WO2024055101A1 - Soupape de régulation de débit de rétroaction haptique - Google Patents

Soupape de régulation de débit de rétroaction haptique Download PDF

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Publication number
WO2024055101A1
WO2024055101A1 PCT/CA2023/051198 CA2023051198W WO2024055101A1 WO 2024055101 A1 WO2024055101 A1 WO 2024055101A1 CA 2023051198 W CA2023051198 W CA 2023051198W WO 2024055101 A1 WO2024055101 A1 WO 2024055101A1
Authority
WO
WIPO (PCT)
Prior art keywords
flow rate
control valve
rate control
flexible closure
flexible
Prior art date
Application number
PCT/CA2023/051198
Other languages
English (en)
Inventor
David Mark Douglas HODGSON
Sara FEDULLO
Brandon Alexander BEACH
Original Assignee
Hollo Medical Inc.
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 Hollo Medical Inc. filed Critical Hollo Medical Inc.
Publication of WO2024055101A1 publication Critical patent/WO2024055101A1/fr

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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
    • A61M15/0001—Details of inhalators; Constructional features thereof
    • A61M15/002—Details of inhalators; Constructional features thereof with air flow regulating means
    • 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
    • A61M15/0001—Details of inhalators; Constructional features thereof
    • A61M15/0013—Details of inhalators; Constructional features thereof with inhalation check valves
    • A61M15/0015—Details of inhalators; Constructional features thereof with inhalation check valves located upstream of the dispenser, i.e. not traversed by the product
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
    • F16K—VALVES; TAPS; COCKS; ACTUATING-FLOATS; DEVICES FOR VENTING OR AERATING
    • F16K15/00—Check valves
    • F16K15/14—Check valves with flexible valve members
    • F16K15/16—Check valves with flexible valve members with tongue-shaped laminae
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
    • F16K—VALVES; TAPS; COCKS; ACTUATING-FLOATS; DEVICES FOR VENTING OR AERATING
    • F16K17/00—Safety valves; Equalising valves, e.g. pressure relief valves
    • F16K17/20—Excess-flow valves
    • F16K17/34—Excess-flow valves in which the flow-energy of the flowing medium actuates the closing mechanism
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
    • F16K—VALVES; TAPS; COCKS; ACTUATING-FLOATS; DEVICES FOR VENTING OR AERATING
    • F16K7/00—Diaphragm valves or cut-off apparatus, e.g. with a member deformed, but not moved bodily, to close the passage ; Pinch valves
    • F16K7/18—Diaphragm valves or cut-off apparatus, e.g. with a member deformed, but not moved bodily, to close the passage ; Pinch valves with diaphragm secured at one side only, e.g. to be laid on the seat by rolling action
    • 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
    • A61M15/0001—Details of inhalators; Constructional features thereof
    • A61M15/0018—Details of inhalators; Constructional features thereof with exhalation check valves
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M15/00—Inhalators
    • A61M15/0086—Inhalation chambers
    • A61M15/0088—Inhalation chambers with variable volume
    • 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
    • A61M15/009—Inhalators using medicine packages with incorporated spraying means, e.g. aerosol cans
    • 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
    • A61M2205/58—Means for facilitating use, e.g. by people with impaired vision
    • A61M2205/582—Means for facilitating use, e.g. by people with impaired vision by tactile feedback

Definitions

  • the present invention relates to flow rate control valves and more specifically to flow rate control valves with a haptic feedback mechanism.
  • An example inhaler may comprise, for example, a plastic holder forming an inlet for a drug canister and a mouthpiece.
  • the drug canister may comprise, for example a propellant with a drug suspension, and a metering valve that is connected to a nozzle for expelling the aerosol drug from the cannister.
  • the cannister may be inserted into the inlet of the plastic holder such that the nozzle of the cannister aligns with the mouthpiece of the plastic holder.
  • inhalers When the cannister is actuated, a drug aerosol is released through the mouthpiece.
  • inhalers may be used on their own whereby a user forms a seal around the mouthpiece of the inhaler and inhales simultaneously with actuating the inhaler.
  • the inhaler mouthpiece may be connected to an aerosol holding chamber (also called a spacer) whereby the user forms a seal around a mouthpiece of the spacer.
  • Facemasks that cover the nose and mouth are also available for use with the spacer and may be prescribed for users that cannot form an airtight seal on a mouthpiece of the spacer or inhaler.
  • the spacer may be used to contain the high-speed dose particles that are expelled from an inhaler when a user actuates the inhaler. This makes dose inhalation independent of actuation and allows a user to inhale the dose particles at their own rate, for example by dividing the dose over multiple breaths. Spacers further enable the formation of smaller aerosols which increase lung deposition and simultaneously reduces local side effects in the mouth and throat. INTRODUCTION
  • Inhalers and spacers available on the market are often performance tested at a flow rate of 28.3 LPM. Accordingly, these spacers and inhalers assume a user’s inhalation flow rate is at or about 28.3 LPM. In practice however, inherent inspiratory flow is much greater than 28.3 LPM and typically rises to more than 60 LPM. Faster inspiration by a user reduces the time available for the dose to dwell in the lungs and results in undesirable amounts of the dose impacting areas other than the lungs, for example in the throat and mouth.
  • Flow rate indicating valves that include reed or whistle feedback mechanisms may be used to signal a user to reduce their inhalation flow rate.
  • reed or whistle feedback mechanisms may be confusing or impractical for some environments and users.
  • the reed and whistle feedback may not be practical in loud environments or for users with auditory or visual impairment.
  • the reed and whistle feedback mechanisms further do not prevent misuse by excessive inhalation flow rate and only indirectly measure flow through the valve into the patient’s mouth.
  • a flow rate control valve may be used to encourage users inhale at a desired flow rate or within a range of desired flow rates.
  • a desirable inspiratory flow rate for an inhaler may be less than about 60 LPM, less than about 30LPM, or less than about 15LPM.
  • a flow rate above a desirable threshold may reduce distal lung dose delivery by about 150% to about 300%, and may cause the dose to impact areas other than the lungs, for example the mouth and throat.
  • a flow rate control valve may achieve flow control to a desired range through conversion of flow energy into a flexible closure resonant vibration.
  • the flow rate control valve may be used in connection with a spacer and/or an inhaler to prompt a user to adjust their inhalation flow rate to within an optimal range.
  • a flow rate control valve according to the present disclosure may be used in connection with a spacer or inhaler to provide haptic feedback to users to control flow rate.
  • the haptic feedback or vibration may provide a warning signal that the user’s inspiration flow rate is too high and may prompt the user to correct their inhalation flow rate to within a range where the vibration ceases.
  • a flow rate control valve may help encourage patients to maintain inhalation at a flow rate such as to result in longer, slower and more consistently controlled inspiration.
  • the flow rate control valve may further provide an additional mechanism for mechanically restricting flow if the user’s inhalation exceeds an upper limit.
  • a flow rate control valve includes a housing defining a cross-sectional area for fluid flow, and a flexible closure that includes a first end connected to the housing and a second end biased in an open position and moveable between i) the open position, and ii) a vibration position. Fluid flowing through the housing moves the second end from the open position to the vibration position when the fluid flow rate is at a vibration-inducing flow rate.
  • the present disclosure provides a housing defining a cross- sectional area for fluid flow, and, a flap connected to the housing and comprising a spring constant of from about 25 N/m to about 650 N/m.
  • a fluid flow rate from about 15 LPM to about 60 LPM is sufficient to induce the flap to vibrate.
  • Figures 1A and 1 B illustrate perspective views of example flow rate control valves according to embodiments of this disclosure.
  • Figure 2 illustrate a front view of an example flow rate control valve according to embodiments of this disclosure.
  • Figure 3A illustrates a flow rate control valve with a flexible closure in an open position according to embodiments of this disclosure.
  • Figure 3B illustrates a flow rate control valve with a flexible closure in a vibration position according to embodiments of this disclosure.
  • Figure 3C illustrates a flow rate control valve with a flexible closure in a closed position according to embodiments of this disclosure.
  • Figure 4 illustrates a flow rate control valve with a by-pass control aperture according to embodiments of this disclosure.
  • Figure 5 is a graph comparing a traditional prior art valve and a flow rate control valve according to embodiments of this disclosure, under the same inspiratory power.
  • Figure 6 is a graph displaying a flexible closure spring characterization relative to vibration onset flowrate.
  • Figure 7A illustrates an open clamshell collapsible chamber design with an integrated flow rate control valve according to embodiments of this disclosure.
  • Figure 7B illustrates a closed clamshell collapsible chamber design with an integrated flow rate control valve according to embodiments of this disclosure.
  • Figure 8A illustrates an exemplary holding chamber in an un-collapsed open position.
  • Figure 8B illustrates the exemplary holding chamber in a collapsed position, where the chamber is collapsed perpendicular to the airflow.
  • Figure 8C illustrates the exemplary holding chamber in a collapsed position, where the chamber is collapsed parallel to the airflow.
  • Figure 9A illustrates a device according to embodiments as disclosed herein comprising a chamber with expendable bellows in a non-expanded position.
  • Figure 9B illustrates a top half of a device as disclosed herein comprising a chamber with expanded bellows.
  • Figure 10A illustrates an open inhaler port on an expandable bellow chamber, in the expanded position, according to embodiments described herein.
  • Figure 10B illustrates the inhaler port of Figure 9A in the closer position.
  • Figure 11 illustrates a cross-sectional side view of an inhaler port with and without an inhaler, wherein the port is on a device with expandable bellows as described in this disclosure.
  • Figure 12A illustrates a nasal occlusion face mask according to embodiments disclosed herein.
  • Figure 12B illustrates a nasal occlusion face mask associated with a flow rate control valve and collapsible bellows chamber according to embodiments disclosed herein.
  • Figure 13 illustrates a ratchet style height adjustment for a nasal occlusion face mark according to embodiments disclosed herein.
  • Figure 14A illustrates an example flow rate control valve connected to an inhaler and a holding chamber according to embodiments of this disclosure.
  • Figure 14B illustrates an example flow rate control valve connected to an inhaler according to embodiments of this disclosure.
  • Figures 15 illustrate a perspective and cross-sectional view of an example flow rate control valve according to embodiments of this disclosure.
  • the present disclosure provides a flow rate control valve that includes a housing defining a cross-sectional area for fluid flow, and a flexible closure that includes a first end connected to the housing and a second end biased in an open position and moveable between i) the open position, and ii) a vibration position. Fluid flowing through the housing moves the second end from the open position to the vibration position when the fluid flow rate is at a vibration-inducing flow rate.
  • fluid as discussed herein comprises gaseous fluid, for example gases and aerosols.
  • the flexible closure may be integrally formed with a housing or formed separately and attached to a housing at one end.
  • the flexible closure may be made of a flexible material, such as for example plastic or silicone.
  • the flexible closure may be made of a rigid material but constructed such that it is thin enough to provide the desired flexibility and vibration.
  • the flexible closure may comprise a rigid plate, a conventional hinge, and an externally attached spring tuned to achieve the desired vibration.
  • the flexible closure may function similar to a spring.
  • the flexible closure may be sized and shaped to have a spring constant of from about 25 N/m to about 650 N/m, for example about 50N/m to about 500N/m, or from about 100 N/m to about 300 N/m, for example from about 150 N/m to 250 N/m, or from about 160N/m to about 200 N/m.
  • the spring constant k of the flexible closure may be determined for example by the thickness, length and elastic modulus of the material of the flexible closure.
  • the spring constant may be used to dictate the balance of forces needed between the inspiratory pressure and the balancing force of the flexible closure such that the flexible closure resonates in phase with the pressure forces acting against it.
  • the spring constant may be measured at or near an end of the flexible closure, for example at the part of the flexible closure furthest away from the connection point of the flexible closure and the housing. In other examples an even smaller spring constant may be needed, for example a spring constant of about 5N/m may be sufficient when the surface area of the flexible closure is small. Similarly, a larger surface area may require a larger spring constant to achieve vibration of the flexible closure at a desired flow rate.
  • a first end of the flexible closure may be thicker than a second end of the flexible closure.
  • the first end may be located for example at the part of the flexible closure closest to the connection point of the flexible closure and the housing, and the second end may be located for example at the part of the flexible closure furthest away from the connection point of the flexible closure and the housing.
  • the flexible closure may comprise a pie-shaped cross-section, such that the first end is thicker than the second end, or such that the second end tapers to a point from the first end.
  • the second end may be about 30% to about 90% the thickness of the first end, or the second end may be about 50% to about 80% the thickness of the first end, or the second end may be about 70% the thickness of the first end.
  • the flexible closure may have a uniform thickness.
  • the flexible closure may have a symmetric or asymmetric profile.
  • the flexible closure may comprise a uniform thickness up until a specified position and then flow into a tapered second end.
  • the flexible closure may have a tapering body from a first end towards a second end, and a further tapered tip that begins a distance from the end of the second end.
  • a tapered second end, or tapered tip may help provide an improved seal when the flexible closure is in a closed position as the tapered end more easily abuts against an orifice plate or a contact surface, as further discussed in this disclosure.
  • a second end before the start of a tapered tip may be a distance from the orifice plate that is equal to a thickness of a first end of the flexible closure.
  • a tapered flexible closure (with or without an additional tapered tip) may form an angle with an adjacent orifice plate. A larger angle may result in a greater inspiratory flow rate before a vibration inducing flow rate is reached.
  • a thicker flexible closure may similarly increase the flow rate required to reach a vibration inducing flow rate.
  • the flexible closure may be for example, a flap that extends from the housing from a first end, for example a cantilevered flap, or may be separately attached to the housing, for example using a hinge or other means.
  • the present disclosure provides a housing defining a cross-sectional area for fluid flow, and, a flap connected to the housing and comprising a spring constant of from about 25 N/m to about 650 N/m. A fluid flow rate from about 15 LPM to about 60 LPM is sufficient to induce the flap to vibrate.
  • the flexible closure may be a single flexible closure or multiple flexible closures.
  • two or three flexible closures may be formed with or attached to a housing.
  • the limit of the number of flexible closures used may be determined by manufacturing limitations and space in the housing.
  • Multiple flexible closures may provide for haptic feedback at different flow rates.
  • the two flexible closures may be configured to have different trigger set points.
  • a first flexible closure may be configured to trigger at 10LPM, for example, to indicate that a user is inhaling at an acceptable flow rate, while a second flexible closure may be configures to trigger at 60LPM, for example, to indicate that the user is inhaling at a flow rate that is too high.
  • a middle column between the flexible closures may be included to split the orifice plate in half such as to form two orifices, each orifice aligned with each of the flexible closures.
  • a small gap may exist between each flexible closure and the orifice plate, for example between the flexible closure and the middle column, when the flexible closures are in a closed position. The small gap may be helpful to provide a path of least resistance, and the most direct flow path, for drug particles through the flow rate control valve which aligns with the location where the highest density, for example the highest number of drug particles, exit the aerosol device (i.e. inhaler).
  • the highest impact density area of drug particles when a user inhales is the center of the valve.
  • this highest density of particles would contact the center of the flexible closure and the particles could lose speed before reaching the user’s lungs.
  • the highest density of particles may benefit from a path of least resistance through the gaps formed between each of the flexible closures and the middle column.
  • an optimized path of least resistance may be formed for the drug delivery by maintaining gaps between the flexible closures and the orifice plate, including between the flexible closures and the middle column (or columns).
  • Multiple flexible closures covering the area of a single flexible closure may further benefit from comprising a more flexible base compared to a single flexible closure with the same dimensional constraints.
  • the narrower flexible closures comprise a relatively longer moment arm providing a higher degree of flexibility. The higher moment arm allows the flexible closure to react to more limited fluid flow rates as compared to the lower moment arm for a single flexible closure.
  • the housing of a flow rate control valve may be formed in a single piece or multiple pieces.
  • the housing may form an air tight or virtually air tight seal around the flexible closure.
  • air or aerosols that enter the housing may not escape the housing other than by passing past the flexible closure or through an optional fail safe or by-pass control, as further described in this disclosure.
  • the flow rate control valve, including the flexible closure and housing is made entirely of an anti-static material in order to minimize aerosol attraction and adherence to the valve.
  • the cross-sectional area for fluid flow defined by the housing may define a flow path connecting a user interface, for example a mouthpiece for the user, to an inhaler opening or port, such that in use, a dose may flow from the inhaler to the user’s mouth.
  • the housing may be connected to or integral with a spacer or inhaler.
  • the cross-sectional area may be further narrowed by one or more contact surfaces forming an orifice plate within the housing.
  • the contact surfaces may be proximate to the flexible closure in the housing, such as to form a seal when the flexible closure abuts the contact surfaces.
  • the contact surfaces may be for example upstream or downstream in the direction of inhalation from the flexible closure.
  • the orifice plate or contact surfaces may define an open area for fluid flow downstream or upstream of the flexible closure.
  • a seal between the orifice plate or contact surfaces and the flexible closure may be formed to substantially close the open area for fluid flow.
  • a seal may be formed when no fluid, or virtually no fluid, for example less than 10% of fluid, is able to pass through the cross sectional area (not accounting for any bypass control).
  • “orifice plate” and “contact surfaces” may be used interchangeably to describe the contact surface against which the flexible closure abuts when in a closed position.
  • the flow rate control valve according to this disclosure may be used to control a user’s inspiratory flow rate using a haptic or vibrational feedback system.
  • the flow rate control valve may be used to encourage a user to inhale at a predetermined flow rate or range of flow rates using, for example, biofeedback and muscle training.
  • the predetermined flow rate may be below a vibration inducing flow rate such that when a user’s inspiratory flow rate is above a vibration inducing flowrate the valve vibrates, providing the user with a mechanical indication that their inspiratory flow rate is above a desired threshold and prompts the user to lower their inhalation rate. Once a user lowers their inhalation rate below the vibration inducing flowrate, the vibrations cease.
  • the predetermined flow rate or range of flow rates may be at or above the vibration inducing flow rate such that when a user’s inspiratory flow rate corresponds to a vibration inducing flowrate, the valve vibrates, providing the user with a mechanical indication to maintain their inspiratory flowrate.
  • the flow rate control valve may provide haptic or vibrational feedback when the user’s inhalation rate is from about 20 to about 30 LPM, but not when the inhalation rate is outside of this range.
  • the vibration threshold may be for example, from about 15LPM to about 60LPM, for example, from about 20LPM to about 50LPM, or about 30LPM.
  • the neutral or equilibrium position of the flexible closure when the flexible closure is at rest and there is no inspiratory flow, or the inspiratory flow is below a threshold, for example below about 15LPM, is the open position.
  • a threshold flow rate for example a flow rate above a vibration inducing flow rate, for example above about 15LPM or above about 30LPM, and up to about 60LPM
  • the flexible closure may move into a vibration position.
  • the flexible closure may begin to move from the open position into the vibration position within about 10% of a vibration inducing flow rate.
  • an inspiratory flow rate of about 10LPM will result in the flexible closure remaining in the open position or stationary in its starting open position, however as the user’s inspiratory flow moves into within 10% of the vibration inducing flow rate, for example 15LPM, the flexible closure moves into a vibration position.
  • the vibration inducing flow rate may be determined or selected for suitability with the user based on the spring constant of the flexible closure.
  • a portion of the kinetic airflow energy is converted to deflect the spring at its resonant frequency.
  • the flexible closure In a vibration position, the flexible closure may extend back and forth, towards the orifice plate without contacting the orifice plate and past equilibrium in the opposite direction. The vibrations of the flexible closure provide haptic feedback to the user.
  • the haptic feedback may trigger a warning or cue for the user that their inspiratory flow rate is in excess and thereby prompts that the user to reduce their inspiratory flow.
  • the flexible closure may vibrate at a range of frequencies, however, the maximum frequency will be its resonance frequency. The whole functional vibration range however may provide feedback to the user.
  • the flexible closure biases to the closed position.
  • the closed position may prevent about 90% of fluid from flowing past the closure (not accounting for any by-pass control).
  • the flexible closure may be sized to cover the entire aperture formed by the orifice plate or at least above 90% of the aperture formed by the orifice plate. In the closed position, the flexible closure may abut or seal against the orifice plate to prevent fluid from flowing past the flexible closure.
  • the flow rate control valve may include a by-pass control. At least one of the orifice plate, the flexible closure and the housing may define for example, a by-pass aperture for fluid flow when the flexible closure is in the closed position. In another example, the closed position of the flexible closure may form a gap between the housing and the flexible closure sufficient to act as a by-pass aperture.
  • the by-pass aperture may be shaped and sized to limit the fluid flow rate to a specified or optimal flow rate. For example, in the event a user’s inhalation far exceeds an optimal inhalation threshold, for example, above a vibration inducing flowrate, such as for example greater than about 60LPM, the valve may close and force the user to inhale only through the by-pass aperture.
  • the by-pass aperture provides a failsafe to restrict the flowrate of the inhaled dose even when the user’s inhalation far exceeds a desired rate.
  • the fluid dose from the inhaler in such cases will be forced to move through only the by-pass aperture that is sized and shaped to control the flowrate to a specified amount.
  • the flow rate control valve may comprise a check valve.
  • the check valve may be positioned downstream, in the direction of inhalation, from an orifice plate.
  • the check valve may be formed separately and attached to the housing or formed integrally with the housing.
  • a plate on a conventional hinge with an externally attached spring for example, may be used for the check valve.
  • the check valve may be a flap. At rest or without any inspiratory flow, the check valve is closed. The closed position may be defined as the check valve abutting against the orifice plate to form a seal. In another example, the check valve may be closed by sealing against another separate contact surface other than the orifice plate.
  • the check valve Since the check valve is at equilibrium or at rest in the closed position, it does not oscillate or vibrate like the flexible closure.
  • the check valve is either in an open position when the user inspires or a closed position when there is no inspiration flow.
  • the spring constant of the check valve may be tuned such that a user’s natural inspiratory flow exceeds the force required to open the valve, quickly or immediately and causes the check valve to open.
  • the check valve may function to ensure that any fluid such as air, mist, or aerosols introduced into the housing from, for example an inhaler, remain in the housing or in an attached chamber, without escaping into the atmosphere when there is no inhalation.
  • the check valve may also function to control the direction of flow and helps prevent a user’s exhalation from passing back through the check valve, the flexible closure or into any attached chamber or inhaler.
  • the check valve may be complemented by an exhalation port.
  • an exhalation port may be present without a check valve.
  • the exhalation port provides a means for expelling a user’s exhalation that enters the housing before it flows back past the flexible closure.
  • the exhalation port may be for example formed in the housing proximate to the user’s mouthpiece.
  • the check valve may comprise one or multiple check valves.
  • the effort to open the check valve during inhalation may be reduced as compared to a single check valve.
  • a lower flow rate may be capable of opening multiple check valves as compared to a single check valve.
  • a more flexible base may be used for multiple smaller check valves as compared to a single check valve with the same dimensional constraints, and may enhance the moment arm with limited flow rate.
  • Figures 1A, 1 B, and 2 illustrate perspective and front views of example flow rate control valves according to embodiments of this disclosure.
  • Each of Figures 1A, 1B and 2 shows a housing and one or more flexible closures. However for the purpose of illustration and identification of parts, the upper half of the housing in Figures 1 A, 1 B, and 2 is omitted.
  • Figure 1A depicts a flow rate control valve 100a according to an embodiment comprising a single flexible closure 101a.
  • the flow rate control valve comprises a housing 102a defining a cross-sectional area 104a for fluid flow.
  • Figure 1A shows two vertical contact surfaces 106a and a horizontal contact surface 107a connecting the bottom of the two vertical contact surfaces to form the lower and side portions of an orifice plate.
  • An additional horizontal contact surface connecting the top of the two vertical contact surfaces may be added, for example from an upper half of the housing. Any one or more of the contact surfaces may be omitted in other examples so long as a substantial seal may be formed when the flexible closure is in a closed position (as described herein).
  • the orifice plate may be formed in a single piece with a cut-out or hole defining a narrowed cross- sectional area wherein when the flexible closure is in a closed position, the open area for fluid flow is substantially sealed.
  • multiple contact surfaces may be connected to one another to form an orifice plate with an open area for fluid flow that is substantially sealed when the flexible closure is in a closed position.
  • Figure 1B depicts a flow rate control valve 100b according to an embodiment comprising two flexible closures 101b.
  • the flow rate control valve comprises a housing 102b defining two cross-sectional areas 104b for fluid flow.
  • Figure 1B shows three vertical contact surfaces 106b and a horizontal contact surface 107b connecting the bottom of the three vertical contact surfaces to form the lower, side and middle column portions of an orifice plate.
  • An additional horizontal contact surface connecting the top of the three vertical contact surfaces may be added, for example from an upper half of the housing. Any one or more of the contact surfaces may be omitted or added in other examples, such as when more or less than two flexible closures are used.
  • each of the flexible closures When more than one flexible closure is sealed, the closed position of each of the flexible closures may allow for a gap for fluid to flow between the side edges of the flexible closures and the vertical contact surfaces of the orifice plate.
  • a gap 110b may be formed between the side edges of each of the flexible closures and the middle column of the orifice plate.
  • the orifice plate may be formed in a single piece with cut-out or holes defining narrowed cross-sectional areas wherein when the flexible closures are in a closed position, the open area for fluid flow is substantially sealed other than the small gaps formed between the vertical contact surfaces and the edges of the flexible closures.
  • multiple contact surfaces may be connected to one another to form the orifice plate with open areas for fluid flow that is substantially sealed except for the small gaps as described above, when the flexible closure is in a closed position.
  • the small gap may be helpful to provide a pathway of least resistance for the greatest proportion of drug particles since the highest impact density area of drug particles when a user inhales is the center of the valve.
  • the highest density of particles may benefit from a path of least resistance through the small gaps formed between each of the flexible closures and the middle column.
  • an optimized path of least resistance may be formed for the drug delivery by maintaining these small gaps between the flexible closures and the orifice plate, including between the flexible closures and the vertical contact surfaces.
  • Figure 2 illustrates a front view of the flow rate control valve according to an example as disclosed herein with a single flexible closure.
  • Other embodiments may include 2 or more flexible closures.
  • the orifice plate 210 and flexible closure 208 are positioned proximate to a mouthpiece 212 (only aperture for mouthpiece pictured).
  • a check valve may be positioned between the mouthpiece 212 and the orifice plate 210.
  • Two or more check valves may be used in other embodiments.
  • the flow rate control valve according to any embodiment as described herein may further include a bypass control, for example a by-pass aperture in the orifice plate, in the one or more flexible closures or in the housing.
  • an aperture sufficient to act as a by-pass control may be alternatively or additionally formed by the flexible closure and the orifice plate when the flexible closure is in the closed position, for example, as a small gap between the flexible closure and the orifice plate.
  • Figures 3A-3C provide an example flow rate control valve 300 in various positions.
  • the flow rate control valve according to this embodiment comprises a flexible closure 308 upstream (in the direction of inspiratory flow) of an orifice plate 310.
  • the flow rate control valve as shown in Figures 3A-3C also includes a check valve 314 positioned downstream of the orifice plate such that the orifice plate 310 is positioned between the flexible closure 308 and the check valve 314.
  • the flexible closure may be positioned downstream of the orifice plate.
  • the flexible closure as shown in Figures 3A-3C tapers about 30% from a first end towards a second end and then further tapers to a tip that is about 40% the thickness of the first end.
  • the flexible closure abuts the orifice plate 310 at a first end and extends away from the orifice plate a distance at the second end, when in the open position, as shown in Figure 3A.
  • the flexible closure 308a as shown in Figure 3A starts in an open position when the flow rate control valve is not in use or when a user’s inspiratory flow is below a vibration inducing flow rate.
  • a vibration flow rate for example when the user’s inhalation flow rate is above about 15LPM or above about 30LPM, and up to about 60LPM
  • the flexible closure 308b moves into a vibration position as shown in Figure 3B.
  • the flexible closure oscillates about its equilibrium (or open) position by moving towards the orifice plate without contacting the orifice plate and in the opposite direction past equilibrium.
  • the oscillation causes mechanical vibrations of the flow rate control valve which may be used to indicate to a user that their inhalation is above a desired inhalation flowrate.
  • the flexible closure may begin to move from the open position into the vibration position within about 10% of the vibration inducing flow rate. The vibrations remind or prompt the user to reduce their inhalation flow rate. If the user increases their flow rate substantially above the vibration inducing flow rate, for example above about 60LPM, the flexible closure moves to a closed position by contacting and sealing against the orifice plate.
  • Figure 3C depicts a flow rate control valve with a flexible closure 308c in the closed position. In a closed position, the flexible closure substantially prevents fluid from flowing through the housing 302, past the closure.
  • the flow rate control valve includes a bypass control aperture 416.
  • the by-pass control aperture 416 is formed in the orifice plate 410 in Figure 4, however in other examples the by-pass control aperture may be formed in the housing 402, or in the flexible closure 408.
  • the closed position of the flow rate control valve may form a gap between the housing and the flexible closure sufficient to act as a by-pass control aperture.
  • the by-pass aperture is sized and shaped to limit the fluid flow to a specific or optimal flow rate, such as for example less than about 40 LPM, for example about 20LPM or for example about 10LPM.
  • Figure 5 is a graph comparing a traditional prior art valve 510 and a flow rate control valve 520 according to embodiments as disclosed herein, under the same inspiratory power.
  • the flow rate control valve according to this example remained in an open position without increasing inspiratory effort (see lower line), it then moved into a vibration position when a user’s inhalation increased to about 30LPM. The vibrations caused the user to reduce their inhalation flow to the optimal rate based on the perceptible vibratory feedback to the user.
  • the prior art device in this case is an AeroChamber® by Trudell Medical International which comprises a chamber but no flow control.
  • the AeroChamber® allowed for inspiratory flow well above an optimal flow threshold as the user’s inherent inspiratory flow was much greater than the desired flow for metered dose inhalation. It is suggested that the AeroChamber® may result in poor distal lung dose delivery and impaction in areas other than the lungs, for example the mouth and throat, because the user’s inhalation is above a desired flow rate.
  • An exemplary flow rate control valve according to this disclosure was constructed with a flexible closure comprising a material with an 80MPa elastic modulus, an area of 472mm A 2 and a thickness as depicted in Figure 3A-C. Exemplary spring constants and related vibration inducing flow rates are depicted in Table 1.
  • the flow rate control valve may be constructed with an integrally attached spacer or aerosol chamber.
  • the device may be constructed in a single piece or multiple pieces, for example, the device may be formed in as few as a single injection molded part.
  • Figures 7A and 7B illustrate an example clamshell design where the chamber and flow rate control valve are integrally formed from a single material.
  • Figure 7A illustrates the clam shell design in an open configuration, wherein the two halves of the device are connected by a living hinge 720.
  • the check valve in this example is integral with a first half 702a, while the flexible closure is integral with a second half 702b.
  • the flow rate control valve may be constructed by the union of the first half and the second half by folding the shell design in half over the living hinge 720.
  • Figure 7B illustrates the closed design.
  • the flow rate control valve is proximate to the user interface mouthpiece 722.
  • An exhalation port 724 is also included in this example.
  • the exhalation port allows a user to exhale without removing the device from their mouth. During exhalation, the exhalation port opens to expel air while the check valve remains closed to prevent exhalation air from entering the chamber 726.
  • the flow rate control valve may be constructed with an integrally or separately attached holding chamber comprising a variable volume.
  • the holding chamber’s volume may be varied by way of expandable (and collapsible) bellows.
  • the variable volume chamber may provide a compact solution to the cumbersome size problem of prior art holding chambers.
  • a chamber comprising expandable bellows may collapse to make the holding chamber compact enough for portability and travel, while remaining large enough in the expanded position to provide a required tidal volume.
  • the expandable bellows may be partially or fully expanded to account for different tidal volume needs. For example, patients of different ages have differing tidal volumes, meaning they require a different number of breaths to clear a device of a fixed volume. Enabling the chamber to have not just one opened position, but two or more, wherein at least one is for a pediatric or lower tidal volume setting, and another is more suited for adults with larger tidal volumes, would be beneficial for universal usage. For example, in one position the device may be open to about a 100mL volume, in another it may be open to about a 300mL volume.
  • the chamber may be expandable and collapsible in a direction parallel to a fluid flow path such as a chamber with expandable bellows arranged such that the bellows expand in the direction parallel to the fluid flow path.
  • a fluid flow path such as a chamber with expandable bellows arranged such that the bellows expand in the direction parallel to the fluid flow path.
  • the chamber volume varies by expanding or collapsing the chamber parallel to the direction of the fluid flow path, the distance between an inhaler port and a mouthpiece may increase or decrease based on the expansion or collapse of the chamber.
  • the chamber may be expanded or collapsed in a direction that is perpendicular to the fluid flow path, such as a chamber with expandable bellows arranged such that the bellows expand in a direction perpendicular to the direction of the fluid flow path.
  • the distance between an inhaler port and a mouthpiece remains relatively unchanged.
  • Varying the volume of the chamber for example by arranging the expandable bellows, in a direction perpendicular to the direction of the fluid flow path may reduce aerosol impaction as compared to holding chambers with expandable bellows parallel to the fluid flow path.
  • geometry that folds parallel to the airflow shortens the distance between the aerosol source (for example an MDI) and the opposing side of the chamber, which may have an adverse effect on the amount of medication that is deposited on the inside of the chamber.
  • the 3D printed chambers represented a holding chamber in an un-collapsed open position (Figure 8A), and two chambers collapsed to 50% volume of the non-collapsed chamber. The latter were created as follows: the first represented a chamber collapsed perpendicular to airflow ( Figure 8B), and the second represented a chamber collapsed parallel to airflow (Figure 8C).
  • Each chamber was placed on top of an aluminum- based deposition sheet, intended to collect the aerosolized particles at impaction.
  • the aerosolized deodorant was sprayed through the three chambers and at completion, each element of the experimental set up was weighed to determine the total mass that had been collected inside the chambers versus the spray that impacted the deposition sheet. Summary results of the experiment are shown below in Table 2 below. Table 2: Summary table of results from dry particle deposition testing
  • Figures 9A and 9B illustrate an example of expandable bellows that expand in a direction that is perpendicular to the fluid flow path.
  • Figure 9A illustrates the expandable bellows 950 in a closed or non-expanded position 952.
  • Figure 9B illustrates a top half of the device with the bellows 950 in the expanded position 954 (bottom half omitted but may be symmetrically expanded or asymmetrical expanded).
  • a truncated cone or funnel shape of the expanded expandable bellows in a direction perpendicular to the flow of fluid, for example as shown in Figure 9B, may further provide central dilation to enable particle expansion, and a slow funneling of particles into the mouthpiece.
  • the bellows comprise angled ringed portions connected by living hinges to form the chamber.
  • the angled rings can rotate approximately 90 degrees from a folded or collapsed position to an open or expanded position and function to reduce the size of the whole device by a factor of 5, in this example, when folded compared to when open.
  • a rigid center structure is also provided to produce an outward force to prevent unfolding.
  • a port for engaging an inhaler to the expandable bellows may be further provided with any of the flow rate control valves as described herein.
  • the inhaler port may be automatically closed when the expandable bellows are in a folded position and opened with inhaler retention features when the bellows are expanded.
  • the inhaler port may be shaped and sized to accept an inhaler or an inhaler housing (for example an inhaler mouthpiece).
  • the inhaler port 1028 comprises an oval shape that is actionable by the opening (10A) and closing (10B) of opposing bellows 1030 of a holding chamber.
  • the port in the active or open position may be open with rib-like projections to allow the insertion and retention of an aerosol generating device, and in the closed position, may be entirely sealed through the collapse of the device’s volume expanding bellows.
  • the collapse of opposing bellows is configured to cause the edge of the bellows to rotate about 90 degrees and form a seal with the edge of an opposing below such as to help prevent dirt from entering the port when in the closed position.
  • the port is simultaneously open as the bellow edges move away from the port hole.
  • the port seals to help prevent debris from collecting and contaminating the chamber, for example, when not in use.
  • FIG. 11 illustrates a cross-sectional side view of an inhaler port with and without an inhaler, wherein the port is on a device with expandable bellows as described in this disclosure. Additional mechanisms, such as fins shown in Figure 11 for example, can be added to the expandable bellows adjacent to the inhaler port. By placing, for example, 4 additional fins 1144 (2 top, 2 bottom shown in Figure 11), it may be possible to cradle the inhaler when it is in its functional position.
  • More or less fins or other retention means may be used in other examples and with any flow rate control valve as described in this disclosure.
  • the inhaler retention features as disclosed herein may enable more robust accommodation and retention of a variety of inhalers with differing mouthpiece profiles. Further, it may also be feasible for the inhaler cradle fins to serve as the inhaler port closure mechanism to prevent dirt and debris from entering the device.
  • the inhaler port may replace the base of a conventional inhaler “boot” or housing which enables the canister to be actuated directly into the chamber without needing the inhaler housing.
  • boot or housing which enables the canister to be actuated directly into the chamber without needing the inhaler housing.
  • the benefit of this may be particularly seen in hospital settings where the sharing of the same canister across multiple devices/patients may be beneficial. For example, a canister with 120 doses, and an inpatient that only requires acute administration of 8-12 doses, may be able to share the same canister. In the outpatient setting, the canister could feasibly be stored alongside the chamber when not in use, via a standard c-shaped clip.
  • the flow rate control valve according to any of the embodiments disclosed herein may be constructed with the addition of a nasal occlusion face mask.
  • Presently available holding chamber facemasks known in the prior art rely on a design which forms a triangular seal from the bridge of the nose to the lateral edges of the chin. This is known to be variably effective due to the unpredictable facial anatomy that needs to be accommodated, for being intrusive and frightening to some patients, for increasing the dead space, or air that first needs to be inhaled into the lungs prior to the active drug, resulting in lower efficacy with smaller tidal volumes, and resulting in facial discoloration due to exposure of inhaled corticosteroids to the skin unnecessarily.
  • the nasal occlusion facemask according this disclosure may accommodate all facial anatomies with a single design, utilize only the optimal route of drug inhalation, and may minimize the material wasted as these parts are used in extremely high volumes. There is further the opportunity to use the nasal occlusion design as disclosed herein to customize accommodations for unique facial geometries such as facial deformities, or those with additional medical equipment use (for example, with nasal cannulas in place).
  • Figure 12A depicts an example nasal occlusion face mask according to this disclosure which may be used with any flow rate control valve or feature as previously discussed in this disclosure.
  • Figure 12B depicts an example nasal occlusion face mask associated with a flow rate control valve 1210 and collapsible bellows chamber 1230.
  • the nasal occlusion face mask comprises an over the lip mask 1250, which utilizes the lips as a gasket to create an airtight seal, along with a contoured surface 1252 designed to bilaterally occlude the narus.
  • the mouth portion of the mask may accommodate for example, the 95%ile of mouths, and any variation in height from the mouth to the tip of the nose can be accommodated through an adjustable height, for example ratchet style, of the nasal occlusion surface.
  • This ratchet style adjustment 1254 shown in Figure 12A is further depicted in Figure 13 in its various heights.
  • the ratchet style adjustment can be used either manually using height adjustment nuts disposed thereon, or during device use when a seal is formed on the face via a cam-sliding mechanism.
  • the distance between the base of the nose and the central incisor in developed humans varies between about 19mm to about 36mm, while the overall mouth width varies between about 41mm to about 62mm.
  • This T-shaped region of human anatomy is predictable and captures the only airway access attainable by masks.
  • a broad, c-shaped over the lip mask can replace a mask which commonly covers the chin, mouth, and entire nose.
  • a single device with a ratcheting nasal occlusion plate can supplant the need for various different sizes of facemasks, which require substantial pressure to form a seal over a large surface area that is not involved with gas exchange at all, nor anatomically reliable for a universal fit.
  • the nasal occlusion face mask may be adapted to accommodate atypical facial geometries, for example due to deformity (i.e. cleft lip), or obstructions for example the use of nasal cannulas by way of hospital oxygenation.
  • atypical facial geometries for example due to deformity (i.e. cleft lip), or obstructions for example the use of nasal cannulas by way of hospital oxygenation.
  • the use of facial scanning, and personalized 3D printed nasal occlusion masks may also be created. This may enable the ability to not only adapt the nasal occlusion plate, but to enhance the mouth mask fit for those with deformities or obstructions around the mouth.
  • the nasal occlusion face mask is formed in a separate piece as shown in Figure 12A and attached to a chamber as shown in Figure 12B.
  • the nasal occlusion face mask may be integrated with a chamber and deployed with the expansion of the chamber bellows and retracted when not in use.
  • the contoured surface configured to bilaterally occlude the narus may be constructed of a bendable material such that it may conform to differing anatomies.
  • Figures 14A and 14B show other embodiments of flow rate control valves as disclosed herein.
  • the flow rate control valves as shown in Figures 14A and 14B maybe be connected directly to an aerosol producing device, for example to an inhaler 1402, without being in contact with the aerosol dispensed from the inhaler.
  • the aerosol producing device or inhaler 1402 may be connected to the flow rate control valve 1404 at an air-inlet end and a spacer or other aerosol or mist-holding chamber 1406 at an aerosol dispensing end.
  • a user lip surface 1408 may be on an aerosol dispensing end of the aerosol producing device 1402 with the flow rate control valve 1404 disposed on an air-inlet end.
  • the flow rate control valve of Figures 14A and 14B is shown in Figure 15 as detached from the aerosol producing device.
  • Figure 15 shows both a perspective and crosssection view of the flow rate control valve.
  • the flow rate control valve 1500 according to this embodiment comprises an orifice plate 1502 and flexible closure 1504 as previously disclosed however, in this embodiment, the orifice plate and flexible closure are disposed upstream (in the direction of inhalation) from the aerosol producing device, for example, at an air inlet end of an inhaler.
  • This configuration may be helpful in controlling a user’s inhalation rate without contacting the drug aerosol expelled from the aerosol producing device, which could otherwise contact the flexible closure.
  • Drug delivery may be optimized by avoiding loss of drug particles contacted with the flexible closure.
  • This embodiment may further be helpful as an addition for a device comprising an inhaler with a conventional holding chamber and check valve, and may be added to the top of the inhaler and removed as desired.
  • a user may choose to add the flow rate control valve to the inhaler for training purposes and remove the flow rate control valve when the user is sufficiently comfortable with an acceptable inhalation range.
  • the flow rate control valve 1500 may comprise a housing 1506 configured to attached to an air inlet end of an aerosol producing device, for example, the housing may be configured to attach to the plastic holder of an inhaler.
  • Inhalers typically include a canister that must be actuated to release the drug aerosol to the user.
  • the flow rate control valve housing may be attached to the air inlet end of the inhaler above the canister.
  • the housing may comprise a flexible diaphragm 1508 that is aligned with the top of the canister such that when a user depresses the flexible diaphragm, an extension of the flexible diaphragm 1508 contacts and actuates the canister to release the drug aerosol to the user through the aerosol dispensing end of the inhaler.
  • the flow rate control valve may comprises one or more flexible closures 1504, such that air inhaled by a user from the air dispensing end of the inhaler enters the housing of the flow rate control valve and thus the air inlet end of the inhaler, via the flexible closure(s).
  • Multiple flexible closures may be configured as previously described in other embodiments of this disclosure.
  • the flexible closure(s) may be adjusted as described in this disclosure to maintain optimal inhalation rates.
  • the flow rate control valve may be used to encourage a user to inhale at a predetermined flow rate or range of flow rates using, for example, biofeedback and muscle training.
  • the predetermined flow rate may be below a vibration inducing flow rate such that the valve vibrates when a user’s inspiratory flow rate is above a vibration inducing flowrate, providing the user with a mechanical indication that their inspiratory flow rate is above a desired threshold and prompting the user to lower their inhalation rate. Once a user lowers their inhalation rate below the vibration inducing flowrate, the vibrations cease.
  • the predetermined flow rate or range of flow rates may be at or above the vibration inducing flow rate such that the valve vibrates when a user’s inspiratory flow rate corresponds to a vibration inducing flowrate, providing the user with a mechanical indication to maintain their inspiratory flowrate.
  • a user may begin to inhale before actuating the aerosol producing device by depressing the diaphragm, and only actuating the diaphragm when the optimal inhalation flow rate is reached based on the feedback provided by the vibrations of the flexible closure.
  • the vibration trigger points may be selected to account for whether the inhaler is also attached to a holding chamber or if it is to be in direct contact with a user’s mouth or with a face mask. For example, inhalers used without a holding chamber need to be inhaled at a higher flow rate as compared to when a holding chamber is used, to ensure that the drug is delivered to the lungs. In such case, the vibration trigger point is selected for the flexible closure to maintain the optimal increased flowrate.
  • the flow rate control valve may be used as a device for delivering a medicated aerosol or mist to a user.
  • the flow rate control valve may be directly connected to an inhaler (for example, a pressurized metered dose inhaler) or connected to a spacer, such as an expandable bellows spacer, that is connected to an inhaler.
  • the spacer is upstream of the flow rate control valve, and the inhaler is upstream of the spacer, in the direction of inspiratory flow.
  • the device may be used for the treatment or prevention of asthma, chronic obstructive pulmonary disease or any other treatment requiring dose delivery through the pulmonary system.

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Abstract

L'invention concerne une soupape de régulation de débit comprenant une fermeture souple. La fermeture souple étant mobile entre une position ouverte et une position de vibration. La position de vibration fournissant une rétroaction haptique à un utilisateur pour signaler un débit inspiratoire supérieur à un débit souhaité. La soupape de régulation de débit peut être utilisée en liaison avec un inhalateur ou une entretoise de dose mesurée sous pression pour fournir, par exemple, une inspiration plus longue, plus lente et constamment contrôlée par restriction d'écoulement et conversion de puissance d'écoulement en un mouvement vibratoire.
PCT/CA2023/051198 2022-09-12 2023-09-08 Soupape de régulation de débit de rétroaction haptique WO2024055101A1 (fr)

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Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5042467A (en) * 1990-03-28 1991-08-27 Trudell Medical Medication inhaler with fitting having a sonic signalling device
US5483954A (en) * 1994-06-10 1996-01-16 Mecikalski; Mark B. Inhaler and medicated package
WO2010070496A1 (fr) * 2008-12-18 2010-06-24 Koninklijke Philips Electronics, N.V. Chambre de retenue à soupape et masque pour celle-ci
US20120304988A1 (en) * 2011-06-06 2012-12-06 Adam Meyer Oscillating Positive Expiratory Pressure Device
US20170333645A1 (en) * 2016-05-19 2017-11-23 Neritan Alizoti Smart valved holding chamber
US20180161531A1 (en) * 2016-12-09 2018-06-14 Trudell Medical International Smart nebulizer

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5042467A (en) * 1990-03-28 1991-08-27 Trudell Medical Medication inhaler with fitting having a sonic signalling device
US5483954A (en) * 1994-06-10 1996-01-16 Mecikalski; Mark B. Inhaler and medicated package
WO2010070496A1 (fr) * 2008-12-18 2010-06-24 Koninklijke Philips Electronics, N.V. Chambre de retenue à soupape et masque pour celle-ci
US20120304988A1 (en) * 2011-06-06 2012-12-06 Adam Meyer Oscillating Positive Expiratory Pressure Device
US20170333645A1 (en) * 2016-05-19 2017-11-23 Neritan Alizoti Smart valved holding chamber
US20180161531A1 (en) * 2016-12-09 2018-06-14 Trudell Medical International Smart nebulizer

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
PETER HAIDL ET AL.: "Inhalation device requirements for patients' inhalation maneuvers", RESPIRATORY MEDICINE, vol. 118, September 2016 (2016-09-01), pages 65 - 75, XP029707078, Retrieved from the Internet <URL:https://www.sciencedirect.com/science/article/pii/S0954611116301603> DOI: 10.1016/j.rmed.2016.07.013 *

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