Described is a method of stimulating airways of a mammal comprising: cyclically occluding a nasal air stream at a frequency rate between 50 Hz to 650 Hz. Also described is an apparatus for stimulating airways of a mammal, comprising: a fluid connection to each of a first and second naris of the mammal; and an occluding device configured to cyclically occlude a nasal air stream within each fluid connection at a frequency rate between 100 Hz to 650 Hz.

The present system (10) comprises a subject interface (22), a segmenter (12), a loosener (14), sensors (18), and computer processors (28). The segmenter is configured to selectively control gas flow through the subject interface to provide high amplitude pressure oscillations (44) during exhalation such that the high amplitude pressure oscillations aid cough productivity in the subject. The loosener controls gas flow through the subject interface to provide low amplitude pressure oscillations (43, 63) during inhalation (48, 68) and exhalation (49) such that the low amplitude pressure oscillations loosen respiratory secretions. The computer processors detect trigger events based on the output signals such that the one or more trigger events include a loosening trigger event and a segmenting trigger event (66); and responsive to detecting the loosening trigger event, control the loosener to provide the low amplitude pressure oscillations, and, responsive to detecting the segmenting trigger event, control the segmenter to provide the high amplitude pressure oscillations.

A respiratory treatment device includes a housing enclosing a chamber, a chamber inlet configured to receive a flow of air into the chamber, a first chamber outlet configured to permit the flow of air to exit the chamber, and a second chamber outlet configured to permit the flow of air to exit the chamber. A vane mounted within the chamber is configured to rotate between a first position where the flow of air is directed to exit the chamber through the first chamber outlet, and a second position where the flow of air is directed to exit the chamber through the second chamber outlet. A blocking member disposed on the vane is moveable relative to the chamber inlet between a closed position where the flow of air through the chamber inlet is restricted, and an open position where the flow of air through the chamber inlet is less restricted.

Disclosed is an autoCPAP respirator which comprises a control unit, a respiration blower and a pressure sensor. The control unit comprises a controller for generating a first control signal, which induces the speed of the blower to generate a pressurized breathing gas flow, a controller for generating a periodically variable control signal, which activates the blower such that the speed of the blower varies in an oscillating manner at a frequency in the range of 1-20 Hz, and a sensor device, which ascertains one or more of instantaneous speed, instantaneous electrical current and instantaneous electrical power of the blower to determine the breathing gas flow and/or breathing gas volume generated by the blower while using characteristic data of the blower stored in a memory.

An improved oscillating positive expiratory pressure (“OPEP”) device, for respiratory therapy having a self sterilizing flow valve capable of insertion into the curved OPEP body without tools or aids. The flow valve is also tear resistant and incorporates a flared reinforced proximal end. To maximize the benefit to patients, the adjustable therapy selector is constrained from withdrawal and is dimensioned to accept commercially available, standardized respiratory fittings adaptors, mouthpieces and “Tees” that are capable of connection to multiple respiratory therapy devices or medicated aerosol delivery units. The aesthetics have been altered by the addition of an arced handle.

The present technology relates generally to cough-assist devices with humidified cough assistance. In one example, a system includes a cough-assist device having a first phase configured to provide insufflating gas to a patient circuit and a second phase configured to draw exsufflating gas from the patient circuit. A humidifier is disposed between the cough-assist device and a distal end of the patient circuit, the humidifier including a chamber configured to contain heated water and fluidically coupled to the cough-assist device and the patient circuit. The system further includes a bypass configured to (a) direct insufflating gas from the cough-assist device through a first route to the patient circuit such that the insufflating gas is humidified in the chamber, and (b) route exsufflating gas from the patient circuit through a second route to the cough-assist device such that the exsufflating gas bypasses the chamber.

A nebulizer assembly for a respiratory device is provided having a housing defining a chamber. The housing also has a nebulizer port configured to receive a nebulizer to discharge atomized medication into the chamber. An outlet of a handle is coupled to the inlet of the housing. A hose is coupled to an inlet of the handle. A patient interface is coupled to the outlet of the housing. Air flows from the hose to the patient interface via the handle and the housing. The air mixes with the atomized medication within the chamber.

A breathing assistance apparatus and method of controlling a breathing assistance apparatus is disclosed. Particularly, the breathing assistance apparatus is controlled such that it has a drying cycle to enable drying of the tubing that supplies gases to a user and prevent the harboring of pathogens within the tube. The drying cycle is preferably operated automatically by internal controllers in the apparatus. However, it may be manually activated by pressing a button on the apparatus. The drying cycle is preferably activated at the end of a user's treatment session.

A breathing assistance apparatus and method of controlling a breathing assistance apparatus is disclosed. Particularly, the breathing assistance apparatus is controlled such that it has a drying cycle to enable drying of the tubing that supplies gases to a user and prevent the harbouring of pathogens within the tube. The drying cycle is preferably operated automatically by internal controllers in the apparatus. However, it may be manually activated by pressing a button on the apparatus. The drying cycle is preferably activated at the end of a user's treatment session.

The present technology relates generally to cough-assist devices with humidified cough assistance. In one example, a system includes a cough-assist device having a first phase configured to provide insufflating gas to a patient circuit and a second phase configured to draw exsufflating gas from the patient circuit. A humidifier is disposed between the cough-assist device and a distal end of the patient circuit, the humidifier including a chamber configured to contain heated water and fluidically coupled to the cough-assist device and the patient circuit. The system further includes a bypass configured to (a) direct insufflating gas from the cough-assist device through a first route to the patient circuit such that the insufflating gas is humidified in the chamber, and (b) route exsufflating gas from the patient circuit through a second route to the cough-assist device such that the exsufflating gas bypasses the chamber.