fonction d'une ouverture (32, 42) ménagée dans un limiteur de flux (18, 20). Un détecteur de dépression (50, 52) se déclenche en réaction à une situation dépressionnaire dans une enceinte (23, 25) se trouvant dans le limiteur de flux (18, 20). On présélectionne des débits cibles en utilisant un limiteur de flux (18, 20) d'une taille particulière. Il est possible de se servir du fonctionnement du détecteur de dépression (50, 52) pour la gestion de traitements à caractère médical. On peut utiliser un signal produit lorsque un débit cible est atteint pour administrer des aérosols lors de l'inspiration, pour la mise en oeuvre d'une thérapeutique basée sur la compression thoracique à haute fréquence ou pour agir sur d'autres traitements à caractère médical. Le dispositif à flux d'air (10) permet de sélectionner une plage étroite de débit pour l'administration d'aérosols lors de l'inspiration et ce, afin de cibler des régions particulières de l'arbre bronchique comme principaux sites de dépôt des aérosols
PCT/US1996/018042 1995-11-15 1996-11-12 Dispositif de detection de debit respiratoire cible WO1997018003A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU77260/96A AU7726096A (en) 1995-11-15 1996-11-12 System for detecting target respiratory flow rates

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US55883895A 1995-11-15 1995-11-15
US08/558,838 1995-11-15

Publications (1)

Publication Number Publication Date
WO1997018003A1 true WO1997018003A1 (fr) 1997-05-22

Family

ID=24231213

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1996/018042 WO1997018003A1 (fr) 1995-11-15 1996-11-12 Dispositif de detection de debit respiratoire cible

Country Status (2)

Country Link
AU (1) AU7726096A (fr)
WO (1) WO1997018003A1 (fr)

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0945101A1 (fr) * 1998-03-26 1999-09-29 Guy Martinot Réducteur de pression pour mesure du débit expiratoire sous NEP
EP0983772A1 (fr) * 1998-09-03 2000-03-08 Georges Boussignac Dispositif pour assistance respiratoire
EP1446172A4 (fr) * 2001-09-06 2005-07-20 Microdose Technologies Inc Adaptateurs destines a des inhalateurs pour ameliorer les performances
DE102005003553A1 (de) * 2005-01-26 2006-08-03 Weinmann Geräte für Medizin GmbH + Co. KG Verfahren und Vorrichtung zur Druckregelung
WO2009105445A1 (fr) * 2008-02-18 2009-08-27 Virginia Commonwealth University Délivrance efficace de nanoparticules et d’aérosols pharmaceutiques de taille micrométrique au poumon par croissance par condensation optimisée
AU2008200226B2 (en) * 2001-09-06 2010-05-13 Microdose Therapeutx, Inc. Adaptors for inhalers to improve performance
US8460223B2 (en) 2006-03-15 2013-06-11 Hill-Rom Services Pte. Ltd. High frequency chest wall oscillation system
WO2016110668A1 (fr) * 2015-01-08 2016-07-14 University Of Surrey Débitmètre
EP3246063A1 (fr) * 2016-05-16 2017-11-22 L'air Liquide, Societe Anonyme Pour L'etude Et L'exploitation Des Procedes Georges Claude Canule nasale
EP4464353A1 (fr) * 2023-05-15 2024-11-20 PARI Pharma GmbH Dispositif de traitement par inhalation

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4977889A (en) * 1989-10-12 1990-12-18 Regents Of The University Of Minnesota Fitting and tuning chest compression device
WO1993015782A1 (fr) * 1992-02-10 1993-08-19 National Research Council Of Canada Appareil d'expiration forçee et procede d'utilisation
US5245995A (en) * 1987-06-26 1993-09-21 Rescare Limited Device and method for monitoring breathing during sleep, control of CPAP treatment, and preventing of apnea
US5287851A (en) * 1991-09-11 1994-02-22 Beran Anthony V Endotracheal tube connector with integral pneumotach transducer
WO1994016759A1 (fr) * 1991-03-05 1994-08-04 Miris Medical Corporation Systeme et procedes de liberation automatique de medicament en aerosol
EP0627196A1 (fr) * 1993-03-10 1994-12-07 Jan Christiaan Vermaak Méthode et appareil pour surveiller le fonctionnement du poumon

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5245995A (en) * 1987-06-26 1993-09-21 Rescare Limited Device and method for monitoring breathing during sleep, control of CPAP treatment, and preventing of apnea
US4977889A (en) * 1989-10-12 1990-12-18 Regents Of The University Of Minnesota Fitting and tuning chest compression device
WO1994016759A1 (fr) * 1991-03-05 1994-08-04 Miris Medical Corporation Systeme et procedes de liberation automatique de medicament en aerosol
US5287851A (en) * 1991-09-11 1994-02-22 Beran Anthony V Endotracheal tube connector with integral pneumotach transducer
WO1993015782A1 (fr) * 1992-02-10 1993-08-19 National Research Council Of Canada Appareil d'expiration forçee et procede d'utilisation
EP0627196A1 (fr) * 1993-03-10 1994-12-07 Jan Christiaan Vermaak Méthode et appareil pour surveiller le fonctionnement du poumon

Cited By (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0945101A1 (fr) * 1998-03-26 1999-09-29 Guy Martinot Réducteur de pression pour mesure du débit expiratoire sous NEP
BE1011855A3 (fr) * 1998-03-26 2000-02-01 Martinot Guy Generateur de depression pour mesure du debit expiratoire sous nep.
EP0983772A1 (fr) * 1998-09-03 2000-03-08 Georges Boussignac Dispositif pour assistance respiratoire
FR2782925A1 (fr) * 1998-09-03 2000-03-10 Georges Boussignac Dispositif pour assistance respiratoire
US6363935B1 (en) 1998-09-03 2002-04-02 Georges Boussignac Device for respiratory assistance
AU2008200226B2 (en) * 2001-09-06 2010-05-13 Microdose Therapeutx, Inc. Adaptors for inhalers to improve performance
AU2002327052B2 (en) * 2001-09-06 2007-10-18 Microdose Therapeutx, Inc. Adaptors for inhalers to improve performance
US7343914B2 (en) 2001-09-06 2008-03-18 Microdose Technologies, Inc. Adaptors for inhalers to improve performance
EP1446172A4 (fr) * 2001-09-06 2005-07-20 Microdose Technologies Inc Adaptateurs destines a des inhalateurs pour ameliorer les performances
DE102005003553A1 (de) * 2005-01-26 2006-08-03 Weinmann Geräte für Medizin GmbH + Co. KG Verfahren und Vorrichtung zur Druckregelung
US9968511B2 (en) 2006-03-15 2018-05-15 Hill-Rom Services Pte. Ltd. High frequency chest wall oscillation system
US8460223B2 (en) 2006-03-15 2013-06-11 Hill-Rom Services Pte. Ltd. High frequency chest wall oscillation system
US11110028B2 (en) 2006-03-15 2021-09-07 Hill-Rom Services Pte. Ltd. High frequency chest wall oscillation system
WO2009105445A1 (fr) * 2008-02-18 2009-08-27 Virginia Commonwealth University Délivrance efficace de nanoparticules et d’aérosols pharmaceutiques de taille micrométrique au poumon par croissance par condensation optimisée
US8479728B2 (en) 2008-02-18 2013-07-09 Virginia Commonwealth University Effective delivery of nanoparticles and micrometer-sized pharmaceutical aerosols to the lung through enhanced condensational growth
WO2016110668A1 (fr) * 2015-01-08 2016-07-14 University Of Surrey Débitmètre
US10466082B2 (en) 2015-01-08 2019-11-05 University Of Surrey Flow meter
EP3246063A1 (fr) * 2016-05-16 2017-11-22 L'air Liquide, Societe Anonyme Pour L'etude Et L'exploitation Des Procedes Georges Claude Canule nasale
EP4464353A1 (fr) * 2023-05-15 2024-11-20 PARI Pharma GmbH Dispositif de traitement par inhalation
WO2024235952A1 (fr) * 2023-05-15 2024-11-21 Pari Pharma Gmbh Dispositif de thérapie par inhalation

Also Published As

Publication number Publication date
AU7726096A (en) 1997-06-05

Similar Documents

Publication Publication Date Title
US5479920A (en) Breath actuated medicinal aerosol delivery apparatus
US9764104B2 (en) Directional flow sensor inhaler
US6705316B2 (en) Pulmonary dosing system and method
CN102762250B (zh) 用于包括具有夹带端口和/或压力特征的非密封通气界面的无创通气的方法、系统和装置
EP1446172B1 (fr) Inhalateur type DPI
JP4199931B2 (ja) 薬剤投与装置における改良及びそれに関連する改良
SE9702710D0 (sv) Verfahrne zur bestimmung der mechanischen eigenschaften des respiratorischen systems eines beatmeten patienten und vorrichtung zur durchführung des verfahrens
WO2004105845A1 (fr) Dispositif portatif de diagnostic respiratoire
CA2126331A1 (fr) Inhalateur intelligent donnant une retroaction aussi bien au patient qu'au personnel medical
WO2004026101A3 (fr) Dispositifs d'epreuve d'efforts et procedes y relatifs
JP2006150096A (ja) 断続的ガス吸入装置及びその方法
JP2008536871A (ja) 上気道の一酸化窒素浄化
CN109475708B (zh) 用于监测对吸入疗法的依从性的装置和方法
WO1997018003A1 (fr) Dispositif de detection de debit respiratoire cible
US20230158341A1 (en) Face mask and system
ATE83939T1 (de) Atemvorrichtung.
WO2013043504A1 (fr) Distribution pulsée d'oxygène pour des applications médicales
WO2003070306A2 (fr) Dispositif respiratoire
Pfenninger et al. Intermittent positive pressure breathing (IPPB) versus incentive spirometer (IS) therapy in the postoperative period
JPH0710278B2 (ja) 吸気ガス供給装置
KR102586589B1 (ko) 천식환자용 약물 모니터링 흡입기와 호흡측정기가 결합된 스마트 흡입기 시스템
CN113041575A (zh) 一种适用于肺部康复训练的洁净式呼吸训练装置
CN107198805A (zh) 一种基于自然呼吸的智能雾化治疗设备

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AL AM AT AU AZ BA BB BG BR BY CA CH CN CU CZ DE DK EE ES FI GB GE HU IL IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MD MG MK MN MW MX NO NZ PL PT RO RU SD SE SG SI SK TJ TM TR TT UA UG UZ VN AM AZ BY KG KZ MD RU TJ TM

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): KE LS MW SD SZ UG AT BE CH DE DK ES FI FR GB GR IE IT LU MC NL PT SE BF BJ CF CG CI

121 Ep: the epo has been informed by wipo that ep was designated in this application
REG Reference to national code

Ref country code: DE

Ref legal event code: 8642

122 Ep: pct application non-entry in european phase
点击 这是indexloc提供的php浏览器服务，不要输入任何密码和下载