Respiratory therapy delivery devices for use with high flow therapy and / or other respiratory support, and associated systems, devices, and methods

Abstract

The present technology is generally directed to systems, devices, and methods for providing respiratory therapy to a patient. In representative embodiments, a respiratory therapy delivery device can include a tube configured to receive a flow of gas and an interface portion coupled to the tube. The interface portion can include a housing fluidly coupled to the tube, a first nasal prong coupled to the housing, and a second nasal prong coupled to the housing. The first nasal prong can be configured to be at least partially inserted in a first nare of the patient without forming a substantial seal thereat. The second nasal prong can be configured to be at least partially inserted in a second nare of the patient to form a substantial seal thereat.

Description

RESPIRATORY THERAPY DELIVERY DEVICES FOR USE WITH HIGH FLOW THERAPYAND / OR OTHER RESPIRATORY SUPPORTCROSS-REFERENCE TO RELATED APPLICATION(S)

[0001] The present application claims priority to U.S. Provisional Patent Application No. 63 / 648.513, filed May 16, 2024, the disclosure of which is incorporated by reference herein in its entirety.TECHNICAL FIELD

[0002] The present disclosure is generally directed to systems, devices, and methods for providing respiratory’ therapy.BACKGROUND

[0003] High flow oxygen therapy has been proposed as an alternative to standard oxygen therapy for treating hypoxemic patients. Standard oxygen therapy involves administering oxygen to the patient at relatively low flow rates using devices such as nasal cannulas, non- rebreathing masks, and bag-valve masks. In contrast, high flow oxygen therapy involves delivering oxygen to the patient at relatively higher flow rates, which enables achievement of a higher fraction of inspired oxygen (FiCh). To facilitate patient comfort, the oxygen is typically- heated and / or humidified before being delivered to the patient. While high flow therapy has advantages such as comfort, safety, and precise humidification and FiCh control, under certain circumstances, high flow therapy still has limitations such as imprecise control of positive end- expiratory- pressure (PEEP), inability to reach high PEEP levels, inability to directly increase tidal volume, and inability to directly recruit atelectatic alveoli. Therefore, there is a need for improved systems and methods for providing respiratory therapy.BRIEF DESCRIPTION OF THE DRAWINGS

[0004] Many aspects of the present technology can be better understood with reference to the following drawings. The components in the drawings are not necessarily to scale. Instead, emphasis is placed on clearly illustrating the principles of the present technology.

[0005] FIG. 1 is a schematic illustration of a system for providing high flow therapy with synchronized intermittent ventilation and configured in accordance with embodiments of the present technology.

[0006] FIG. 2 is a perspective view of a respiratory therapy delivery device configured in accordance with embodiments of the present technology.

[0007] FIGS. 3A and 3B are enlarged front and schematic cross-sectional views, respectively, of the respiratory therapy delivery device of FIG. 2.

[0008] FIG. 4 is a graph illustrating example measurements associated with slow deep breathing and rapid shallow breathing in accordance with embodiments of the present technology.

[0009] FIG. 5A is a graph illustrating a relationship between patient breathing and blower speed during high flow7therapy, and FIG. 5B is a graph illustrating triggering of synchronized intermittent ventilation during high flow therapy in accordance with embodiments of the present technology.

[0010] FIG. 6 is a graph illustrating example measurements associated with obstructed airway event detection in accordance with embodiments of the present technology.

[0011] FIG. 7 is another graph illustrating example measurements associated with obstructed airway event detection in accordance with embodiments of the present technology.

[0012] FIG. 8 is a flowchart illustrating a method of providing respiratory therapy to a patient in accordance with embodiments of the present technology7.

[0013] FIG. 9 is a perspective view of another respiratory' therapy delivery device configured in accordance with embodiments of the present technology.

[0014] FIG. 10 is a schematic cross-sectional view' of the respiratory' therapy delivery device of FIG. 9.DETAILED DESCRIPTION

[0015] High flow therapy (HFT) includes delivering heated and humidified oxygen gas to a patient at relatively high floyv rates, such as betyveen 15 liters per minute (“1pm”) and 70 1pm. Generally, the gas is heated to about body temperature (e.g., to about 37°C or 98.6 °F) and delivered with precise FiO2 (e.g., 21-100%) to a patient through a nasal cannula. HFT creates a flow-dependent, variable level of positive end-expiratory pressure (PEEP), washes CO2 out ofanatomical dead space, and uses dead space as an oxygen reservoir to increase inspired FiCh. Physiological effects of HFT include improved mucociliary clearance, improvement in blood gas values, and reduced work of breathing. HFT has grown in popularity in part due to patient tolerance and acceptance, safety, and overall ease of use. However, HFT has primarily been used in lieu of standard supplemental oxygen therapy, and not as an adjunct or replacement therapy for ventilation. This is due to certain limitations of HFT that may render it less ideal in certain situations where specific ventilatory support is needed. For example, limitations of HFT include imprecise control of PEEP, low PEEP levels that can be achieved, inability to control for volume or pressure, inability to directly increase tidal volume, inability to directly recruit atelectatic alveoli, etc.

[0016] Some embodiments of the present technology7are directed to systems, devices, and methods that are expected to address some or all of the foregoing shortcomings of standard HFT. For example, many embodiments described herein provide high flow therapy with synchronized intermittent ventilation, which is also referred to herein as hybrid high flow therapy. In some embodiments, the present technology7includes a respiratory therapy delivery' device or patient interface designed for the hybrid high flow therapy. In some embodiments, the delivery device can be generally similar to a nasal cannula, and include a tube configured to receive a flow of gas (e.g., from a high flow therapy device, a ventilator, etc.) and an interface portion coupled to the tube. The interface portion can include a housing for receiving gas from the tube, a first nasal prong configured to be at least partially inserted in a first nare of the patient, and a second nasal prong configured to be at least partially inserted in a second nare of the patient. In some embodiments, the first nasal prong can be shaped and sized to provide between about 25% and about 75% (e.g., about 50%) occlusion of the first nare, and the second nasal prong can be shaped and sized to seal at the second nare (e.g., provide 100% or at least about 100% occlusion of the second nare). In some embodiments, a method of providing respiratory therapy to a patient includes (i) delivering, using a blower, respiratory gas to the patient at a flow rate between 15 Ipm and 60 1pm, (ii) detecting a respiratory event based on a blower speed of the blower, and (iii) providing a modification to the flow rate of the respiratory' gas delivered to the patient following the detected respiratory7event to provide for flow, pressure, or volume controlled intermittent ventilation.

[0017] In some embodiments, the present technology includes respiratory therapy delivery devices or patient interfaces designed to provide ventilatory support, e.g., via flow, pressure, or volume-controlled ventilation with PEEP control. In such embodiments, the delivery device mayinclude a patient interface comprising a housing and two nasal prongs. However, when providing ventilatory support, e.g.. as opposed to hybrid high flow therapy, the device can be configured such that both nasal prongs seal at the corresponding nares (e.g., both provide 100% or at least about 100% occlusion of the respective nares). One of the nasal prongs can provide an inflow path for gas to flow into the patient’s nasopharynx, and the other of the nasal prongs can provide an outflow path to a fixed leak or exhaust vent / port.

[0018] Accordingly, as will be described in greater detail throughout this Detailed Description, various embodiments of the present technology are expected to precisely deliver continuous or intermittent extrinsic PEEP, pressure support, and / or volume targeted ventilation, and also improve elimination of CO2, resulting in normalization of gas exchange and improved patient response to ventilatory support. Various embodiments of the present technology' are also expected to avoid marked impairment of oxygenation while facilitating mask-free time. Without being bound by theory, this may improve quality of life (QoL) measures, reduce exacerbations of conditions such as chronic obstructive pulmonary disease (COPD) (e g., AE-COPD), reduce hospitalizations, etc. Further aspects and advantages of the devices, methods, and uses will become apparent from the ensuing description that is given by way of example only.

[0019] The terminology' used in the description presented below is intended to be interpreted in its broadest reasonable manner, even though it is being used in conjunction with a detailed description of certain specific embodiments of the present technology. Certain terms may even be emphasized below; however, any terminology intended to be interpreted in any restricted manner will be overtly and specifically defined as such in this Detailed Description section. Additionally, the present technology' can include other embodiments that are within the scope of the claims or examples but are not described in detail with respect to FIGS. 1-10.

[0020] Reference throughout this specification to “one embodiment” or “an embodiment” means that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment of the present technology. Thus, the appearances of the phrases “in one embodiment” or “in an embodiment” in various places throughout this specification are not necessarily all referring to the same embodiment. Furthermore, the particular features or characteristics may be combined in any suitable manner in one or more embodiments.

[0021] Reference throughout this specification to relative terms such as, for example, “generally,” “approximately,” and “about” are used herein to mean the stated value plus orminus 10%. The term “substantially” or grammatical variations thereof refers to at least about 50%. for example, 75%, 85%, 95%, or 98%.

[0022] The term “high flow” and variations thereof as used herein refer to gas delivery at a rate greater than 15 1pm. The term “low flow” and variations thereof as used herein refer to gas delivery at a rate of less than 15 1pm.

[0023] The headings included below are provided for convenience only and should not be used to interpret the scope of the present technology.A. Respiratory Therapy Delivery Devices for Hybrid High Flow Therapy, and Associated Systems and Methods

[0024] FIG. 1 is a schematic illustration of a system 100 for providing high flow therapy with synchronized intermittent ventilation to a patient 102, and configured in accordance with embodiments of the present technology. The system 100 includes a respiratory device 110 such as a high flow therapy device, a multi-functional ventilator, or the like, for providing gas flow to a patient. The system 100 further includes a humidifier 120 operably coupled to the respiratory device 110, and a respiratory therapy delivery device 130 (which can also be referred to herein as “the delivery device 130” and / or “the patient connection 130”) operably coupled to the humidifier 120.

[0025] The respiratory device 110 can include a controller 112, one or more gas sources 114 for providing a gas 115, a blower 111 for directing flow of the gas 115 from the gas source 114 to an outlet port 118, and one or more sensors 116. The one or more gas sources 114 can include an oxygen source, an air source, and / or other gas source for providing gas 115 suitable for respiration. For example, the gas sources 114 can provide oxygen (e.g., concentrated oxygen that is greater than 21% O2. such as between 80% and about 100% O2). air (e.g.. ambient air, pressurized air), etc. In embodiments in which the one or more gas sources 114 include multiple gas sources, the multiple gas sources can be included in the same device 110 or in different respiratory devices. For example, the one or more gas sources 114 can include an external oxygen tank. The one or more sensors 116 can include flow rate sensors, pressure sensors, and / or other sensors positioned to measure one or more parameters of the gas 115 provided by the gas sources 114. The sensors 116 can also include sensors that monitor various operational aspects of the blower 111, such as the blower speed (e.g., in revolutions per minute (RPM)).

[0026] The controller 112 can be operably coupled to the blower 111 , the gas sources 114, and the sensors 116. More specifically, the controller 112 can be configured to receivemeasurements from the sensors 116 as inputs (e.g.. flow rate, pressure), and to control the blower 111 and / or the gas sources 114 based on at least one of one of the received measurements. For example, the controller 112 can operate the blower 111 and / or gas sources 114 to maintain or change a flow rate, pressure, and / or composition of the gas 115. In some embodiments, the controller 112 can operate the blower 111 to provide a flow rate within a range of from about 15 1pm to about 80 1pm. such as about 15 1pm, about 30 1pm, about 45 1pm, about 60 1pm, about 70 1pm, about 80 1pm. or other values. The outlet port 118 can be positioned to receive and output the gas 115 from the blower 1 11 to the humidifier 120. In some embodiments, the blower 1 11, the controller 112, the gas sources 114, and / or the sensors 116 are enclosed in a housing of the respiratory device 110, and the outlet port 118 provides a path for the gas 115 to exit the housing. In some embodiments, the respiratory’ device 110 includes multiple outlet ports 118 for outputting the same or different flow of gases 115. In some embodiments, the gas sources 114 are positioned external to the housing of the respiratory’ device 110.

[0027] The humidifier 120 can heat and / or humidify the gas 115 received from the respiratory’ device 110. In other words, the humidifier 120 can condition the gas 115 before reaching the patient 102 via the respiratory' therapy delivery' device 130. The humidifier can therefore be coupled in series between the respiratory device 110 and the delivery device 130, e.g., as part of a patient circuit. In other embodiments, the humidifier 120 can be included within the respiratory device 110 (e.g., immediately upstream of the outlet port 118) and / or within the delivery' device 130.

[0028] The delivery' device 130 can be fluidly coupled to the respiratory device 110 (e.g., via a patient circuit or other conduit) and positioned (e.g., removably attached to the patient 102) to deliver the gas 115 from the respiratory device 110 to the patient 102. As described in greater detail below with reference to FIGS. 2-3B, the delivery device 130 can have one or more features that physically interface with the patient 102 to direct the gas 115 to flow into the patient’s airway.

[0029] In operation, the respiratory' device 110 can be configured to provide high flow therapy integrated with synchronized intermittent pressure control and / or volume targeted breaths. For example, as discussed in further detail below, the sensors 116 can be used to detect each breath phase (e.g., inspiration and exhalation) and trigger, in a timely manner, the synchronized intermittent pressure control and / or volume targeted breaths. In some embodiments, the controller 112 is programmed with an algorithm that can automate and adaptvarious elements of the hybrid mode of ventilatory support, including any of the modes of operation described throughout this Detailed Description. Without intending to be bound by theory, embodiments of the present technology are expected to improve gas exchange, maintain oxygen saturation, humidify the respiratory tract, and improve adherence while maintaining a high degree of comfort and safety for patients.

[0030] FIG. 2 is a perspective view of a respiratory therapy delivery device 230 (which can also be referred to as “the delivery device 230” or “the patient connection 230”) configured in accordance with embodiments of the present technology. The delivery device 230 can be an example of the delivery device 130 illustrated in FIG. 1, and can be used in conjunction with the respiratory device 110 and the humidifier 120, and / or other system components. As described in detail below, the delivery7device 230 can be configured to facilitate the delivery7of high flow therapy with synchronized intermittent ventilation.

[0031] In the illustrated embodiment, the delivery7device 230 comprises a nasal cannula having a patient interface portion 240 (“the interface portion 240”). ahead strap 232 coupled to the interface portion 240, and a tube 236 extending from the patient interface portion 240 and terminating at a connector 234. In operation, the head strap 232 can be elastically and / or adjustably positioned around the head of a patient to secure the interface portion 240 at the patient's nose. The tube 236 can be coupled (e.g., fluidly coupled) to another system component (e.g.. the respiratory device 110 and / or the humidifier 120 of FIG. 1) via the connector 234. The tube 236 can therefore direct gas received from a respiratory device to the patient via the interface portion 240. The interface portion 240 can facilitate the delivery of precise FiCh via warmed and / or humidified gases.

[0032] FIGS. 3A and 3B are enlarged front and schematic cross-sectional views, respectively, of the interface portion 240. Referring first to FIG. 3A, the interface portion 240 includes a housing 342, a first nasal prong 344 coupled to and extending from the housing 342, and a second nasal prong 346 coupled to and extending from the housing 342. The first nasal prong 344 and the second nasal prong 346 can be sized and spaced apart to be at least partially inserted in the nostrils or nares of a patient. Notably, the first nasal prong 344 and the second nasal prong 346 are shaped and sized differently such that the second nasal prong 346 provides a greater degree of nare occlusion or seal than the first nasal prong 344. For example, as shown in FIG. 3A, the first nasal prong 344 has a relatively narrow and linear form factor while the second nasal prong 346 has a relatively wide and pillow-style cushion form factor (e.g.,resembling a portion of a spinning top). In some embodiments, the first nasal prong 344 is shaped and sized to occlude less than about 40%. less than about 50%, or less than about 60%, or less than about 70% of the corresponding nare opening area. In some embodiments, the second nasal prong 346 is shaped and sized to occlude at least 80%, at least 90%, at least 95%, at least 99%, and / or 100% of the corresponding nare opening area. Accordingly, in some embodiments the second nasal prong 346 is sized and shaped to form a substantial or complete seal at the patient's nare. As one skilled in the art will appreciate, the exact degree of nare occlusion can depend on the patient’s nare size, shape, and other features, and how deep each of the first nasal prong 344 and the second nasal prong 346 is inserted when the delivery' device 230 is secured to the patient.

[0033] Referring next to FIG. 3B, the housing 342 defines an interior channel or reservoir 348 for receiving a flow of gas 315 from the tube 236 (FIG. 2). Each of the first nasal prong 344 and the second nasal prong 346 can be in fluid communication with the reservoir 348 such that the gas 315 can be delivered to the patient via both the first nasal prong 344 and the second nasal prong 346, similar to standard nasal cannulas. Accordingly, during patient inhalation, gas 315 flows into the patient’s airways (e.g., nasophary nx) from both the first nasal prong 344 and the second nasal prong 346. However, during patient exhalation, exhalation gases generally cannot escape around the second nasal prong 346 because the second nasal prong 346 provides a relatively high degree of nare occlusion (e.g., 90% or greater). As a result, assuming the patient is not respirating through their mouth, a majority of the exhaled gas must exit through the nare with the first nasal prong 344. For example, the exhaled gas can exit through the gap between the first nasal prong 344 and the corresponding nare (e.g.. the portion of the corresponding nare not occupied by the first nasal prong 344), similar to how a patient can exhale when receiving gas from a standard nasal cannula. This occurs even as the first nasal prong 344 and the second nasal prong 346 continue to deliver high flow therapy during patient exhalation.

[0034] Without intending to be bound by theory, sealing a nasal cannula at a first nasal prong while leaving the second nasal prong unsealed is expected to provide several advantages. For example, sealing the second nasal prong 346 but not the first nasal prong 344 can facilitate flushing of CO2 from the patient’s anatomical dead space by instigating turbulent air flow that generally' travels in a single direction through the patient’s nasopharynx during patient exhalation. Second, by sealing the second nasal prong 346, the second nasal prong 346 can facilitate accurate control of pressure support (e.g., pressure-controlled ventilation, control of PEEP, etc.) and volume targeted ventilation (TgV). as described in greater detail below. Other potential advantages include, but are not limited to, increasing lung volume to improve gasexchange, increasing variable PEEP levels, mitigating expiratory flow limitation, and / or decreasing dynamic hyperinflation.

[0035] During high flow therapy, different parameters such as blower speed or circuit pressure can be used to identify different phases of a patient's breath, including, e.g., the start of inspiration and the start of exhalation. FIG. 4 is a graph 400 illustrating example measurements associated with a patient performing slow deep breathing and rapid shallow breathing, respectively, while receiving standard hybrid high flow therapy. More specifically, the graph 400 plots the blower speed 410 (e.g., in RPM) of a blower (e.g., the blower 111), the flow rate 420 of the gas (e.g., the gas 115) within the patient circuit, and the pressure 430 of the gas (e.g., the gas 115) within the patient circuit over time (e.g., in seconds). The flow rate 420 and the pressure 430 are included to show the general shape of the flow and pressure waveforms, respectively, rather than specific values. The blower speed 410, the flow rate 420. and the pressure 430 can be measured using various sensors within or coupled to the respiratory device used to provide the therapy (e.g., the sensors 116 or other sensors positioned within the delivery device 130 or 230). As described further herein, the various measurements illustrated in the graph 400 can be processed or otherwise analyzed to determine various aspects of the patient's breathing, including breath phase detections.

[0036] To deliver high flow therapy, the blower can be set to maintain a predetermined flow rate (e.g., 60 1pm). Accordingly, the blower speed 410 is continuously adjusted to maintain the set flow rate. More specifically, to maintain constant flow, the blower speed 410 generally decreases during patient inhalation (due to decreased resistance in the patient’s airways) and increases during patient exhalation (due to increased resistance in the patient's airways). As a result, the blower speed 410 exhibits a general sinusoidal pattern comprising peaks 412 (e.g., local maximums) corresponding to maximum exhalations (e.g., minimum lung volume) and troughs 414 (e.g., local minimums) corresponding to maximum inhalation (e.g., maximum lung volume). Accordingly, as described in further detail below' with reference to FIG. 5A, the period from a peak 412 to a subsequent trough 414 corresponds to inhalation, the period from a trough 414 to a subsequent peak 412 corresponds to exhalation, and the period from one peak 412 to a subsequent peak 412 (or from one trough 414 to a subsequent trough 414) corresponds to one breath cycle. Also, changes in the blower speed 410 can be proportional to the degree of inspiration and exhalation. Therefore, the plot of the blower speed 410 can be used to determine the inhalation phase, inspiratory time (Ti), exhalation phase, expiratory time (TE), frequency / respiratory rate (RR), and inspiratory to expiratory ratio (EE).

[0037] The flow rate 420 exhibits a linear pattern such that the patient receives a constant (e.g., high) flow rate of gas. as is standard for high for therapy. While the plot of the pressure 430 also exhibit a wave-like pattern, the pressure waveform can become attenuated as flow rate increases (e.g., during high flow therapy) and also exhibits less sensitivity to changes in patient breathing depths, described below. By contrast, the blower speed 410 can exhibit a clearer wave pattern (more conducive to analysis), and since the blower speed 410 responds to changes to maintain a constant flow rate 420 (e.g., if set to maintain target flow), the plot of the blower speed 410 can provide a better method for analyzing breath phases of the patient. In some embodiments, the blower speed 410, the flow rate 420, and the pressure 430 are used to create a composite signal for creating or taking redundant measures to confirm the breath phases and reduce artifacts in the signal. For example, the blower speed 410 (in isolation or in combination with a plurality of redundant signals) can facilitate precise delivery of the pressure support and / or TgV for enhanced comfort and decreased work of breathing (WOB) and patient ventilatory asynchrony.

[0038] Furthermore, the plots of the blower speed 410, the flow rate 420, and / or the pressure 430 can be used to identify and distinguish between slow deep breathing and rapid shallow breathing. Detection of rapid shallow breathing can indicate increased WOB. As shown, the graph 400 illustrates a first period 402 associated with slow deep breathing, followed by a second period 404 associated with rapid shallow breathing. During the first period 402, the wave pattern of the blower speed 410 can have an amplitude Al and a period Pl. During the second period 404. the wave pattern of the blower speed 410 can have an amplitude A2 and a period P2. As shown, the amplitude A2 and the period P2 are smaller than the amplitude A2 and the period Pl, respectively, indicating the differences between slow deep breathing and rapid shallow breathing. The decrease in amplitude A2 and period P2 can be proportional to the degree of shallow breathing — the greater the decrease, the greater the change in breath pattern. Thus, blower speed can be monitored to identify changes in a patient’s breathing pattern.

[0039] As set forth above, in some embodiments the systems and methods described herein track blower speed to identify patient breath phases. As described in detail below, this enables intermittent and synchronized ventilation to be delivered in combination w ith high flow therapy. For example, FIG. 5 A is a graph 500 illustrating a relationship between patient breathing and blower speed during high flow therapy. As shown, the patient flow 510 increases during patient inspiration and decreases during patient exhalation. During high flow therapy in which the flow rate 530 is set to a constant rate (e.g., 60 1pm), the blower speed 520 continuouslychanges to adapt to changing patient breath conditions to maintain the set flow rate 530. Specifically, as described above with reference to FIG. 4, blower speed decreases from a peak value 522 to a trough value 524 during patient inhalation (e.g., due to decreased resistance within the patient’s airways) and increases from the trough value 524 to a peak value 522 during patient exhalation (e.g., due to increased resistance within the patient’s airways). Thus, blower speed 520 can be monitored to determine a patient's breath phase. As described below, determining patient breath phase using the blower speed 520 enables the delivery of synchronized, intermittent ventilation during high flow therapy.

[0040] FIG. 5B is a graph 505 illustrating triggering of synchronized intermittent ventilation (e.g., “hybrid high flow therapy”) based on blower speed and in accordance with embodiments of the present technology. Relative to the graph 500 of FIG. 5A, the graph 505 of FIG. 5B illustrates bursts or pulses 532 of increased flow that originate from and terminate at the set high flow rate 530. The particular shape, intensity, duration, and other aspects of the pulses 532 can vary depending on the patient and the ventilation being delivered. In some embodiments, the pulses 532 can be controlled according to a variable flow pattern, transitioning from a first target flow (e.g., 60 1pm) during patient exhalation to a second target flow (e.g., 70 1pm) during patient inhalation. In other embodiments, the pulses 532 can be pressure-controlled or volume-controlled.

[0041] In the illustrated embodiment, each pulse 532 is synchronized with a particular phase of patient breath, such as during patient inhalation, although in other embodiments the pulses 532 can be synchronized with patient exhalation, and / or offset so that they occur partially during inhalation and partially during exhalation. In some embodiments, for example, patient inhalation can be detected by (i) determining the patient’s maximum exhalation by identifying a peak 522 in the blower speed 520 (as also discussed above with reference to FIGS. 4 and 5A), corresponding to the patient’s minimum lung volume, and (ii) initiating the pulse 532 within a triggering window that begins at the identified peak 522. The triggering window can be between the identified peak 522 and a subsequent trough 524, or shorter. In some embodiment, the triggering window is about 1-500 milliseconds, such as 10 milliseconds, 100 milliseconds, 300 milliseconds, etc. from a detected peak 522. Thus, the pulse 532 can be automatically triggered such that delivery of the pulse 532 generally coincides with patient inhalation (and / or with the patient's peak inspiratory flow demand), as shown in FIG. 5B. Synchronizing the ventilation 532 with the patient’s peak inspiratory flow demand can improve patient comfort and decrease the perception of dyspnea. Moreover, regardless of which breath phase the pulses 532 aresynchronized with, the pulses 532 can be provided at every breath cycle or intermittently. Examples of intermittent delivery include delivering the pulses 532 every’ two, three, four, five, six, etc. breath cycles, according to a dynamically changing frequency, or upon demand or necessity as deemed by the sensors 116 or the patient.

[0042] Without intending to be bound by theory, intermittently superimposing increased variable higher flow, pressure support and / or volume targeted breaths on the baseline, constant flow rate of the respiratory therapy, the synchronized intermittent ventilation 532 can serve as a mechanism to increase tidal volume, decrease blood carbon dioxide (e.g., PaCCh), improve gas exchange, decrease work in breathing, meet or exceed the patient’s peak inspiratory flow demand, etc. The delivery' of the synchronized intermittent ventilation 532 can be controlled (e.g., via the controller 112 illustrated in FIG. 1) to help the patient reach a stable breathing period, which may be indicated by the frequency and / or breath depth (which in turn represent the WOB) of the patient. In some embodiments, the controller is configured to adjust the frequency and / or shape of the pulse of the synchronized intermittent ventilation based on signals indicating the patient’s WOB. For example, the controller can adjust the pressure support level and / or increase the TgV to optimize ventilatory support and decrease WOB.

[0043] In some embodiments, the controller can continue to change (e.g., increase or decrease) the frequency and / or level of the synchronized intermittent ventilation in a feedback loop until a minimally optimal frequency and / or level of the synchronized intermittent ventilation has been reached, then maintain that frequency and / or level. The feedback loop can include sensor measurements (e.g., from the sensors 116) and / or patient or physician feedback as inputs. In some embodiments, the controller can increase or decrease the flow rate (e.g., byincreasing breath depth and decreasing frequency) to determine an optimal flow rate, which can be the flow rate prior to detecting an increase in WOB.

[0044] In some embodiments, the pulses 532 could be synchronized with other portions of a patient’s breath, e.g., instead of with patient inhalation. For example, the pulses 532 can by synchronized with patient exhalation to control for PEEP (e.g., maintain a constant value for PEEP).

[0045] In some embodiments, the synchronized intermittent ventilation is facilitated at least in part by the delivery- device 230, described above with reference to FIG. 2. In particular, the delivery device 230 may be able to better facilitate pressure-controlled ventilation, volume- controlled ventilation, PEEP or the like, as compared to traditional nasal cannulas used forconventional high flow therapy. This is because the second nasal prong 346 (FIGS. 3A and 3B) forms a substantial or complete seal at one of the patient’s nostrils.

[0046] In addition to or in lieu of controlling synchronized intermittent ventilation based on breath phase, the systems and methods described herein can include detecting obstructed airway events. For example, FIG. 6 is a graph 600 illustrating example measurements associated with obstructed airway event detection in accordance with embodiments of the present technology. A patient can be wearing a respiratory therapy delivery device (e.g., the deliverydevice 130, 230) connected to a respiratory device (e.g., the respiratory device 110). The graph 600 plots the blower speed 610 (e.g., in RPM), the flow rate 620 of the gas delivered to the patient, and the pressure 630 of the gas delivered to the patient over time (e.g., in seconds). The blower speed 610, the flow rate 620, and the pressure 630 can be measured using various sensors (e.g., the sensors 116). As described further herein, the graph 600 illustrates how embodiments of the present technology detect and resolve obstructed airway events (e.g., obstructive sleep apnea).

[0047] The graph 600 initially plots a first period 602 corresponding to unobstructed or normal breathing by the patient. During the first period 602, the blower speed 610 and the pressure 630 can exhibit relatively clear wave patterns and the flow rate 620 can exhibit a generally linear pattern, as shown. The change in each of the blower speed 610 and the pressure 630 to relatively flat lines, at the time indicated by the vertical dotted line 612. indicates the onset of a second period 604. The second period 604, which lasts for about 20 seconds in the illustrated example, is marked by relatively flat lines at the beginning of the second period 604 in each of the blower speed 610 and the pressure 630, indicating cessation of breathing and / or obstructive apnea (e.g., obstructive sleep apnea). Therefore, the controller (e.g., the controller 112) can detect an obstructed airway event by detecting a period of flat lines in the blower speed 610 and / or the pressure 630. A wave portion 618 with a relatively large amplitude in the blower speed 610 can confirm that the apnea was related to the upper airway obstruction.

[0048] In response to detecting the obstructed airway event, the controller can initiate a recovery in patient breathing by increasing the flow rate 620, e.g., from the baseline high flow rate. In the graph 600, the flow rate 620 is increased at a constant rate, as indicated by the ramp 622. In some embodiments, the flow rate 620 is increased to increase the variable PEEP. In some embodiments, the flow rate 620 is increased to reach a target PEEP level (e.g., a predetermined, fixed value). In some embodiments, the flow rate 620 is increased to increase the pressure 630and provide pneumatic splinting of the oropharynx (e.g., particularly during exhalation, peak exhalation, and / or end exhalation). The flow rate 620 can be increased until unobstructed recovery breathing resumes, as indicated by bumps 616 in the blower speed 610 beginning at the time indicated by the vertical dotted line 614. In other embodiments, the flow rate 620 is increased at varying rates or decreased. Once unobstructed breathing resumes, the flow rate 620 can be maintained at the new flow rate indicated by the flat line 624, e.g., for a period of time until normal breathing is stable. The second period 604 is followed by a third period 606 corresponding to resumed normal breathing. Thus, embodiments of the present technology can resolve obstructed airway events such as obstructive sleep apnea.

[0049] FIG. 7 is a graph 700 illustrating example measurements associated with another obstructed airway event detection in accordance with embodiments of the present technology'. Like the graph 600, the graph 700 plots the blower speed 710 (e.g., in RPM), the flow rate 720 of the gas delivered to the patient, and the pressure 730 of the gas delivered to the patient over time (e g., in seconds). Like the graph 600, the graph 700 illustrates how embodiments of the present technology' detect and resolve obstructed airway event detect on (e.g., obstructive sleep apnea). For example, the graph 700 plots a first period 702 corresponding to unobstructed or normal breathing by the patient, a second period 704 following the first period 702 and indicating cessation of breathing and / or obstructive apnea, and a third period 706 following the second period 704 and corresponding to resumed normal breathing. A wave portion 718 with a relatively large amplitude in the blower speed 710 can confirm that the apnea was related to the upper airway obstruction.

[0050] Unlike the graph 600, however, the graph 700 illustrates, during the second period 704, each of the blower speed 710 and the pressure 730 as having wave patterns with smaller amplitudes and shorter periods compared to the wave patterns during the first period 702 or the third period 706, as opposed to flat lines as shown in the graph 600. As set forth above with reference to FIG. 4, these wave patterns can also indicate increased WOB, e.g., due to rapid, shallow breathing caused by an obstructed airway event such as sleep apnea. Accordingly, in some embodiments, the controller can also detect an obstructed airway event by detecting a change in the delta between peak inspiration and peak expiration. In some embodiments, the controller can detect an obstructed airw ay event by detecting reduced amplitude(s) in inspiratory' efforts, followed by the wave portion 718 characteristic of recovery breath(s) signaling the microarousal and termination of the obstructed / partially obstructed breathing event associated with a transitory return of muscle tone. The threshold amplitude and / or period / frequency forqualifying as an obstructed airway event can be predetermined based on. for example, the patient's normal breathing pattern. A similar increase in the flow rate 720 as described above with reference to FIG. 6 can be used to recover normal breathing.

[0051] Referring to FIGS. 6 and 7 together, obstructed airway event detection in accordance with embodiments of the present technology is expected to assist in addressing a variety of disorders associated with acute and chronic respiratory7failure (e.g., during sleep). Medical conditions associated with obstructed airway events include overlap syndrome (e.g., the overlap of chronic obstructive pulmonary disease (COPD) and obstructive sleep apnea (OSA)), obesity hypoventilation syndrome, neuromuscular conditions (e.g., amyotrophic lateral sclerosis (ALS)), etc. Also, combining high flow- therapy with synchronized intermittent ventilation (as discussed w ith reference to FIG. 5B) and / or obstructed airway event detection (as discussed with reference to FIGS. 6 and 7) is expected to improve patient outcomes compared to providing only high flow therapy to both adult and pediatric patients.

[0052] FIG. 8 is a flowchart illustrating a method 800 of providing respiratory therapy to a patient in accordance with embodiments of the present technology7. It is appreciated that while the method 800 is described below with reference to the embodiments illustrated in FIGS. 1-7, the method 800 can be performed with other embodiments. Moreover, while the steps of the method 800 are presented in a particular order, one or more steps can be performed in a different order or omitted entirely, and / or the method 800 can include additional steps.

[0053] The method 800 begins at block 802 by delivering, using a respiratory device (e.g., the respiratory device 110) having a blower (e.g., the blower 1 11 ), a respiratory gas to the patient (e.g., the patient 102) at a flow- rate of between 15 1pm and 80 1pm, such as between 15 1pm and 60 1pm. The flow7rate can be controlled to be constant (e.g., fixed at a particular value such as about 30 1pm) or varied (e.g., in a wave pattern).

[0054] At block 804, the method 800 continues by detecting a respiratory7event based on a speed of the blower. In some embodiments, the detected respiratory event comprises a maximum exhalation of the patient corresponding to a local maximum (e.g., peak) of the blower speed (e.g., as discussed with reference to FIGS. 5A and 5B). In some embodiments, the detected respiratory event comprises an obstructed airway event corresponding to a decrease in at least one of an amplitude or period of the blower speed greater than a predetermined threshold (e.g., as discussed with reference to FIGS. 6 and 7).

[0055] At block 806. the method 800 continues by adjusting the flow rate of the respiratory' gas delivered to the patient following the detected respiratory event for a duration of the respiratory event. In some embodiments, the modification to the flow rate comprises a temporary increase in the flow rate synchronized with an inhalation of the patient (e.g., as discussed with reference to FIG. 5B). The temporary' increase in the flow rate can be provided at various frequencies (e.g., every other maximum exhalation of the patient). In some embodiments, the modification to the flow rate comprises an increase in the flow rate to restore normal breathing patterns (e.g., as discussed with reference to FIGS. 6 and 7).

[0056] The temporary increase can be maintained for a predetermined period of time (e.g., corresponding to an estimated duration of a patient’s breath), or until a second respiratory event is detected. In some embodiments, the second respiratory' event can include an end of patient inhalation and / or a beginning of patient exhalation. In other embodiments, the second respiratory event can include a return to normal (e.g.. unobstructed) breathing. Regardless, flow can be decreased following the predetermined period of time or upon detection of the second respiratory event. The operations of increasing and decreasing flow can be iteratively repeated for a predetermined number of breathing cycles, such as one, two, three, four, five, six, or more.

[0057] In some embodiments, some or all of the method 800 can be a computer- implemented method performed by a computing system of a respiratory device, such as (but not limited to) the controller 112 of the device 110 of FIG. 1. In such embodiments, the respiratory devices described herein can include a n on-transitory computer-readable medium storing instructions that, when executed by a corresponding processor, cause the operations of the method 800 to be performed.B. Respiratory Therapy Delivery Devices for Ventilation Therapy, and Associated Systems and Methods

[0058] The present technology further includes respiratory therapy delivery devices designed for providing conventional ventilatory support to a patient via the patient’s nares. For example, FIG. 9 is a perspective view of a respiratory therapy delivery' device 930 (“the delivery device 930”) for providing ventilatory' support to a patient and configured in accordance with embodiments of the present technology. In the illustrated embodiment, the delivery device 930 comprises a nasal cannula having a patient interface portion 940 (“the interface portion 940”), a head strap 932 coupled to the interface portion 940, and a tube 936 extending from the patient interface portion 940 and terminating at a connector 934. In operation, the head strap 932 can beelastically and / or adjustably positioned around the head of a patient to secure the interface portion 940 at the patient’s nose. The tube 936 can be coupled (e.g., fluidly coupled) to another system component (e.g., to a respiratory device such as a ventilator, either directly or via additional tubing) via the connector 934. The tube 936 can direct gas received from the respiratory device to the patient via the interface portion 940. The interface portion 940 can therefore facilitate the delivery of respiratory therapy, as described in greater detail below.

[0059] The interface portion 940 can include a housing 942, a first nasal prong 944 coupled to the housing 942, a second nasal prong 946 coupled to the housing 942, and an outlet port 950 (which can also be referred to as a vent, fixed orifice leak, or the like) coupled to the housing 942. The first nasal prong 944 and the second nasal prong 946 can be sized and spaced to be at least partially inserted in the nostrils or nares of the patient. Unlike the embodiments described above with reference to FIGS. 1-3B. the first nasal prong 944 and the second nasal prong 946 are shaped and sized similarly or generally identically to one another. Also, each of the first nasal prong 944 and the second nasal prong 946 is shaped to have a relatively wide and pillow-style cushion form factor (e.g., resembling a portion of a spinning top), similar to the second nasal prong 346 described above with reference to FIG. 3 A. In some embodiments, each of the first nasal prong 944 and the second nasal prong 946 is shaped and sized to occlude at least 80%, at least 90%, at least 95%, at least 99%, and / or 100% of the corresponding nare opening area. Accordingly, in some embodiments the first nasal prong 944 and the second nasal prong 946 are sized and shaped to form a substantial or complete seal at the patient’s nares. As one skilled in the art will appreciate, the exact degree of nare occlusion can depend on the patient’s nare size, shape, and other features, and how deep each of the first nasal prong 944 and the second nasal prong 946 is inserted when the respiratory therapy delivery device 930 is secured. However, the first and second nasal prongs 944, 946 can be designed to form a substantial and / or complete seal at the patient’s nares when properly fitted to the patient.

[0060] FIG. 10 is a schematic cross-sectional view of the interface portion 940. As shown, the housing 942 can include a partition or wall 1049 that divides the interior of the housing 942 into a first reservoir or chamber 1048a and a second reservoir or chamber 1048b. The first reservoir 1048a can be fluidly coupled to the tube 936 and the first nasal prong 944. In this way, gas 1015 flowing into the interface portion 940 via the tube 936 is directed into the patient via the first reservoir 1048a and the first nasal prong 944. The second reservoir 1048b can be fluidly coupled to the second nasal prong 946 and the outlet port 950. In this way. exhaled gas 1045 from the patient flows into the second reservoir 1048b via the second nasal prong 946, and outof the second reservoir 1048b into the environment via the outlet port 950. Due to the partition 1049, the second reservoir 1048b and the second nasal prong 946 are not directly fluidly coupled to the tube 936, and thus do not deliver the gas 1015 from the tube 936 to the patient.

[0061] In operation, because the first reservoir 1048a is separated from the second reservoir 1048b by the partition 1049, inhalation gas 1015 is provided to the patient only via the first nasal prong 944, and not via the second nasal prong 946. Moreover, because each of the first nasal prong 944 and the second nasal prong 946 provides a relatively high degree of nare occlusion, most or all of the exhaled gas 1045 is released to the environment via the second nasal prong 946 (and the second reservoir 1048b and the outlet port 950) as opposed to, e.g., through gaps between the nares and the first nasal prong 944 and the second nasal prong 946. By providing a substantial or complete seal at the first nasal prong 944 through which ventilation gases are delivered to the patient and a fixed leak at the second nasal prong 946, the delivery device 930 can be used to deliver non-invasive ventilation (e.g.. pressure-controlled non- invasive ventilation, volume-controlled non-invasive ventilation, etc.) Moreover, by providing gas flow into only one nostril, gases are expected to flow in a generally uni-directional pattern through the patient's nasophary nx, which may assist with purging CO2 from the patient's airways. Therefore, the interface portion 940 can provide continuous respiratory’ therapy (e.g., through the patient’s nasopharynx) by routing flow in through one nasal prong and flow out through a different nasal prong.C. Examples

[0062] Several aspects of the present technology are set forth in the following examples:1. A respiratory7therapy delivery' device configured to be worn by a patient to provide respiratory therapy, the device comprising: a tube configured to receive a flow of gas from a respiratory device; and an interface portion fluidly coupled to the tube, wherein the interface portion includes: a housing fluidly coupled to the tube; a first nasal prong fluidly coupled to the housing, wherein the first nasal prong is configured to be at least partially inserted in a first nare of the patient without forming a substantial seal thereat; anda second nasal prong coupled to the housing, wherein the second nasal prong is configured to be at least partially inserted in a second nare of the patient to form a substantial seal thereat.2. The device of example 1 wherein the second nasal prong has a spinning top form factor.3. The device of example 1 or example 2 wherein the second nasal prong is sized and shaped to occlude 100% of a nare opening area at the patient’s second nare.4. The device of any of examples 1-3 wherein the first nasal prong is sized and shaped to occlude less than about 60% of a nare opening area at the patient’s first nare.5. The device of any one of examples 1-4 wherein the housing of the interface portion includes a reservoir for receiving the stream of gas from the tube, and wherein each of the first nasal prong and the second nasal prong is in fluid communication with the reservoir.6. A patient interface for delivering respiratory gas to a patient, the patient interface, comprising: a housing, the housing including: a chamber, and an inflow port fluidly coupled to the chamber and configured to be connected to a tube for receiving inhalation gases therefrom; a first nasal prong fluidly coupled to the chamber, wherein the first nasal prong is configured to be at least partially inserted in a first nare of the patient without forming a substantial seal thereat; and a second nasal prong fluidly coupled to the chamber, wherein the second nasal prong is configured to be at least partially inserted in a second nare of the patient to form a substantial seal thereat.7. The patient interface of example 6 wherein the second nasal prong has a spinning top form factor.8. The patient interface of example 6 or example 7 wherein the second nasal prong is sized and shaped to occlude 100% of a nare opening area at the patient's second nare.9. The patient interface of any of examples 6-8 wherein the first nasal prong is sized and shaped to occlude less than about 60% of a nare opening area at the patient’s first nare.10. A method of providing respiratory therapy to a patient, the method comprising: delivering, using a respiratory device having a blower, a respiratory' gas to the patient at a flow rate between 15 1pm and 80 1pm; detecting a respiratory event based at least in part on a speed of the blower, wherein the respiratory even includes an obstructive breathing event and / or an increase in a work of breathing parameter; and in response to detecting the respiratory' event, adjusting the flow rate of the respiratory' gas delivered to the patient.11. The method of example 10 wherein detecting the respiratory' event based at least in part on the speed of the blower comprises identifying a decrease in at least one of an amplitude or period of the blower speed greater than a predetermined threshold.12. The method of example 10 wherein detecting the respiratory even based at least in part on the speed of the blower comprises identify ing a constant blower speed.13. The method of any of examples 10-12 wherein adjusting the flow rate in response to detecting the respiratory' flow rate includes increasing the flow rate.14. The method of example 13 wherein increasing the flow rate includes increasing the flow rate in a linear manner.15. The method of example 13 or example 14 wherein increasing the flow rate includes increasing the flow rate until the respiratory event is in a recovery phase.16. The method of example 15 wherein the recovery phase is identified based at least in part on the speed of the blower.17. A method of providing respiratory therapy to a patient, the method comprising: delivering, using a respiratory device having a blower, a respiratory gas to the patient at a flow rate between 15 1pm and 80 1pm; detecting an end of an exhalation phase and / or beginning of an inhalation phase of a breath of the patient based at least in part on a speed of the blower; and temporarily increasing the flow rate of the respiratory gas delivered to the patient synchronized with the inhalation phase of the breath.18. The method of example 17 wherein detecting the end of the exhalation phase and / or the beginning of the inhalation phase includes detecting a maximum exhalation of the patient.19. The method of example 18 wherein the maximum exhalation is determined based on a local maximum of the speed of the blower.20. The method of any of examples 17-19 wherein temporarily increasing the flow rate includes increasing the flow rate to achieve a target volume or pressure during the inhalation phase of the breath.21. The method of any of examples 17-20, further comprising: detecting an end of patient inhalation and / or a beginning of patient exhalation based at least in part on the speed of the blower; and decreasing the flow rate in response to detecting the end of the patient inhalation and / or the beginning of the patient exhalation.22. The method of example 21 wherein the operations of temporarily increasing the flow rate and decreasing the flow rate include increasing and decreasing the flow rate to achieve a target variable flow rate.23. The method of example 21 or example 22, further comprising iteratively repeating the operations of (i) detecting the end of the exhalation phase and / or beginning of the inhalation phase, (ii) temporarily increasing the flow rate, (iii) detecting the end of patientinhalation and / or the beginning of patient exhalation, and (iv) decreasing the flow rate for a predetermined number of breath cycles.24. The method of any of examples 17-20, further comprising decreasing the flow rate after a predetermined duration.25. The method of example 24 wherein the operations of temporarily increasing the flow rate and decreasing the flow rate includes increasing and decreasing the flow rate to achieve a target variable flow rate.26. The method of example 24 or example 25, further comprising iteratively repeating the operations of (i) detecting the end of the exhalation phase and / or beginning of the inhalation phase, (ii) temporarily increasing the flow rate, and (iii) decreasing the flow rate for a predetermined number of breath cycles.27. A respiratory7therapy delivery' device configured to be worn by a patient to provide respiratory therapy, the device comprising: a tube configured to receive a flow of gas from a respiratory device; and an interface portion coupled to and / or coupleable to the tube, wherem the interface portion includes: a housing having a first chamber and a second chamber, wherein the first chamber is fluidly coupled to the tube and the second chamber is not fluidly coupled to the tube; a first nasal prong fluidly coupled to the first chamber, wherein the first nasal prong is configured to be at least partially inserted in a first nare of the patient to form a substantial seal thereat; and a second nasal prong fluidly coupled to the second chamber, wherein the second nasal prong is configured to be at least partially inserted in a second nare of the patient to form a substantial seal thereat.28. The device of example 27 wherein the first nasal prong is sized and shaped to occlude 100% of a nare opening area at the patient’s first nare, and wherein the second nasal prong is sized and shaped to occlude 100% of a nare opening area at the patient’s second nare.29. The device of any of example 27 or example 28 wherein the interface portion further includes a partition fluidly isolating the first chamber and the second chamber.30. The device of any of examples 27-29 wherein the interface portion further comprises an exhalation vent fluidly coupled to the second chamber.31. The device of example 30 wherein the device is configured such that, in operation: gas is delivered to the patient via the tube, the first chamber, and the first nasal prong; and exhaled gas from the patient is purged via the second nasal prong, the second chamber, and the exhalation vent.32. A patient interface for delivering respiratory gas to a patient, the patient interface comprising: a housing having a first chamber and a second chamber, wherein the first chamber and the second chamber are fluidly isolated within the housing; a first nasal prong fluidly coupled to the first chamber, wherein the first nasal prong is configured to be at least partially inserted in a first nare of the patient; a second nasal prong fluidly coupled to the second chamber, wherein the second nasal prong is configured to be at least partially inserted in a second nare of the patient; and an exhalation vent fluidly coupled to the second chamber.33. The patient interface of example 32 wherein the first nasal prong is sized and shaped to form a substantial or complete seal at the first nare, and wherein the second nasal prong is sized and shaped to form a substantial or complete seal at the second nare.34. The patient interface of example 32 or example 33 wherein the housing includes a partition between the first chamber and the second chamber.35. The patient interface of any of examples 32-34 wherein the housing includes an inflow port configured to connect to a tube for receiving inhalation gas, the opening being in fluid communication with the first chamber.36. The patient interface of any of examples 32-35 wherein the interface is configured such that, in operation: gas is delivered to the patient via the first chamber and the first nasal prong; and exhaled gas from the patient is purged via the second nasal prong, the second chamber, and the exhalation vent.Conclusion

[0063] As one of skill in the art will appreciate from the disclosure herein, various components of the systems described above can be omitted without deviating from the scope of the present technology. Likewise, additional components not explicitly described above may be added to the systems without deviating from the scope of the present technology. For example, it will be appreciated that specific embodiments of the technology have been described herein for purposes of illustration, but well-known structures and functions have not been shown or described in detail to avoid unnecessarily obscuring the description of the embodiments of the technology7. Moreover, although specific embodiments of, and examples for, the technology7are described above for illustrative purposes, various equivalent modifications are possible within the scope of the technology as those skilled in the relevant art will recognize. For example, although steps are presented in a given order, alternative embodiments may perform steps in a different order. The various embodiments described herein may also be combined to provide further embodiments. Accordingly, the present technology is not limited to the configurations expressly identified herein, but rather encompasses variations and alterations of the described systems and methods.

[0064] Further, while advantages associated with some embodiments of the technology have been described in the context of those embodiments, other embodiments may also exhibit such advantages, and not all embodiments need necessarily exhibit such advantages to fall within the scope of the technology. Accordingly, the disclosure and associated technology can encompass other embodiments not expressly shown or described herein.

[0065] Unless the context clearly requires otherwise, throughout the description and the examples, the words "‘comprise.” “comprising,” and the like are to be construed in an inclusivesense, as opposed to an exclusive or exhaustive sense; that is to say, in the sense of “including, but not limited to." As used herein, the terms “connected,’" “coupled,” or any variant thereof, means any connection or coupling, either direct or indirect, between two or more elements; the coupling of connection between the elements can be physical, logical, or a combination thereof. Additionally, the words “herein,” “above,” “below,” and words of similar import, when used in this application, shall refer to this application as a whole and not to any particular portions of this application. Where the context permits, words in the above Detailed Description using the singular or plural number may also include the plural or singular number respectively. As used herein, the phrase “and / or” as in “A and / or B” refers to A alone, B alone, and A and B. Further, where specific integers are mentioned herein which have known equivalents in the art to which the embodiments relate, such known equivalents are deemed to be incorporated herein as if individually set forth.

Claims

CLAIMSI / W e claim:

1. A respiratory therapy deliver}' device configured to be worn by a patient to provide respiratory therapy, the device comprising: a tube configured to receive a flow of gas from a respirator}’ device; and an interface portion fluidly coupled to the tube, wherein the interface portion includes: a housing fluidly coupled to the tube; a first nasal prong fluidly coupled to the housing, wherein the first nasal prong is configured to be at least partially inserted in a first nare of the patient without forming a substantial seal thereat; and a second nasal prong coupled to the housing, wherein the second nasal prong is configured to be at least partially inserted in a second nare of the patient to form a substantial seal thereat.

2. The device of claim 1 wherein the second nasal prong has a spinning top form factor.

3. The device of claim 1 wherein the second nasal prong is sized and shaped to occlude 100% of a nare opening area at the patient’s second nare.

4. The device of claim 1 wherein the first nasal prong is sized and shaped to occlude less than about 60% of a nare opening area at the patient’s first nare.

5. The device of claim 1 wherein the housing of the interface portion includes a reservoir for receiving the stream of gas from the tube, and wherein each of the first nasal prong and the second nasal prong is in fluid communication with the reservoir.

6. A patient interface for delivering respiratory gas to a patient, the patient interface, comprising: a housing, the housing including: a chamber, andan inflow port fluidly coupled to the chamber and configured to be connected to a tube for receiving inhalation gases therefrom; a first nasal prong fluidly coupled to the chamber, wherein the first nasal prong is configured to be at least partially inserted in a first nare of the patient without forming a substantial seal thereat; and a second nasal prong fluidly coupled to the chamber, wherein the second nasal prong is configured to be at least partially inserted in a second nare of the patient to form a substantial seal thereat.

7. The patient interface of claim 6 wherein the second nasal prong has a spinning top form factor.

8. The patient interface of claim 6 wherein the second nasal prong is sized and shaped to occlude 100% of a nare opening area at the patient's second nare.

9. The patient interface of claim 6 wherein the first nasal prong is sized and shaped to occlude less than about 60% of a nare opening area at the patient’s first nare.

10. A method of providing respiratory therapy to a patient, the method comprising: delivering, using a respiratory device having a blower, a respiratory gas to the patient at a flow rate between 15 1pm and 80 1pm; detecting a respiratory event based at least in part on a speed of the blower, wherein the respiratory even includes an obstructive breathing event and / or an increase in a work of breathing parameter; and in response to detecting the respiratory event, adjusting the flow rate of the respiratory gas delivered to the patient.

11. The method of claim 10 wherein detecting the respiratory event based at least in part on the speed of the blower comprises identifying a decrease in at least one of an amplitude or period of the blower speed greater than a predetermined threshold.

12. The method of claim 1 wherein detecting the respiratory' even based at least in part on the speed of the blower comprises identifying a constant blower speed.-Ti13. The method of claim 10 wherein adjusting the flow rate in response to detecting the respiratory flow rate includes increasing the flow rate.

14. The method of claim 13 wherein increasing the flow rate includes increasing the flow rate in a linear manner.

15. The method of claim 13 wherein increasing the flow rate includes increasing the flow rate until the respiratory event is in a recovery phase.

16. The method of claim 15 wherein the recovery phase is identified based at least in part on the speed of the blower.

17. A method of providing respiratory therapy to a patient, the method comprising: delivering, using a respiratory device having a blower, a respiratory gas to the patient at a flow rate between 15 1pm and 80 1pm; detecting an end of an exhalation phase and / or beginning of an inhalation phase of a breath of the patient based at least in part on a speed of the blower; and temporarily increasing the flow rate of the respiratory gas delivered to the patient synchronized with the inhalation phase of the breath.

18. The method of claim 17 wherein detecting the end of the exhalation phase and / or the beginning of the inhalation phase includes detecting a maximum exhalation of the patient.

19. The method of claim 18 wherein the maximum exhalation is determined based on a local maximum of the speed of the blower.

20. The method of claim 17 wherein temporarily increasing the flow rate includes increasing the flow rate to achieve a target volume or pressure during the inhalation phase of the breath.

21. The method of claim 17, further comprising: detecting an end of patient inhalation and / or a beginning of patient exhalation based at least in part on the speed of the blower; anddecreasing the flow rate in response to detecting the end of the patient inhalation and / or the beginning of the patient exhalation.

22. The method of claim 21 wherein the operations of temporarily increasing the flow rate and decreasing the flow rate include increasing and decreasing the flow rate to achieve a target variable flow rate.

23. The method of claim 21, further comprising iteratively repeating the operations of (i) detecting the end of the exhalation phase and / or beginning of the inhalation phase, (ii) temporarily increasing the flow rate, (iii) detecting the end of patient inhalation and / or the beginning of patient exhalation, and (iv) decreasing the flow rate for a predetermined number of breath cycles.

24. The method of claim 17, further comprising decreasing the flow rate after a predetermined duration.

25. The method of claim 24 wherein the operations of temporarily increasing the flow rate and decreasing the flow rate includes increasing and decreasing the flow rate to achieve a target variable flow rate.

26. The method of claim 24, further comprising iteratively repeating the operations of (i) detecting the end of the exhalation phase and / or beginning of the inhalation phase, (ii) temporarily increasing the flow rate, and (iii) decreasing the flow rate for a predetermined number of breath cycles.

27. A respiratory therapy deliver)’ device configured to be worn by a patient to provide respiratory therapy, the device comprising: a tube configured to receive a flow of gas from a respirator)’ device; and an interface portion coupled to and / or coupleable to the tube, wherein the interface portion includes: a housing having a first chamber and a second chamber, wherein the first chamber is fluidly coupled to the tube and the second chamber is not fluidly coupled to the tube;a first nasal prong fluidly coupled to the first chamber, wherein the first nasal prong is configured to be at least partially inserted in a first nare of the patient to form a substantial seal thereat; and a second nasal prong fluidly coupled to the second chamber, wherein the second nasal prong is configured to be at least partially inserted in a second nare of the patient to form a substantial seal thereat.

28. The device of claim 27 wherein the first nasal prong is sized and shaped to occlude 100% of a nare opening area at the patient’s first nare, and wherein the second nasal prong is sized and shaped to occlude 100% of a nare opening area at the patient’s second nare.

29. The device of any of claim 27 wherein the interface portion further includes a partition fluidly isolating the first chamber and the second chamber.

30. The device of claim 27 wherein the interface portion further comprises an exhalation vent fluidly coupled to the second chamber.

31. The device of claim 30 wherein the device is configured such that, in operation: gas is delivered to the patient via the tube, the first chamber, and the first nasal prong; and exhaled gas from the patient is purged via the second nasal prong, the second chamber, and the exhalation vent.

32. A patient interface for delivering respiratory gas to a patient, the patient interface comprising: a housing having a first chamber and a second chamber, wherein the first chamber and the second chamber are fluidly isolated within the housing; a first nasal prong fluidly coupled to the first chamber, wherein the first nasal prong is configured to be at least partially inserted in a first nare of the patient; a second nasal prong fluidly coupled to the second chamber, wherein the second nasal prong is configured to be at least partially inserted in a second nare of the patient; and an exhalation vent fluidly coupled to the second chamber.

33. The patient interface of claim 32 wherein the first nasal prong is sized and shaped to form a substantial or complete seal at the first nare. and wherein the second nasal prong is sized and shaped to form a substantial or complete seal at the second nare.

34. The patient interface of claim 32 wherein the housing includes a partition between the first chamber and the second chamber.

35. The patient interface of claim 32 wherein the housing includes an inflow port configured to connect to a tube for receiving inhalation gas, the opening being in fluid communication with the first chamber.

36. The patient interface of claim 32 wherein the interface is configured such that, in operation: gas is delivered to the patient via the first chamber and the first nasal prong; and exhaled gas from the patient is purged via the second nasal prong, the second chamber, and the exhalation vent.

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