US20130255684A2 - Ventilation Mask with Integrated Piloted Exhalation Valve And Method of Ventilating a Patient Using the Same - Google Patents
Ventilation Mask with Integrated Piloted Exhalation Valve And Method of Ventilating a Patient Using the Same Download PDFInfo
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- US20130255684A2 US20130255684A2 US13/431,827 US201213431827A US2013255684A2 US 20130255684 A2 US20130255684 A2 US 20130255684A2 US 201213431827 A US201213431827 A US 201213431827A US 2013255684 A2 US2013255684 A2 US 2013255684A2
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- ventilator
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- nasal interface
- diaphragm
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/20—Valves specially adapted to medical respiratory devices
- A61M16/208—Non-controlled one-way valves, e.g. exhalation, check, pop-off non-rebreathing valves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/06—Respiratory or anaesthetic masks
- A61M16/0605—Means for improving the adaptation of the mask to the patient
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/03—Detecting, measuring or recording fluid pressure within the body other than blood pressure, e.g. cerebral pressure; Measuring pressure in body tissues or organs
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/087—Measuring breath flow
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs
- A61B5/097—Devices for facilitating collection of breath or for directing breath into or through measuring devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/48—Other medical applications
- A61B5/4836—Diagnosis combined with treatment in closed-loop systems or methods
-
- 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. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/06—Respiratory or anaesthetic masks
- A61M16/0605—Means for improving the adaptation of the mask to the patient
- A61M16/0616—Means for improving the adaptation of the mask to the patient with face sealing means comprising a flap or membrane projecting inwards, such that sealing increases with increasing inhalation gas pressure
- A61M16/0622—Means for improving the adaptation of the mask to the patient with face sealing means comprising a flap or membrane projecting inwards, such that sealing increases with increasing inhalation gas pressure having an underlying cushion
-
- 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. mouth-to-mouth respiration; Tracheal tubes
- A61M16/06—Respiratory or anaesthetic masks
- A61M16/0666—Nasal cannulas or tubing
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- A—HUMAN NECESSITIES
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- 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. mouth-to-mouth respiration; 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
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; 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. mouth-to-mouth respiration; Tracheal tubes
- A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
- A61M16/0875—Connecting tubes
-
- 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. mouth-to-mouth respiration; Tracheal tubes
- A61M16/10—Preparation of respiratory gases or vapours
- A61M16/1045—Devices for humidifying or heating the inspired gas by using recovered moisture or heat from the expired gas
-
- 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. mouth-to-mouth respiration; Tracheal tubes
- A61M16/20—Valves specially adapted to medical respiratory devices
- A61M16/201—Controlled valves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/20—Valves specially adapted to medical respiratory devices
- A61M16/201—Controlled valves
- A61M16/207—Membrane valves with pneumatic amplification stage, i.e. having master and slave membranes
-
- 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. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/0027—Accessories therefor, e.g. sensors, vibrators, negative pressure pressure meter
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3331—Pressure; Flow
- A61M2205/3334—Measuring or controlling the flow rate
Definitions
- the present invention relates to systems and methods for controlling delivery of a pressurized flow of breathable gas to a patient and, more particularly, to a ventilation mask such as a nasal mask, nasal prongs mask or nasal pillows mask for use in critical care ventilation, respiratory insufficiency or PAP (Positive Airway Pressure) therapy and incorporating a piloted exhalation valve inside the mask.
- a ventilation mask such as a nasal mask, nasal prongs mask or nasal pillows mask for use in critical care ventilation, respiratory insufficiency or PAP (Positive Airway Pressure) therapy and incorporating a piloted exhalation valve inside the mask.
- PAP Personal Airway Pressure
- mechanical ventilators comprise medical devices that either perform or supplement breathing for patients.
- Early ventilators such as the “iron lung”, created negative pressure around the patient's chest to cause a flow of ambient air through the patient's nose and/or mouth into their lungs.
- the vast majority of contemporary ventilators instead use positive pressure to deliver gas to the patient's lungs via a patient circuit between the ventilator and the patient.
- the patient circuit typically consists of one or two large bore tubes (e.g., 22 mm ID for adults; 15 mm ID for pediatric) that interface to the ventilator on one end and a patient mask on the other end.
- the patient mask is not provided as part of the ventilator system, and a wide variety of patient masks can be used with any ventilator.
- the interfaces between the ventilator, patient circuit and patient masks are standardized as generic 15 mm/22 mm conical connectors, the size and shape of which are specified by regulatory bodies to assure interoperability.
- Ventilators using single limb patient circuit are most typically used for less acute clinical requirements, such as treatment of obstructive sleep apnea or respiratory insufficiency. Ventilators using dual limb patient circuits are most typically used for critical care applications.
- Single limb patient circuits are used only to carry gas flow from the ventilator to the patient and patient mask, and require a patient mask with vent holes.
- the pressure/flow characteristics of the vent holes in the mask are maintained according to standards that assure interoperability of masks with a multitude of ventilators that follow the standard.
- the patient inspires fresh gas from the patient circuit, and expires CO2-enriched gas, which is purged from the system through the vent holes in the mask and partially breathed down the tube to the ventilator and re-breathed during the next breath.
- CPAP systems typically have a minimum-required pressure of 4 cmH2O whenever the patient is wearing the mask, which produces significant discomfort, claustrophobia and/or feeling of suffocation to early CPAP users and leads to a high (approximately 50%) non-compliance rate with CPAP therapy.
- the patient inspires fresh gas from one limb (the “inspiratory limb”) of the patient circuit and expires CO2-enriched gas from the second limb (the “expiratory limb”) of the patient circuit.
- Both limbs of the dual limb patient circuit are connected together in a “Y” proximal to the patient to allow a single 15 mm or 22 mm conical connection to the patient mask.
- the ventilator pressurizes the gas to be delivered to the patient inside the ventilator to the intended patient pressure, and then delivers that pressure to the patient through the patient circuit.
- Very small pressure drops develop through the patient circuit, typically around 1 cmH2O, due to gas flow though the small amount of resistance created by the 22 mm or 15 mm ID tubing.
- Ventilators that utilize a dual limb patient circuit typically include an exhalation valve at the end of the expiratory limb proximal to the ventilator.
- the ventilator controls the exhalation valve, closes it during inspiration, and opens it during exhalation.
- Less sophisticated ventilators have binary control of the exhalation valve, in that they can control it to be either open or closed.
- More sophisticated ventilators are able to control the exhalation valve in an analog fashion, allowing them to control the pressure within the patient circuit by incrementally opening or closing the valve. Valves that support this incremental control are referred to as active exhalation valves.
- active exhalation valves are most typically implemented physically within the ventilator, and the remaining few ventilation systems with active exhalation valves locate the active exhalation valve within the patient circuit proximal to the ventilator.
- Active exhalation valves inside ventilators are typically actuated via an electromagnetic coil in the valve, whereas active exhalation valves in the patient circuit are typically pneumatically piloted from the ventilator.
- a mask for achieving positive pressure mechanical ventilation (inclusive of PAP, ventilatory support, critical care ventilation, emergency applications), and a method for a operating a ventilation system including such mask.
- the mask may include a pressure sensing modality proximal to the patient connection.
- Such pressure sensing modality may be a pneumatic port with tubing that allows transmission of the patient pressure back to the ventilator for measurement, or may include a transducer within the mask.
- the pressure sensing port if included in the mask, is used in the system to allow pressure sensing for achieving and/or monitoring the therapeutic pressures.
- the mask may include a flow sensing modality located therewithin for achieving and/or monitoring the patient and/or therapeutic flows.
- the mask of the present invention also includes a piloted exhalation valve that is used to achieve the target pressures/flows to the patient.
- the pilot for the valve is pneumatic and driven from the gas supply tubing from the ventilator.
- the pilot can also be a preset pressure derived in the mask, a separate pneumatic line from the ventilator, or an electro-mechanical control.
- the valve can be implemented with a diaphragm or with a flapper.
- valve inside the mask provides a path for patient-expired CO2 to exit the system without the need for a dual-limb patient circuit, and without the disadvantages associated with traditional single-limb patient circuits. For instance, in applications treating patients with sleep apnea, having the valve inside the mask allows patients to fall asleep while wearing the mask without the treatment pressure turned on, thereby preventing patient discomfort typically experienced with falling asleep while breathing at a positive pressure.
- the sensing described above may be used to sense a predetermined event, such as a set time, the detection of an event indicating patient airway obstruction, or the detection of a patient falling asleep, and start the positive airway pressure therapy upon sensing any such event, unlike existing devices which attempt to alleviate patient discomfort by starting at a lower pressure level (typically 4 cmH2O) and ramping the pressure up to a therapeutic level over a period of time.
- a valve inside the mask mitigates the need to have vent holes within the patient mask (a typical feature of mask used for sleep apnea) coincident with a purge flow to bleed patient expired CO2 from the system.
- Alleviating the mask vent holes and associated extra flow of gas through the mask helps reduce noise generated by the mask, reduce CO2 re-breathing, reduce patient nose dryness cause by excess gas flowing past the patient, and reduce flow requirements of the ventilator.
- Yet another benefit of the mask without vent holes and having the valve inside the same is that because there is not a constant flow through the mask and out of any vent holes, a heat moisture exchanger can also be incorporated into the mask, allowing a simple method of providing heated and humidified gas to the patient.
- valve inside the mask allows for a significant reduction in the tubing size, as it supports the ventilator delivering higher pressures than the patient's therapeutic pressure.
- pressure from the ventilator is significantly higher than the patient's therapeutic pressure.
- Pressure sensing can be implemented inside the mask near the patient interface port(s), facilitating the ventilator to have a means to servo control pressure at the patient interface port(s).
- Having higher pressure from the ventilator and an active exhalation valve in the mask allows for the tubing size to be significantly smaller (e.g. 1-9 mm ID) compared to conventional ventilators (22 mm ID for adults/15 mm ID for pediatric).
- One obvious benefit of smaller tubing is that it provides less bulk for patient and/or caregivers to manage.
- the bulk of the tubing is as significant as the bulk of the ventilator.
- Another benefit of the smaller tubing is that is allows for more convenient ways of affixing the mask to the patient. For instance, the tubing can go around the patient's ears to hold the mask to the face, instead of requiring straps (typically called “headgear”) to affix the mask to the face.
- the discomfort, complication, and non-discrete look of the headgear is another significant factor leading to the high non-compliance rate for CPAP therapy.
- Another benefit to the smaller tubing is that the mask can become smaller because it does not need to interface with the large tubing. Indeed, large masks are another significant factor leading to the high non-compliance rate for CPAP therapy since, in addition to being non-discrete, they often cause claustrophobia.
- FIG. 1 is an isometric view of a nasal pillows mask constructed in accordance with a first embodiment of the present invention and including an integrated diaphragm-implementation piloted exhalation valve;
- FIG. 2 is a front elevational view of the nasal pillows mask shown in FIG. 1 ;
- FIG. 3 is a cross-sectional view of the nasal pillows mask shown in FIG. 2 ;
- FIG. 4 is an exploded, cross-sectional front view of the nasal pillows mask shown in FIG. 3 ;
- FIG. 5 is a front elevational view of a nasal pillows mask constructed in accordance with a second embodiment of the present invention and including an integrated flapper-implementation exhalation valve;
- FIG. 6 is a top plan view of the nasal pillows mask shown in FIG. 5 ;
- FIG. 7 is a bottom plan view of the nasal pillows mask shown in FIG. 5 ;
- FIG. 8 is a cross-sectional, isometric view of the nasal pillows mask shown in FIG. 5 ;
- FIG. 9 is a cross-sectional view of the nasal pillows mask shown in FIG. 5 .
- FIGS. 1-4 depict a ventilation mask 10 constructed in accordance with a first embodiment of the present invention.
- the mask is depicted as a nasal prongs mask, however those skilled in the art will recognize that other ventilation masks are contemplated herein such as nasal pillows masks, nasal masks and oronasal masks and for purposes of this application the term mask and/or ventilation mask will include all such mask structures.
- the term “direct nasal interface mask” will be deemed to encompass those masks which are configured to facilitate the direct introduction of therapeutic fluid pressure into the nostrils of a patent, such masks including, but not being limited to, nasal pillows masks, nasal prongs masks, and nasal cradle masks.
- the mask 10 includes an integrated, diaphragm-implemented, piloted exhalation valve 12 , the structural and functional attributes of which will be described in more detail below.
- the mask 10 comprises a housing 14 which defines first and second fluid flow passages 16 , 18 .
- the flow passages 16 , 18 are formed within the housing 14 to have substantially identical shapes or contours. Although illustrated with a pair of flow passages, 16 , 18 , those skilled in the art will recognize that a single flow passage is additionally contemplated herein.
- one end of each of the flow passages 16 , 18 is defined by a respective one of an identically configured pair of generally cylindrical, tubular protrusions 20 a, 20 b of the housing 14 .
- each of the flow passages 16 , 18 is defined by a respective one of an identically configured pair of connector ports 22 a, 22 b of the housing 14 .
- the connector ports 22 a, 22 b are each sized and configured to accommodate the advancement of a distal end portion of a tubular fluid line 24 therein.
- the operative engagement of a fluid line 24 to each of the connector ports 22 a, 22 b effectively places such fluid lines 24 into fluid communication with respective ones of the flow passages 16 , 18 .
- the spacing between the protrusions 20 a, 20 b is selected to facilitate the general alignment thereof with the nostrils of an adult patient when the mask 10 is worn by such patient.
- the flow passages 16 , 18 are preferably not fluidly isolated from each other. Rather, as also seen in FIGS. 3 and 4 , the housing 14 may define an optional cross passage 26 which extends between the protrusions 20 a, 20 b thereof, and effectively places the flow passages 16 , 18 into fluid communication with each other.
- the cross passage 26 is further placed into fluid communication with ambient air by an optional vent port 28 which is fluidly coupled thereto.
- the vent port 28 is defined by and extends axially through a generally cylindrical boss 30 of the housing 14 which protrudes upwardly between the protrusions 20 a, 20 b thereof.
- the housing 14 of the mask 10 further defines an internal valve chamber 32 which fluidly communicates with the cross passage 26 .
- a tubular projection 34 of the housing 14 disposed at the junction between the cross passage 26 and valve chamber 32 is a tubular projection 34 of the housing 14 .
- the projection 34 defines an annular distal rim or seating surface 36 which is used in the operation of the valve 12 in manner which will be described in more detail below.
- the projection 34 protrudes into the valve chamber 32 , and defines the conduit which places the valve chamber 32 into fluid communication with the cross passage 26 .
- valve chamber 32 is defined in large measure by a valve wall 38 of the housing 14 which is generally oriented between the flow passages 16 , 18 thereof and, when viewed from the perspective shown in FIGS. 1-4 , is disposed below the cross passage 26 .
- the valve wall 38 has a perforated construction, thus facilitating the fluid communication between the valve chamber 32 partially defined thereby and ambient air.
- valve cap 40 which may be removably attached or permanently attached to the distal portion or rim of the valve wall 38 in the manner best seen in FIG. 3 .
- the valve cap 40 includes a pilot port 42 which, when the valve cap 40 is coupled to the valve wall 38 , is placed into fluid communication with the valve chamber 32 .
- the pilot port 42 is partially defined by and extends axially through a generally cylindrical connector 44 of the valve cap 40 . As best seen in FIGS. 3 and 4 , one end of the pilot port 42 is disposed within a generally planar base surface 46 defined by the valve cap 40 .
- valve cap 40 defines a continuous shoulder 48 which, from the perspective shown in FIG. 4 , is elevated above the base surface 46 .
- This embodiment shows a pneumatically piloted diaphragm; it is additionally contemplated that the valve 12 can be driven in an electromechanical manner (e.g., with an electromagnet instead of using the above mentioned pilot port 42 ).
- the mask 10 of the present invention further comprises a diaphragm 50 which resides within the valve chamber 32 .
- the diaphragm 50 has an enlarged, central main body portion 52 , and a peripheral flange portion 54 which is integrally connected to and circumvents the main body portion 52 .
- the flange portion 54 includes an arcuately contoured central region which is oriented between the distal region thereof and the main body portion 52 , and defines a continuous, generally concave channel 56 .
- the diaphragm 50 is preferably fabricated from a suitable resilient material.
- the distal region of the flange portion 54 of the diaphragm 50 which is disposed outward of the arcuate central region thereof is normally captured between the valve cap 40 and the valve wall 38 when the valve cap 40 is operatively engaged to the valve wall 38 . More particularly, as seen in FIG. 3 , the distal region of the flange portion 54 is compressed and thus captured between the shoulder 48 of the valve cap 40 and a lip portion 58 of the valve wall 38 which protrudes inwardly from the inner surface thereof.
- the diaphragm 50 is preferably sized such that when the distal region of the flange portion 54 thereof is captured between the shoulder 48 and lip portion 58 in the aforementioned manner, the arcuate central region of the flange portion 54 is disposed directly adjacent the inner peripheral surface of the lip portion 58 . Additionally, the channel 56 defined by the flange portion 54 is directed toward and thus faces the base surface 46 of the valve cap 40 .
- the diaphragm 50 effectively segregates the valve chamber 32 into a patient side or region 32 a, and a pilot side or region 32 b. More particularly, due to the aforementioned manner in which the diaphragm 50 is captured between the valve cap 40 and the valve wall 38 , the patient and pilot regions 32 a, 32 b of the valve chamber 32 are separated from each other by the diaphragm 50 , and are of differing volumes.
- the fluid conduit defined by the projection 34 communicates directly with the patient region 32 a of the valve chamber 32
- the pilot port 42 defined by the connector 44 communicates directly with the pilot region 32 b of the valve chamber 32 .
- the diaphragm 50 (and hence the valve 12 ) is selectively moveable between an open position (shown in FIG. 3 ) and a closed position. Importantly, in either of its open or closed positions, the diaphragm 50 is not seated directly against the base surface 46 of the valve cap 40 . Rather, a gap is normally maintained therebetween. As seen in FIG. 3 , the width of such gap when the diaphragm 50 is in its open position is generally equal to the fixed distance separating the base surface 46 of the valve cap 40 from the shoulder 48 thereof. When the diaphragm 50 is in its open position, it is also disposed in spaced relation to the projection 34 of the housing 14 , and in particular the seating surface 36 defined thereby.
- the diaphragm 50 may be resiliently deformable from its open position (to which it may be normally biased) to its closed position. It is an important feature of the present invention that the diaphragm 50 is normally biased in its open position which provides a fail safe to allow a patient to inhale ambient air through the valve and exhale ambient air through the valve even during any ventilator malfunction.
- the main body portion 52 of the diaphragm 50 When moved or actuated to the closed position, the main body portion 52 of the diaphragm 50 is firmly seated against the seating surface 36 defined by the projection 34 , thus effectively blocking fluid communication between the cross passage 26 (and hence the flow passages 16 , 18 ) and the valve chamber 32 . More particularly, when viewed from the perspective shown in FIG. 3 , the peripheral region of the top surface of the main body portion 52 is seated against the seating surface 36 , with a central region of the top surface of the main body portion 52 protruding slightly into the interior of the projection 34 , i.e., the fluid conduit defined by the projection 34 .
- the valve 12 in the mask 10 , the valve 12 thereof is collectively defined by the projection 34 , valve wall 38 , valve cap 40 and diaphragm 50 . Additionally, in the mask 10 , it is contemplated that the valve 12 will be piloted, with the movement of the diaphragm 50 to the closed position as described above being facilitated by the introduction of positive fluid pressure into the gap normally defined between the diaphragm 50 and the base surface 46 via the pilot port 42 , i.e., into the pilot region 32 b of the valve chamber 32 . In this regard, it is contemplated that during the use of the mask 10 by a patient, a pilot fluid line (not shown) from a ventilator will be coupled to the connector 44 .
- the fluid pressure level introduced into the pilot region 32 b of the valve chamber 32 via the pilot port 42 will be sufficient to facilitate the movement of the diaphragm 50 to its closed position.
- a biasing spring (not shown) operatively coupled to the main body portion 52 of the diaphragm 50 , and/or positive pressure applied to the main body portion 52 of the diaphragm 50 , will facilitate the movement of the diaphragm 50 back to the open position.
- the movement of the diaphragm 50 to the open position allows the air exhaled from the patient to be vented to ambient air after entering the patient region 32 a of the valve chamber 32 via the perforated openings of the valve wall 38 communicating with the valve chamber 32 .
- the diaphragm 50 travels from a fully open position through a partially open position to a fully closed position.
- the diaphragm 50 will be partially open or partially closed during exhalation to maintain desired ventilation therapy.
- a positive airway pressure can be controlled with any expiratory flow value by modulating the pilot pressure within the pilot region 32 b of the valve chamber 32 and hence the position of the diaphragm 50 .
- pilot pressure is discontinued to the diaphragm, the diaphragm 50 moves to an open position wherein the patient can inhale and exhale through the mask with minimal restriction and with minimal carbon dioxide retention within the mask 10 .
- This feature is highly advantageous for the treatment of obstructive sleep apnea where patients complain of discomfort with ventilation therapy due to mask and pressure discomfort.
- the ventilation therapy can be started (i.e., in an obstructive sleep apnea situation).
- the present invention contemplates a method of ventilation utilizing a mask wherein patient inhalation and patient exhalation is facilitated through the mask to ambient air when the ventilator is not delivering a therapeutic level of pressure.
- additional valving in the mask may be implemented for this purpose. Since the mask does not facilitate CO2 buildup, the ventilator can remain off while the mask is worn by the patient and ventilation therapy can be initiated upon sensing or detecting a patient requirement, such as sleep apnea therapy, by conventional sensors incorporated into the mask and ventilator.
- conventional ventilators can be readily modified via conventional software changes to allow the mask to be worn without supplying pressure to the mask unless and until a patient requirement is sensed and subsequently communicated to the ventilator to provide necessary ventilation to the patient.
- Such modification may additionally require the use of a conventional check valve to ensure that patient exhalation is facilitated through the exhalation valve on the mask and not back into the ventilator delivery circuit.
- the diaphragm 50 is pneumatically piloted, with the position thereof being regulated by selectively modulating the pilot pressure within the pilot region 32 b of the valve chamber 32 .
- alternative modalities such as an electromagnetic actuator, can be used to drive the valve 12 .
- the valve 12 may be driven in an electromechanical manner through the use of an electromagnet instead of using the above-described pilot port 42 .
- valve cap 40 is releasably attached to the valve wall 38 of the housing 14 .
- the selective detachment of the valve cap 40 from the housing 14 allows for the removal of the diaphragm 50 from within the valve chamber 32 as permits the periodic cleaning or disinfection thereof.
- the detachment of the valve cap 40 from the valve wall 38 of the housing 14 also permits access to and the cleaning or disinfection of the interior surfaces of the valve chamber 32 .
- Port 28 provides a means for pressure measurement inside the mask.
- FIGS. 5-9 there is shown a nasal pillows mask 100 constructed in accordance with a second embodiment of the present invention.
- the mask 100 includes an integrated, flapper-implemented exhalation valve 112 , the structural and functional attributes of which will be described in more detail below.
- the mask 100 comprises a housing 114 which defines first and second fluid flow passages 116 , 118 .
- the flow passages 116 , 118 are formed within the housing 114 to have substantially identical shapes or contours.
- a single flow passage is additionally expressly contemplated herein.
- one end of each of the flow passages 116 , 118 is defined by a respective one of an identically configured pair of generally cylindrical, tubular protrusions 120 a, 120 b of the housing 114 .
- each of the flow passages 116 , 118 is defined by a respective one of an identically configured pair of connector ports 122 a, 122 b of the housing 114 .
- the connector ports 122 a, 122 b are each sized and configured to accommodate the advancement and frictional retention of a distal end portion of a tubular fluid line 124 therein.
- the operative engagement of a fluid line 124 to each of the connector portions 122 a, 122 b effectively places such fluid lines 124 into fluid communication with respective ones of the flow passages 116 , 118 .
- the spacing between the protrusions 120 a, 120 b is selected to facilitate the general alignment thereof with the nostrils of an adult patient when the mask 100 is worn by such patient.
- the flow passages 116 , 118 are not fluidly isolated from each other. Rather, as seen in FIGS. 8 and 9 , the housing 114 further defines an optional cross passage 126 which extends between the protrusions 120 a, 120 b thereof, and effectively places the flow passages 116 , 118 into fluid communication with each other.
- the cross passage 126 is further placed into communication with ambient air by an identically configured pair of vent ports 128 which are fluidly coupled thereto.
- the vent ports 128 which are disposed in side-by-side, spaced relation to each other, are formed within the housing 14 between the protrusions 120 a, 120 b thereof and, when viewed from the perspective shown in FIG. 9 , face downwardly in a direction opposite that of the open distal ends of the protrusions 120 a, 120 b.
- the protrusions 120 a, 120 b are preferably formed as separate and distinct components or sections of the housing 114 which, when mated to the remainder thereof, facilitate the formation of an identically configured pair of arcuate, semi-circular shoulders 130 a, 130 b.
- the shoulders 130 a, 130 b defined by the housing 114 are located within the interiors of respective ones of the protrusions 120 a, 120 b thereof. More particularly, each shoulder 130 a, 130 b is formed in close proximity to that end of the corresponding protrusion 120 a, 120 b disposed furthest from the open distal end thereof. The use of the shoulders 130 a, 130 b will be described in more detail below.
- the cross passage 126 is partially defined by one or more valve projections 132 a, 132 b of the housing 114 which are integrally connected to respective ones of the protrusions 120 a, 120 b, and protrude generally perpendicularly from the inner surfaces thereof in opposed relation to each other.
- the valve projections 132 a, 132 b are not sized to completely span or cover those portions of the flow passages 116 , 118 defined by the protrusions 120 a, 120 b.
- each of the valve projections 132 a, 132 b is formed to define an arcuate peripheral edge segment, and sized such that the arcuate peripheral edge segment thereof is separated or spaced from the inner surface of the corresponding protrusion 120 a, 120 b by a gap which is of a prescribed width.
- each of the valve projections 132 a, 132 b preferably includes a plurality of flow openings 134 disposed therein in a generally circular pattern. The flow openings 134 of the valve projections 132 a, 132 b each fluidly communicate with the cross passage 126 , and are used for purposed which will also be described in more detail below.
- the mask 100 of the present invention further comprises a flapper, which is preferably segregated into an identically configured pair of flapper segments 136 a, 136 b.
- the flapper segments 136 a, 136 b are each preferably fabricated from a suitable, resilient material. As seen in FIGS. 8 and 9 , the flapper segments 136 a, 136 b reside within the interiors of respective ones of the protrusions 120 a, 120 b. Additionally, when viewed from the perspective shown in FIGS. 8 and 9 , an inner end portion of each of the flapper segments 136 a, 136 b is firmly secured to the housing 114 as a result of being captured between prescribed components or sections thereof. However, those portions of the flapper segments 136 a, 136 b not rigidly secured to the housing 114 are free to resiliently move relative thereto, in a manner which will be described in more detail below.
- the flapper segments 136 a, 136 b are selectively moveable between a closed position (shown in FIGS. 8 and 9 ) and an open position.
- a closed position shown in FIGS. 8 and 9
- an open position When the flapper segments 136 a, 136 b are each in the open position, that portion of the peripheral edge thereof not secured to the housing 114 (i.e., not captured between separate sections of the housing 114 ) is normally seated against a corresponding one of the shoulders 130 a, 130 b.
- any fluid e.g., air exhaled from the nose of a patient wearing the mask
- flowing into the flow passages 116 , 118 via the open distal ends of the protrusions 120 a, 120 b is vented to ambient air via the cross passage 126 and vent ports 128 .
- such fluid is able to enter the cross passage 126 through the gaps defined between the valve projections 132 a, 132 b and inner surfaces of the corresponding protrusions 120 a, 120 b.
- the flapper segments 136 a, 136 b may be resiliently deformable from the open position described above (to which they are normally biased) to the closed position shown in FIGS. 8 and 9 . More particularly, when moved or actuated to the closed position, those portions of the flapper segments 136 a, 136 b not secured to the housing 114 are effectively placed into sealed contact with peripheral portions of respective ones of the valve projections 132 a, 132 b in a manner substantially covering or obstructing the opposed ends of the cross passage 126 fluidly communicating the flow passages 116 , 118 .
- valve 112 in the mask 100 , the valve 112 thereof is collectively defined by the shoulders 130 a, 130 b, valve projections 132 a, 132 b, and flapper segments 136 a, 136 b of the flapper. Additionally, in the mask 100 , it is contemplated that the flapper segments 136 a, 136 b will normally be biased to the open position.
- the mask 100 constructed in accordance with the present invention has a total flow requirement which is much lower in comparison to that of a traditional vented PAP mask.
- This provides the mask 100 with several advantages, including: reduced flow from the ventilator, and thus the ability to use smaller tubes; a reduction in the conducted noise from the ventilator to ambient air through the open vent ports 128 in the mask 100 ; a reduction in oxygen consumption when required with the PAP therapy due to lower flow requirements; and a reduction in water consumption of a humidifier due to lower flow requirements.
Abstract
Description
- The present application claims priority to U.S. Provisional Patent Application Ser. No. 61/499,950 entitled VENTILATION MASK WITH INTEGRATED PILOTED EXHALATION VALVE filed Jun. 22, 2011, and U.S. Provisional Patent Application Ser. No. 61/512,750 entitled VENTILATION MASK WITH INTEGRATED PILOTED EXHALATION VALVE AND METHOD OF VENTILATING A PATIENT USING THE SAME filed Jul. 28, 2011
- Not Applicable
- 1. Field of the Invention
- The present invention relates to systems and methods for controlling delivery of a pressurized flow of breathable gas to a patient and, more particularly, to a ventilation mask such as a nasal mask, nasal prongs mask or nasal pillows mask for use in critical care ventilation, respiratory insufficiency or PAP (Positive Airway Pressure) therapy and incorporating a piloted exhalation valve inside the mask.
- 2. Description of the Related Art
- As is known in the medical arts, mechanical ventilators comprise medical devices that either perform or supplement breathing for patients. Early ventilators, such as the “iron lung”, created negative pressure around the patient's chest to cause a flow of ambient air through the patient's nose and/or mouth into their lungs. However, the vast majority of contemporary ventilators instead use positive pressure to deliver gas to the patient's lungs via a patient circuit between the ventilator and the patient. The patient circuit typically consists of one or two large bore tubes (e.g., 22 mm ID for adults; 15 mm ID for pediatric) that interface to the ventilator on one end and a patient mask on the other end. Most often, the patient mask is not provided as part of the ventilator system, and a wide variety of patient masks can be used with any ventilator. The interfaces between the ventilator, patient circuit and patient masks are standardized as generic 15 mm/22 mm conical connectors, the size and shape of which are specified by regulatory bodies to assure interoperability.
- Current ventilators are designed to support either single limb or dual limb patient circuits. Ventilators using single limb patient circuit are most typically used for less acute clinical requirements, such as treatment of obstructive sleep apnea or respiratory insufficiency. Ventilators using dual limb patient circuits are most typically used for critical care applications.
- Single limb patient circuits are used only to carry gas flow from the ventilator to the patient and patient mask, and require a patient mask with vent holes. The pressure/flow characteristics of the vent holes in the mask are maintained according to standards that assure interoperability of masks with a multitude of ventilators that follow the standard. When utilizing single limb circuits, the patient inspires fresh gas from the patient circuit, and expires CO2-enriched gas, which is purged from the system through the vent holes in the mask and partially breathed down the tube to the ventilator and re-breathed during the next breath. This constant purging of flow through vent holes in the mask when using single-limb circuits provides several disadvantages: 1) it requires the ventilator to provide significantly more flow than the patient requires, adding cost/complexity to the ventilator and requiring larger tubing; 2) the constant flow through the vent holes creates noise, which has proven to be a significant detriment to patients with sleep apnea that are trying to sleep with the mask, and also to their sleep partners; 3) the additional flow coming into proximity of the patient's nose and then exiting the system often causes dryness in the patient, which often drives the need for adding humidification to the system; and 4) patient-expired CO2 flows partially out of the vent holes in the mask and partially into the patient circuit tubing, requiring a minimum flow through the tubing at all times in order to flush the CO2. To address the problem of undesirable flow of patient-expired CO2 back into the patient circuit tubing, currently known CPAP systems typically have a minimum-required pressure of 4 cmH2O whenever the patient is wearing the mask, which produces significant discomfort, claustrophobia and/or feeling of suffocation to early CPAP users and leads to a high (approximately 50%) non-compliance rate with CPAP therapy.
- When utilizing dual limb circuits, the patient inspires fresh gas from one limb (the “inspiratory limb”) of the patient circuit and expires CO2-enriched gas from the second limb (the “expiratory limb”) of the patient circuit. Both limbs of the dual limb patient circuit are connected together in a “Y” proximal to the patient to allow a single 15 mm or 22 mm conical connection to the patient mask.
- In the patient circuits described above, the ventilator pressurizes the gas to be delivered to the patient inside the ventilator to the intended patient pressure, and then delivers that pressure to the patient through the patient circuit. Very small pressure drops develop through the patient circuit, typically around 1 cmH2O, due to gas flow though the small amount of resistance created by the 22 mm or 15 mm ID tubing. Some ventilators compensate for this small pressure either by mathematical algorithms, or by sensing the tubing pressure more proximal to the patient.
- Ventilators that utilize a dual limb patient circuit typically include an exhalation valve at the end of the expiratory limb proximal to the ventilator. The ventilator controls the exhalation valve, closes it during inspiration, and opens it during exhalation. Less sophisticated ventilators have binary control of the exhalation valve, in that they can control it to be either open or closed. More sophisticated ventilators are able to control the exhalation valve in an analog fashion, allowing them to control the pressure within the patient circuit by incrementally opening or closing the valve. Valves that support this incremental control are referred to as active exhalation valves. In existing ventilation systems, active exhalation valves are most typically implemented physically within the ventilator, and the remaining few ventilation systems with active exhalation valves locate the active exhalation valve within the patient circuit proximal to the ventilator. Active exhalation valves inside ventilators are typically actuated via an electromagnetic coil in the valve, whereas active exhalation valves in the patient circuit are typically pneumatically piloted from the ventilator.
- In accordance with the present invention, there is provided a mask for achieving positive pressure mechanical ventilation (inclusive of PAP, ventilatory support, critical care ventilation, emergency applications), and a method for a operating a ventilation system including such mask. The mask may include a pressure sensing modality proximal to the patient connection. Such pressure sensing modality may be a pneumatic port with tubing that allows transmission of the patient pressure back to the ventilator for measurement, or may include a transducer within the mask. The pressure sensing port, if included in the mask, is used in the system to allow pressure sensing for achieving and/or monitoring the therapeutic pressures. Alternately or additionally, the mask may include a flow sensing modality located therewithin for achieving and/or monitoring the patient and/or therapeutic flows.
- The mask of the present invention also includes a piloted exhalation valve that is used to achieve the target pressures/flows to the patient. In the preferred embodiment, the pilot for the valve is pneumatic and driven from the gas supply tubing from the ventilator. The pilot can also be a preset pressure derived in the mask, a separate pneumatic line from the ventilator, or an electro-mechanical control. In accordance with the present invention, the valve can be implemented with a diaphragm or with a flapper.
- One of the primary benefits attendant to including the valve inside the mask is that it provides a path for patient-expired CO2 to exit the system without the need for a dual-limb patient circuit, and without the disadvantages associated with traditional single-limb patient circuits. For instance, in applications treating patients with sleep apnea, having the valve inside the mask allows patients to fall asleep while wearing the mask without the treatment pressure turned on, thereby preventing patient discomfort typically experienced with falling asleep while breathing at a positive pressure. In accordance with the present invention, the sensing described above may be used to sense a predetermined event, such as a set time, the detection of an event indicating patient airway obstruction, or the detection of a patient falling asleep, and start the positive airway pressure therapy upon sensing any such event, unlike existing devices which attempt to alleviate patient discomfort by starting at a lower pressure level (typically 4 cmH2O) and ramping the pressure up to a therapeutic level over a period of time. Additionally, having a valve inside the mask mitigates the need to have vent holes within the patient mask (a typical feature of mask used for sleep apnea) coincident with a purge flow to bleed patient expired CO2 from the system. Alleviating the mask vent holes and associated extra flow of gas through the mask helps reduce noise generated by the mask, reduce CO2 re-breathing, reduce patient nose dryness cause by excess gas flowing past the patient, and reduce flow requirements of the ventilator. Yet another benefit of the mask without vent holes and having the valve inside the same is that because there is not a constant flow through the mask and out of any vent holes, a heat moisture exchanger can also be incorporated into the mask, allowing a simple method of providing heated and humidified gas to the patient.
- Another benefit for having the valve inside the mask is that it allows for a significant reduction in the tubing size, as it supports the ventilator delivering higher pressures than the patient's therapeutic pressure. In this regard, pressure from the ventilator is significantly higher than the patient's therapeutic pressure. Pressure sensing can be implemented inside the mask near the patient interface port(s), facilitating the ventilator to have a means to servo control pressure at the patient interface port(s). Having higher pressure from the ventilator and an active exhalation valve in the mask allows for the tubing size to be significantly smaller (e.g. 1-9 mm ID) compared to conventional ventilators (22 mm ID for adults/15 mm ID for pediatric). One obvious benefit of smaller tubing is that it provides less bulk for patient and/or caregivers to manage. For today's smallest ventilators, the bulk of the tubing is as significant as the bulk of the ventilator. Another benefit of the smaller tubing is that is allows for more convenient ways of affixing the mask to the patient. For instance, the tubing can go around the patient's ears to hold the mask to the face, instead of requiring straps (typically called “headgear”) to affix the mask to the face. Along these lines, the discomfort, complication, and non-discrete look of the headgear is another significant factor leading to the high non-compliance rate for CPAP therapy. Another benefit to the smaller tubing is that the mask can become smaller because it does not need to interface with the large tubing. Indeed, large masks are another significant factor leading to the high non-compliance rate for CPAP therapy since, in addition to being non-discrete, they often cause claustrophobia.
- The present invention is best understood by reference to the following detailed description when read in conjunction with the accompanying drawings.
- These, as well as other features of the present invention, will become more apparent upon reference to the drawings wherein:
-
FIG. 1 is an isometric view of a nasal pillows mask constructed in accordance with a first embodiment of the present invention and including an integrated diaphragm-implementation piloted exhalation valve; -
FIG. 2 is a front elevational view of the nasal pillows mask shown inFIG. 1 ; -
FIG. 3 is a cross-sectional view of the nasal pillows mask shown inFIG. 2 ; -
FIG. 4 is an exploded, cross-sectional front view of the nasal pillows mask shown inFIG. 3 ; -
FIG. 5 is a front elevational view of a nasal pillows mask constructed in accordance with a second embodiment of the present invention and including an integrated flapper-implementation exhalation valve; -
FIG. 6 is a top plan view of the nasal pillows mask shown inFIG. 5 ; -
FIG. 7 is a bottom plan view of the nasal pillows mask shown inFIG. 5 ; -
FIG. 8 is a cross-sectional, isometric view of the nasal pillows mask shown inFIG. 5 ; and -
FIG. 9 is a cross-sectional view of the nasal pillows mask shown inFIG. 5 . - Common reference numerals are used throughout the drawings and detailed description to indicate like elements.
- Referring now to the drawings wherein the showings are for purposes of illustrating various embodiments of the present invention only, and not for purposes of limiting the same,
FIGS. 1-4 depict aventilation mask 10 constructed in accordance with a first embodiment of the present invention. The mask is depicted as a nasal prongs mask, however those skilled in the art will recognize that other ventilation masks are contemplated herein such as nasal pillows masks, nasal masks and oronasal masks and for purposes of this application the term mask and/or ventilation mask will include all such mask structures. Additionally, for purposes of this application, the term “direct nasal interface mask” will be deemed to encompass those masks which are configured to facilitate the direct introduction of therapeutic fluid pressure into the nostrils of a patent, such masks including, but not being limited to, nasal pillows masks, nasal prongs masks, and nasal cradle masks. Themask 10 includes an integrated, diaphragm-implemented, pilotedexhalation valve 12, the structural and functional attributes of which will be described in more detail below. - As seen in
FIGS. 1-4 , themask 10 comprises ahousing 14 which defines first and secondfluid flow passages FIGS. 3 and 4 , theflow passages housing 14 to have substantially identical shapes or contours. Although illustrated with a pair of flow passages, 16, 18, those skilled in the art will recognize that a single flow passage is additionally contemplated herein. In themask 10, one end of each of theflow passages tubular protrusions housing 14. The opposite end of each of theflow passages connector ports housing 14. As seen inFIGS. 3 and 4 , theconnector ports tubular fluid line 24 therein. As is apparent fromFIG. 3 , the operative engagement of afluid line 24 to each of theconnector ports such fluid lines 24 into fluid communication with respective ones of theflow passages housing 14, the spacing between theprotrusions mask 10 is worn by such patient. - In the
mask 10, theflow passages FIGS. 3 and 4 , thehousing 14 may define anoptional cross passage 26 which extends between theprotrusions flow passages cross passage 26 is further placed into fluid communication with ambient air by anoptional vent port 28 which is fluidly coupled thereto. Thevent port 28 is defined by and extends axially through a generallycylindrical boss 30 of thehousing 14 which protrudes upwardly between theprotrusions - The
housing 14 of themask 10 further defines aninternal valve chamber 32 which fluidly communicates with thecross passage 26. As further seen inFIGS. 3 and 4 , disposed at the junction between thecross passage 26 andvalve chamber 32 is atubular projection 34 of thehousing 14. Theprojection 34 defines an annular distal rim or seatingsurface 36 which is used in the operation of thevalve 12 in manner which will be described in more detail below. Theprojection 34 protrudes into thevalve chamber 32, and defines the conduit which places thevalve chamber 32 into fluid communication with thecross passage 26. - As best seen in
FIGS. 3 and 4 , thevalve chamber 32 is defined in large measure by avalve wall 38 of thehousing 14 which is generally oriented between theflow passages FIGS. 1-4 , is disposed below thecross passage 26. As is also apparent fromFIGS. 1 and 2 , thevalve wall 38 has a perforated construction, thus facilitating the fluid communication between thevalve chamber 32 partially defined thereby and ambient air. - In the
mask 10, the end of thevalve chamber 32 disposed furthest from thecross passage 26 is enclosed by avalve cap 40 which may be removably attached or permanently attached to the distal portion or rim of thevalve wall 38 in the manner best seen inFIG. 3 . Thevalve cap 40 includes apilot port 42 which, when thevalve cap 40 is coupled to thevalve wall 38, is placed into fluid communication with thevalve chamber 32. Thepilot port 42 is partially defined by and extends axially through a generallycylindrical connector 44 of thevalve cap 40. As best seen inFIGS. 3 and 4 , one end of thepilot port 42 is disposed within a generallyplanar base surface 46 defined by thevalve cap 40. In addition to thebase surface 46, thevalve cap 40 defines acontinuous shoulder 48 which, from the perspective shown inFIG. 4 , is elevated above thebase surface 46. This embodiment shows a pneumatically piloted diaphragm; it is additionally contemplated that thevalve 12 can be driven in an electromechanical manner (e.g., with an electromagnet instead of using the above mentioned pilot port 42). - The
mask 10 of the present invention further comprises adiaphragm 50 which resides within thevalve chamber 32. Although various configurations ofdiaphragms 50 are contemplated herein, as is also best seen inFIGS. 3 and 4 , thediaphragm 50 has an enlarged, centralmain body portion 52, and aperipheral flange portion 54 which is integrally connected to and circumvents themain body portion 52. Theflange portion 54 includes an arcuately contoured central region which is oriented between the distal region thereof and themain body portion 52, and defines a continuous, generallyconcave channel 56. Thediaphragm 50 is preferably fabricated from a suitable resilient material. - In the
mask 10, the distal region of theflange portion 54 of thediaphragm 50 which is disposed outward of the arcuate central region thereof is normally captured between thevalve cap 40 and thevalve wall 38 when thevalve cap 40 is operatively engaged to thevalve wall 38. More particularly, as seen inFIG. 3 , the distal region of theflange portion 54 is compressed and thus captured between theshoulder 48 of thevalve cap 40 and a lip portion 58 of thevalve wall 38 which protrudes inwardly from the inner surface thereof. Thediaphragm 50 is preferably sized such that when the distal region of theflange portion 54 thereof is captured between theshoulder 48 and lip portion 58 in the aforementioned manner, the arcuate central region of theflange portion 54 is disposed directly adjacent the inner peripheral surface of the lip portion 58. Additionally, thechannel 56 defined by theflange portion 54 is directed toward and thus faces thebase surface 46 of thevalve cap 40. - In the
mask 10, thediaphragm 50 effectively segregates thevalve chamber 32 into a patient side orregion 32 a, and a pilot side or region 32 b. More particularly, due to the aforementioned manner in which thediaphragm 50 is captured between thevalve cap 40 and thevalve wall 38, the patient andpilot regions 32 a, 32 b of thevalve chamber 32 are separated from each other by thediaphragm 50, and are of differing volumes. Along these lines, the fluid conduit defined by theprojection 34 communicates directly with thepatient region 32 a of thevalve chamber 32, while thepilot port 42 defined by theconnector 44 communicates directly with the pilot region 32 b of thevalve chamber 32. - The diaphragm 50 (and hence the valve 12) is selectively moveable between an open position (shown in
FIG. 3 ) and a closed position. Importantly, in either of its open or closed positions, thediaphragm 50 is not seated directly against thebase surface 46 of thevalve cap 40. Rather, a gap is normally maintained therebetween. As seen inFIG. 3 , the width of such gap when thediaphragm 50 is in its open position is generally equal to the fixed distance separating thebase surface 46 of thevalve cap 40 from theshoulder 48 thereof. When thediaphragm 50 is in its open position, it is also disposed in spaced relation to theprojection 34 of thehousing 14, and in particular theseating surface 36 defined thereby. As such, when thediaphragm 50 is in its open position, fluid is able to freely pass between theflow passages cross passage 26, the flow conduit defined by theprojection 34, and the perforated openings within thevalve wall 38 partially defining thevalve chamber 32. - The
diaphragm 50 may be resiliently deformable from its open position (to which it may be normally biased) to its closed position. It is an important feature of the present invention that thediaphragm 50 is normally biased in its open position which provides a fail safe to allow a patient to inhale ambient air through the valve and exhale ambient air through the valve even during any ventilator malfunction. - When moved or actuated to the closed position, the
main body portion 52 of thediaphragm 50 is firmly seated against theseating surface 36 defined by theprojection 34, thus effectively blocking fluid communication between the cross passage 26 (and hence theflow passages 16, 18) and thevalve chamber 32. More particularly, when viewed from the perspective shown inFIG. 3 , the peripheral region of the top surface of themain body portion 52 is seated against theseating surface 36, with a central region of the top surface of themain body portion 52 protruding slightly into the interior of theprojection 34, i.e., the fluid conduit defined by theprojection 34. - As is apparent from the foregoing description, in the
mask 10, thevalve 12 thereof is collectively defined by theprojection 34,valve wall 38,valve cap 40 anddiaphragm 50. Additionally, in themask 10, it is contemplated that thevalve 12 will be piloted, with the movement of thediaphragm 50 to the closed position as described above being facilitated by the introduction of positive fluid pressure into the gap normally defined between thediaphragm 50 and thebase surface 46 via thepilot port 42, i.e., into the pilot region 32 b of thevalve chamber 32. In this regard, it is contemplated that during the use of themask 10 by a patient, a pilot fluid line (not shown) from a ventilator will be coupled to theconnector 44. It is also contemplated that during the inspiratory phase of the breathing cycle of the patient wearing themask 10, the fluid pressure level introduced into the pilot region 32 b of thevalve chamber 32 via thepilot port 42 will be sufficient to facilitate the movement of thediaphragm 50 to its closed position. Conversely, during the expiratory phase of the breathing cycle of the patient wearing themask 10, it is contemplated that the discontinuation of the fluid flow through thepilot port 42, coupled with the resiliency of thediaphragm 50, a biasing spring (not shown) operatively coupled to themain body portion 52 of thediaphragm 50, and/or positive pressure applied to themain body portion 52 of thediaphragm 50, will facilitate the movement of thediaphragm 50 back to the open position. As will be recognized, the movement of thediaphragm 50 to the open position allows the air exhaled from the patient to be vented to ambient air after entering thepatient region 32 a of thevalve chamber 32 via the perforated openings of thevalve wall 38 communicating with thevalve chamber 32. - As will be recognized, based upon the application of pilot pressure, the
diaphragm 50 travels from a fully open position through a partially open position to a fully closed position. In this regard, thediaphragm 50 will be partially open or partially closed during exhalation to maintain desired ventilation therapy. Additionally, a positive airway pressure can be controlled with any expiratory flow value by modulating the pilot pressure within the pilot region 32 b of thevalve chamber 32 and hence the position of thediaphragm 50. Further, when pilot pressure is discontinued to the diaphragm, thediaphragm 50 moves to an open position wherein the patient can inhale and exhale through the mask with minimal restriction and with minimal carbon dioxide retention within themask 10. This is an important feature of the present invention which allows a patient to wear themask 10 without ventilation therapy being applied to the mask such that themask 10 is comfortable to wear and can be worn without carbon dioxide buildup. This feature is highly advantageous for the treatment of obstructive sleep apnea where patients complain of discomfort with ventilation therapy due to mask and pressure discomfort. When it is detected that a patient requires sleep apnea therapy, the ventilation therapy can be started (i.e., in an obstructive sleep apnea situation). - In this regard, the present invention contemplates a method of ventilation utilizing a mask wherein patient inhalation and patient exhalation is facilitated through the mask to ambient air when the ventilator is not delivering a therapeutic level of pressure. For instance, additional valving in the mask may be implemented for this purpose. Since the mask does not facilitate CO2 buildup, the ventilator can remain off while the mask is worn by the patient and ventilation therapy can be initiated upon sensing or detecting a patient requirement, such as sleep apnea therapy, by conventional sensors incorporated into the mask and ventilator. In this regard, conventional ventilators can be readily modified via conventional software changes to allow the mask to be worn without supplying pressure to the mask unless and until a patient requirement is sensed and subsequently communicated to the ventilator to provide necessary ventilation to the patient. Such modification may additionally require the use of a conventional check valve to ensure that patient exhalation is facilitated through the exhalation valve on the mask and not back into the ventilator delivery circuit.
- As indicated above, in the embodiment shown in
FIGS. 1-4 , thediaphragm 50 is pneumatically piloted, with the position thereof being regulated by selectively modulating the pilot pressure within the pilot region 32 b of thevalve chamber 32. However, it is contemplated that alternative modalities, such as an electromagnetic actuator, can be used to drive thevalve 12. For example, as also indicated above, in an alternative embodiment, thevalve 12 may be driven in an electromechanical manner through the use of an electromagnet instead of using the above-describedpilot port 42. - As indicated above, in the
mask 10, thevalve cap 40 is releasably attached to thevalve wall 38 of thehousing 14. As a result, the selective detachment of thevalve cap 40 from thehousing 14 allows for the removal of thediaphragm 50 from within thevalve chamber 32 as permits the periodic cleaning or disinfection thereof. In addition, the detachment of thevalve cap 40 from thevalve wall 38 of thehousing 14 also permits access to and the cleaning or disinfection of the interior surfaces of thevalve chamber 32.Port 28 provides a means for pressure measurement inside the mask. - Referring now to
FIGS. 5-9 , there is shown a nasal pillows mask 100 constructed in accordance with a second embodiment of the present invention. Themask 100 includes an integrated, flapper-implementedexhalation valve 112, the structural and functional attributes of which will be described in more detail below. - As seen in
FIGS. 5-9 , themask 100 comprises ahousing 114 which defines first and secondfluid flow passages FIGS. 8 and 9 , theflow passages housing 114 to have substantially identical shapes or contours. As with the first embodiment of this invention, a single flow passage is additionally expressly contemplated herein. In themask 100, one end of each of theflow passages tubular protrusions housing 114. The opposite end of each of theflow passages connector ports housing 114. Theconnector ports tubular fluid line 124 therein. As most apparent fromFIGS. 8 and 9 , the operative engagement of afluid line 124 to each of theconnector portions such fluid lines 124 into fluid communication with respective ones of theflow passages housing 114, the spacing between theprotrusions mask 100 is worn by such patient. - In the
mask 100, theflow passages FIGS. 8 and 9 , thehousing 114 further defines anoptional cross passage 126 which extends between theprotrusions flow passages cross passage 126 is further placed into communication with ambient air by an identically configured pair ofvent ports 128 which are fluidly coupled thereto. Thevent ports 128, which are disposed in side-by-side, spaced relation to each other, are formed within thehousing 14 between theprotrusions FIG. 9 , face downwardly in a direction opposite that of the open distal ends of theprotrusions - As is best seen in
FIGS. 8 and 9 , theprotrusions housing 114 which, when mated to the remainder thereof, facilitate the formation of an identically configured pair of arcuate,semi-circular shoulders shoulders housing 114 are located within the interiors of respective ones of theprotrusions shoulder corresponding protrusion shoulders - In the
mask 100, thecross passage 126 is partially defined by one ormore valve projections housing 114 which are integrally connected to respective ones of theprotrusions FIGS. 6 , 8, and 9, thevalve projections flow passages protrusions valve projections corresponding protrusion FIGS. 6 and 8 , each of thevalve projections flow openings 134 disposed therein in a generally circular pattern. Theflow openings 134 of thevalve projections cross passage 126, and are used for purposed which will also be described in more detail below. - The
mask 100 of the present invention further comprises a flapper, which is preferably segregated into an identically configured pair offlapper segments 136 a, 136 b. Theflapper segments 136 a, 136 b are each preferably fabricated from a suitable, resilient material. As seen inFIGS. 8 and 9 , theflapper segments 136 a, 136 b reside within the interiors of respective ones of theprotrusions FIGS. 8 and 9 , an inner end portion of each of theflapper segments 136 a, 136 b is firmly secured to thehousing 114 as a result of being captured between prescribed components or sections thereof. However, those portions of theflapper segments 136 a, 136 b not rigidly secured to thehousing 114 are free to resiliently move relative thereto, in a manner which will be described in more detail below. - The
flapper segments 136 a, 136 b (and hence the valve 112) are selectively moveable between a closed position (shown inFIGS. 8 and 9 ) and an open position. When theflapper segments 136 a, 136 b are each in the open position, that portion of the peripheral edge thereof not secured to the housing 114 (i.e., not captured between separate sections of the housing 114) is normally seated against a corresponding one of theshoulders flow passages protrusions cross passage 126 and ventports 128. In this regard, such fluid is able to enter thecross passage 126 through the gaps defined between thevalve projections protrusions - The
flapper segments 136 a, 136 b may be resiliently deformable from the open position described above (to which they are normally biased) to the closed position shown inFIGS. 8 and 9 . More particularly, when moved or actuated to the closed position, those portions of theflapper segments 136 a, 136 b not secured to thehousing 114 are effectively placed into sealed contact with peripheral portions of respective ones of thevalve projections cross passage 126 fluidly communicating theflow passages flapper segments 136 a, 136 b are in the closed position, some measure of fluid may still be vented from theflow passages cross passage 126 via theflow openings 134 included in each of thevalve projections - As is apparent from the foregoing description, in the
mask 100, thevalve 112 thereof is collectively defined by theshoulders valve projections flapper segments 136 a, 136 b of the flapper. Additionally, in themask 100, it is contemplated that theflapper segments 136 a, 136 b will normally be biased to the open position. In this regard, it is contemplated that during the inspiratory phase of the breathing cycle of a patient using themask 100, positive fluid pressure introduced into theflow passages fluid lines 124 will act against theflapper segments 136 a, 136 b in a manner facilitating the movement ofsuch flapper segments 136 a, 136 b from their normally open position, to the closed position shown inFIGS. 8 and 9 . As a result, fluid is able to flow freely through theflow passages cross passage 126, except for a small portion of flow that passes throughflow openings 134. This small flow throughflow openings 134 provides for a means to bleed off pressure and therefore more easily control the valve. - Conversely, during the expiratory phase of the breathing cycle of the patient wearing the
mask 100, it is contemplated that a reduction in the fluid pressure level introduced into theflow passages fluid lines 124 to below a prescribed level will allow theflapper segments 136 a, 136 b to resiliently return to their normal, open positions engaging respective ones of theshoulders flapper segments 136 a, 136 b return to their open positions, air exhaled from the patient's nostrils during the expiratory phase of the patient's breathing circuit is vented to ambient air via thecross passage 126 and ventports 128. In this regard, though the movement of theflapper segments 136 a, 136 b to the open positions effectively blocks those portions of theflow passages valve projections protrusions cross passage 126. - Advantageously, the
mask 100 constructed in accordance with the present invention has a total flow requirement which is much lower in comparison to that of a traditional vented PAP mask. This provides themask 100 with several advantages, including: reduced flow from the ventilator, and thus the ability to use smaller tubes; a reduction in the conducted noise from the ventilator to ambient air through theopen vent ports 128 in themask 100; a reduction in oxygen consumption when required with the PAP therapy due to lower flow requirements; and a reduction in water consumption of a humidifier due to lower flow requirements. - This disclosure provides exemplary embodiments of the present invention. The scope of the present invention is not limited by these exemplary embodiments. Numerous variations, whether explicitly provided for by the specification or implied by the specification, such as variations in structure, dimension, type of material and manufacturing process may be implemented by one of skill in the art in view of this disclosure.
Claims (20)
Priority Applications (2)
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US13/431,827 US9616194B2 (en) | 2011-06-22 | 2012-03-27 | Ventilation mask with integrated piloted exhalation valve and method of ventilating a patient using the same |
PCT/US2012/043011 WO2012177566A1 (en) | 2011-06-22 | 2012-06-18 | Ventilation mask with integrated piloted exhalation valve and method of ventilating a patient using the same |
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US13/431,827 US9616194B2 (en) | 2011-06-22 | 2012-03-27 | Ventilation mask with integrated piloted exhalation valve and method of ventilating a patient using the same |
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US20130255684A2 true US20130255684A2 (en) | 2013-10-03 |
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US13/431,827 Active 2035-11-02 US9616194B2 (en) | 2011-06-22 | 2012-03-27 | Ventilation mask with integrated piloted exhalation valve and method of ventilating a patient using the same |
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Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9333318B2 (en) | 2012-04-13 | 2016-05-10 | Fresca Medical, Inc. | Sleep apnea device |
US9492086B2 (en) | 2012-03-21 | 2016-11-15 | Fresca Medical, Inc. | Apparatus, systems, and methods for treating obstructive sleep apnea |
US10272226B2 (en) | 2012-04-13 | 2019-04-30 | Fresca Medical, Inc. | Auto-feedback valve for a sleep apnea device |
US10307562B2 (en) | 2012-04-13 | 2019-06-04 | Fresca Medical, Inc. | Auto-feedback valve for a sleep apnea device |
Families Citing this family (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20160095996A1 (en) * | 2010-10-25 | 2016-04-07 | Insleep Technologies, Llc | Nasal interface |
US9486602B2 (en) * | 2011-06-22 | 2016-11-08 | Breathe Technologies, Inc. | Ventilation mask with integrated piloted exhalation valve and method of ventilating a patient using the same |
WO2014042862A1 (en) | 2012-09-12 | 2014-03-20 | Silverbow Development Llc | Nasal interface apparatus and systems for use with a respiratory assist device |
US11904096B2 (en) | 2012-09-12 | 2024-02-20 | Inogen, Inc. | Nasal interface apparatus and systems for use with a respiratory assist device |
JP6640081B2 (en) | 2013-07-29 | 2020-02-05 | レスメド・プロプライエタリー・リミテッド | Heat-moisture exchanger for patient interface |
WO2015038666A1 (en) * | 2013-09-10 | 2015-03-19 | Ahmad Samir S | Zero pressure start continuous positive airway pressure therapy |
EP3057636B1 (en) * | 2013-10-18 | 2021-11-17 | Inogen, Inc. | Apparatus and system for determining patient airway pressure |
CN103638585B (en) * | 2013-12-06 | 2016-03-16 | 孙亚东 | A kind of breathing equipment by respiratory control |
NL2019418B1 (en) * | 2017-08-15 | 2019-02-25 | Van Woerkum Holding B V | Portable air treatment device and method for supplying filtered air to a person |
US11666722B2 (en) | 2020-03-04 | 2023-06-06 | 3B Medical, Inc. | Nasal cannula without nostril prongs |
Citations (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3675649A (en) * | 1970-08-21 | 1972-07-11 | Westland Aircraft Ltd | Electronically controlled oxygen regulators |
US5273031A (en) * | 1990-10-31 | 1993-12-28 | Siemens Aktiengesellschaft | Ventilator |
US5697364A (en) * | 1995-06-07 | 1997-12-16 | Salter Labs | Intermittent gas-insufflation apparatus |
US6006748A (en) * | 1996-10-16 | 1999-12-28 | Resmed Limited | Vent valve apparatus |
US20090151724A1 (en) * | 2007-09-26 | 2009-06-18 | Breathe Technologies, Inc. | Methods and devices for providing inspiratory and expiratory flow relief during ventilation therapy |
US20100252037A1 (en) * | 2009-04-02 | 2010-10-07 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive open ventilation with gas delivery nozzles within nasal pillows |
US20110197885A1 (en) * | 2008-04-18 | 2011-08-18 | Breathe Technologies ,Inc. | Methods and devices for sensing respiration and controlling ventilator functions |
US20110253147A1 (en) * | 2010-04-19 | 2011-10-20 | Gusky Michael H | Breathing apparatus |
US20120060837A1 (en) * | 2010-09-10 | 2012-03-15 | Yong Liu | Nasal intermittent mandatory ventilation (nimv) control system in a ventilator |
US20120330183A1 (en) * | 2011-06-22 | 2012-12-27 | Todd Allum | Ventilation mask with integrated piloted exhalation valve and method of ventilating a patient using the same |
US20140000610A1 (en) * | 2010-12-03 | 2014-01-02 | Fisher & Paykel Healthcare Limited | System, apparatus and method for supplying gases |
US8844533B2 (en) * | 2011-06-22 | 2014-09-30 | Breathe Technologies, Inc. | Ventilation mask with integrated piloted exhalation valve |
Family Cites Families (360)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US252515A (en) | 1882-01-17 | Moses w | ||
US42346A (en) | 1864-04-19 | Improved anchor | ||
US189153A (en) | 1877-04-03 | Improvement in attachments for automatically closing cocks and faucets | ||
US432325A (en) | 1890-07-15 | Finlay mcintyre | ||
US321600A (en) | 1885-07-07 | hecker | ||
US430380A (en) | 1890-06-17 | Charles a | ||
US306346A (en) | 1884-10-07 | Javal | ||
US539217A (en) | 1895-05-14 | Mowing-machine | ||
US516494A (en) | 1894-03-13 | Limery la veck | ||
US474434A (en) | 1892-05-10 | Paint-oil | ||
US53695A (en) | 1866-04-03 | Improved process of generating gases to be used for motive power | ||
US416701A (en) | 1889-12-03 | yocom | ||
US53694A (en) | 1866-04-03 | Improvement in thrashing-machines | ||
US8413A (en) | 1851-10-07 | Improvement in apparatus for warming air and water for dwellings | ||
US546673A (en) | 1895-09-24 | Platform-scale | ||
US694089A (en) | 1901-11-18 | 1902-02-25 | Horatio J Brewer | Zinc element for primary batteries. |
US3326214A (en) | 1963-10-10 | 1967-06-20 | Perma Pier Inc | Breath warmer apparatus |
US3802431A (en) | 1971-10-08 | 1974-04-09 | Bard Inc C R | Nasal cannula |
US3726275A (en) | 1971-12-14 | 1973-04-10 | I Jackson | Nasal cannulae |
DE2342521A1 (en) | 1972-08-29 | 1974-04-25 | Paul Guichard | PORTABLE NASAL DIFFUSER DEVICE FOR PURIFYING AND MODIFYING BREATHING AIR |
SE414708B (en) | 1972-11-06 | 1980-08-18 | Norabel Ab | DEVICE FOR HEATING AND HEATING THE INHALED AIR AT TRAKEOTOMIOCH ENDOTRAKEAL INTUBATION |
US4121583A (en) | 1976-07-13 | 1978-10-24 | Wen Yuan Chen | Method and apparatus for alleviating asthma attacks |
US4062359A (en) | 1976-08-09 | 1977-12-13 | Geaghan Mark E | Low temperature breathing apparatus |
US4266540A (en) | 1978-10-13 | 1981-05-12 | Donald Panzik | Nasal oxygen therapy mask |
US4245633A (en) | 1979-01-31 | 1981-01-20 | Erceg Graham W | PEEP providing circuit for anesthesia systems |
US4278082A (en) | 1979-05-11 | 1981-07-14 | Blackmer Richard H | Adjustable nasal cannula |
DE2929584A1 (en) | 1979-07-21 | 1981-02-05 | Draegerwerk Ag | MOISTURE EXCHANGER IN BREATHING DEVICES |
US4325365A (en) | 1980-12-11 | 1982-04-20 | Barbuto John P | Athlete's breathing apparatus |
US4458679A (en) | 1982-06-01 | 1984-07-10 | Ward Russell G | Cold weather respiratory mask |
US4535767A (en) | 1982-10-01 | 1985-08-20 | Tiep Brian L | Oxygen delivery apparatus |
US4559941A (en) | 1983-12-22 | 1985-12-24 | Timmons John W | Eyeglass frame and nasal cannula assembly |
US4572177A (en) | 1984-06-25 | 1986-02-25 | Tiep Brian L | Oxygen therapy apparatus |
SU1342514A1 (en) | 1984-11-26 | 1987-10-07 | Всесоюзный научно-исследовательский институт горноспасательного дела | Moisture-heat-exchanger of respiratory system based on chemically bound oxygen |
US4620537A (en) | 1985-03-04 | 1986-11-04 | Brown Thomas M | Cold weather face mask |
US4699139A (en) | 1985-09-30 | 1987-10-13 | Marshall Marie F | Nasal cannula assembly with patient comfort pad |
AU7943387A (en) | 1986-10-16 | 1988-04-21 | Intertech Resources Inc. | Heat and moisture exchanger for respiratory gases |
US5072729A (en) | 1986-11-04 | 1991-12-17 | Bird Products Corporation | Ventilator exhalation valve |
US4739757A (en) | 1986-11-13 | 1988-04-26 | Edwards Anna M | Oxygen tube retaining headband |
US4787105A (en) | 1987-02-10 | 1988-11-29 | Burlington Industries, Inc. | Sleeping bag with snorkel hood and draft curtain |
US5199424A (en) | 1987-06-26 | 1993-04-06 | Sullivan Colin E | Device for monitoring breathing during sleep and control of CPAP treatment that is patient controlled |
CA1315174C (en) | 1987-08-18 | 1993-03-30 | Patrick W. J. Fantin | Emergency breathing device for miners |
US4793343A (en) | 1987-08-20 | 1988-12-27 | Cummins Jr James M | Respiratory heated face mask |
GB2209123A (en) | 1987-08-29 | 1989-05-04 | M S A | Breathing apparatus |
NZ221689A (en) | 1987-09-07 | 1990-09-26 | Fisher & Paykel | Humidifier: float in gas chamber controls water inlet |
USD311609S (en) | 1987-10-28 | 1990-10-23 | Stoneburner Sr Edwin R | Ear protector for oxygen feed line |
FR2623404A1 (en) | 1987-11-19 | 1989-05-26 | Air Liquide | RESPIRATORY ASSISTANCE DEVICE |
US5065756A (en) | 1987-12-22 | 1991-11-19 | New York University | Method and apparatus for the treatment of obstructive sleep apnea |
US4873972A (en) | 1988-02-04 | 1989-10-17 | Moldex/Metric Products, Inc. | Disposable filter respirator with inner molded face flange |
US4836200A (en) | 1988-02-29 | 1989-06-06 | Edward H. Lacey | Oxygen tube support strap |
US4949733A (en) | 1988-07-21 | 1990-08-21 | Sampson Robert D | Nasal oxygen cannula pad |
NZ226784A (en) | 1988-09-29 | 1992-10-28 | Fisher & Paykel | Gas humidifier with microporous wall |
US5111809A (en) | 1988-12-01 | 1992-05-12 | Avstar Aerospace Corporation | Breathing system |
GB8908647D0 (en) | 1989-04-17 | 1989-06-01 | Glaxo Group Ltd | Device |
US5134995A (en) | 1989-05-19 | 1992-08-04 | Puritan-Bennett Corporation | Inspiratory airway pressure system with admittance determining apparatus and method |
GB8916361D0 (en) | 1989-07-18 | 1989-09-06 | Smiths Industries Plc | Filters |
DK162426C (en) | 1989-09-04 | 1992-03-23 | Ambu Int As | PROTECTION AGENT FOR USE BY LUNGE VENTILATION BY ORAL ORAL OR Mouth-to-nose method |
US5239995A (en) | 1989-09-22 | 1993-08-31 | Respironics, Inc. | Sleep apnea treatment apparatus |
CA2003895C (en) | 1989-11-16 | 1999-03-30 | Jean-Pierre Robitaille | Filtre intra-nasal |
EP0462412B1 (en) | 1990-06-18 | 1996-07-10 | Engström Medical Ab | Y-piece connector for ventilator |
NZ238544A (en) | 1990-06-18 | 1994-10-26 | Ponnet Gilman En Anthony | Respirator with hygroscopic material adjacent outlet to patient |
US5025805A (en) | 1990-07-11 | 1991-06-25 | Betty Nutter | Nasal cannula assembly |
US5018519B1 (en) | 1990-08-03 | 2000-11-28 | Porter Instr Company Inc | Mask for administering an anesthetic gas to a patient |
DE4126028A1 (en) | 1990-11-02 | 1992-05-07 | Lang Volker | DEVICE FOR HEATING AND HUMIDIFYING GASES, ESPECIALLY BREATHING GASES WITH ARTIFICIAL VENTILATION WITH A SMALL DEADROOM VOLUME AND SPECIFIC SUITABILITY FOR EARLY, NEWBORN, INFANTS AND CHILDREN |
FI87625C (en) | 1990-12-28 | 1993-02-10 | Olavi Ebeling | ANDNINGSMASK |
IT1245392B (en) | 1991-03-22 | 1994-09-20 | Kontron Instr Holding | METHOD AND DEVICE FOR THE REDUCTION OF THE PULMONARY CURRENT VOLUME APPLICABLE TO MECHANICAL PULMONARY FANS |
US5193534A (en) | 1991-04-12 | 1993-03-16 | Peppler James H | Respiratory aid glasses |
US5529060A (en) | 1991-05-22 | 1996-06-25 | Fisher & Paykel Limited | Humidifiers with control systems to prevent condensation |
AU660718B2 (en) | 1991-10-04 | 1995-07-06 | Fisher & Paykel Healthcare Limited | Improvements in or relating to humidifiers |
FR2683150B1 (en) | 1991-10-30 | 1994-01-21 | Robert Bezicot | ARTIFICIAL NOSE FOR TRACHEOTOMIZED SUBJECT, WITH A SURGICAL ORIFICE ENDING THE TRACHEA WITH THE SKIN. |
US5284160A (en) | 1991-11-13 | 1994-02-08 | Dryden Gale E | Consolidated anesthesia circuit |
US5303699A (en) | 1991-11-18 | 1994-04-19 | Intermed Equipamento Medico Hospitalar Ltda. | Infant ventilator with exhalation valves |
AU3713193A (en) | 1992-04-24 | 1993-10-28 | Fisher & Paykel Limited | Humidifier apparatus and/or gases distribution chambers and/or temperature probes for the same |
GB9214716D0 (en) | 1992-07-10 | 1992-08-19 | Emmark Technology | Tracheostomy filter |
EP0588214B1 (en) | 1992-09-14 | 1998-12-02 | Minnesota Mining And Manufacturing Company | Superabsorbent fiber compositions demonstrating efficient retention of exhaled heat and moisture |
US5353788A (en) | 1992-09-21 | 1994-10-11 | Miles Laughton E | Cardio-respiratory control and monitoring system for determining CPAP pressure for apnea treatment |
JP3433397B2 (en) | 1992-09-23 | 2003-08-04 | フィッシャー アンド ペイケル アプライアンシーズ リミテッド | Float valve device and humidifier for breathing |
EP0590289A1 (en) | 1992-09-28 | 1994-04-06 | Engström Medical Ab | Patient connector |
US5617913A (en) | 1992-10-29 | 1997-04-08 | Elastek, Inc. | Elastomer bed for heating and moisturizing respiratory gases |
US7004162B1 (en) | 1992-11-09 | 2006-02-28 | Canadian Monaghan, Ltd. | Exhalation valve |
NZ250105A (en) | 1992-11-09 | 1996-07-26 | Monaghan Canadian Ltd | Inhalator mask; one-way valve opens upon exhalation |
US5331957A (en) | 1993-02-05 | 1994-07-26 | Liu Chin Chia | Respirator for only filtering air inhaled |
US5813399A (en) | 1993-03-16 | 1998-09-29 | Puritan Bennett Corporation | System and method for closed loop airway pressure control during the inspiratory cycle of a breath in a patient ventilator using the exhalation valve as a microcomputer-controlled relief valve |
FR2706311B1 (en) | 1993-06-09 | 1995-09-22 | Intertechnique Sa | Respiratory protection equipment. |
US5400776A (en) | 1993-07-09 | 1995-03-28 | Proprietary Technology, Inc. | Apparatus for maintaining a bend in a medical insufflation tube |
US5685296A (en) | 1993-07-30 | 1997-11-11 | Respironics Inc. | Flow regulating valve and method |
SE501042C2 (en) | 1993-09-17 | 1994-10-24 | Gibeck Respiration Ab | Device for moisture-heat exchanger |
CH685678A5 (en) | 1993-09-23 | 1995-09-15 | Newpharm S A | Oxygen inhaler with pressurised oxygen storage box |
GB2284356B (en) | 1993-11-22 | 1997-10-29 | Fisher & Paykel | Respiratory humidifier conduit |
US5542416A (en) | 1994-01-12 | 1996-08-06 | Societe D'applications Industrielles Medicales Et Electroniques (Saime) | Apparatus for assisting ventilation including reduced exhalation pressure mode |
JPH08109984A (en) | 1994-03-15 | 1996-04-30 | Fisher & Paykel Ltd | Conduit for forwarding humidified gas and manufacturing process thereof |
DE9409320U1 (en) | 1994-06-08 | 1995-07-06 | Berlin Florence | Respirator and microphone holder for use therein |
SE503155C2 (en) | 1994-07-28 | 1996-04-01 | Comasec International Sa | Methods and apparatus for functional control of breathing apparatus |
DE19534001B4 (en) | 1994-09-20 | 2006-05-18 | Fisher & Paykel, East Tamaki | humidification chamber |
DE4434236A1 (en) | 1994-09-24 | 1996-03-28 | Schreiber Hans | System for pre=operative oxygenation for medical use |
US5505768A (en) | 1994-10-11 | 1996-04-09 | Altadonna; Anthony J. | Humidity moisture exchanger |
US5503146A (en) | 1994-10-26 | 1996-04-02 | Devilbiss Health Care, Inc. | Standby control for CPAP apparatus |
US5551419A (en) | 1994-12-15 | 1996-09-03 | Devilbiss Health Care, Inc. | Control for CPAP apparatus |
US5537997A (en) | 1995-01-26 | 1996-07-23 | Respironics, Inc. | Sleep apnea treatment apparatus and passive humidifier for use therewith |
US5598838A (en) | 1995-04-07 | 1997-02-04 | Healthdyne Technologies, Inc. | Pressure support ventilatory assist system |
US5937855A (en) | 1995-04-21 | 1999-08-17 | Respironics, Inc. | Flow regulating valve in a breathing gas delivery system |
US5598837A (en) | 1995-06-06 | 1997-02-04 | Respironics, Inc. | Passive humidifier for positive airway pressure devices |
US5564415A (en) | 1995-06-07 | 1996-10-15 | Lifecare International, Inc. | Humidifier for a ventilator |
US6338473B1 (en) | 1995-06-08 | 2002-01-15 | Resmed Limited | Humidifier |
AUPN344095A0 (en) | 1995-06-08 | 1995-07-06 | Rescare Limited | A humidifier |
US5595173A (en) | 1995-06-29 | 1997-01-21 | Dodd, Jr.; Nevin W. | Rehumidification filter for ventilation mask |
GB9514527D0 (en) | 1995-07-15 | 1995-09-13 | Smiths Industries Plc | Heat and moisture exchangers |
US5586551A (en) | 1995-07-17 | 1996-12-24 | Hilliard; Kenneth R. | Oxygen mask with nebulizer |
GB9515213D0 (en) | 1995-07-25 | 1995-09-20 | Kaptex Healthcare Limited | Filter assembly |
AUPN547895A0 (en) | 1995-09-15 | 1995-10-12 | Rescare Limited | Flow estimation and compenstion of flow-induced pressure swings cpap treatment |
AU718139B2 (en) | 1995-11-13 | 2000-04-06 | Fisher & Paykel Healthcare Limited | Heated respiratory conduit |
US5704916A (en) | 1995-11-30 | 1998-01-06 | Byrd; Timothy N. | Oxygen tube support apparatus and associated method |
US5701891A (en) | 1995-12-01 | 1997-12-30 | Nellcor Puritan Bennett Incorporated | Olefin heat and moisture exchanger |
US5570684A (en) | 1995-12-29 | 1996-11-05 | Behr; R. Douglas | Heating and humidifying respiratory mask |
US6308706B1 (en) | 1996-03-08 | 2001-10-30 | LAMMERS LéON | Device and process for monitoring the respiration parameters of an artificial respiration system |
US5735267A (en) | 1996-03-29 | 1998-04-07 | Ohmeda Inc. | Adaptive control system for a medical ventilator |
US5853884A (en) | 1997-03-26 | 1998-12-29 | Whatman, Inc. | Method for producing unsupported fiber bundles for HME and other filtration applications |
US5829428A (en) | 1996-05-29 | 1998-11-03 | Alliance Pharmaceutical Corp. | Methods and apparatus for reducing the loss of respiratory promoters |
US6394091B1 (en) | 1996-06-05 | 2002-05-28 | Scott Technologies, Inc. | Breathing apparatus |
FI104312B1 (en) | 1996-06-27 | 1999-12-31 | Instrumentarium Oy | An arrangement for treating the respiratory gas of an intubated patient |
JPH1028737A (en) | 1996-07-16 | 1998-02-03 | Metoran:Kk | Humidification adjusting unit and humidifier for artificial respirator and manufacture of humidification adjusting unit |
JP3748466B2 (en) | 1996-08-23 | 2006-02-22 | 株式会社メトラン | Humidification adjustment unit and method for manufacturing humidification adjustment unit |
US5694923A (en) | 1996-08-30 | 1997-12-09 | Respironics, Inc. | Pressure control in a blower-based ventilator |
US5836303A (en) | 1996-09-17 | 1998-11-17 | Thermal Air Products, Inc. | Respirator apparatus |
AUPO247496A0 (en) | 1996-09-23 | 1996-10-17 | Resmed Limited | Assisted ventilation to match patient respiratory need |
US6014890A (en) | 1996-09-25 | 2000-01-18 | Breen; Peter H. | Fast response humidity and temperature sensor device |
US6165105A (en) | 1996-09-27 | 2000-12-26 | Boutellier; Urs | Apparatus and method for training of the respiratory muscles |
US5709204A (en) | 1996-11-04 | 1998-01-20 | Lester; Richard | Aircraft passenger oxygen, survival and escape mask |
US5730122A (en) | 1996-11-12 | 1998-03-24 | Cprx, Inc. | Heart failure mask and methods for increasing negative intrathoracic pressures |
SE507802E (en) | 1996-11-14 | 2001-11-28 | Gibeck Ab Louis | Apparatus and method for the reuse of anesthetics in inhalation anesthesia |
US6439231B1 (en) | 1996-11-18 | 2002-08-27 | Medlis Corp. | Artificial ventilation systems and components thereof, and methods for providing, assembling and utilizing same |
CA2222830C (en) | 1996-12-02 | 2004-03-30 | Fisher & Paykel Limited | Humidifier sleep apnea treatment apparatus |
AUPO418696A0 (en) | 1996-12-12 | 1997-01-16 | Resmed Limited | A substance delivery apparatus |
US6561191B1 (en) | 1997-02-10 | 2003-05-13 | Resmed Limited | Mask and a vent assembly therefor |
GB9704241D0 (en) | 1997-02-28 | 1997-04-16 | Smiths Industries Plc | Gas-treatment devices |
US5785050A (en) * | 1997-03-03 | 1998-07-28 | Davidson; Brian R. | Oxygen valve system |
JPH10248947A (en) | 1997-03-11 | 1998-09-22 | Hisashi Nishida | Mask for evacuation |
US20040221844A1 (en) | 1997-06-17 | 2004-11-11 | Hunt Peter John | Humidity controller |
US7106955B2 (en) | 1999-08-23 | 2006-09-12 | Fisher & Paykel Healthcare Limited | Humidity controller |
CA2619893C (en) | 1997-06-17 | 2011-11-15 | Fisher & Paykel Healthcare Limited | Respiratory humidification system |
AUPO742297A0 (en) | 1997-06-18 | 1997-07-10 | Resmed Limited | An apparatus for supplying breathable gas |
US5957131A (en) | 1997-07-31 | 1999-09-28 | The United States Of America As Represented By The Secretary Of The Army | Biological warfare mask |
JP2001516623A (en) | 1997-09-19 | 2001-10-02 | レスピロニックス・インコーポレイテッド | Medical respirator |
AUPP026997A0 (en) | 1997-11-07 | 1997-12-04 | Resmed Limited | Administration of cpap treatment pressure in presence of apnea |
US5992413A (en) | 1997-12-24 | 1999-11-30 | Enternet Medical, Inc. | Heat and moisture exchanger and generator |
US6318369B1 (en) | 1998-03-05 | 2001-11-20 | Kenneth M. Gregory | Eye ear and respiration protection apparatus |
US6026811A (en) | 1998-03-12 | 2000-02-22 | Settle; Romaine A. | Protective cover for nasal air supply hose |
US6550476B1 (en) | 1998-05-21 | 2003-04-22 | Steven L. Ryder | Heat-moisture exchanger and nebulization device |
US6363930B1 (en) | 1998-07-10 | 2002-04-02 | Enternet Medical, Inc. | Apparatus for providing heat/moisture to respiratory gases |
US6095135A (en) | 1998-07-10 | 2000-08-01 | Enternet Medical, Inc. | Apparatus for providing benefits to respiratory gases |
IT1301860B1 (en) | 1998-07-24 | 2000-07-07 | Fausto Ferraro | AIR FILTERING EQUIPMENT EQUIPPED WITH ABOCCAGLIO GRIP |
US6561193B1 (en) | 1998-10-30 | 2003-05-13 | Linda J. Noble | Nasal gas delivery apparatus and a nasal vestibular airway |
AUPP693398A0 (en) | 1998-11-05 | 1998-12-03 | Resmed Limited | Fault diagnosis in CPAP and NIPPV devices |
US6360741B2 (en) | 1998-11-25 | 2002-03-26 | Respironics, Inc. | Pressure support system with a low leak alarm and method of using same |
SE9804148D0 (en) | 1998-12-01 | 1998-12-01 | Siemens Elema Ab | System and method for determining changes in body resources during aided breathing |
AUPP783198A0 (en) | 1998-12-21 | 1999-01-21 | Resmed Limited | Determination of mask fitting pressure and correct mask fit |
AU756477C (en) | 1998-12-23 | 2003-09-11 | Fisher & Paykel Healthcare Limited | Fault protection system for a respiratory conduit heater element |
EP1140263B1 (en) | 1999-01-15 | 2011-05-11 | ResMed Limited | Method and apparatus to counterbalance intrinsic positive end expiratory pressure |
US6103181A (en) | 1999-02-17 | 2000-08-15 | Filtrona International Limited | Method and apparatus for spinning a web of mixed fibers, and products produced therefrom |
US6330883B1 (en) | 1999-02-17 | 2001-12-18 | Filtrona Richmond, Inc. | Heat and moisture exchanger comprising hydrophilic nylon and methods of using same |
US6776162B2 (en) | 2000-03-13 | 2004-08-17 | Innomed Technologies, Inc. | Ventilation interface for sleep apnea therapy |
US6478026B1 (en) | 1999-03-13 | 2002-11-12 | Thomas J. Wood | Nasal ventilation interface |
US6595215B2 (en) | 2000-03-13 | 2003-07-22 | Innomed Technologies, Inc. | Ventilation interface for sleep apnea therapy |
US6398197B1 (en) | 1999-05-10 | 2002-06-04 | Fisher & Paykel Limited | Water chamber |
SE514362C2 (en) | 1999-06-04 | 2001-02-12 | Atos Medical Ab | Vocal valve |
US6581601B2 (en) | 1999-06-18 | 2003-06-24 | Saeed Ziaee | Nasal mask with balloon exhalation valve |
US6805120B1 (en) | 1999-09-20 | 2004-10-19 | Fisher & Paykel Healthcare Limited | Breathing assistance apparatus |
US6318366B1 (en) | 1999-09-22 | 2001-11-20 | Salter Labs | Supply valve and diaphragm for a pneumatically-operated gas demand apparatus |
US6772758B2 (en) | 1999-09-30 | 2004-08-10 | Atos Medical | Breathing protector |
AUPQ339099A0 (en) | 1999-10-13 | 1999-11-04 | Resmed Limited | A humidifier |
US6536436B1 (en) | 1999-10-26 | 2003-03-25 | Mcglothen Roberta | Strap for nasal cannula |
IT1310042B1 (en) | 1999-11-26 | 2002-02-05 | Pier Luigi Delvigo | FILTER WITHOUT DEAD SPACE |
US6523538B1 (en) | 2000-01-05 | 2003-02-25 | Instrumentarium Corp. | Breathing circuit having improved water vapor removal |
US6435178B1 (en) | 2000-01-06 | 2002-08-20 | Cheng-Chi Lin | Swim mask with floating air-suction device |
US6679264B1 (en) | 2000-03-04 | 2004-01-20 | Emphasys Medical, Inc. | Methods and devices for use in performing pulmonary procedures |
US6516798B1 (en) | 2000-03-07 | 2003-02-11 | Timothy A. Davies | Method of breathing tracheally |
US7588029B2 (en) | 2000-03-21 | 2009-09-15 | Fisher & Paykel Healthcare Limited | Humidified gases delivery apparatus |
US7111624B2 (en) | 2000-03-21 | 2006-09-26 | Fisher & Paykel Healthcare Limited | Apparatus for delivering humidified gases |
US6918389B2 (en) | 2000-03-21 | 2005-07-19 | Fisher & Paykel Healthcare Limited | Breathing assistance apparatus |
US7120354B2 (en) | 2000-03-21 | 2006-10-10 | Fisher & Paykel Healthcare Limited | Gases delivery conduit |
US6584977B1 (en) | 2000-04-06 | 2003-07-01 | Respironics, Inc. | Combined patient interface and exhaust assembly |
WO2001078838A2 (en) | 2000-04-17 | 2001-10-25 | Scott Technologies, Inc. | Respiratory mask and service module |
US20010035185A1 (en) | 2000-04-26 | 2001-11-01 | Christopher Kent L. | Method and apparatus for pharyngeal augmentation of ventilation |
EP1289590B1 (en) | 2000-06-14 | 2017-08-09 | Fisher & Paykel Healthcare Limited | Breathing assistance apparatus |
CA2350351C (en) | 2000-06-14 | 2008-11-25 | Fisher And Paykel Limited | Nasal mask |
US7559324B2 (en) | 2000-06-21 | 2009-07-14 | Fisher & Paykel Healthcare Limited | Conduit with heated wick |
AU780911C (en) | 2000-06-21 | 2005-09-22 | Fisher & Paykel Healthcare Limited | Conduit with heated wick |
US6668828B1 (en) | 2000-10-16 | 2003-12-30 | Pulmonox Technologies Corporations | System and elements for managing therapeutic gas administration to a spontaneously breathing non-ventilated patient |
US6571794B1 (en) | 2000-10-19 | 2003-06-03 | Mallinckrodt, Inc. | Multi-lumen hose for respirators |
US6609520B1 (en) | 2000-10-31 | 2003-08-26 | Kimberly-Clark Worldwide, Inc. | Closed suction catheter adaptor and assembly containing the same |
US6769430B1 (en) | 2000-10-31 | 2004-08-03 | Kimberly-Clark Worldwide, Inc. | Heat and moisture exchanger adaptor for closed suction catheter assembly and system containing the same |
DE20122937U1 (en) | 2000-12-29 | 2010-09-30 | Resmed Ltd., North Ryde | Characterization of mask systems |
US7013361B2 (en) | 2001-01-24 | 2006-03-14 | Grass Valley Group Inc. | Routing switcher with variable input/output architecture |
US7043979B2 (en) | 2001-01-31 | 2006-05-16 | Fisher & Paykel Healthcare Limited | Respiratory humidification system |
EP2465565B1 (en) | 2001-02-16 | 2016-11-30 | ResMed Limited | Humidifier with structure to prevent backflow of liquid through the humidifier inlet |
JP2004524088A (en) | 2001-02-16 | 2004-08-12 | レスメッド・リミテッド | Monitoring pneumatic signals in devices for treating sleep-disordered breathing |
DE10123278C1 (en) | 2001-05-10 | 2002-06-13 | Univ Hamburg | Breathing device used in intensive care or during anesthesia comprises a respirator, an outlet, an inhalation tube, a twin-channel endotracheal tube, flow meters, pressure meters, and an evaluation device |
US6851425B2 (en) | 2001-05-25 | 2005-02-08 | Respironics, Inc. | Exhaust port assembly for a pressure support system |
DE60226101T2 (en) | 2001-06-27 | 2009-06-25 | Fisher & Paykel Healthcare Ltd., East Tamaki | Exhalation valve for a nasal respiratory mask |
US6776158B1 (en) | 2001-07-26 | 2004-08-17 | Euthanex Corporation | System for anesthetizing laboratory animals |
DE10139881B4 (en) | 2001-08-20 | 2017-06-08 | Resmed R&D Germany Gmbh | Apparatus for supplying a breathing gas and method for controlling the same |
SE519766C2 (en) | 2001-08-28 | 2003-04-08 | Phase In Ab | Device containing a passive breath humidifier for quantitative analysis of breathing gases, where light rays are emitted through a dehumidified gas flow |
SE523461C2 (en) | 2001-08-28 | 2004-04-20 | Phase In Ab | Device for quantitative analysis of respiratory gases using a fuel cell and a bacterial filter |
SE519779C2 (en) | 2001-08-28 | 2003-04-08 | Phase In Ab | Device for quantitative analysis of respiratory gases |
CA2408983A1 (en) | 2001-10-19 | 2003-04-19 | Saeed Ziaee | Nasal mask with balloon exhalation valve |
US6679265B2 (en) | 2001-10-25 | 2004-01-20 | Worldwide Medical Technologies | Nasal cannula |
EP1314445B1 (en) | 2001-11-22 | 2005-09-28 | Resmed Limited | Respiratory mask with porous gas washout vent |
US6505624B1 (en) | 2002-01-29 | 2003-01-14 | George Campbell, Sr. | Gas delivery system retention device and method for retaining a gas delivery system |
US7140367B2 (en) | 2002-02-20 | 2006-11-28 | Fisher & Paykel Healtcare Limited | Conduit overheating detection system |
SE0201858L (en) | 2002-02-27 | 2003-08-28 | Octagon Med Prod | Device for heat and moisture exchange between inhalation and exhalation air flows |
US7438073B2 (en) | 2002-03-08 | 2008-10-21 | Kaerys S.A. | Air assistance apparatus for computing the airflow provided by only means of pressure sensors |
CA2689568C (en) | 2002-03-22 | 2014-02-18 | Invacare Corporation | Nasal mask with central body supported brace |
US7086399B2 (en) | 2002-05-29 | 2006-08-08 | Fisher & Paykel Healthcare Limited | Apparatus for delivery of humidified gases therapy, associated methods and analysis tools |
US6953354B2 (en) | 2002-06-05 | 2005-10-11 | Fisher & Paykel Healthcare Limited | Connector for breathing conduits |
SE0201855D0 (en) | 2002-06-18 | 2002-06-18 | Siemens Elema Ab | Gas dosing device |
GB0215733D0 (en) | 2002-07-06 | 2002-08-14 | Kapitex Healthcare Ltd | Tracheostoma cannula mounting |
US7146976B2 (en) | 2002-08-06 | 2006-12-12 | Mckown Joseph R | Nasal cannula retainer |
US6986353B2 (en) | 2002-08-21 | 2006-01-17 | Medical Device Group, Inc. | Divided nasal cannula assembly |
US20040035431A1 (en) | 2002-08-21 | 2004-02-26 | Wright Clifford A. | Ear cannula system and method of using same |
US6807966B2 (en) | 2002-08-21 | 2004-10-26 | Medical Device Group, Inc. | Oxygen delivery system and method of using same |
WO2004020031A1 (en) | 2002-08-30 | 2004-03-11 | Fisher & Paykel Healthcare Limited | Humidification system |
US6766800B2 (en) | 2002-08-30 | 2004-07-27 | Sensormedics Corporation | Pressure regulating valve for use in continuous positive airway pressure devices |
JP4162126B2 (en) | 2002-09-13 | 2008-10-08 | 宗行 石塚 | Oxygen inhaler |
CA2495653C (en) | 2002-09-17 | 2013-01-08 | Fisher & Paykel Healthcare Limited | Apparatus for delivering humidified gases |
US6976488B2 (en) | 2002-10-30 | 2005-12-20 | Allegiance Corporation | Medication bypass heat and moisture exchange unit |
US7225811B2 (en) | 2002-10-30 | 2007-06-05 | Ruiz Sherrie E | Headgear apparatus |
US7497215B1 (en) | 2002-12-20 | 2009-03-03 | Koninklijke Philips Electronics N.V. | Medical ventilator with compressor heated exhalation filter |
JP2004215996A (en) | 2003-01-16 | 2004-08-05 | Masafumi Kuroki | Fashion mask allowing easy breathing |
EP1590030B1 (en) | 2003-02-04 | 2017-05-24 | Fisher & Paykel Healthcare Limited | Breathing assistance apparatus |
US8844528B2 (en) | 2003-02-18 | 2014-09-30 | Joseph Fisher | Breathing circuits to facilitate the measurement of cardiac output during controlled and spontaneous ventilation |
US20040211421A1 (en) | 2003-02-20 | 2004-10-28 | Bird Products Corporation, A California Corporation | Air-to-air heat exchange for medical ventilator |
US7493902B2 (en) | 2003-05-30 | 2009-02-24 | Fisher & Paykel Healthcare Limited | Breathing assistance apparatus |
US7559326B2 (en) | 2003-06-18 | 2009-07-14 | Resmed Limited | Vent and/or diverter assembly for use in breathing apparatus |
CA2753378C (en) | 2003-06-20 | 2016-01-19 | Resmed Limited | Breathable gas apparatus with humidifier |
AU2003903139A0 (en) | 2003-06-20 | 2003-07-03 | Resmed Limited | Breathable gas apparatus with humidifier |
FR2858236B1 (en) | 2003-07-29 | 2006-04-28 | Airox | DEVICE AND METHOD FOR SUPPLYING RESPIRATORY GAS IN PRESSURE OR VOLUME |
CA2536090C (en) | 2003-08-18 | 2014-07-22 | Anthony D. Wondka | Method and device for non-invasive ventilation with nasal interface |
EP3050590B1 (en) | 2003-08-20 | 2020-07-29 | Fisher & Paykel Healthcare Limited | Water chamber for humidifier |
WO2005028012A1 (en) | 2003-09-19 | 2005-03-31 | Fisher & Paykel Healthcare Limtied | A connector |
SE526142C2 (en) | 2003-11-10 | 2005-07-12 | Hudson Rci Ab | Moisture-heat exchanger unit |
NZ585133A (en) | 2003-12-31 | 2011-11-25 | Resmed Ltd | Compact oronasal patient interface with inner and outer walls each having convex shape |
WO2005063326A1 (en) | 2003-12-31 | 2005-07-14 | Resmed Limited | Mask system |
US7913497B2 (en) | 2004-07-01 | 2011-03-29 | Respironics, Inc. | Desiccant cartridge |
NZ553013A (en) | 2004-08-10 | 2010-12-24 | Resmed Ltd | Method and apparatus for humidification of breathable gas with profiled varying humidity setting delivery |
US7525663B2 (en) | 2004-08-20 | 2009-04-28 | Resmed Limited | Method and apparatus for humidification of breathable gas by condensation and/or dehumidification |
EP1629859A1 (en) | 2004-08-27 | 2006-03-01 | John Storey Talbot | Face mask |
US7469698B1 (en) | 2004-09-14 | 2008-12-30 | Winthrop De Childers | Parameter optimization in sleep apnea treatment apparatus |
WO2006063339A2 (en) | 2004-12-08 | 2006-06-15 | Ventus Medical, Inc. | Respiratory devices and methods of use |
US8061357B2 (en) | 2004-12-08 | 2011-11-22 | Ventus Medical, Inc. | Adhesive nasal respiratory devices |
US7806120B2 (en) | 2004-12-08 | 2010-10-05 | Ventus Medical, Inc. | Nasal respiratory devices for positive end-expiratory pressure |
US7428902B2 (en) | 2004-12-15 | 2008-09-30 | Newport Medical Instruments, Inc. | Humidifier system for artificial respiration |
US20080099013A1 (en) | 2005-01-06 | 2008-05-01 | Mark Andrew Graham | Gas-Treatment Devices |
US7594509B2 (en) | 2005-01-18 | 2009-09-29 | Teleflex Medical Incorporated | Heat and moisture exchange device for respiratory therapy |
US7069928B1 (en) | 2005-03-04 | 2006-07-04 | Waldo Jr James V | Heat-moisture exchanger with aerosol by-pass |
US7624731B2 (en) | 2005-03-16 | 2009-12-01 | Dennis R Walstrom | HME/MDI apparatus having MDI in parallel to HME |
JP2006289093A (en) | 2005-04-12 | 2006-10-26 | Woorhitech Co Ltd | Multi-functional mask |
US7870857B2 (en) | 2005-05-23 | 2011-01-18 | Aeon Research And Technology, Inc. | Patient interface assemblies for use in ventilator systems to deliver medication to a patient |
US9032955B2 (en) | 2005-06-06 | 2015-05-19 | Resmed Limited | Mask system |
WO2006133494A1 (en) | 2005-06-14 | 2006-12-21 | Resmed Limited | Methods and apparatus for controlling mask leak in cpap treatment |
US7634998B1 (en) | 2005-07-15 | 2009-12-22 | Fenley Robert C | HME shuttle system |
US7487774B2 (en) | 2005-08-05 | 2009-02-10 | The General Electric Company | Adaptive patient trigger threshold detection |
EP1924312B1 (en) | 2005-08-15 | 2016-06-29 | ResMed Limited | Humidifier tub for cpap device |
WO2007019628A1 (en) | 2005-08-15 | 2007-02-22 | Resmed Ltd | Low cost cpap flow generator and humidifier assembly |
JP2009504277A (en) | 2005-08-15 | 2009-02-05 | レスメド・リミテッド | Humidifier and / or flow generator for CPAP devices |
CN103585709B (en) | 2005-08-29 | 2016-08-10 | 瑞思迈有限公司 | Mouth seal assembly for nasal mask system |
US20070056590A1 (en) | 2005-09-14 | 2007-03-15 | Wolfson Ivan A | Holder for nasal cannula |
GB0520614D0 (en) | 2005-10-11 | 2005-11-16 | Lifelab Innovations Ltd | Respiratory protection device |
WO2007045008A1 (en) | 2005-10-17 | 2007-04-26 | Resmed Limited | Anti-asphyxia valve assembly for respiratory mask |
US7305988B2 (en) | 2005-12-22 | 2007-12-11 | The General Electric Company | Integrated ventilator nasal trigger and gas monitoring system |
EP1960025B1 (en) | 2005-12-16 | 2018-12-19 | Hamilton Medical AG | Flexible conduit system for respiratory devices |
CN2880043Y (en) | 2005-12-21 | 2007-03-21 | 天津医科大学总医院 | Oxygen bag type mattress for transporting injured person for first-aid |
US8459262B2 (en) | 2005-12-21 | 2013-06-11 | Maquet Critical Care Ab | Manual ventilation with electronically controlled APL valve |
US20080142015A1 (en) | 2006-01-27 | 2008-06-19 | David Groll | Apparatus to provide continuous positive airway pressure |
RU2336907C2 (en) | 2006-02-06 | 2008-10-27 | Сергей Леонидович Устьянцев | Individual ustjantsev-velichkovsky respiratory device |
US8074645B2 (en) | 2006-04-10 | 2011-12-13 | Somnetics Global Pte. Ltd. | Apparatus and methods for providing humidity in respiratory therapy |
GB0609400D0 (en) | 2006-05-12 | 2006-06-21 | Intersurgical Ag | Improvements relating to respiratory masks |
EP2026723B1 (en) | 2006-05-23 | 2018-11-21 | Theravent, Inc. | Nasal respiratory devices |
EP2032213A4 (en) | 2006-06-07 | 2014-02-19 | Theravent Inc | Nasal devices |
WO2007143792A1 (en) | 2006-06-16 | 2007-12-21 | Resmed Ltd | Elbow assembly |
ES2576454T3 (en) | 2006-07-28 | 2016-07-07 | Resmed Ltd. | Administration of respiratory therapy |
ES2458618T3 (en) | 2006-07-28 | 2014-05-06 | Resmed Limited | Patient interface |
US8161971B2 (en) | 2006-08-04 | 2012-04-24 | Ric Investments, Llc | Nasal and oral patient interface |
WO2008028228A1 (en) | 2006-09-07 | 2008-03-13 | Resmed Ltd | Systems for reducing exhalation pressure in a mask system |
US7810499B2 (en) | 2006-09-19 | 2010-10-12 | Nellcor Puritan Bennett Llc | Gas exhaust system for a mask apparatus for use in a breathing assistance system |
US8567391B2 (en) | 2006-10-10 | 2013-10-29 | Furrex Co., Ltd. | Heat and moisture exchanger, heat and moisture exchanging device, and mask |
JP4413217B2 (en) | 2006-11-07 | 2010-02-10 | 文雄 笠井 | Nose breathing mask |
NZ625605A (en) | 2006-11-08 | 2016-04-29 | Resmed Ltd | Conduit for use in a respiratory apparatus |
EP4166184A1 (en) | 2006-11-08 | 2023-04-19 | ResMed Pty Ltd | Respiratory apparatus |
JP2008136826A (en) | 2006-12-01 | 2008-06-19 | Nao Tanaka | Putting gauze and mask with valve curtain at nose and lip parts |
WO2008070989A1 (en) | 2006-12-13 | 2008-06-19 | Ludwik Fedorko | Method and apparatus for ventilation assistance |
JP5911189B2 (en) | 2006-12-15 | 2016-04-27 | レスメド・リミテッドResMed Limited | Respiratory therapy |
US20080223367A1 (en) | 2007-01-29 | 2008-09-18 | Cox Brian J | Method and apparatus for treating airway obstruction |
CN200995037Y (en) | 2007-01-30 | 2007-12-26 | 诚加兴业股份有限公司 | Swimming-mask structure |
CN101069764A (en) | 2007-02-06 | 2007-11-14 | 何靖 | Self-aid high-concentration oxygen respirator |
WO2008095245A1 (en) | 2007-02-09 | 2008-08-14 | Resmed Ltd | Humidification arrangement for a respiratory apparatus |
DE202007004247U1 (en) | 2007-03-22 | 2007-05-24 | Bartec Gmbh | Respirator e.g. for intensive care units, has feeding arrangement to supply air to patient, discharge equipment to remove expiration air from patient and sensor to determine condensation of supplied air and or expiration air |
US20090241948A1 (en) | 2007-03-28 | 2009-10-01 | Dermot Joseph Clancy | Humidification in breathing circuits |
FR2915106B3 (en) | 2007-04-18 | 2009-03-06 | Diffusion Tech Francaise Sarl | PNEUMATIC NEBULIZER DEVICE OF AEROSOLS. |
US20080257343A1 (en) | 2007-04-19 | 2008-10-23 | Leslie William Peterson | Hingeless oxygen delivery apparatus |
EP2113275B1 (en) | 2007-05-21 | 2012-08-15 | Covidien AG | Medical heat and moisture exchanger (HME) |
EP3893600A1 (en) | 2007-06-05 | 2021-10-13 | ResMed Pty Ltd | Electrical heater with particular application to humification and fluid warming |
US8365726B2 (en) | 2007-06-07 | 2013-02-05 | Resmed Limited | Tub for humidifier |
US8550075B2 (en) | 2007-06-28 | 2013-10-08 | Resmed Limited | Removable and/or replaceable humidifier |
NZ615814A (en) | 2007-07-30 | 2015-05-29 | Resmed Ltd | Patient interface |
US8459259B2 (en) | 2007-07-31 | 2013-06-11 | Resmed Limited | Heating element, humidifier for respiratory apparatus including heating element, and respiratory apparatus |
US20090065005A1 (en) | 2007-09-06 | 2009-03-12 | Ades Abraham J | Nose mask assembly to be worn during sleep having a suspension support bracket and a retractable line |
ES2381585T3 (en) | 2007-09-24 | 2012-05-29 | Covidien Ag | System for conditioning respiratory gases |
US20100282247A1 (en) | 2007-09-25 | 2010-11-11 | Novartis Ag | Treatment of pulmonary disorders with aerosolized medicaments such as vancomycin |
WO2009042973A1 (en) | 2007-09-26 | 2009-04-02 | Breathe Technologies, Inc. | Methods and devices for treating sleep apnea |
DE102007048893C5 (en) | 2007-10-11 | 2011-06-01 | Dräger Medical GmbH | Device for adsorption and desorption of anesthetic |
US8052127B2 (en) | 2007-10-19 | 2011-11-08 | Philip Morris Usa Inc. | Respiratory humidification system |
WO2009058080A1 (en) | 2007-10-29 | 2009-05-07 | Poseidon Diving Systems | Mouth piece for a breathing apparatus |
CN201123948Y (en) | 2007-10-30 | 2008-10-01 | 王双卫 | Double-layer suction type nose mask without repetition |
US8261741B2 (en) | 2007-11-05 | 2012-09-11 | Resmed Limited | Method and apparatus for backspill prevention |
US7913640B2 (en) | 2007-11-09 | 2011-03-29 | Kimberly-Clark Worldwide, Inc. | Moisture indicator for heat and moisture exchange devices |
RU2423158C1 (en) | 2007-11-27 | 2011-07-10 | 3М Инновейтив Пропертиз Компани | Unidirectional lock face mask |
NZ605600A (en) | 2008-03-04 | 2014-11-28 | Resmed Ltd | Unobtrusive interface systems |
US9802022B2 (en) | 2008-03-06 | 2017-10-31 | Resmed Limited | Humidification of respiratory gases |
CN201161072Y (en) | 2008-03-21 | 2008-12-10 | 李昌军 | Antipoisoning case |
US7981097B2 (en) | 2008-03-27 | 2011-07-19 | Paoli Jr Alexander Delli | Medical device for the treatment and prevention of eye and respiratory tract conditions |
DE202009019113U1 (en) | 2008-03-28 | 2016-07-28 | Stamford Devices Limited | Ventilation circuit with aerosol introduction device |
US8464715B2 (en) | 2008-04-16 | 2013-06-18 | Stephen Donald Flynn, SR. | Multipurpose therapeutic face mask |
CA2726116C (en) | 2008-05-27 | 2023-01-24 | Fisher & Paykel Healthcare Limited | Control of humidifier chamber temperature for accurate humidity control |
US20090293881A1 (en) | 2008-05-30 | 2009-12-03 | Graham William B | Mask for oxygen delivery with medication inlet |
US20090301476A1 (en) | 2008-06-05 | 2009-12-10 | Neil Alex Korneff | Heat and moisture exchange unit |
US20090301477A1 (en) | 2008-06-05 | 2009-12-10 | Brian William Pierro | Heat and moisture exchange unit with check valve |
US8561606B2 (en) | 2008-06-05 | 2013-10-22 | Carefusion 2200, Inc. | Heat and moisture exchange unit |
NZ742900A (en) | 2008-06-05 | 2020-02-28 | ResMed Pty Ltd | Treatment of respiratory conditions by automatic control of flow and/or temperature and/or humidity independently to nares via separate flow paths |
US20090301474A1 (en) | 2008-06-05 | 2009-12-10 | Neil Alex Korneff | Heat and moisture exchange unit with resistance indicator |
CN201249002Y (en) | 2008-07-17 | 2009-06-03 | 深圳市富隆特塑胶制品有限公司 | Diving mask with drainage function |
CN201239409Y (en) | 2008-08-19 | 2009-05-20 | 彦大有限公司 | Improved structure of positive-pressure respiratory organ face helmet |
JP5715950B2 (en) | 2008-08-22 | 2015-05-13 | ブリーズ・テクノロジーズ・インコーポレーテッド | Method and apparatus for providing mechanical ventilation with an open airway interface |
WO2010028427A1 (en) | 2008-09-10 | 2010-03-18 | Resmed Ltd | Improved power management in respiratory treatment apparatus |
US20100071699A1 (en) | 2008-09-24 | 2010-03-25 | Campbell Cecil E | Air filtration apparatus and method |
US8439032B2 (en) | 2008-09-30 | 2013-05-14 | Covidien Lp | Wireless communications for a breathing assistance system |
CN201279335Y (en) | 2008-10-15 | 2009-07-29 | 陈光宴 | Novel respirator |
US9180269B2 (en) | 2008-10-16 | 2015-11-10 | Paul Erby Dureus | Breathing mask and methods thereof |
US8714152B2 (en) | 2008-10-16 | 2014-05-06 | Koninklijke Philips N.V. | Ventilator with limp mode |
EP2337603A1 (en) | 2008-10-16 | 2011-06-29 | Koninklijke Philips Electronics N.V. | Accessory connection and data synchronication in a ventilator |
CN102256649B (en) | 2008-10-17 | 2014-12-17 | 皇家飞利浦电子股份有限公司 | Porting block for a medical ventilator |
US20100101584A1 (en) | 2008-10-29 | 2010-04-29 | Hannah Bledstein | Reusable porous filtration mask with concealed respiratory filter and exhalation valves |
CN101474449A (en) | 2008-12-11 | 2009-07-08 | 邓培友 | Nose mask for breathing oxygen |
WO2010076704A1 (en) | 2008-12-30 | 2010-07-08 | Koninklijke Philips Electronics N.V. | System and respiration appliance for supporting the airway of a subject |
CN201356075Y (en) | 2009-01-06 | 2009-12-09 | 秦邦山 | Multifunctional protective mask |
US9132250B2 (en) | 2009-09-03 | 2015-09-15 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with an entrainment port and/or pressure feature |
US20120097156A1 (en) | 2009-02-17 | 2012-04-26 | Somnetics Global Pte. Ltd. | Positive airway pressure therapy mask humidification systems and methods |
US8453649B2 (en) | 2009-02-18 | 2013-06-04 | 0200L, Llc | Apparatus for positioning a nasal cannula |
IT1393213B1 (en) | 2009-03-17 | 2012-04-11 | Covidien Ag | SYSTEM FOR CONDITIONING RESPIRATORY GASES |
US9962512B2 (en) | 2009-04-02 | 2018-05-08 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with a free space nozzle feature |
JP2010264183A (en) | 2009-05-18 | 2010-11-25 | Takeuchi Kaisoku Noko:Kk | Multifunctional preventive mask |
EP2269681A3 (en) | 2009-06-30 | 2011-02-09 | Covidien AG | Humidifier for humidifying a gas in a respiratory circuit |
AU2010206053B2 (en) | 2009-07-31 | 2014-08-07 | ResMed Pty Ltd | Wire Heated Tube with Temperature Control System, Tube Type Detection, and Active Over Temperature Protection for Humidifier for Respiratory Apparatus |
EP2473221B1 (en) | 2009-09-03 | 2020-11-11 | Breathe Technologies, Inc. | Systems for non-invasive ventilation including a non-sealing ventilation interface with an entrainment port and/or pressure feature |
ATE546185T1 (en) | 2009-09-29 | 2012-03-15 | Covidien Ag | RESPIRATORY DEVICE FOR DELIVERING MEDICINAL PRODUCTS |
CN102049080A (en) | 2009-11-10 | 2011-05-11 | 崇仁(厦门)医疗器械有限公司 | Breathing mask |
US8439037B2 (en) | 2009-12-01 | 2013-05-14 | Covidien Lp | Exhalation valve assembly with integrated filter and flow sensor |
US8439036B2 (en) | 2009-12-01 | 2013-05-14 | Covidien Lp | Exhalation valve assembly with integral flow sensor |
US20110203595A1 (en) | 2010-02-19 | 2011-08-25 | Julia Hashemieh | Cannula Security Piece |
US8978648B2 (en) | 2010-04-07 | 2015-03-17 | Resmed Limited | Air delivery conduit |
US10265492B2 (en) | 2010-04-30 | 2019-04-23 | Resmed Limited | Respiratory mask |
CN101816466B (en) | 2010-05-06 | 2012-01-04 | 上海大胜卫生用品制造有限公司 | Bowl-shaped three-dimensional folding dustproof mask |
-
2012
- 2012-03-27 US US13/431,821 patent/US9486602B2/en active Active
- 2012-03-27 US US13/431,827 patent/US9616194B2/en active Active
- 2012-06-18 WO PCT/US2012/043011 patent/WO2012177566A1/en active Application Filing
Patent Citations (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3675649A (en) * | 1970-08-21 | 1972-07-11 | Westland Aircraft Ltd | Electronically controlled oxygen regulators |
US5273031A (en) * | 1990-10-31 | 1993-12-28 | Siemens Aktiengesellschaft | Ventilator |
US5697364A (en) * | 1995-06-07 | 1997-12-16 | Salter Labs | Intermittent gas-insufflation apparatus |
US6006748A (en) * | 1996-10-16 | 1999-12-28 | Resmed Limited | Vent valve apparatus |
US20090151724A1 (en) * | 2007-09-26 | 2009-06-18 | Breathe Technologies, Inc. | Methods and devices for providing inspiratory and expiratory flow relief during ventilation therapy |
US20110197885A1 (en) * | 2008-04-18 | 2011-08-18 | Breathe Technologies ,Inc. | Methods and devices for sensing respiration and controlling ventilator functions |
US20100252037A1 (en) * | 2009-04-02 | 2010-10-07 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive open ventilation with gas delivery nozzles within nasal pillows |
US20110253147A1 (en) * | 2010-04-19 | 2011-10-20 | Gusky Michael H | Breathing apparatus |
US20120060837A1 (en) * | 2010-09-10 | 2012-03-15 | Yong Liu | Nasal intermittent mandatory ventilation (nimv) control system in a ventilator |
US20140000610A1 (en) * | 2010-12-03 | 2014-01-02 | Fisher & Paykel Healthcare Limited | System, apparatus and method for supplying gases |
US20120330183A1 (en) * | 2011-06-22 | 2012-12-27 | Todd Allum | Ventilation mask with integrated piloted exhalation valve and method of ventilating a patient using the same |
US8844533B2 (en) * | 2011-06-22 | 2014-09-30 | Breathe Technologies, Inc. | Ventilation mask with integrated piloted exhalation valve |
Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9492086B2 (en) | 2012-03-21 | 2016-11-15 | Fresca Medical, Inc. | Apparatus, systems, and methods for treating obstructive sleep apnea |
US9333318B2 (en) | 2012-04-13 | 2016-05-10 | Fresca Medical, Inc. | Sleep apnea device |
US10272226B2 (en) | 2012-04-13 | 2019-04-30 | Fresca Medical, Inc. | Auto-feedback valve for a sleep apnea device |
US10307562B2 (en) | 2012-04-13 | 2019-06-04 | Fresca Medical, Inc. | Auto-feedback valve for a sleep apnea device |
Also Published As
Publication number | Publication date |
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US20120330183A1 (en) | 2012-12-27 |
US20120325211A1 (en) | 2012-12-27 |
US9616194B2 (en) | 2017-04-11 |
US9486602B2 (en) | 2016-11-08 |
WO2012177566A1 (en) | 2012-12-27 |
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