Patent Application
20240157081
This invention relates to a respiratory humidifying device and a method of operation.
Respiratory support devices, such as asthma nebulizers, positive airway pressure devices (including PAP, CPAP, APAP and BiPAP), anaesthesia machines, ventilators or even tracheotomy, are used to restore or provide a proper respiration cycle in some patients. These therapies disturb the natural lubrication and normal air conditioning process because there is an increase in pressure and turbulent effect, or the nasal cavity, which is the most important air conditioning part, is bypassed. Breathing devices, can cause drying and trauma of the mucosa where ciliated cells are inactivated and reduced (Malik & Kenyon, 2004). Therefore, the inspiratory airflow has to be warmed and humidified in order to reach the lungs at 37° C. with near 100% relative humidity, and to maintain an optimum mucociliary transport.
This airflow is delivered to a patient (or, in some cases, a user who is not sick) through a patient interface such as a facial mask, nasal mask, nasal pillow mask, tracheotomy tube, endotracheal tube or fabric face mask. Between the respiratory support device and the patient interface it is common to have tubes, valves, Y-connections, suction ports, sampling ports etc., together known as a breathing circuit. The type of patient interface and breathing circuit depends on the application.
WO 2019/093910 discloses a moisture exchanger that is heated to change from being hydrophilic to hydrophobic (or vice versa), and a respiratory humidifying device comprising the moisture exchanger and heating element. The respiratory humidifying device may receive supplied airflow from a respiratory support device, or it may heat and humidify ambient air.
The moisture exchanger of the respiratory humidifying device comprises a temperature-responsive polymer and a substrate that physically supports the temperature-responsive polymer to hold a desired shape and provides a large multiplicity of surfaces for the polymer to be placed in contact with the inspiratory and expiratory airflow. Examples of substrates which might be suitable include fibrous material such as natural fibres (Cotton, Linen, Chitin or Chitosan among others), synthetic or processed fibres (Rayon, Polyvinyl alcohol (PVA), or Polypropylene (PP) among others) or a mix thereof, and non-fibrous materials with a very large number of grains, crystals or pores such as certain manufactured or naturally occurring structures of metals or polymers. Substrates may be created with a regular structure or an irregular structure or a combination of both, for example a woven textile or a non-woven textile, a 3D printed metal matrix or a sintered metal matrix. Some implementations may include a substrate which is a textile while others may use an open-celled foam or yet other suitable materials.
The necessary characteristics of substrates suitable for use with the invention include that they have a very large surface area compared to their volume, and permit air to pass through easily. Ideally the substrate is porous, with a porosity exceeding 10% or 25%, and more preferably 50% or 75%.
The temperature-responsive polymer may be grafted onto the substrate; a co-polymer grafted from the substrate; polymerized to form the substrate; or a co-polymer polymerized to form the substrate. The substrate and temperature-responsive polymer may be the same, for example: a network polymer or co-polymer structure; a network polymeric structure made from one or more polymers or co-polymers; electro-spun fibres; woven fibres; or non-woven fibres. WO 2019/093910 discloses suitable temperature-responsive polymers.
It is acknowledged that the terms “comprise”, “comprises” and “comprising” may, under varying jurisdictions, be attributed with either an exclusive or an inclusive meaning. For the purpose of this specification, and unless otherwise noted, these terms are intended to have an inclusive meaning—i.e., they will be taken to mean an inclusion of the listed components which the use directly references, and possibly also of other non-specified components or elements.
The term airflow is used generally, and may include flows of oxygen-enriched air, anaesthetic gases, or pure oxygen, for example.
Reference to any document in this specification does not constitute an admission that it is prior art, validly combinable with other documents or that it forms part of the common general knowledge.
An object of the invention is to develop an improved respiratory humidifying device which is hygienic to use, or to at least provide the public or industry with a useful choice.
According to one example embodiment there is provided a respiratory humidifying device comprising:
Preferably further comprising a power supply for supplying the supply of power to the heater.
Preferably the first target temperature is above the second target temperature.
Preferably the first target temperature is above the critical solution temperature.
Preferably the first target temperature is at least 0.5° C. above the critical solution temperature.
Preferably the first target temperature is at least 1° C. above the critical solution temperature.
Preferably the second target temperature is below the critical solution temperature.
Preferably the second target temperature is at least 0.5° C. below the critical solution temperature.
Preferably the second target temperature is at least 1° C. below the critical solution temperature.
Preferably the critical solution temperature is a lower critical solution temperature (LCST) and the first target point occurs at least during inspiration.
Preferably the moisture exchanger is heated at least during inspiration.
Preferably the LCST is between 25° C. and 50° C.
Preferably the LCST is between 30° C. and 45° C.
Preferably the first target point is beginning of inspiration.
Preferably the controller increases the heater power or switches the heater on before the change in respiratory flow from expiration to inspiration.
Preferably wherein the second target point is beginning of expiration.
Preferably the controller decreases the heater power or switches the heater off before the change in respiratory flow from inspiration to expiration.
Preferably the critical solution temperature is an upper critical solution temperature (UCST) and the first target point occurs during expiration.
Preferably the moisture exchanger is heated at least during expiration.
Preferably the UCST is between 20° C. and 50° C.
Preferably the UCST is between 30° C. and 45° C.
Preferably the first target point is beginning expiration.
Preferably the controller increases the heater power or switches the heater on before the change in respiratory flow from inspiration to expiration.
Preferably the second target point is beginning inspiration.
Preferably the controller decreases the heater power or switches the heater off before the change in respiratory flow from expiration to inspiration.
Preferably the heater is selected from the group consisting of at least an element, a filament, spiral wires, an inductive coil, radiation, and an infrared heater.
Preferably the respiratory humidifying device further comprising a bias vent.
Preferably the respiratory humidifying device further comprising a water source.
Preferably further comprising a user interface for adjusting the operation of the controller.
Preferably the controller is a processor.
Preferably the controller is a predictive controller based on one or more of a time offset, a static time and a flow rate.
Preferably the controller operates to adjust the amount of moisture extracted from or added to the airflow.
Preferably further comprising sensors and wherein the controller operation is responsive to information received from the sensors.
Preferably the first target temperature or the second target temperature is adjustable depending on the desired inspiration air temperature or the mode of the respiratory humidifying device.
Preferably the mode is invasive or non-invasive ventilation
Preferably further comprising a bacterial filter.
According to one example embodiment there is provided a method of controlling the water vapour release and absorption of a moisture exchanger providing humidified air in a respiratory system having an inspiration and expiration respiratory cycle, the moisture exchanger positioned such that airflow occurring in the inspiration and expiration respiratory cycle is in contact with the moisture exchanger, the moisture exchanger being temperature-responsive and having a critical solution temperature, the method comprising using a controller to control a heater by controlling the supply of power to the heater such that the heater causes the moisture exchanger temperature to rise to or above a target temperature by about a first target point in the respiratory cycle; and the moisture exchanger temperature falls to or is below a second target temperature by about a second target point in the respiratory cycle, wherein during inspiration moisture is added to the incoming air and during expiration the moisture exchanger extracts moisture from the air.
Preferably the first target temperature is above the second target temperature.
Preferably the first target temperature is above the critical solution temperature.
Preferably the first target temperature is at least 1° C. above the critical solution temperature.
Preferably the second target temperature is below the critical solution temperature.
Preferably the second target temperature is at least 0.5° C. below the critical solution temperature.
Preferably the second target temperature is at least 1° C. below the critical solution temperature.
Preferably the critical solution temperature is a lower critical solution temperature (LCST) and the first target point occurs during inspiration.
Preferably the moisture exchanger is heated at least during inspiration.
Preferably the LCST is between 25° C. and 50° C.
Preferably the LCST is between 30° C. and 45° C.
Preferably the first target point is beginning inspiration.
Preferably the controller increases the heater power or switches the heater on before the change in respiratory flow from expiration to inspiration.
Preferably the second target point is beginning of expiration.
Preferably the controller decreases the heater power or switches the heater off before the change in respiratory flow from inspiration to expiration.
Preferably the critical solution temperature is an upper critical solution temperature (UCST) and the first target point occurs during expiration.
Preferably the moisture exchanger is heated at least during expiration.
Preferably the UCST is between 20° C. and 50° C.
Preferably the UCST is between 30° C. and 45° C.
Preferably the first target point is beginning expiration.
Preferably the controller increases the heater power or switches the heater on before the change in respiratory flow from inspiration to expiration.
Preferably the second target point is beginning inspiration.
Preferably the controller decreases the heater power or switches the heater off before the change in respiratory flow from expiration to inspiration.
Preferably the heater is selected from the group consisting of at least an element, a filament, spiral wires, an inductive coil, radiation, and an infrared heater.
Preferably the moisture exchanger further comprises a user interface for adjusting the operation of the controller.
Preferably the controller is a mechanical switch biased with the use of a spring, magnet or other means, to be on or off.
Preferably the controller is a processor.
Preferably the controller is a predictive controller based on one or more of a time offset, a static time and a flow rate.
Preferably the controller operates to adjust the amount of moisture extracted from or add to the airflow.
Preferably the moisture exchanger further comprising sensors and wherein the method further comprises the controller operating in response to information received from the sensors.
Preferably the method further comprises adjusting the first target temperature or the second target temperature depending on the desired inspiration air temperature or the mode of the moisture exchanger.
Preferably the mode is invasive or non-invasive ventilation.
According to a one example embodiment there is provided a moisture exchanger configured for use in a respiratory humidifying device the moisture exchanger being temperature-responsive and having a critical solution temperature, the respiratory humidifying device comprising:
Preferably further comprising a power supply for supplying the supply of power to the heater.
Preferably the first target temperature is above the second target temperature.
Preferably the first target temperature is above the critical solution temperature.
Preferably the first target temperature is at least 0.5° C. above the critical solution temperature.
Preferably the first target temperature is at least 1° C. above the critical solution temperature.
Preferably the second target temperature is below the critical solution temperature.
Preferably the second target temperature is at least 0.5° C. below the critical solution temperature.
Preferably the second target temperature is at least 1° C. below the critical solution temperature.
Preferably the critical solution temperature is a lower critical solution temperature (LCST) and the first target point occurs during inspiration.
Preferably the moisture exchanger is heated at least during inspiration.
Preferably the LCST is between 25° C. and 50° C.
Preferably the LCST is between 30° C. and 45° C.
Preferably the first target point is beginning inspiration.
Preferably the controller increases the heater power or switches the heater on before the change in respiratory flow from expiration to inspiration.
Preferably the second target point is beginning of expiration.
Preferably the controller decreases the heater power or switches the heater off before the change in respiratory flow from inspiration to expiration.
Preferably the critical solution temperature is an upper critical solution temperature (UCST) and the first target point occurs during expiration.
Preferably the moisture exchanger is heated at least during expiration.
Preferably the UCST is between 20° C. and 50° C.
Preferably the UCST is between 30° C. and 45° C.
Preferably the first target point is beginning expiration.
Preferably the controller increases the heater power or switches the heater on before the change in respiratory flow from inspiration to expiration.
Preferably the second target point is beginning inspiration.
Preferably the controller decreases the heater power or switches the heater off before the change in respiratory flow from expiration to inspiration.
Preferably the heater is selected from at the group consisting of at least an element, a filament, spiral wires, radiation, and an infrared heater.
Preferably further comprising a bias vent.
Preferably further comprising a water source.
Preferably further comprising a user interface for adjusting the operation of the controller.
Preferably the controller is a mechanical switch biased with the use of a spring, magnet or other means, to be on or off.
Preferably the controller is a processor.
Preferably the controller is a predictive controller based on one or more of a time offset, a static time and a flow rate.
Preferably the controller operates to adjust the amount of moisture extracted from or add to the airflow.
Preferably further comprising sensors and wherein the controller operation is responsive to information received from the sensors.
Preferably the first target temperature or the second target temperature is adjustable depending on the desired inspiration air temperature or the mode of moisture exchanger.
Preferably the mode is invasive or non-invasive ventilation
Preferably further comprising a bacterial filter.
According to a one example embodiment there is provided a respiratory humidifying device comprising:
Preferably further comprising a power supply for supplying the supply of power to the heater.
Preferably the controller decreases the power to the heater to less than 5% of the available power.
Preferably the controller decreases the power to the heater at least 500 ms before the start of expiration.
Preferably the controller decreases the power to the heater at least 250 ms before the start of expiration.
Preferably the controller decreases the power based on a distinctive point occurring in the inspiration and expiration respiratory cycle.
Preferably the distinctive point is calculated based on a transition from above to below a threshold value or vice versa.
Preferably the threshold value is calculated over a plurality of respiratory cycles.
Preferably the controller further controls the supply of power to the heater such that power to the heater is increased before the beginning of inspiration.
Preferably the controller increases the power to the heater to greater than 90% of available power.
Preferably the controller increases the power to the heater at least 500 ms before the start of inspiration.
Preferably the controller increases the power to the heater at least 250 ms before the start of expiration.
Preferably the controller increases the power based on a distinctive point occurring in the inspiration and expiration respiratory cycle.
Preferably the distinctive point is calculated based on a transition from above to below a threshold value or vice versa.
Preferably the threshold value is calculated over a plurality of respiratory cycles.
Preferably the controller controls the heater to cause the moisture exchanger temperature to rise to or above a first target temperature by about a first target point in the respiratory cycle and the moisture exchanger temperature falls to or is below a second target temperature by about a second target point in the respiratory cycle.
Preferably the first target temperature is above the second target temperature.
Preferably the first target temperature is above the critical solution temperature.
Preferably the first target temperature is at least 0.5° C. above the critical solution temperature.
Preferably the first target temperature is at least 1° C. above the critical solution temperature.
Preferably the second target temperature is below the critical solution temperature.
Preferably the second target temperature is at least 0.5° C. below the critical solution temperature.
Preferably the second target temperature is at least 1° C. below the critical solution temperature.
Preferably the critical solution temperature is a lower critical solution temperature (LCST) and the first target point occurs at least during inspiration.
Preferably the moisture exchanger is heated at least during inspiration.
Preferably the LCST is between 25° C. and 50° C.
Preferably the LCST is between 30° C. and 45° C.
Preferably the first target point is beginning of inspiration.
Preferably the second target point is beginning of expiration.
Preferably the critical solution temperature is an upper critical solution temperature (UCST) and the first target point occurs during expiration.
Preferably the UCST is between 20° C. and 50° C.
Preferably the UCST is between 30° C. and 45° C.
Preferably the first target point is beginning expiration.
Preferably the second target point is beginning inspiration.
Preferably the first target temperature or the second target temperature is adjustable depending on the desired inspiration air temperature or the mode of the respiratory humidifying device.
Preferably the mode is invasive or non-invasive ventilation.
Preferably the heater is selected from the group consisting of at least an element, a filament, spiral wires, an inductive coil, radiation, and an infrared heater.
Preferably further comprising a bias vent.
Preferably further comprising a water source.
Preferably further comprising a user interface for adjusting the operation of the controller.
Preferably the controller is a mechanical switch biased with the use of a spring, magnet or other means, to be on or off.
Preferably the controller is a processor.
Preferably the controller is a predictive controller based on one or more of a time offset, a static time and a flow rate.
Preferably the controller operates to adjust the amount of moisture extracted from or added to the airflow.
Preferably further comprising sensors and wherein the controller operation is responsive to information received from the sensors.
Preferably further comprising a bacterial filter.
According to one example embodiment there is provided a method of controlling the water vapour release and absorption of a moisture exchanger providing humidified air in a respiratory system having an inspiration and expiration respiratory cycle, the moisture exchanger positioned such that airflow occurring in the inspiration and expiration respiratory cycle is in contact with the moisture exchanger, the moisture exchanger being temperature-responsive and having a critical solution temperature, the method comprising using a controller to control a heater by controlling the supply of power to the heater such that the supply of power to the heater such that power to the heater is decreased before the beginning of expiration, wherein during inspiration moisture is added to the incoming air and during expiration the moisture exchanger extracts moisture from the air.
Preferably the controller decreases the power to the heater to less than 5% of the available power.
Preferably the controller decreases the power to the heater at least 500 ms before the start of expiration.
Preferably the controller decreases the power to the heater at least 250 ms before the start of expiration.
Preferably the controller decreases the power based on a distinctive point occurring in the inspiration and expiration respiratory cycle.
Preferably the distinctive point is calculated by the controller based on a transition from above to below a threshold value or vice versa.
Preferably threshold value is calculated by the controller over a plurality of respiratory cycles.
Preferably the controller further controls the supply of power to the heater such that power to the heater is increased before the beginning of inspiration.
Preferably the controller increases the power to the heater to greater than 90% of available power.
Preferably the controller increases the power to the heater at least 500 ms before the start of inspiration.
Preferably the controller increases the power to the heater at least 250 ms before the start of expiration.
Preferably the controller increases the power based on a distinctive point occurring in the inspiration and expiration respiratory cycle.
Preferably the distinctive point is calculated by the controller based on a transition from above to below a threshold value or vice versa.
Preferably threshold value is calculated by the controller over a plurality of respiratory cycles.
Preferably the controller the heater causes the moisture exchanger temperature to rise to or above a first target temperature by about a first target point in the respiratory cycle and the moisture exchanger temperature falls to or is below a second target temperature by about a second target point in the respiratory cycle.
Preferably the first target temperature is above the second target temperature.
Preferably the first target temperature is above the critical solution temperature.
Preferably the first target temperature is at least 0.5° C. above the critical solution temperature.
Preferably the first target temperature is at least 1° C. above the critical solution temperature.
Preferably the second target temperature is below the critical solution temperature.
Preferably the second target temperature is at least 0.5° C. below the critical solution temperature.
Preferably the second target temperature is at least 1° C. below the critical solution temperature.
Preferably the critical solution temperature is a lower critical solution temperature (LCST) and the first target point occurs during inspiration.
Preferably the moisture exchanger is heated at least during inspiration.
Preferably the LCST is between 25° C. and 50° C.
Preferably the LCST is between 30° C. and 45° C.
Preferably the first target point is beginning inspiration.
Preferably the controller increases the heater power or switches the heater on before the change in respiratory flow from expiration to inspiration.
Preferably wherein the second target point is beginning of expiration.
Preferably the critical solution temperature is an upper critical solution temperature (UCST) and the first target point occurs during expiration.
Preferably the moisture exchanger is heated at least during expiration.
Preferably the UCST is between 20° C. and 50° C.
Preferably the UCST is between 30° C. and 45° C.
Preferably the first target point is beginning expiration.
Preferably the controller increases the heater power or switches the heater on before the change in respiratory flow from inspiration to expiration.
Preferably the second target point is beginning inspiration.
Preferably the method further comprises adjusting the first target temperature or the second target temperature depending on the desired inspiration air temperature or the mode of the moisture exchanger.
Preferably the mode is invasive or non-invasive ventilation.
Preferably the heater is selected from the group consisting of at least an element, a filament, spiral wires, an inductive coil, radiation, and an infrared heater.
Preferably the moisture exchanger further comprises a user interface for adjusting the operation of the controller.
Preferably the controller is a mechanical switch biased with the use of a spring, magnet or other means, to be on or off.
Preferably the controller is a processor.
Preferably the controller is predictive controller based on one or more of a time offset, a static time and a flow rate.
Preferably the controller operates to adjust the amount of moisture extracted from or add to the airflow.
Preferably the moisture exchanger further comprising sensors and wherein the method further comprises the controller operating in response to information received from the sensors.
According to one example embodiment there is provided a moisture exchanger configured for use in a respiratory humidifying device the moisture exchanger being temperature-responsive and having a critical solution temperature, the respiratory humidifying device comprising:
Preferably further comprising a power supply for supplying the supply of power to the heater.
Preferably the controller decreases the power to the heater to less than 5% of the available power.
Preferably the controller decreases the power to the heater at least 500 ms before the start of expiration.
Preferably the controller decreases the power to the heater at least 250 ms before the start of expiration.
Preferably the controller decreases the power based on a distinctive point occurring in the inspiration and expiration respiratory cycle.
Preferably the distinctive point is calculated based on a transition from above to below a threshold value or vice versa.
Preferably the threshold value is calculated over a plurality of respiratory cycles.
Preferably the controller further controls the supply of power to the heater such that power to the heater is increased before the beginning of inspiration.
Preferably the controller increases the power to the heater to greater than 90% of available power.
Preferably the controller increases the power to the heater at least 500 ms before the start of inspiration.
Preferably the controller increases the power to the heater at least 250 ms before the start of expiration.
Preferably the controller increases the power based on a distinctive point occurring in the inspiration and expiration respiratory cycle.
Preferably the distinctive point is calculated based on a transition from above to below a threshold value or vice versa.
Preferably the threshold value is calculated over a plurality of respiratory cycles.
Preferably the controller the heater causes the moisture exchanger temperature to rise to or above a first target temperature by about a first target point in the respiratory cycle and the moisture exchanger temperature falls to or is below a second target temperature by about a second target point in the respiratory cycle.
Preferably the first target temperature is above the second target temperature.
Preferably the first target temperature is above the critical solution temperature.
Preferably the first target temperature is at least 0.5° C. above the critical solution temperature.
Preferably the first target temperature is at least 1° C. above the critical solution temperature.
Preferably the second target temperature is below the critical solution temperature.
Preferably the second target temperature is at least 0.5° C. below the critical solution temperature.
Preferably the second target temperature is at least 1° C. below the critical solution temperature.
Preferably the critical solution temperature is a lower critical solution temperature (LCST) and the first target point occurs during inspiration.
Preferably the LCST is between 25° C. and 50° C.
Preferably the LCST is between 30° C. and 45° C.
Preferably the first target point is beginning inspiration.
Preferably the second target point is beginning of expiration.
Preferably the critical solution temperature is an upper critical solution temperature (UCST) and the first target point occurs during expiration.
Preferably the UCST is between 20° C. and 50° C.
Preferably the UCST is between 30° C. and 45° C.
Preferably the first target point is beginning expiration.
Preferably the second target point is beginning inspiration.
Preferably the first target temperature or the second target temperature is adjustable depending on the desired inspiration air temperature or the mode of moisture exchanger.
Preferably the mode is invasive or non-invasive ventilation.
Preferably the heater is selected from at the group consisting of at least an element, a filament, spiral wires, radiation, and an infrared heater.
Preferably further comprising a bias vent.
Preferably further comprising a water source.
Preferably further comprising a user interface for adjusting the operation of the controller.
Preferably the controller is a mechanical switch biased with the use of a spring, magnet or other means, to be on or off.
Preferably the controller is a processor.
Preferably the controller is predictive controller based on one or more of a time offset, a static time and a flow rate.
Preferably the controller operates to adjust the amount of moisture extracted from or add to the airflow.
Preferably further comprising sensors and wherein the controller operation is responsive to information received from the sensors.
Preferably further comprising a bacterial filter.
The accompanying drawings which are incorporated in and constitute part of the specification, illustrate embodiments of the invention and, together with the general description of the invention given above, and the detailed description of embodiments given below, serve to explain the principles of the invention, in which:
The respiratory humidifying device can be integrated in the patient interface, such as CPAP and Non-invasive Ventilation (NIV) masks, where the moisture exchanger is located inside the mask;
or located between the mask frame inlet and the main breathing circuit.
Many CPAP and Non-invasive Ventilation (NIV) patient interfaces have a bias flow vent (outlet) located on the mask frame or elbow (see
Connectors
Masks designed with no bias flow vent on the frame, elbow or generally on the patient side of the respiratory humidifying device should have mechanical connections that are designed not to connect directly to standard CPAP circuits, such as 22 mm tapered connectors (or similar ISO standard connectors). This will prevent the patient or healthcare providers from accidently connecting standard CPAP breathing circuits directly to the mask, without using the respiratory humidifying device. Doing so may harm the patient as no bias flow vent would be provided in the system (of a non-vented mask). Warnings, colours and/or words may be placed on such masks to provide additional protection.
The connector on the non-patient (upstream) side of the respiratory humidifying device may be any standard ISO medical connector, such as a 22 mm male or female tapered connector. This will enable the respiratory humidifying device to connect to standard hospital or home breathing circuits. There may be more than one upstream connector.
The patient (downstream) side of the respiratory humidifying device preferably should not have a standard removeable connector, in order to avoid accidentally connecting it to a non-vented mask, when the respiratory humidifying device is designed to be used with a non-vented mask. Alternatively, the downstream connector may be a standard connector, depending on the application.
The respiratory humidifying device requires a moisture exchanger to be positioned in the airflow.
In some applications, for example CPAP, APAP or BiPAP shown in
The bias flow vent may be incorporated into the respiratory humidifying device or removeable module housing and may be a single or multiple holes and may additionally be covered with a diffuser or filter-like material to diffuse the flow of air escaping out the bias flow vent to reduce patient annoyance.
Preferably the bias flow vent is located close to the moisture exchanger, preferably within 5 cm or more preferably within 3 cm of the moisture exchanger, and is positioned such that air supplied by a respiratory support device reaches the bias flow vent before reaching the moisture exchanger.
Preferably the bias flow vent is arranged such that some of the bias flow passing therethrough is directed against the moisture exchanger to create a cooling flow, which cools the moisture exchanger during expiration or at the end of inspiration. The cooling flow may be turbulent eddies of the bias flow created by the bias flow exiting through the bias flow vent, or it may be the bias flow itself directed parallel with the surface of the moisture exchanger by virtue of the relative arrangement of an upstream connector supplying air from the respiratory support device and the bias flow vent. Therefore, there may be bias flow guides within the respiratory humidifying device which direct the cooling flow to the moisture exchanger.
The cooling flow must not be so strong as to substantially pass through the moisture exchanger, as in doing so it would cool the walls of the device downstream (towards the patient) of the moisture exchanger and thereby create condensation. Therefore, there may also be bias flow baffles on the opposite side of the moisture exchanger to the bias flow vent to prevent the cooling flow from cooling. Preferably also the bias flow vent is at least 1 cm, and preferably at least 2 cm, from the moisture exchanger.
The removeable module comprises a moisture exchanger as shown in
The upstream tube contains two wires to carry power from the controller to the heater. The heater is held in contact with the two wires by rotationally latching the upstream and downstream tubes into the housing, at a predetermined rotation relative to the housing and the upstream tube determined by its design and the design of the housing and arranged to ensure that the heater is powered by the two wires coming from the upstream tube.
The upstream tube connects to the respiratory support device and the two wires connect to the controller of the respiratory humidifying device via a connector, so that the controller can heat the moisture exchanger. The wires may be formed into the upstream tube, or may be removably clipped to it, or may take another path altogether.
In use, the removeable module may be separated by a twisting motion, allowing the moisture exchanger and/or heater to be replaced. Also, the removeable module may be replaced at different times to the upstream or downstream tubes.
In an alternative embodiment, the housing is part of the upstream tube, the heater is fixed in the housing, and only the moisture exchanger is removeable.
The controller, sensors and power supply of the respiratory humidifying device may all be located within one housing also containing the moisture exchanger and heater, as shown in
For example, in
The wires may be held to the breathing circuit, mechanically clipped or secured to the outside of the breathing circuit. Alternatively, they may be located inside the breathing circuit or built into the wall of the breathing circuit, as is common with heated wall respiratory support device tubes and is shown in
Signals may also be sent between the respiratory humidifying device housing and respiratory support device via wireless technology, such as Bluetooth, WiFi or inductive power transfer with communication.
The respiratory humidifying device, and in particular the removeable module, can include zero, one or more integral bacterial/viral filters in the inspiratory or expiratory airflow path. Where the respiratory device includes zero integral filters, it may be used with an external filter(s) fitted to the main breathing circuit to filter inspiratory or expiratory flow, or both.
The removeable module 8001 in
Where a bias flow vent is also integrated and expiratory filtering is required, the filter, or filters, should be located between the moisture exchanger and any bias flow outlet vents.
Filter embodiments may include one or more individual filters to address the functions described above. Where filtration material is directional, the more hydrophobic filtration surface shall be orientated to face the moisture exchanger for each filter. The bacterial/viral filter(s) and design embodiment of filter retention shall ensure all airflow in the required filtration directions must pass through the filter.
The respiratory humidifying device may be used in combination with a breathing system filter such as pleated hydrophobic filter or electrostatic filter placed upstream of the moisture exchanger in order to provide bacterial and viral filtration (>99%) to provide an extra protection to the patient.
The heater preferably comprises a resistive heater in thermal contact (preferably direct thermal contact) with the moisture exchanger. Examples of a resistive heater include wire or conductive polymer filaments sewn into or woven into the moisture exchanger, or said filaments pressed into contact with the moisture exchanger, or a flexible printed circuit glued to or otherwise pressed against them. An exemplary heater and moisture exchanger arrangement is described below.
In some embodiments the heater may be an infrared heater. An infrared heater offers many advantages, such as it can almost instantaneously be turned on and/or off (there is less lag than a wire heater element). An infrared heat may be hygienically separated from the moisture exchanger and inspiratory and expiratory airflow path. This may reduce the cost of operation, as the infrared heat source could be reusable, either between the same or other patients. The infrared heat source could be sealed in a glass or plastic housing, along with the controller, or otherwise separated from the airflow by a light permeable or light bending material.
Any reflected infrared light could also be detected by a light sensor in order to calculate the humidity level of the air passing though the device (being inhaled and/or exhaled by the patient), or the moisture capture by the moisture exchanger.
There may be more than one heater that could be controlled together or independently to deliver different temperature profiles to different locations of the respiratory humidifying device or to different regions of the moisture exchanger.
With cold room conditions, a respiratory humidifying device with just a first heater may not allow the moisture exchanger or the heater to cool down quick enough to capture substantially all of the patient's expired moisture. Therefore, a second heater which is not in contact with the moisture exchanger may cool down faster. Furthermore, during inspiration the second heater is able to pass more thermal energy to the inspired air before it reaches the moisture exchanger; with just a first heater, the first heater may have to be so hot that it would damage the moisture exchanger. Therefore, having two heaters provides a better control of the humidifying performance and more comfort to the user.
Various combination of heater and location (e.g. upstream or downstream of the moisture exchange) are possible. Multiple heaters may also be used, and they may be controlled separately or together by the controller.
The respiratory humidifying device can include a user interface for turning the respiratory humidifying device on and off, changing the humidification performance, cancelling alarms, or checking on the respiratory humidifying device operation. To achieve these goals, the user interface can change parameters related to the desired inspiratory airflow. These parameters can determine, through look up tables or calculations, the target points or target temperatures used to control the timing and magnitude of power applied to the heater.
In alternative embodiments, a button may select between nasal, full face or intubated/tracheostomy options, or a knob might select a humidification or temperature anywhere within a range of 20 mg/L to 40 mg/L or more. The user interface may include the selection and/or display of multiple parameters, such as independently setting/displaying temperature, humidity and/or absolute or relatively humidity.
The user interface may include both an indication of the selected setting and an indication of the achieved level of performance, for example inspiratory airflow humidity or temperature. For example, a red LED indicator could show that a setting has been chosen, but not yet achieved, and a green LED indicator could show that the selected level of humidification is being delivered.
The user interface may also incorporate sounds and/or lights to provide alarms that the respiratory humidifying device has an error condition, for example due to excessive mask leak that may lower the delivered humidification level.
The respiratory humidifying device may include controls for calibrating the respiratory humidifying device or its sensors, changing the function or operation of status lights or alarms, or connect or disconnect a remote management device. Some controls may have multiple functions.
The respiratory humidifying device may incorporate status indicators such as graphical displays, value readouts, lights and speakers or beepers to indicate the functionality of the device (such as a mode or setpoint), the battery charge, correct operation, error conditions, a need to change any consumable element or removeable module, or connection to or disconnection from a remote management device. The user interface may also allow users to configure a sequence of changes in respiratory humidifying device humidification and/or temperature performance over time, e.g. 1 hour at 20 mg/L humidity, 4 hours at 25 mg/L. The user interface may also allow the display of recorded data on respiratory humidifying device performance or use over time periods, such as the previous hour, 24 hours, or longer periods.
The respiratory humidifying device may have a remote management interface to allow a remote management device to configure the respiratory humidifying device.
The remote management device preferably uses the remote management interface to achieve all the functions described above with reference to the user interface. The remote management device can preferably also retrieve data from the respiratory humidifying device, for example times and amounts of usage or non-usage; inspiratory and expiratory airflow parameters measured by sensors or otherwise inferred; occurrence or frequency of episodes of sleep apnoea, respiratory distress, difficulty breathing etc; the need for or act of replacement of parts; or error conditions.
The remote management interface may comprise one or more of wireless communication (e.g. cellular network, Wide Area Network e.g. Lorawan, Sigfox, Bluetooth, WiFi, Zigbee, Z-Wave, NFC) or wired communication (e.g. USB, 12C, SPI, RS-232, RS-485).
The remote management device may be a respiratory support device, mobile phone, tablet computer, computer server or internet cloud service. The remote management device may be an artificial intelligence remote management device which is able to retrieve data from the respiratory humidifying device and to take actions based on the data including configuring the respiratory humidifying device and alerting human users or patients.
In each of
The user interface and the controller do not have to be in the same unit. For example, it is also possible for the controller to be placed in the module connector, and the user interface to be a separate unit. Such an embodiment would be indistinguishable from
Rather than using an electronic controller to determine when to provide power to the heater, the controller may be a mechanical switch used to control power to the heater. For example, a mechanical switch could be located within the air flow path. The switch could be toggled from on to off by the change in direction of the patient's breath. When the patient inhales the flow switch could toggle to on, and supply power to the heater. When the patient breaths out the flow switch could be toggled to off, removing power from the heater and thus mechanically controlling power to the heater.
The mechanical flow switch is preferably biased, for example with the use of a spring, magnet or other system, to be on, or off. For example, if the flow switch is biased to be on, when the patient is nearing the end of their expiration cycle, the biasing of the flow switch will cause the switch to change to the on state, thus providing power to the heater allowing it time to heat up and provide heat to the moisture exchanger for the start of the inspiration part of the respiratory cycle. Alternatively, if the flow switch is biased to be off, when the patient is nearing the end of their inspiration cycle, the biasing of the flow switch will cause the switch to change to the off state, this removing power from the heater allowing the moisture exchanger time to cool down before the start of the expiration part of the respiratory cycle. This bias can be user adjustable to delivery different levels of humidity and/or temperature.
The removeable module in
Firstly, there is an SHT30 temperature and humidity sensor located on the support structure and placed in the airflow on the patient side, i.e. it is a downstream temperature sensor. The SHT temperature and humidity sensor is sufficiently removed from the other components to avoid interference in the readings, for example from heat emitted as part of the flow sensor operation.
Secondly, a flow sensor (
Thirdly, a thermistor acting as the moisture exchanger temperature sensor (
The removeable module in
This sensor and heater combination includes a connection point for a module connector, in this case a reversible connector incorporated into the module.
One probe is an upstream temperature sensor and one probe is a downstream temperature sensor. The removeable module includes two slightly tapered tubes to accept the two probes, and has an upstream end and a downstream end. The module connector includes alignment wings shaped in arcs to partially envelope the outside of the removeable module. Due to being closer to one probe than the other, and also tapering to a smaller diameter on the upstream side of each arc, the wings make it impossible to attach the removeable module incorrectly. The control cable connects to the non-patient side of the module connector and goes to a controller or power supply.
The removeable modules in
The controller also comprises an upstream and downstream ultrasonic transducer which, when the module connector is attached to the removeable module, fit into flow sensor protuberances in the wall of the removeable module and send an ultrasonic signal in alternating directions between them. In use, the controller uses the difference in time of flight of sound travelling upstream and downstream in the airflow, to determine when the patient is breathing in or breathing out. The protuberances protect the transducers from contact with the airflow.
Further, the heater includes contacts on the outer wall of the removeable module, which engage with contact pads on the PCB that protrude through the plastic housing.
Finally, an infra-red (IR) sensor receives light from the heater and moisture exchanger through the wall of the removeable module, and, once calibrated, allows the controller to measure the moisture exchanger and heater temperature. Alternatively, the resistance of the heating element could be measured to estimate the heater and moisture exchanger temperature.
Therefore, no part of the controller is in contact with the airflow, improving the hygiene of the respiratory humidifying device.
The user may select between one of several modes using the user interface, as described with reference to
Instead of measuring the resistance, alternative embodiments include the module connector having three contacts to connect with the heater element, and the controller detecting which type of removeable module has been connected based on the combination of contacts which connect to form a circuit. In yet another alterative, the controller may be able to measure the presence, absence or characteristic of a physical feature unique to each type of removeable module, such as a coloured patch on the removeable module.
In this way, the user does not have to change settings on a user interface to select the mode—they simply choose the labelled or colour-coded removeable module suitable for the intended application, and the respiratory humidifying device will configure itself appropriately. The LED indicator may, for example, match a colour printed on the removeable module, making it easy to establish that the respiratory humidifying device is configured correctly.
Due to manufacturing tolerances, each removeable module may be slightly different from the other. Therefore, it may be necessary to calibrate the controller to each individual removeable module.
The controller similar calibration process may be required for any sensors in the removeable module.
The respiratory humidifying device may be used with respiratory support devices where heated humidifiers, non-heated humidifiers and/or HMEs are used, for example anaesthetic delivery; tracheotomy; CPAP devices; Bi-level PAP devices; and home or hospital ventilators.
It may also be used in other applications where the patient is perfectly healthy, such as personal protection masks for general pollution, industrial pollution and for use in other dry environments, such as aircraft or desert or alpine settings, or any part of the world where people or animals experience dry air, especially cold dry air. In that case the system may have to operate off battery or non-mains power.
The respiratory humidifying device may be used in combination with a water humidifier in order to: provide higher humidification performance, different humidity profiles, use one to maximize the performance of the other, control rainout condensation in a patient interface and/or tubing, provide more accurate temperature control or provide more accurate humidity control.
The respiratory humidifying device may be used in combination with a liquid water reservoir to fill the moisture exchanger with liquid water droplets during inhale and release it during exhale by increasing the moisture exchanger temperature to 80° C. approximately, to evaporate the liquid water.
As disclosed above, it is desirable for the controller to apply power to heat the moisture exchanger not only during the inspiration phase, but before the beginning of inspiration (and before any sensor(s) detect the beginning of inspiration); and to remove power (and heat) not only during the expiration phase but before the beginning of expiration (and before any sensor(s) detect the beginning of expiration) or at least provide the public with a useful choice.
In this embodiment, the controller decreases the heater power (switches the heater off) before the change in respiratory flow from inspiration to expiration. Preferably this is done such that the moisture exchanger temperature falls to or below a second target temperature before expiration starts or at least before expiration has reached a significant portion of peak flow or total volume, for example 5%, 10%, 20% or even perhaps 30% thereof. Preferably the second target temperature is the LCST, or even 0.5° C. or 1° C. below the LCST.
Preferably this is done such that the moisture exchanger temperature rises to or above the first target temperature before inspiration starts or at least before inspiration has reached a significant portion of peak flow or total volume, for example 5%, 10%, 20% or even perhaps 30% thereof. Preferably also the controller controls (limits) the heater power (or keeps the heater off until close to the beginning of inspiration) such that the moisture exchanger temperature does not reach or exceed an undesired temperature before the end of expiration or before the majority of expiratory volume has passed the moisture exchanger (preferably 70% or 80% or even more preferably 90% thereof) or before the expiratory flow has significantly fallen (preferably below 30% or 20%, or even more preferably below 10% of peak expiratory flow). Preferably the desired or undesired temperature is the LCST, or more preferably they are at least 0.5° C. or 1° C. above and below the LCST respectively.
The controller may detect the magnitude or direction of the respiratory airflow using any of the known flow sensors available to the market.
In order to determine when to change the heater power, the controller may sense a measured parameter relating to the airflow through the moisture exchanger and uses the measured parameter to detect one or more distinctive points in the respiratory cycle. Preferably the measured parameter is the air flow rate and direction but in some alternative embodiments it may be the airflow pressure for example.
Ideally the one or more distinctive points include the change from inspiration to expiration and/or vice versa, or equivalently the beginning/end of expiration or inspiration. The beginning and/or end of inspiration and expiration may be detected by calculating when the measured parameter transitions from above to below a threshold value or from below to above the threshold value.
When the measured parameter is the airflow, the threshold value may be zero and, especially if the airflow sensor provides a direction, the beginning or end of expiration may be easy to detect. However, many cost effective sensors do not provide the airflow or the airflow direction, and even if the sensor does provide the airflow and direction the wide variety of ambient conditions the respiratory humidifying device has to operate in, and in particular the possibility of a patient interface leak error condition, means that in some embodiments the threshold value is determined by calculating a mean value of the measured parameter over an immediately preceding period of time which encompasses a plurality of respiratory cycles, for example 30s or 60s. The threshold value may then be the mean value of the measured parameter or it may be set a pre-determined amount above to below the mean value, or a proportional amount above or below the mean value compared to the maximum or minimum value of the measured parameter in the immediately preceding period of time which encompasses a plurality of respiratory cycles. By way of a specific example, the measured parameter may be the airflow (including its direction) through the moisture exchanger and the predictive controller may calculate the mean value of the airflow, detecting the approximate beginning of inspiration when the airflow goes above the mean of the airflow and the beginning of expiration when the airflow goes below the mean of the airflow.
In other embodiments the one or more distinctive points may be determined by the rate of change of the measured parameter being above or below a threshold value.
Using Time Offsets from Distinctive Points
In order to achieve the desirable feature of changing the heater power before the beginning of inspiration or expiration, the controller may be a predictive controller which monitors successive inspiration or expiration cycles or distinctive points to learn the typical period of those cycles, or the period of the respiratory cycle as a whole. With knowledge of those periods, the predictive controller may change the heater power a time offset after one of more of the distinctive points in the respiratory cycle, with the expectation that it will be a known amount before the subsequent one.
In a preferred embodiment the time offset is proportional to the respiratory cycle period. The respiratory cycle period may be calculated from the mean of the elapsed time between one or more of the previous distinctive points.
Further, there may be a plurality of time offsets relating to different distinctive points in a respiratory cycle and/or different changes in the power supply.
The plurality of distinctive points may be the beginning of inspiration and the beginning of expiration, so that the plurality of time offsets comprise an inspiration time offset and an expiration time offset. The inspiration time offset is the time offset after the change in respiratory flow from expiration to inspiration. In one embodiment the controller decreases the heater power (or switches the heater off) at the time which is the inspiration time offset after the change in respiratory flow from expiration to inspiration. The expiration time offset is the time offset after the change in respiratory flow from inspiration to expiration. The controller increases the heater power (or switches the heater on) at the time which is the expiration time offset after the change in respiratory flow from inspiration to expiration.
The time offset, inspiration time offset or the expiration time offset are preferably less than the time period of inspiration or the time period of expiration, or less than the sum of the time period of inspiration or time period of expiration. They are preferably less than 75% of, and more preferably less than 50% of, and even more preferably less than 33% of the time period of inspiration or time period of expiration.
Options for the minimum time offset are, for example 1s, 1.5s, or between 1s and 3s.
In one embodiment the time offset may be pre-determined based on one or more of the time constant of the heater, the transfer rate of heat into the moisture exchanger, and the moisture exchanger response rate to temperature changes and the rate of absorption or desorption of moisture from the moisture exchanger.
The time offset may be a dynamic time offset that varies over time. The dynamic time offset may be determined using one or more of the respiratory cycle period, the desired or actual temperature and humidity of the inspiratory airflow, the humidity, temperature or flow rate of the expiratory airflow, and the temperature or humidity of the ambient air or supplied airflow.
In some embodiments an increase in the desired temperature or humidity of the inspiratory airflow leads to the dynamic time offset becoming smaller, i.e. leads to the controller changing the power supplied to the heating element earlier. Conversely, a decrease in the desired temperature or humidity of the inspiratory airflow leads to the dynamic time offset becoming larger, i.e. leads to the controller changing the power supplied to the heating element later.
Another way of achieving the desirable feature of changing the heater power before the beginning of inspiration or expiration, is to use a Phase- and Frequency-locked Loop (PLL) which is synchronised to the respiratory cycle and driven by the measured parameter. The phase output of the PLL is used to determine whether to turn the heater on or off. The controller may turn the heater on and off at pre-determined or calculated phases with respect to the (PLL estimation of) respiratory cycle. The controller may change the target temperature at pre-determined or calculated phases with respect to the (PLL estimation of) respiratory cycle.
Alternatively, the controller may apply heat when the airflow rate falls below a threshold. For example, when the expiratory airflow rate drops below 40% of the peak expiratory flow, or mean flow, heating may be applied. This percentage is an example, and in practice other flow rate thresholds may be apply, such as 20%, 30% or 50%. This allows time for the heat source to provide heat and to heat the moisture exchanger. This is a useful method as the end of the expiration cycle tends to be a relatively low flow rate over an extended period.
An alternative to this could be a tidal volume threshold, where a sensor, for example a flow sensor, is used to calculate the typical tidal volume and the heating is triggered when the tidal volume of the expiration reaches, for example 80% of the average tidal volume. This percentage is an example, and in practice other tidal volume thresholds may be apply, such as between, 40-80%, 80-90% or 90-99%.
The same triggering can be applied to the inspiration cycle, where the heating is stopped after inspiration flow drops below a threshold or tidal volume inspired exceeds a certain threshold. For example, when the inspiration flow rate drops below 40% of the peak flow, or mean flow, or the tidal volume inspired exceeds 80% of the expected tidal volume, heating may be stopped. This percentage is an example, and in practice other flow rate (or tidal volume) thresholds may be apply, such as between 20%, 30% or 50% (or 40-80%, 80-90% or 90-99%). This allows time for the heat source to provide heat and to heat the moisture exchanger.
The controller may actively adjust any of these thresholds to achieve the optimal moisture exchanger temperature profile, and this may vary from patient to patient depending on their tidal volume, breathing frequency, a setting controlled by a trained operator, and/or the wave form of their breathing. The controller may have a feedback loop, to control the timing of heating to reach the desired timing of moisture exchanger temperature, air temperature and/or humidity delivery in the breath cycle.
The threshold may also be adjusted to achieve a desired level of humidity. For example, if less humidity is required the cooling of the moisture exchanger on expiration may be delayed to reduce moisture build up in the moisture exchanger. Alternatively heating of the moisture exchanger on inspiration may be delayed. This may also be varied depending on the ambient temperature and humidity.
The above thresholds may be actively adjusted using feedback loops or may be pre-set values or be obtained from look up tables. Alternatively, they may be user controlled via an interface that increases or decreases the desired level of humidification.
The controller may apply heat to or remove heat from the moisture exchanger for a fixed period which does not (directly) depend on the respiratory cycle period. For example, the controller may apply heat for 1s or 2s, or most preferably 1.5s. In this way the controller can ensure that the all the moisture is released from the moisture exchanger, that a predictable temperature is reached, and that the moisture exchanger begins to cool at the earliest possible time once all the moisture is released from the moisture exchanger.
Preferably the controller of the respiratory humidifying device provides a peak of power at the beginning of its on stage to rapidly bring the element and moisture exchanger up to temperature, then reduces its power after a short period of time or once a certain temperature (resistance) is reached or calculated or expected to be reached.
Preferably there are a plurality of changes in power supplied to the heating element within a respiratory cycle which include a high power phase followed by a low power phase followed by a no power phase.
Preferably the high power phase is 100% of the maximum power that can be supplied by the controller, or at least 75%.
Preferably the low power phase is <70%, <50%, or less than 30%, of the maximum power that can be supplied by the controller.
Preferably the low power phase lasts for at least 2× as long, or at least 3× as long, or at least 4× as long as the high power phase.
Preferably the high power phase and low power phase together last for less than half the respiratory cycle period, or more preferably less than 40% of the respiratory cycle period.
Alternatively, the delivered power may be controlled in relation to the flow rate, or proportional to the flow rate, at any stage in the breathing cycle.
Alternatively, the delivered power may be controlled by an open loop feedforward or closed loop feedback controller (or a combination thereof) to maintain a desired moisture exchanger temperature or air temperature for inspiration, including different temperatures at different points during inspiration or expiration.
Preferably the high power phase and the low power phase are controlled such that they maintain the moisture exchanger at the desired moisture exchanger temperature for at least 100 ms, or more preferably at least 200 ms, during inspiration to allow time for the moisture exchanger to release moisture into the inspiratory airflow. The desired moisture exchanger temperature is preferably at or above the LCST. The times discussed depend on the application of the humidifying device, if used in a CPAP device the times are shorted, but if used on a tracheotomy tube or ventilator the times will be longer, up to 2 seconds probably. The power (%) provided may also adjust.
In another embodiment the controller controls the temperature of the moisture exchanger using feedback from a moisture exchanger temperature sensor. The controller could use a PID controller or bang-bang (thermostat) controller.
The respiratory humidifying device/apparatus is preferably able to detect one or more error conditions. Error conditions include error of sensors (open circuit, short circuit, invalid signal, loss of signal etc.); error of the heater/device (open circuit, short circuit, incorrect impedance); contamination of the heater or moisture exchanger; power supply out of allowable range; missing or incorrect moisture exchanger component or removeable module; ambient air conditions (temperature, humidity, pressure) out of correct operating range; error to replace removeable modules or other replaceable components in time (for example because their use has exceeded a safe amount since installation); breathing problems such as the patient interface being removed, falling off or leaking; loss of or change in air supply; blockage on the moisture exchanger not allowing air passing through (e.g. high condensation, sputum, secretions).
These error conditions may lead to unnecessary power consumption, unsafe operation, inadequate or excessive therapeutic output (flow, humidity, temperature, pressure) or patient annoyance.
Therefore, upon detecting an error condition the respiratory humidifying device preferably alerts the user or patient through sounds (tones, noises, spoken messages), flashing light(s), interruption of or restriction of the air flow, or communicating with the patient, users, healthcare professionals or a remote management device or another part of the breathing circuit.
The respiratory humidifying device may cease operation in some error conditions.
The respiratory humidifying device may also alert the user or patient through any of the above means during episodes of sleep apnoea, respiratory distress, difficulty breathing etc., or when their frequency or number exceeds a threshold.
A critical error condition in respiratory assistive devices is leakage of air from the patient interface, around the seal between the patient and the interface. This is particularly true of the respiratory humidifying device of the present invention, because the device generally needs to capture as much of the expired moisture as possible to provide the maximum humidity. Therefore, it is desirable to have a method of detecting patient interface leak error conditions.
It is a further aspect of the present invention to provide a method of detecting patient interface leak error conditions in a respiratory humidifying device according to other aspects of the invention, the method comprising monitoring at least one sensor value associated with the air flow through the respiratory humidifying device and comparing it to a set of expected sensor values, and detecting an error condition when the at least one sensor value is not within the set of expected sensor values. The method is preferably performed at least every 10 respiratory cycles, and preferably every cycle.
The at least one sensor value may be a rate of change or a sensor value.
A patient interface leak error condition may be detected by any of the methods disclosed in the prior art, for example measuring the average or peak flow rates through the respiratory humidifying device. However, the leak detection according to the above description may be advantageous as it is carried out closer to the patient and may be more sensitive, or more easily able to distinguish between leaks at the patient interface or leaks at another point in the air supply upstream from the moisture exchanger.
While the present invention has been illustrated by the description of the embodiments thereof, and while the embodiments have been described in detail, it is not the intention of the Applicant to restrict or in any way limit the scope of the appended claims to such detail. Additional advantages and modifications will readily appear to those skilled in the art. Therefore, the invention in its broader aspects is not limited to the specific details, representative apparatus and method, and illustrative examples shown and described. Accordingly, departures may be made from such details without departure from the spirit or scope of the Applicant's general inventive concept.
| Number | Date | Country | Kind |
|---|---|---|---|
| 2021900849 | Mar 2021 | AU | national |
| 2021900851 | Mar 2021 | AU | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/NZ2022/050033 | 3/23/2022 | WO |
