A system for managing lung health

Abstract

To provide systems and methods for pulmonary health management using one or more inhalation devices.SOLUTION: In one aspect, air inhalation devices each comprise one or more sensors configured to capture pulmonary health date for a patient. Using this data, air analytics may be generated pertaining to individualized patient health, general health for people living within a particular geographical location, air quality for a particular geographical region, operational parameters of the inhalation devices, and the like. The air analytics may be output, for example, for display on a user device, such as a patient user device, a health care provider user device, and / or an administrator user device.SELECTED DRAWING: Figure 2

Description

[Technical field]

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS This application is a continuation of U.S. Provisional Patent Application No. 62 / 331,328, filed May 3, 2016, entitled "DISPOSABLE PULMONARY DRUG DELIVERY APPARATUS AND METHODS OF USE," U.S. Provisional Patent Application No. 62 / 332,352, filed May 5, 2016, entitled "DISPOSABLE PULMONARY DRUG DELIVERY APPARATUS AND METHODS OF USE," U.S. Provisional Patent Application No. 62 / 334,076, filed May 10, 2016, entitled "DISPOSABLE PULMONARY DRUG DELIVERY APPARATUS AND METHODS OF USE," U.S. Provisional Patent Application No. 62 / 334,076, filed June 24, 2016, entitled "DISPOSABLE PULMONARY DRUG DELIVERY APPARATUS AND METHODS OF USE," DELIVERY APPARATUS No. 62 / 354,437, filed September 23, 2016, entitled "DISPOSABLE PULMONARY DRUG DELIVERY APPARATUS AND METHODS OF USE," and U.S. Provisional Patent Application No. 62 / 399,091, filed November 1, 2016, entitled "DISPOSABLE PULMONARY DRUG DELIVERY APPARATUS AND METHODS OF USE." No. 62 / 416,026, entitled "DISPOSABLE PULMONARY DRUG DELIVERY APPARATUS AND METHODS OF USE," filed November 16, 2016; U.S. Provisional Patent Application No. 62 / 422,932, entitled "DISPOSABLE PULMONARY DRUG DELIVERY APPARATUS AND METHODS OF USE," filed December 1, 2016; U.S. Provisional Patent Application No. 62 / 428,696, entitled "DISPOSABLE PULMONARY DRUG DELIVERY APPARATUS AND METHODS OF USE," filed January 20, 2017; No. 62 / 448,796, entitled "DISPOSABLE PULMONARY DRUG DELIVERY APPARATUS AND METHODS OF USE," filed on March 15, 2017, and U.S. Provisional Patent Application No. 62 / 471,929, entitled "DISPOSABLE PULMONARY DRUG DELIVERY APPARATUS AND METHODS OF USE," filed on March 15, 2017, the contents of each of which are incorporated herein by reference in their entirety.

[0002]

[0002] Aspects of the present disclosure relate to pulmonary health management for one or more patients, and more particularly to generating pulmonary health management analyses using one or more inhalation devices configured to monitor pulmonary conditions and deliver medications through the lungs to treat various pulmonary and / or non-pulmonary conditions. [Background technology]

[0003]

[0003] Aerosol generating devices are often used to treat various respiratory diseases. For example, inhalation provides delivery of aerosolized drugs to treat asthma, chronic obstructive pulmonary disease (COPD) and site-specific conditions with reduced systemic adverse effects. A key challenge is to find a suitable aerosol for successful delivery to targeted lung passageways. The object of the present invention is to provide a device that delivers an accurate, consistent, and verifiable dosage with a certain droplet size. Effective delivery of drugs through the alveoli to the deep lung region of the lung has always presented a problem, especially for children and the elderly, as well as people with medical conditions, due to their limited lung capacity and narrowing of the breathing passageway. The effect of the narrowed lung passageway limits the patient's deep inspiration and synchronization of the administered dosage with the respiratory cycle, including inspiration and expiration.

[0004]

[0004] Conventional devices often fail to provide either a high enough momentum to achieve dose ejection from the device or a low enough momentum to prevent dose deposition in the back of the throat. More specifically, many conventional inhaler systems, such as metered dose inhalers (MDIs) and pressurized metered dose inhalers (p-MDIs) or pneumatic and ultrasonically driven devices, generally generate droplets with high momentum and kinetic energy, high velocity and a wide range of droplet sizes, including large droplets. Such high momentum droplets and aerosols do not reach the distal lung or lower lung passages, but are instead deposited in the oral cavity and throat. As a result, a larger total drug dose is required to achieve the desired deposition in the targeted area. These large dosages increase the possibility of unwanted side effects.

[0005]

[0005] An additional challenge arises when aerosol plumes generated from conventional aerosol delivery systems, as a result of their high release rate and fast expansion of the drug-loaded propellant, lead to localized cooling and subsequent condensation, deposition and crystallization of drug on the ejector surfaces. Such obstruction of the ejector opening by deposited drug residues can inhibit effective delivery of the dosage. This phenomenon of surface condensation and drug deposition is also a challenge for conventional nebulizers.

[0006]

[0006] Furthermore, many patients are unable to use inhalers correctly, exacerbating the challenges for healthcare providers in treating various conditions. Delivery and inhalation of the correct dosage at the prescribed times is critical to treatment. However, conventional devices cannot verify dosage delivery and quality, leaving providers struggling to interpret current treatment results and reconsider prescribed treatments when therapeutic outcomes are not achieved. Similarly, providers must rely on patients' descriptions of symptoms in combination with clinical trials. However, this often fails to provide a comprehensive picture of the condition and the effectiveness of a particular drug therapy in treating pulmonary conditions.

[0007]

[0007] It is with particularity in mind these observations that the various aspects of the present disclosure have been conceived and developed. Summary of the Invention [Problem to be solved by the invention]

[0008] [Means for solving the problem]

[0009]

[0008] Implementations described and claimed herein address the above problems by providing a system and method for pulmonary health management. In one implementation, pulmonary health management information is received from one or more inhalation devices over a network. Each of the one or more inhalation devices has one or more pressure sensors that measure the flow rate of airflow through a tube of the inhalation device. Environmental data is received for one or more geographic locations where the one or more inhalation devices are deployed. The environmental data is captured using the one or more environmental sensors and corresponds to ambient air conditions at each of the one or more geographic locations. The pulmonary health management information is correlated with the environmental data based on at least one management parameter using at least one computing unit, and an air analysis is generated from the correlated data using at least one computing unit.

[0010]

[0009] Other implementations are also described and illustrated herein. Moreover, while multiple implementations are disclosed, still other implementations of the disclosed technology will become apparent to those skilled in the art from the following detailed description, which shows and describes exemplary implementations of the disclosed technology. As will be appreciated, the disclosed technology can be modified in various ways, all without departing from the spirit and scope of the disclosed technology. Thus, the drawings and detailed description should be regarded as illustrative in nature, and not restrictive. [Brief description of the drawings]

[0011] [Figure 1]

[0010] FIG. 1 illustrates an exemplary inhalation device for use by a patient for pulmonary health management. [Diagram 2]

[0011] FIG. 1 is a functional block diagram of exemplary components of an inhalation device, including a drug cartridge. [Diagram 3]

[0012] FIG. 1 illustrates an exemplary operation for drug delivery to a patient using an inhalation device. [Figure 4]

[0013] FIG. 1 illustrates a pulmonary health management system including an air analyzer that may operate on a computer server, computing device, or other network device for pulmonary health management using one or more inhalation devices. [Diagram 5]

[0014] FIG. 1 illustrates an exemplary air analysis user interface for managing the pulmonary health of one or more patients or geographic areas. [Figure 6]

[0015] FIG. 1 illustrates an exemplary operation for pulmonary health management. [Figure 7]

[0016] FIG. 1 is a functional block diagram of an electronic device including operational units arranged to perform pulmonary health management operations. [Figure 8]

[0017] FIG. 1 illustrates an example computing system in which various systems and methods of the techniques of this disclosure may be implemented. [Figure 9]

[0018] 9A, 9B, and 9C are front, rear, and back perspective views of an exemplary inhalation device. [Figure 10]

[0019] 9D is a cross-sectional view of the inhalation device taken along the line indicated in FIG. 9C. [Figure 11]

[0020] FIG. 2 is an exploded view of the inhalation device. [Figure 12A]

[0021] FIG. 1 is a bottom perspective view of an exemplary drug cartridge. [Figure 12B]

[0022] FIG. 2 is an exploded view of the ejector assembly of the drug cartridge. [Figure 12C]

[0023] FIG. 13 is a cross-sectional view of a drug cartridge with a detailed view of the ejector O-ring. [Figure 13]

[0024] FIG. 13 is a detailed view of an exemplary aperture plate with ejector holes having multiple diameters configured to generate droplets of multiple sizes to target different regions of the lung airways. [Figure 14]

[0025] 14A and 14B show an example inhalation device configured to sense airflow by detecting a pressure difference across a flow restriction, illustrating the restriction inside the aerosol delivery tube, respectively. [Figure 15]

[0026] 15A, 15B, and 15C are diagrams illustrating an example of a pressure sensor assembly; [Figure 16A]

[0027] FIG. 2 is a circuit diagram for an exemplary power on / off circuit for an exemplary inhalation device. [Figure 16B]

[0028] FIG. 2 is a circuit diagram for an exemplary power connector circuit for an exemplary inhalation device. [Figure 16C]

[0029] FIG. 2 is a circuit diagram for an exemplary voltage power conditioning circuit for an exemplary inhalation device. [Figure 16D]

[0030] FIG. 2 is a circuit diagram for an exemplary controller circuit for an exemplary inhalation device. [Figure 16E]

[0031] FIG. 1 is a circuit diagram for an exemplary controller programming connector circuit for an exemplary inhalation device. [Figure 16F]

[0032] FIG. 1 is a circuit diagram for an exemplary piezoelectric connector circuit for an exemplary inhalation device. [Figure 16G]

[0033] FIG. 1 is a circuit diagram for an exemplary user switch with debounce circuit for an exemplary inhalation device. [Figure 16H]

[0034] FIG. 1 is a circuit diagram for an exemplary piezoelectric driver circuit for an exemplary inhalation device. [Figure 16I]

[0035] FIG. 2 is a circuit diagram for an exemplary pressure sensor circuit for an exemplary inhalation device. [Figure 16J]

[0036] FIG. 1 is a circuit diagram for an exemplary light emitting diode indicator circuit for an exemplary inhalation device. [Figure 16K]

[0037] FIG. 2 is a circuit diagram for an exemplary buzzer driver circuit for an exemplary inhalation device. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0012]

[0038] Aspects of the present disclosure generally relate to systems and methods for pulmonary health using one or more inhalation devices. In one aspect, the air inhalation devices each include one or more sensors configured to capture pulmonary health data about a patient. Using this data, air analyses can be generated that relate to personalized patient health, overall health for people living within a particular geographic location, air quality for a particular geographic area, operating parameters of the inhalation device, and the like. The air analyses can be output for display on a user device, such as, for example, a patient user device, a healthcare provider user device, and / or an administrator user device.

[0013]

[0039] In general, an inhalation device provides for the delivery of a fluid in the form of an aerosol containing drug(s) to a patient's lungs for local pulmonary and / or systemic delivery of the drug(s). The inhalation device is configured to provide an aerosol droplet size within the human respirable range such that effective, repeatable dosage delivery is achieved. The human respirable range includes droplets with an aerodynamic diameter of less than 5 μm, which are transported almost entirely by the air stream and the movement of the entrained air, rather than by their own momentum. More specifically, for optimal deposition in the alveolar airways, the human respirable range includes droplets with an aerodynamic diameter in the range of 1-5 μm, with particles below 4 μm reaching the alveolar region of the lungs. Larger droplets (i.e., greater than 5 μm) are often deposited on the tongue or strike the throat and coat the bronchial passages. Particles smaller than 1 μm in diameter that penetrate deeper into the lungs have a tendency to be exhaled. Thus, the inhaler device described herein delivers particles in a suitable size range, avoids surface fluid deposition and blockage of apertures, while providing a verifiable dosage, thus providing feedback to patients and health care providers regarding correct and consistent usage of the inhaler device.

[0014]

[0040] Additionally, inhaler devices can monitor a patient's breathing patterns to diagnose conditions and / or manage treatment. For example, a drop in peak flow is a useful indicator of an increased likelihood of an asthma attack, and measurements of pulmonary output (i.e., FEV1) can help determine the effectiveness of a particular drug therapy in treating a pulmonary condition.

[0015]

[0041] Many of the exemplary implementations described herein refer to pulmonary conditions. However, it will be appreciated by those skilled in the art that the techniques of the present disclosure are applicable to non-pulmonary conditions that may be diagnosed and / or treated via analysis and delivery of drugs via the lungs. Furthermore, the various inhalation devices described herein are merely examples. Other health monitoring devices may be used to generate air analysis.

[0016]

[0042] 1, an exemplary inhalation device 100 is shown for use by a patient 104 for pulmonary health management. In one implementation, the inhalation device 100 includes a cartridge 102, which may be disposable or reusable, for releasing a dosage of medication during an inhalation cycle for delivery to the lungs of the patient 104. The inhalation device 100 may further capture pulmonary health data about the patient 104 for use in diagnosing the patient's condition and / or generating an air analysis, as described herein.

[0017]

[0043] In one implementation, the inhalation device 100 is configured for electronically activated breath actuation. The inhalation device 100 includes a pressure sensor assembly that automatically detects a trigger point during the inhalation cycle of the patient 104 to activate and trigger the nebulization and delivery of the drug. For example, the pressure sensor assembly can be programmed to trigger nebulization 2 seconds when the airflow is 10 standard liters per minute (SLM). The trigger point during the inhalation cycle can provide an optimal point during the inhalation cycle of the patient 104 to activate and trigger the nebulization and delivery of the drug. Because breath actuation does not require patient-device coordination, the breath actuation triggering mechanism of the inhalation device 100 for delivering an aerosol dosage ensures optimal delivery of the drug.

[0018]

[0044] As shown in Fig. 1, the inhalation device 100 generates entrained air from droplets released from the cartridge 102 as a result of the combined momentum transfer from the droplets to the ambient air and the large specific surface area of ​​the droplet particles (e.g., less than 5 μm in diameter). Fig. 1 shows the inertial filter mechanism provided by the inhalation device 100 to filter and exclude larger droplets (e.g., greater than 5 μm in diameter) from the aerosol plume due to their higher inertial force and momentum. In one implementation, the droplets undergo a change of about 90 degrees in spray direction from a first region 108 to a second region 110 as they emerge from the cartridge 102 and are swept away by the airflow 106 through a laminar flow element before inhalation into the pulmonary airways of the patient 104.

[0019]

[0045] If droplet particles having an aerodynamic diameter larger than 5 microns are generated by the cartridge 102, the inhalation device 100 removes the particles from the airflow 106 by using the increased inertial mass of the particles to deposit them on the airway tract. Alternatively, if all emitted particles are directed to a target for delivery as a dosage, the velocity of the airflow 106 can be increased so that the larger droplet particles can be carried to the pulmonary airways of the patient 104. This feature of the inhalation device 100 further increases the respirable dosage, thus providing improved targeted delivery of either medication deep to the lower alveolar airways or onto the upper respiratory regions of the patient 104.

[0020]

[0046] The inhalation device 100 may further verify the dosage through verification of the presence of a plume of drug droplets. In one implementation, the inhalation device 100 verifies the plume through measurements of light absorption or scattering by the droplets between the cartridge 102 and the patient 104. The optical measurements were made using a solar-blind ultraviolet light source and detector. In another implementation, the inhalation device 100 verifies the plume by measuring the temperature of the air stream carrying the plume.

[0021]

[0047] As further described herein, in one implementation, the inhalation device 100 generates diagnostics for pulmonary pathology monitoring using an airflow sensor assembly with increased sensitivity at low differential pressures, no drift, low hysteresis, and a sensor output that is independent of air density and temperature. More specifically, the inhalation device 100 may capture one or more diagnostic indicators of the patient's 104 pulmonary function, including, but not limited to, peak inhalation flow rate, inhaled volume, nitric oxide concentration, pulmonary output, etc. The inhalation device 100 may capture the diagnostic indicators by measuring the pressure drop between the inhalation tube of the inhalation device 100 and the surrounding atmosphere using a preset flow resistance element, an adjustable flow resistance element, etc. The diagnostic indicators may be stored in the inhalation device 100 and / or communicated to a user device for generating an air analysis.

[0022]

[0048] Generally, the inhalation device 100 includes a cartridge 102 for delivering a safe, suitable, and repeatable dosage for pulmonary use to a patient 104. Upon application, the cartridge 102 delivers a defined volume of fluid in the form of aerosol droplets that have the properties to deliver a suitable, repeatable, high rate of deposition to the alveolar airways of the patient 104.

[0023]

[0049] As described in more detail herein, in one implementation, the cartridge 102 includes a reservoir for receiving a volume of fluid and an ejector assembly having a piezoelectric actuator plate and an aperture plate (mesh plate) configured to eject a stream of aerosol droplets having an average ejected droplet diameter of less than 5 microns. Aerosol droplets this small have low inertia and momentum and are transported almost entirely to the lungs by the movement of the air stream (entrained air), reaching the lower alveolar airways of the subject during use.

[0024]

[0050] In other words, the inhalation device 100 delivers aerosols to the lungs of the patient 104 for delivery of small molecules, large molecules, and biological agents for local pulmonary or systemic drug delivery. In one implementation, the inhalation device 100 provides aerosol droplet sizes within a range suitable for human respirability (e.g., less than 5 microns) such that effective, repeatable dosage delivery is achieved. Furthermore, the inhalation device 100 generates aerosols in a manner that does not generate elevated in-situ temperatures or forces that tend to denature or degrade the active agent. Thus, the inhalation device 100 can be used to deliver biologics and other large molecules that are sometimes susceptible to denaturation and degradation in conventional inhalers and nebulizers.

[0025]

[0051] In one implementation, the cartridge 102 includes an ejector assembly constructed to eject an aerosol stream of droplets. The ejector assembly includes an aperture plate coupled to a piezoelectric actuator. In some implementations, the aperture plate can be coupled to an actuator plate coupled to a piezoelectric actuator. The aperture plate includes a plurality of openings formed through its thickness, and the piezoelectric actuator oscillates the aperture plate with fluid in contact with one surface of the aperture plate at a frequency and voltage to generate a directed aerosol stream of droplets through smaller openings in the aperture plate and into the lungs when the patient 104 inhales. The aperture plate is actuated by a piezoelectric actuator. In another implementation coupled to an actuator plate, the actuator plate is oscillated by a piezoelectric oscillator at a frequency and voltage to generate a directed aerosol stream or plume of aerosol droplets.

[0026]

[0052] The cartridge 102 may be replaced or disposable on either a daily or weekly or monthly basis appropriate for the prescribed treatment. The disposable nature of the cartridge 102 may minimize and prevent the accumulation of surface deposits on the aperture plate or surface microbial contamination due to its short in-use time. Alternatively, the cartridge 102 may be reusable to deliver multiple drugs or drug flavors for multi-drug therapy. Thus, the inhalation device 100 may deliver multiple drugs prescribed to a patient and delivered through the same device. The cartridge 102 may include a dual drug cartridge module with an aperture plate that is similar in design and capable of delivering inhaled drug dosages with droplets targeted to similar areas of the lung airways and with similar aerodynamic particle size distribution. Alternatively, the use of multiple drugs or multi-drug therapy may require delivery of drugs to different areas of the lung airways. Under these circumstances, each of the dual cartridge modules of the cartridge 102 may have aperture plates with different ejector hole designs and different inlet and outlet orifice sizes to deliver different droplet sizes that target different areas of the patient's 104 pulmonary airways.

[0027]

[0053] In one implementation, the cartridge 102 delivers multiple drug or drug flavors for multi-drug therapy, where the ejector aperture plate of each drug-containing cartridge unit has a design with different sized ejector holes. This design provides a system and method for producing different droplet sizes using one aperture plate. This design can facilitate compliance with drug regimens by children and adults by providing flavored drugs that target different regions of the lung airways, thereby improving the taste of the drug in the mouth and throat. In some embodiments, this system and method of designing aperture plates with different sized ejector holes can improve the taste or feel of a nicotine delivery device by delivering droplets large enough to deposit on the tongue and throat, as well as delivering droplets to the deep alveolar airways.

[0028]

[0054] The ejector assembly of the cartridge 102 may be oriented horizontally and positioned such that the fluid or agent contained therein is in constant contact with the inlet surface of the aperture plate. The horizontally oriented ejector assembly may enable and provide uniform distribution of fluid and uniform coating of fluid onto the aperture plate. In some implementations, the horizontally positioned ejector assembly provides a uniform fluid / agent coating to the aperture plate, which also has the benefit of providing a uniform load across the aperture plate. This design may provide a more efficient, stable aperture plate oscillation, provide a more efficient release of fluid, and minimize the possibility of chaotic membrane oscillation. In some embodiments, chaotic oscillation may lead to delivery of an inappropriate dosage, as well as minimize or completely stop release, or lead to deposition of fluid and / or agent on the aperture plate surface, leading to blockage of the aperture. The reduction or elimination of chaotic oscillation provides a more efficient, stable aperture plate oscillation and a more efficient, stable delivery of the drug.

[0029]

[0055] In one implementation, the inhalation device 100 monitors and detects the amount of fluid expelled and the drug remaining in the cartridge 102 after the dosage is expelled from the piezoelectric ejector of the expelling assembly. A frequency shift in the resonant frequency oscillation of the aperture plate is related to a change in mass loading, for example, as described by the Sauerbrey equation. In some implementations, detection of a change in the resonant frequency of the aperture plate oscillation can provide dosage verification, since the change in the resonant frequency of the aperture plate oscillation is correlated with a change in mass or loading on the piezoelectric actuator.

[0030]

[0056] The inhalation device 100 may include a surface tension plate, such as a porous grid or a perforated plate. The surface tension plate may include a collection of vertices, edges, and holes that define a shape, which may be, but is not limited to, a square, triangle, polygon, or any shape grid form, arranged behind the aperture plate at the fluid inlet surface side and configured to maintain a constant fluid load. The spacing of the openings on the surface tension plate, as well as the distance and arrangement of the surface tension plate relative to the aperture plate surface, may be optimized and specified by the surface tension of the fluid. In some embodiments, the presence of a surface tension plate located behind the aperture plate also leads to a more stable and controlled oscillation and actuation of the aperture plate, minimizing chaotic oscillations and deposition of fluid and / or drug on the aperture plate surface.

[0031]

[0057] In one implementation, the ejector assembly of the cartridge 102 may be oriented vertically, and thus the placement of the surface tension plate behind the vertically oriented ejector assembly on the fluid side of the aperture plate provides a constant, uniform fluid load on the aperture plate. This configuration provides a uniform fluid coating on the aperture plate, and also has the benefit of providing a uniform load across the aperture plate. In some implementations, this configuration also provides a more efficient, stable aperture plate oscillation, which may lead to more efficient fluid ejection and aerosol formation, and minimize the probability of chaotic membrane oscillation.

[0032]

[0058] The inhalation device 100 may be insensitive to orientation. More specifically, the placement of the surface tension plate behind and next to the aperture plate provides a constant uniform fluid load on the aperture plate and is not dependent on the overall orientation of the inhalation device 100 with respect to fluid load or placement or availability of fluid behind the aperture plate prior to actuation and nebulization. This may also provide a more efficient, stable aperture plate oscillation, which may lead to a more efficient release of fluid and minimize the probability of chaotic membrane oscillation.

[0033]

[0059] The inhalation device 100 may be insensitive to pressure differences that may occur when the patient 104 travels from sea level to below sea level, and at high altitudes while traveling by airplane, or weather-related changes in atmospheric pressure. In some embodiments, the application and use of a superhydrophobic air exchange valve located adjacent to the drug reservoir in the cartridge 102 provides protection against the ingress or exchange of both water and drug beyond the valve, and avoids leakage from the reservoir. In some implementations, the superhydrophobic air exchange valve allows free exchange of air beyond the valve into and out of the reservoir, but prevents moisture or fluids from passing through the air exchange valve. This high-efficiency particulate air filter also normalizes the pressure difference between the environment and the reservoir with highly filtered air that has removed all particles and pathogens (including viral pathogens, bacteria, and spores) when the inhalation device 100 experiences fluctuations in atmospheric pressure and therefore pressure differences. Also, by allowing free exchange of air, the pressure inside the reservoir of the cartridge 102 is maintained in equilibrium with its environment, thus providing an active and dynamic mechanism for highly efficient air filtration, providing and preventing medication leakage.

[0034]

[0060] The inhalation device 100 is insensitive to changes in ambient air pressure caused by weather or altitude fluctuations. This allows for use of the inhalation device 100 without the possibility of fluid leakage as it transitions to different altitudes. The inhalation device 100 also reduces fluid and drug deposition on the aperture plate surface and can prevent blockage of the apertures, which can prevent improper delivery of a dosage or render the inhalation device 100 inoperable.

[0035]

[0061] The inhalation device 100 delivers a volume of fluid as an aerosol plume or fine mist of liquid that rides on the entrained air with laminar flow as it advances into the pulmonary airways of the patient 104. A single source of entrained air with laminar flow may be configured with multiple tubular aerosols having either a hexagonal or other cross section. A laminar flow element with parallel tubes is provided, as described herein, at the air inlet end of the aerosol delivery tube of the inhalation device 100. The laminar flow element generates the laminar air flow 106 by dividing the air flow into many parallel flow passages having diameters small enough to generate a laminar air flow 106, but not too small to create a significant pressure difference between the inlet side of the laminar flow element and the outlet side of the laminar flow element. Because only a small flow passes through each laminar flow element passage, the Reynolds number of the flow through each passage is small enough that the laminar flow 106 is maintained. In some implementations, the air drawn into the inhalation device 100 has laminar flow characteristics as the air is drawn through the laminar flow element, sweeping across the face of the aperture plate, entraining the expelled particles and transporting them further downstream in a trajectory to the airways of the patient 104.

[0036]

[0062] The inhalation device 100 may include a mini fan or centrifugal blower located on the air inlet side of the laminar flow element. The mini fan may provide additional air flow and pressure to the output of the air stream. When the patient 104 has low pulmonary output, this additional air stream ensures that droplets containing the drug are pushed through the inhalation device 100 and into the airways of the patient 104. In some implementations, this additional air flow source ensures that the ejector face of the cartridge 102 is cleared of aerosol droplets and also diffuses the droplet plume in the stream, thereby creating greater separation between the droplets. The air flow provided by the mini fan may also act as a carrier gas and ensure significant dilution, which reduces the possibility of sudden dosing and rapid drug intake. In the case of some drugs, this rapid drug intake may result in unwanted side effects. Additionally, if the patient 104 has low pulmonary output or is suffering from a deterioration, a bladder that is squeezed manually or by an electromechanical component may be used to generate high air pressure during dosing to improve drug deposition in the lungs for that person. A manual button on the inhalation device 100 may be used to trigger the release of drug during "rescue" mode.

[0037]

[0063] In one implementation, the inhalation device 100 provides a highly elastic polymeric aperture plate, the periodic oscillation of which generates acoustic waves emanating from the nozzle plate surface as it accelerates and decelerates during the aerosol emission cycle. The surface acoustic waves generate pressure or compression waves that further enhance droplet generation and propagation on the entrained air. The highly elastic polymeric aperture plate with its multiple apertures ejects the fluid as droplets through inlet and outlet orifices contained in the accelerating aperture plate. In some implementations, when the oscillating highly elastic aperture plate is at its maximum displacement, its velocity at the surface of the aperture plate membrane is 0, while its acceleration is between 0.1 and 50 Km / s. 2 , 5~50Km / s 2 , but not limited to 5~25Km / s 2 A directed stream of aerosol droplets, directed through an aperture in the thickness of the aperture plate surface, emerges from the aperture with a maximum inertial force that is sufficient to carry the aerosol far downstream from the aperture plate.

[0038]

[0064] The inhalation device 100 may further employ a Laser Doppler Vibrometer (LDV) system and method for characterization of electromechanical systems and piezoelectric actuators to measure the instantaneous phase, displacement, velocity, and acceleration of the oscillating membrane. In some embodiments, the LDV may provide a three-dimensional representation of the phase relationship between displacement, velocity, and acceleration to identify resonances and eigenmodes of electromechanical systems with piezoelectric actuators that enable efficient optimization of piezoelectric materials, piezoelectric geometry optimization, and design of ejector systems for optimal aerosol droplet generation and nebulization characteristics. Such analysis parameters may be simultaneously detected, captured, and stored for subsequent analysis by the inhalation device 100 and / or air analyzer.

[0039]

[0065] The inhalation device 100 electrostatically delivers the charged pharmaceutical aerosol particles generated during ejection and droplet formation as the fluid emerges from the exit orifice of the oscillating nozzle plate. In one implementation, the surface of the exit chamber or tube through which the aerosol plume emerges is coated with a surfactant to reduce the charge. The electrostatic coating can increase the particulate dosage delivered into the lung airways and reduce deposition of drug particles on the inner surface of the device tube of the inhalation device 100. Alternatively, the exit tube or the entire body of the inhalation device 100 is made from a charge-dissipative polymer that further reduces electrostatic charge accumulation in the exit chamber.

[0040]

[0066] In one implementation, the inhalation device 100 includes a nebulization verification system for detecting a pressure difference between the interior and exterior areas of the ejector tube for verification of aerosol nebulization and drug delivery. A signal provided by a pressure sensor of the nebulization verification system provides a trigger for activation of nebulization at or during a peak period of the patient's 104 inhalation cycle to ensure optimal deposition of the aerosol nebulization and drug delivery to the lung airways.

[0041]

[0067] The aerosol verification system of the inhalation device 100 may include, for example, an infrared light emitting diode (LED) having a wavelength of about 850 nm and an infrared photodetector. In one implementation, the aerosol verification system may use a solar blind photo detector and a UV-C LED with a peak emission wavelength below about 280 nm to measure and sense in either transmission or backscatter mode to detect the presence and amount of drug released.

[0042]

[0068] Aerosol verification system for the inhalation device 100 in a fluorescence mode where the air stream is exposed to an energy source such as ultraviolet light and substances in the air stream fluoresce and emit photons of light having a particular wavelength. This mode can be used to detect and measure a variety of airborne substances, providing maximum detection for aerosol verification and assurance of elimination of inaccurate or false detection of aerosol. The solar blind detector provides greater flexibility in use and operation of the inhalation device 100 when outdoors, in bright sunlight, without interference.

[0043]

[0069] In another implementation, the inhalation device 100 uses an audio signal for nebulization verification either when a dosage is administered by breath actuation and / or when an aerosol stream of droplets is detected. The addition of a sound chip to the electronics board of the inhalation device 100, along with a speaker, can provide instant feedback to the patient 104 when a dosage has been successfully delivered. By providing real-time feedback, the audio signal can maximize patient compliance by providing assurance that the dosage has been successfully delivered.

[0044]

[0070] Alternatively or additionally, the inhalation device 100 may measure and quantify the amount of drug released during emission and nebulization. The absorbance of the nebulized drug dose may be provided by measuring the absorbance of light. The drug solution may be pre-adjusted using known concentrations to provide a drug absorbance value at a specified wavelength. The inhalation device 100 verifies that the drug has been nebulized and emitted, as well as providing the quantity and amount of drug in the emitted aerosol stream and the amount of drug remaining in the cartridge 102 reservoir.

[0045]

[0071] For the diagnosis of lung conditions and / or for air analysis, the inhalation device 100 can sense and detect disease biomarkers in the exhaled breath. Human breath contains several volatile organic compounds (VOCs), the accurate detection of which can give essential information for the early diagnosis of diseases in the human or animal body in general. For example, nitric oxide can be used to assess and detect asthma diagnosis, while acetone, ammonia, H2S, and toluene can be used to assess diabetes, kidney dysfunction, halitosis, and lung cancer, respectively. The diagnosis of these diseases can be performed using small MEMS-based amperometric sensors. This can be achieved by the inclusion of a MEMS sensor inside the mouthpiece or droplet exit cavity of the device to analyze the concentration of nitric oxide in the exhaled breath for ASTM D621 monitoring and diagnosis. Furthermore, variations in the concentration of exhaled VOCs can act as biomarkers for specific diseases and can be used to distinguish healthy patients from those who are ill.

[0046]

[0072] The inhalation device 100 may include one or more visual, audio and / or tactile indicators for providing instructions or feedback to the patient 104. The indicators may alternatively or additionally be provided via a user device in communication with the inhalation device 100 as described herein. For example, the inhalation device 100 may instruct the patient to initialize the inhalation device 100 by taking a set number (e.g., five) of slow, deep breaths. This provides information that is used to determine a trigger point during inhalation for generating a breath-actuated release of the drug by the piezoelectric-driven ejector to maximize the inhalation of the prescribed drug by the patient 104. It also provides a baseline for diagnosing changes in the pulmonary condition of the patient 104. For example, the minimum pressure achieved during inhalation corresponds directly to the peak inspiratory flow rate. A decrease in the peak flow rate during inhalation may be predictive of an asthma exacerbation. When measurements of exhaled nitric oxide and peak flow rate measurements are combined, the predictive capabilities of the on-board diagnostics configured on the inhalation device 100 and / or air analyzer become even more powerful.

[0047]

[0073] In one implementation, the inhalation device 100 captures a measurement that correlates to pulmonary output (FEV1) by measuring the peak flow rate achieved during maximum exhalation. The air analyzer described herein prompts the patient 104 using indicators to guide the patient 104 through the breathing movements required to make a measurement that correlates to pulmonary output.

[0048]

[0074] Additionally, the inhalation device 100 may include a differential (delta P) sensor to allow measurement of the inhalation pressure required to achieve a predetermined flow rate. This measurement may allow the device to approximate the change in dynamic airway resistance by comparing the pressure required to produce the airflow rate measured during initialization. Although not a measurement of absolute airway resistance, this measurement of the change in pressure measured on one side of the airway at a given flow rate during inhalation measures the change in the patient's lung health if the patient 104 suffers from asthma or COPD. This may be referred to herein as the relative change in dynamic airway resistance (RCDAR), expressed as a percentage change in pressure measured at 50% of the airflow rate measured at baseline. For example, a reading of 10% RCDAR is a 10% decrease in the pressure required to achieve 50% of the maximum flow rate measured at baseline. Additionally, the inhalation device 100 may be used to ascertain the velocity of the emitted plume prior to inhalation, which may serve as confirmation that the flow sensor of the inhalation device 100 is properly calibrated and operating.

[0049]

[0075] The delta P sensor measures airflow by measuring the pressure drop between the inside of the inhalation device 100 and the ambient atmosphere. The flow rate is calculated from the measured pressure drop between the delta P sensor ports, one located upstream in the device aerosol delivery tube, close to the air inlet port, in the vicinity of the laminar flow element, and the second delta P sensor port measuring the ambient pressure outside the inhalation device 100, as described in more detail herein. This measurement is also used to trigger the start and end of the droplet ejection cycle to coordinate the optimal point of the inhalation cycle with the ejection and nebulization of the aerosol plume. The pressure measurement subsystem also distinguishes between inhalation and exhalation, so that droplet particles are administered only at the inhalation during the inhalation cycle.

[0050]

[0076] In one implementation, the optical aerosol sensor of the inhalation device 100 measures and detects the presence of droplets by detecting light emitted from an LED source arranged across the diameter of the inhalation tube by a photodetector and detecting light scattered or absorbed by the droplets. The light source is a narrow viewing angle (e.g., less than 8 degrees) LED or laser diode. In addition, multiple light sources and multiple detectors arranged, for example, along the inhalation device 100 exit port or in front of the cartridge 102 ejector plate can determine the shape, including the cross section and length, of the aerosol plume to estimate the emitted mass.

[0051]

[0077] For example, where the inhalation device 100 includes a flow tube having an average diameter of 20 mm, a 4 second inhalation of 100 to 500 milliliters of air will have an average velocity of 8 to 40 centimeters per second. If the optical sensor is located 20 mm downstream from the ejector assembly of the cartridge 102, the leading edge of the aerosol particle will arrive at the optical detector 50 to 250 milliseconds after emission.

[0052]

[0078] A typical photodetector that may be used in the inhalation device 100 may have a response time of less than 1 millisecond, thus allowing for accurate resolution of entrained droplet velocity. A second LED / photodetector system may be added and used to provide finer resolution of the aerosol velocity. In one implementation, the inhalation device 100 measures and detects the arrival of the aerosol plume at two downstream points several centimeters apart. In this case, the LED sources for each system are pulsed and a synchronous detector is used to synchronize each detector with its associated light source.

[0053]

[0079] To continue the detailed description of a particular implementation 200 of the inhalation device 100, reference is made to FIG. 2. The various components of the inhalation device 200 coordinate all operational functions, as well as archive and communicate captured air pulmonary health care data, including nebulization confirmation data, diagnostic indicators, and device operating parameters for generating air analysis. Additionally, cartridge 202 identification information or dosage size parameters may also be stored in the memory of the inhalation device 200 and / or cartridge 202. For on-board data storage, the controller 222 may include a low-power microprocessor with several kilobytes of data memory, several channels of 10-12 bit analog-to-digital conversion, and several digital outputs. However, other controllers are contemplated.

[0054]

[0080] The inhalation device 200 may include a pressure sensor 206, a plume sensor 208, a tilt sensor 210, a plume illuminator 212, a switch 214, a traffic light 216, a display 218, a wired or wireless link 220 to one or more user devices 204, a cartridge controller 224, and a power source 226. The cartridge controller 224 may control the operation of and / or capture information from the cartridge 202, including a cartridge tag 228, an ejector assembly 230, and a cartridge sensor 232. It will be appreciated that more or less of these components may be included in the inhalation device 200.

[0055]

[0081] In one implementation, the controller 222 activates when the power button is pressed, monitors the pressure sensor 206, waits for a dosing command or an inhalation profile of rapidly falling pressure, activates a cartridge controller 224, such as a piezoelectric driver with a predetermined frequency and voltage, monitors the cartridge controller 224 to assess the dosing status, monitors the flow rate and plume using the pressure sensor 206 and plume sensor 208, respectively, to dose at trigger points, and appropriately lights on and off a traffic light 216, such as an LED, to signal a valid or invalid dose or provide other user feedback.

[0056]

[0082] The controller 222 may have an internal clock to wake and signal when the next dose for the patient 104 is scheduled. This event may be signaled by a traffic light 216, such as a blinking LED or a piezoelectric buzzer. Alternatively, an alert may be output to the user device 204 via the link 220. The controller 222 may be configured to operate with or without communication with the user device 204 and store the time and success of each dose accordingly. Profiles of the inhalation flow rate and plume at 0.1-0.01 second resolution during a 5-10 second interval surrounding the dose may further be stored. Additionally, if the inhalation device 200 has a tilt sensor 210, such as an attitude or piezoelectric mesh sensor, that data may also be stored or processed in real time to indicate a good or potentially good dose. The controller 222 may also track and display the number of doses and the remaining dose left in the cartridge 202 using the display 218 and / or the user device 204.

[0057]

[0083] The power source 226 may include one or more power sources configured to store and provide power to the components of the inhalation device 200, such as solar energy, battery power, or DC or AC power. In one implementation, the power source 226 includes a non-rechargeable battery system, such as a lithium polymer. There may be connectors on the inhalation device 200 to charge such batteries or other methods of charging, including, but not limited to, solar cells, inductive links, or even mechanical movement. The controller 222 may be configured to become inactive at very low levels of power consumption, but still monitor the input buttons and respond to presses by going to a fully awake state.

[0058]

[0084] In one implementation, to ensure and maximize patient compliance and ensure proper use of the aerosol delivery device, the inhalation device 200 and / or user device 204 may communicate various information to the patient 104. Examples of such information to promote adherence to the prescribed aerosol therapy include, but are not limited to, device on (ON), good / bad dose, number of doses remaining, time for another dose, and a description of an error condition for the inhalation device 200 (such as incorrect orientation for delivery or plume not visible). Some of this information may be communicated using the two to three light sources of the traffic light 216, one to signal that the unit is on and the other to signal a successful or unsuccessful dose. For a more user-friendly communication of information, a two- or three-color (red-green-yellow) LED may be used. Error codes based on the blinking of either or both LEDs are possible. Similarly, a four-digit LCD display may be used to indicate the number of doses remaining or the number of error codes. An explanation of the error code or more detailed information may be communicated via the user device 204. One or two user input buttons can turn on (wake up) the inhalation device 200 and begin dosing or request an error code or provide remaining dosage information.

[0059]

[0085] The link 220 can facilitate archiving, analysis and training for the patient 104, and can communicate usage and pulmonary / airway diagnosis to a health provider via the user device 204. The user device 204 can also be a resource for understanding correct usage and diagnosis of the inhalation device 200. The user device 204 can also communicate password protected information from a health provider to the inhalation device 200, such as a corrected dosage amount or frequency based on respiratory flow measured by the device with or without actual administration. In one implementation, the user device 204 can initiate a reorder when the remaining dosage falls below a preset limit.

[0060]

[0086] The link 220 may also be used at the clinical facility or pharmacy to set basic parameters or to retrieve archived information from the inhalation device 200. This information includes, but is not limited to, the following setups that may be communicated to the device: dose duration, ejector frequency, number of breaths per dose, inhalation flow rate to trigger dosing, desired dosing interval (e.g., twice a day or once every 12 hours), maximum number of good doses allowed in a time period (e.g., 2 hours), maximum number of erroneous doses allowed in a time period, number of doses administered until an almost empty signal is given, parameters describing a good dose (post-dose inhalation volume, plume opacity), date / time, expiration date or interval for the medication, password for use with the provider or pharmacy office to change settings, and / or other information describing good or bad dosage limits.

[0061]

[0087] In one implementation, the piezoelectric ejector frequency and voltage of the ejector assembly 230 may be preset during factory filling of the cartridge 202. Such values ​​may be modified using the user device 204 via the link 220. Similarly, a fill date or expiration date, drug type, or even a security code to guard against general use may be carried by the cartridge tag 228. Examples of information that may be stored and / or communicated via the cartridge tag 228 may include, but are not limited to, dosage volume and dosage interval (number of times per day), acceptable inhalation flow rate or characteristics, and / or an option to allow repeat dosing if a poor application is detected.

[0062]

[0088] There may be three additional components that may be part of the inhalation device 200, such as a mesh monitoring component, an orientation monitoring component (e.g., via tilt sensor 210), and a reservoir fluid measurement component. Mesh monitoring allows for an immediate determination that the mesh is vibrating correctly by detecting vibrations with a small piece of piezoelectric material mechanically coupled to the piezoelectric mesh. The electrical output from the small piezoelectric may be amplified, rectified, and measured using one analog digital input of the controller 222. This may supplement or replace the mesh monitoring, which is done by electronic driver impedance measurement. Orientation monitoring determines that the inhalation device 200 is correctly oriented so that the fluid in the reservoir wets the back of the mesh for good droplet generation. This same attitude measurement sensor may also be used to verify the amount of fluid (and therefore the dosage) remaining in the reservoir. This is accomplished by gently tilting the inhalation device 200 until fluid is detected, either by a lead, a capacitive sensor on the reservoir housing, or an optical sensor of the fluid. Tilt is indicated at the moment the fluid sensor transitions from not detecting fluid to detecting fluid. A simple algorithm (or lookup table) in the controller 222 gives the amount of fluid remaining as a function of tilt angle. This function can be used for a more accurate assessment of the number of doses remaining in the cartridge 202, which is particularly important when a pharmacy blind fills a reservoir and confirmation of the remaining doses available is required.

[0063]

[0089] As described herein, the inhalation device 200 generates droplets and controls the operation and monitoring of both the inhalation flow rate and plume to verify effective delivery of medication. Below are examples of how the patient 104 operates the inhalation device 200 in different user modes. In manual dispense mode, the patient 104 turns on and presses the dispense button, and the inhalation device 200 signals a plume that is visible in the correct inhalation window, and the patient 104 turns the inhalation device 200 off or It will automatically deactivate. In the trained triggered dispense mode, the patient 104 activates the device and inhales. The inhalation device 200 triggers a dose at a trigger point corresponding to a specific inhalation flow rate set by the provider. The inhalation device 200 signals a successful dose and powers off. In the trained triggered dispense mode, the patient 104 turns on the inhalation device 200 and takes several breaths during a complete breathing cycle of inhalation and exhalation. The inhalation device 200 records and dispenses a dose at a trigger point that is automatically detected using the pressure sensor 206. The inhalation device 200 signals a successful dose and becomes inactive. In the training or diagnostic mode, the patient 104 turns on the inhalation device 200 and the inhalation device 200 or the user device 204 prompts the patient 104 through a breathing cycle. Diagnostic indicators and other lung health data are captured with the inhalation device 200, which are then archived on the controller 222 and / or communicated to an air analyzer via the link 220 and / or the user device 204. The inhalation device 200 becomes inactive.

[0064]

[0090] In one implementation of the normal automatic mode of the inhalation device 200, the patient 104 is prompted to deliver a dosage. The inhalation device 200 and / or the user device 204 instruct the patient 104 to breathe one or more cycles and press a dose button. The inhalation device 200 detects the inhalation and releases a plume into the air stream. If the pressure sensor 206 indicates a correct breath and dose timing, the traffic light 216 gives feedback, such as a flashing green light. If the dose is not fully administered, the red or yellow light of the traffic light 216 flashes. If the yellow light of the traffic light 216 flashes, the patient 104 is prompted to take another dose, and a correct or incorrect dose is signaled. After 30 seconds of no activity, the controller 222 turns off the inhalation device 200. If there are multiple insufficient doses, an error code is generated by the controller 222 and communicated to the patient 104, for example, using the user device 204. The signal 216 may include a visual, audio and / or tactile signal prompting the next dose. A counter may be displayed via the display 218, including the number of doses remaining.

[0065]

[0091] The user device 204 and / or the inhalation device 200 may provide feedback to the patient 104 and / or communicate information to the provider as described herein. The feedback may include information regarding the error, including error codes and potential remedial actions, which may include, but are not limited to, no cartridge, wrong medication cartridge, no plume seen, out of dose by count, insufficient inhalation, low battery, ejector vibration problem, dosage requirement not consistent with prescription, or diagnostic information collection, etc.

[0066]

[0092] 3, operations 300 for drug delivery to a patient using an inhalation device are shown. In one implementation, operation 302 activates the inhalation device and operation 304 detects an inhalation by a user. Operation 306 generates a dosage for inhalation by the user corresponding to the detected inhalation. Operation 308 detects the quality of the dosage and operation 310 deactivates the inhalation device.

[0067]

[0093] 4 is an exemplary pulmonary health management system 400 including an air analyzer 402 running on a computer server, computing device, or other network device for pulmonary health management. In one implementation, a user, such as a patient 104, accesses and interacts with the air analyzer 402 and / or one or more inhalation devices 100 via a network 406 (e.g., the Internet). In another implementation, a user device 204 runs the air analyzer 402 locally, and the inhalation device 100 connects to the user device 204 using a wired or wireless connection. Other users may be one or more parties that sell, operate, manage, and / or otherwise monitor the inhalation device 100, including physicians, health clinics, health laboratories, etc.

[0068]

[0094] The network 404 is used by one or more computing or data storage devices (e.g., one or more databases 406) to implement the pulmonary health management system 400. A user may access and interact with the air analyzer 402 using a user device 204 communicatively connected to the network 404. The user device 204 is generally any form of computing device capable of interacting with the network 404, such as a desktop computer, a workstation, a terminal, a portable computer, a mobile device, a smartphone, a tablet, a multimedia console, etc. Depending on the user, the user device 204 may be a patient user device, a provider user device, etc.

[0069]

[0095] The server 408 may host the pulmonary health management system 400. The server 408 may also host an application, such as a website or air analyzer 402, that a user visits to access the system 400. The server 408 may be one single server, multiple servers, each such server being a physical server or a virtual machine, or a collection of both physical servers and virtual machines. In another implementation, a cloud hosts one or more components of the system 400. One or more inhalation devices 100, user devices 204 employed by users, the server 408, and other resources, such as one or more databases 406, connected to the network 404 may access one or more other servers for access to one or more websites, applications, web service interfaces, etc., used for pulmonary health management. The server 408 may also host a search engine that the system 100 uses to access and modify information used for pulmonary health management.

[0070]

[0096] The inhalation device 100 communicates with an air analyzer 402 implemented by a user device 204 over a network 404, via a wireless connection such as Bluetooth®, or via a wired connection such as a USB connection. The inhalation device 100 can be connected in a similar manner to other computers, such as smart watches, smartphones, tablets, computers, music players, Bluetooth®-enabled devices, etc. The device may be in communication with a computing device.

[0071]

[0097] In one implementation, the inhalation device includes one or more sensors for capturing lung health data, including diagnostic indicators, operating parameters of the inhalation device 100, aerosol validation data, and the like. The sensors may include, but are not limited to, one or more pressure sensors, plume sensors, tilt sensors, humidity sensors, temperature sensors, particle sensors, heart rate sensors, carbon dioxide sensors, oxide sensors, ozone sensors, nitric oxide sensors, microphones, imaging sensors, and the like. Such data may be stored in a storage medium of the inhalation device 100 and / or communicated to the air analyzer 402 via the user device 204. By way of example, data captured by the sensors may be retrieved and stored on the consumer device 204 and / or uploaded to a secure cloud via the network 404 to a database 406.

[0072]

[0098] Once data is acquired by the air analyzer 402, it may be utilized in many ways by the patient 104, providers, and other authorized parties. As described herein, the inhalation device 100 generates a large amount of sensor data, which the air analyzer 402 may correlate to generate associations and understand patterns and trends to improve healthcare, save lives, and reduce costs. Additionally, the air analysis generated by the air analyzer 402 may provide clinical decision support, disease surveillance, and healthcare management in real time while the patient 104 is undergoing treatment.

[0073]

[0099] The air analyzer 402 generates an air analysis including date / time and inhalation flow rate for each administration, which not only provides the provider with key personal information but also provides useful data for comprehensive analysis, which supports the patient 104 and other groups of people with pulmonary diseases, such as asthma and COPD. The air analysis generated by the air analyzer 402 may alert or warn individuals as well as groups of users regarding dangerous or troublesome health deterioration or environmental conditions. The air analysis for a particular patient may include, for example, a comparison of the pattern of use of the inhalation device 100 with the inhalation flow rate, frequency of use, medication, and dosing information for the patient 104. Other diagnostic indicators, such as airway resistance, inhalation volume, inhalation lung capacity and corresponding diagnosis, peak inhalation flow rate (PIF), and maximum inhalation flow rate at 50% (MIF at 50%), may be recorded and stored in the database 406.

[0074]

[0100] The air analyzer 402 detects changes in the use of the inhalation device 100 or changes in the patient 104. An air analysis may be generated through a comparison of the pulmonary health care data with previous stored data to determine when there is a change in lung function during inhalation and may further predict COPD exacerbations. Pulmonary health care information from multiple patients may be anonymized by the air analyzer 402 to determine general user classification data such as general usage patterns, inhaled volume and vital cycle status, date / time and local location of each use, disease type and severity, age, medication type(s), and generalized patient history. Operating parameters for each of the inhalation devices 100 may further be captured and processed by the air analyzer 402 for use in generating an air analysis for troubleshooting, improvement, and the like.

[0075]

[0101] Air analysis can be used to predict and determine local locations and times of day that pose the greatest threat to patients with similar conditions. For example, if reduced inspiratory volume or increased use of inhalation device 100 is reported for people with asthma in a particular area, possibly due to unidentified environmental conditions such as pollen or other allergens, an alert can be communicated via user device 204 and / or inhalation device 100 to other people in that area with asthma or other lung conditions to suggest that they should stay indoors. Such a system can also take into account and incorporate local or regional environmental monitoring by government or third parties.

[0076]

[0102] 5, an exemplary air analysis user interface 500 is shown. The air analysis user interface 500 displays air analytics generated by the air analyzer 402, including, but not limited to, air quality 502, disease information 504, healthcare information 506, device information 508, alerts / trends 510, and other analytics 512. Navigation tabs 502-512 are by way of example only and not by way of limitation.

[0077]

[0103] Air quality 502 may include air analysis for a particular geographic location(s) based on pulmonary health care information and environmental data captured using one or more environmental sensors deployed in the ambient air of the geographic location(s). Air quality 502 includes an air quality interface 51 that provides air quality monitoring and air pollution for a geographic location(s), such as Beijing, China. 4. The air quality interface 514 may include correlations and effects of various air pollution conditions and pollutants on respiratory illnesses. Air quality factors such as PM2.5, PM10, O3, NO2, SO2, and CO, in addition to weather conditions such as temperature, dew, air pressure, humidity, and wind speed, are employed as inputs captured by environmental sensors to monitor or predict the onset of respiratory problems or generate alerts to suggest staying indoors.

[0078]

[0104] The disease information 504 may be correlated for one or more patients to diagnose a pulmonary condition. The health information 506 may include diagnostic indicators captured by the inhalation device 100 related to the patient's condition. An overview of the incidence of disease conditions may be provided for a particular geographic location(s) to identify any environmental or other causes, as well as to monitor the overall condition of a population. Healthcare information 506 may be used by an individual patient or group of patients to track treatments, diagnoses, conditions, etc. Device information 508 may include information regarding the operation of the inhalation device 100 for troubleshooting, improvement, quality control, etc. Various alerts and / or trends corresponding to the various tabs 502-508 and 512 may be included in the alerts / trends 210 for management of one or more patients, groups, and / or inhalation devices 100.

[0079]

[0105] For example, correlation of real-time reported occurrences of acute exacerbations of COPD with recorded environmental conditions can lead to refined alert levels and, in combination with the effects of prescribed medications and dosage levels on patient recovery and outcomes, provide a better understanding and potential discovery of trends and patterns of the impact of environmental irritants. The use of air analysis and real-time detection and reporting provides a means to rapidly identify improved medication regimens or drug combinations, or to rapidly identify problematic or potentially illegally tampered batches of medication. Air analysis is beneficial for medical and pharmaceutical surveillance for clinical decision making and disease surveillance, which can lead to improved health care, lives saved, and lower costs.

[0080]

[0106] As explained above, the inhalation device 100 is The air analyzer 402 collects and distributes non-meter information. Additional user data may include inhaled air temperature, humidity, ozone and nitrogen dioxide levels, the amount of various gases in the patient's 104 exhaled breath, and even particulate levels in the inhaled air. Once communicated to the air analyzer 402, alerts may be issued to individual users or groups of users based on the real-time environmental and pulmonary health management information.

[0081]

[0107] The air analyzer 402 provides personalized healthcare by providing a means to compare and optimize the effectiveness of individual therapies with larger group results. The air analyzer 402 discovers relationships between prescribed therapies, air pollutants or other environmental conditions. This information can be used to improve healthcare or predict impending deterioration for the user. The combination of individual measurements and real-time support from the air analyzer 402 improves the quality of healthcare delivery while reducing costs, as well as providing insights to make better informed healthcare decisions.

[0082]

[0108] As applied to personalized healthcare, the air analysis generated by the air analyzer 402 alerts the patient 104 based on the patient's own patterns of use of the inhalation device 100 while visiting different environments. For example, a patient who occasionally visits a friend's home where formaldehyde or other harmful vapors are emitted by rugs or building materials may show effects on the patient later in the day, leading to a change in the patient's inhalation device 100 usage and medication dosing patterns. The air analyzer 402 can detect this change in pattern and alert the patient 104 to a new trend of a more frequent medication regimen after spending time in a particular location. The patient 104 is notified of developments and the user is alerted to newly discovered correlations.

[0083]

[0109] The air analyzer 402 can apply air analysis to the inhalation device 100 to sense and detect disease biomarkers in the exhaled breath. Human breath contains several volatile organic compounds (VOCs), the accurate detection of which can give essential information for early diagnosis of diseases in the human or animal body in general. For example, nitric oxide can be used to assess and detect asthma diagnosis, and acetone, ammonia, H2S, and toluene can be used to assess diabetes, kidney failure, halitosis, and lung cancer, respectively.

[0084]

[0110] Relative measurements of lung function taken between doses or at other times can provide useful information to the user or physician. Together with the air analyzer 402, it can be used to instruct the user on when and how to administer a dosage of medication with the help of a healthcare provider. Pulmonary function measurements can be used to instruct the user on when to take action and provide the user with relative lung function information. This education can be done via the air analyzer 402, which shows the user the degree to which lung function has declined in various situations.

[0085]

[0111] One useful diagnostic indicator for airway obstructive disease is called FEV1. , which is the volume of air forcedly expired in one second. Ideally, lung function measurements would be made so that it was independent of the user's muscular effort to breathe, but current medical diagnostic equipment eliminates this variable by using a chamber surrounding the user that varies the pressure surrounding the user to assess airway and alveolar restriction to breathing. Generally, FEV1 is expressed as the volume of air exhaled in one second by a forced expiration following full inspiration. This number is expressed as a percentage of vital capacity.

[0086]

[0112] The availability of FEV1 values ​​measured multiple times per day over multiple days is Analysis can provide the physician with useful diagnostic indicators. In restrictive lung diseases (such as pulmonary fibrosis), the lung capacity is reduced below normal levels, but the rate of exhalation is normal. In obstructive lung diseases (such as asthma, emphysema, bronchitis), the lung tissue is not damaged and its compliance is unchanged, so the lung capacity is normal. In asthma, the small airways (bronchioles) constrict, increasing resistance to airflow. The lung capacity is normal, but the increased airway resistance makes exhalation more difficult and takes longer. Obstructive disorders are diagnosed by tests that measure the rate of forced exhalation, such as FEV1 and FEV25-75; a significant decrease in these values ​​suggests obstructive lung disease.

[0087]

[0113] The pulmonary diagnostic system provided by the air analyzer 402 may be achieved by measuring the flow rate over several breaths by the user using the inhalation device 100 with the same sensor used to time dosing to the optimal period between inhalations. Diagnostic indicators may be derived by comparison of each test to a benchmark pattern or number performed under the supervision of a physician of the patient 104. Comparisons may be performed using a portion of the inhalation cycle or just the peak measured flow rate at each inhalation or exhalation.

[0088]

[0114] To measure FV1, the user is first asked to perform several forced exhalations after a complete inhalation, and the inhalation device 100 measures and records the flow rate. The FEV1 is then calculated by integrating the flow rate over the entire exhalation as well as over one second intervals. These results are stored and communicated later or immediately to the air analyzer 402. If the calculated FEV1 falls below a preset limit, the device will feedback that the airway obstruction is greater than a preset value. The preset value can be determined by a medical professional and provided via the air analyzer 402.

[0089]

[0115] The diagnostic indicators listed above are not necessarily a complete list of all possible diagnoses. For example, alveolar limitation is inferred from the relative difference in inhalation and exhalation flow rates, and a decrease in the inhalation to exhalation ratio may infer more restriction in expanding the alveoli. Integration of flow rates over the entire inhalation and / or exhalation portion of one or more respiratory cycles estimates the total volume of air inhaled. Like FEV1, such values ​​may be measured and recorded multiple times per day.

[0090]

[0116] In addition to peak flow rate and 1 second flow rate, the inhalation device 100 can perform more sophisticated methods of assessing airway resistance and even lung compliance. For example, the effect of airway resistance is modeled using the air analyzer 402 by the formula F=(P1-P2) / R, where airflow F (often called dV / dt) is equal to the pressure in the mouth P1-alveolar pressure P2 divided by the resistance of the air wave R. Since P2 is the pressure in the alveolar sac of the lung, it is difficult to measure it directly. However, by measuring the flow rate at two different values ​​of P1 (pressure in the mouth) for a relatively constant alveolar pressure, airway resistance R can be calculated as follows:

[0091] For oral pressure P1a, flow rate Fa=(P2-P1) / R For oral pressure P1b, flow rate Fb=(P2-P1b) / R

[0117] The flow and pressure in these conditions can be used to directly calculate a value for airway resistance by:

[0092] R = (P1b-P1a) / (Fa-Fb)

[0118] Note that this assumes a relatively quick transition between the two oral pressures, since both airway resistance and alveolar pressure change significantly with changes in lung and airway geometry during the respiratory cycle. With the quick transitions in pressure, the assumption of a nearly constant alveolar pressure between the two pressures is true. There is a limit to how quickly the pressure can be made to vary, since the compliance of the air and flow resistance effectively removes the fluctuations so that a low pass filter minimizes high frequency signals.

[0093]

[0119] The inhalation device 100 may generate the two different oral pressures required by the above formula by various means, such as a rapidly changing pressure source such as a cylinder and piston, or even a long-throw audio speaker. Both of these methods and means require significant volume, weight, and power. Similarly, direct or centrifugal fans may be used. However, the inertial forces generated within these devices may make it difficult to measure the rapid changes in pressure that occur over a single breath.

[0094]

[0120] In one implementation, the air analyzer 402 uses a variable resistance valve between the oral cavity and atmosphere to achieve the small, rapid pressure changes that occur during the breathing cycle. As a non-limiting example, a flapper valve may be used to open and close portions of the airflow path from the atmosphere to the inhaler. This valve may consist of a rotating disk with half of the disk open and half nearly blocked, so that as the disk turns it fully opens or partially closes the air inlet port to the inhaler. Such a disk may be easily spun at 1-10 Hz with a small, relatively low power 60-600 rpm miniature gear motor. When the disk is in the open position C, with flow resistance Rc, the flow rate to the oral cavity is Fc=Pc / Rc.

[0095]

[0121] where Pc is the pressure in the mouth measured against the atmosphere. When the disk is in the restricted flow state D, the flow rate into the mouth is Fd=Pd / Rd. Substituting these two flow and pressure states in the above equation gives the airway resistance, This results in R = (P1c - P1d) / (P1c / Rc - P1d / Rd).

[0096]

[0122] If the inhaler flow restriction from state C to state D is increased by a factor of K=Rd / Rc, the equation for airway resistance reduces to: R=(P1c-P1d) / (P1c / Rc-P1d / KRc) or R=(1 / Rc)*(P1c-P1d) / (P1c-P1d / K).

[0097]

[0123] Therefore, by rapidly varying the flow resistance in the inhalation device 100 , the airway flow resistance can be directly estimated by the air analyzer 402 .

[0124] The air analyzer 402 can generate additional air analysis of lung compliance, and the location of airway resistance can be evaluated by performing the above two-pressure test with different cycle times. In this case, instead of cycling between two different pressures, the flow resistance in the inhalation device 100 is varied as a sinusoid to approximate the linear signal processing assumption.

[0098]

[0125] The patient has significant airway resistance and tolerates the extra airflow resistance from the inhalation device. If this is not possible, a small fan can be used to create additional pressure on the atmospheric side of the variable resistance valve. By stacking fans, additional pressure can be created so that the total pressure is the sum of the pressure gain at each fan.

[0099]

[0126] The air analyzer 402 measures airway resistance for patient diagnostics by comparing the patient's 104 current airway resistance with previous data generated by the device inhalation 100. The comparison data may also be used to evaluate the effectiveness of inhaled medication droplets to improve restricted airways. The inhalation device and / or air analyzer 402 may further track fluctuating pressure sources or flow restrictions, monitoring internal pressure before and after administration of various medications.

[0100]

[0127] Because of the inhalation device 100 and / or user device 204's ability to store, process, and communicate data, the inhalation device 100 may include additional sensors related to diagnosis or alerting the user. For example, a N02 sensor may be added to the device to provide additional diagnostics on airway conditions and flow resistance, and to help both the user and the user's physician understand how the patient 104 is responding to an asthma condition.

[0101]

[0128] 6 illustrates example operations 600 for pulmonary health management for one or more patients. In one implementation, operation 602 receives pulmonary health data from one or more inhalation devices over a network. Operation 604 correlates the pulmonary health data with environmental data using at least one management parameter. Operation 606 generates an air analysis from the correlated data, and operation 608 outputs the air filtering analysis.

[0102]

[0129] Referring to FIG. 7, an electronic device 700 is shown including operational units 702-710 arranged to perform various operations of the techniques of the present disclosure. The operational units 702-710 of the device 700 are implemented by hardware or a combination of hardware and software to execute the principles of the present disclosure. It will be understood by those skilled in the art that the operational units 702-710 described in FIG. 7 can be combined or separated into sub-blocks to implement the principles of the present disclosure. Thus, the description herein supports possible combinations or separations or further definitions of the operational units 702-710.

[0103]

[0130] In one implementation, the electronic device 1700 includes a display unit 702 for displaying information, such as a graphical user interface, a processing unit 704 in communication with the display unit 1702, and an input unit 706 for receiving data from one or more input devices or systems, such as the air analyzer 402, the inhalation device 100, etc. Various operations described herein may be implemented by the processing unit 704 using data received by the input unit 706 to output information for display using the display unit 702.

[0104]

[0131] Further, in one implementation, the electronic device 700 includes a correlation unit 708 and an air analysis generation unit 710. The correlation unit 708 correlates the lung health information with the environmental information, and the air analysis generation unit 710 generates an air analysis using the correlated information.

[0105]

[0132] In another implementation, the electronic device 700 includes units for implementing the operations described with respect to Figure 6. For example, operation 602 may be implemented by the input unit 706, operation 604 may be implemented by the correlation unit 1108, operation 606 may be implemented by the air analysis generating unit 710, and operation 608 may be implemented by the output unit 702.

[0106]

[0133] 8, a detailed description of an exemplary computing system 800 having one or more computing units that may implement the various systems and methods described herein is provided. The computing system 800 may be applicable to the air analyzer 402, the controller 222, the server 408, the inhalation device 100, and other computing or network devices. It will be appreciated that the specific implementations of these devices may be of different possible specific computing architectures, not all of which are described in detail herein, but which will be understood by those skilled in the art.

[0107]

[0134] Computer system 800 may be a computing system capable of executing a computer program product to execute a computer process. Data and program files may be input to computer system 800, which reads the files and executes the programs therein. Some of the elements of computer system 800 are shown in FIG. 8, including one or more hardware processors 802, one or more data storage devices 804, one or more memory devices 808, and / or one or more ports 1808-1810. Additionally, other elements that will be recognized by those skilled in the art may be included in computing system 800, but are not explicitly shown in FIG. 8 or further described herein. The various elements of computer system 800 may communicate with each other via one or more communication buses, point-to-point communication paths, or other communication means not explicitly shown in FIG. 8.

[0108]

[0135] The processor 802 may include, for example, a central processing unit (CPU), a microprocessor, a microcontroller, a digital signal processor (DSP), and / or one or more internal level caches. There may be one or more processors 802, and thus the processor 1202 comprises a single central processing unit or multiple processing units capable of executing instructions and performing operations in parallel with each other, commonly referred to as a parallel processing environment.

[0109]

[0136] The computer system 800 may be a conventional computer, a distributed computer, or other types of computers, such as one or more external computers made available via a cloud computing architecture. The techniques described herein are optionally implemented in software stored on data storage device(s) 804, stored on memory device(s) 806, and / or communicated via one or more of ports 808-810, thereby turning the computer system 1200 of FIG. 8 into a dedicated machine for implementing the operations described herein. Examples of computer system 800 include personal computers, terminals, workstations, mobile phones, tablets, laptops, personal computers, multimedia consoles, gaming consoles, set-top boxes, etc.

[0110]

[0137] The one or more data storage devices 804 may include any non-volatile data storage device capable of storing data generated or employed within the computing system 800, such as computer-executable instructions for implementing computer processes, which may include instructions for both application programs and an operating system (OS) that manages the various components of the computing system 800. The data storage devices 804 may include, but are not limited to, magnetic disk drives, optical disk drives, solid-state drives (SSDs), flash drives, and the like. The data storage devices 1804 may include removable data storage media, non-removable data storage media, and / or external storage devices made available via a wired or wireless network architecture with such computer program products, including one or more database management products, web server products, application server products, and / or other additional software components. Examples of removable data storage media include compact disc read only memory (CD-ROM), digital versatile disc read only memory (DVD-ROM), magneto-optical disks, flash drives, and the like. Examples of non-removable data storage media include internal magnetic hard disks, SSDs, and the like. The one or more memory devices 1206 may include volatile memory (e.g., dynamic random access memory (DRAM), static random access memory (SRAM), etc.) and / or non-volatile memory (e.g., read only memory (ROM), flash memory, etc.).

[0111]

[0138] A computer program product including mechanisms for implementing systems and methods according to the techniques described herein may reside in data storage device 804 and / or memory device 806, which may be referred to as a machine-readable medium. It will be appreciated that a machine-readable medium may include any tangible, non-transitory medium capable of storing or encoding instructions for performing any one or more of the operations of the present disclosure for execution by a machine, or capable of storing or encoding data structures and / or modules utilized by or associated with such instructions. A machine-readable medium may include a single medium or multiple media (e.g., a centralized or distributed database, and / or associated caches and servers) that store one or more executable instructions or data structures.

[0112]

[0139] In some implementations, computer system 800 includes one or more ports, such as input / output (I / O) port 1808 and communication port 810, for communicating with other computing, network, or vehicle devices. It will be appreciated that ports 808-810 may be combined or separate and that more or fewer ports may be included in computer system 1200.

[0113]

[0140] I / O ports 808 may be connected to I / O devices or other devices by which information is input to or output from computing system 800. Such I / O devices may include, but are not limited to, one or more input devices, output devices, and / or environmental transducer devices.

[0114]

[0141] In one implementation, an input device converts human-generated signals, such as human voice, physical movement, physical touch or pressure, into electrical signals as input data to the computing system 800 via the I / O port 808. Similarly, an output device may convert electrical signals received from the computing system 800 via the I / O port 808 into signals that can be sensed by a human as output, such as sound, light, and / or touch. An input device may be an alphanumeric input device, including alphanumeric and other keys for communicating information and / or command selections to the processor 802 via the I / O port 808. An input device may be another type of user input device, including, but not limited to, a direction and selection control device, such as a mouse, a trackball, cursor direction keys, a joystick, and / or a wheel, one or more sensors, such as a camera, a microphone, a position sensor, an orientation sensor, a gravity sensor, an inertial sensor, and / or an accelerometer, and / or a touch-sensitive display screen ("touch screen"). An output device may include, but is not limited to, a display, a touch screen, a speaker, a tactile and / or haptic output device, and / or the like. In some implementations, the input device and the output device may be the same device, for example, in the case of a touch screen.

[0115]

[0142] An environmental transducer device converts one form of energy or signal into another for input to or output from the computing system 800 via the I / O ports 808. For example, an electrical signal generated within the computing system 800 may be converted to another type of signal and / or vice versa. In one implementation, the environmental transducer device senses properties or aspects of the environment that are local to or remote from the computing device 800, such as light, sound, temperature, pressure, magnetic fields, electric fields, chemistry, physical movement, orientation, acceleration, gravity, etc. Additionally, the environmental transducer device may generate a signal to impose some effect on the environment that is either local to or remote from the exemplary computing device 800, such as the physical movement of some object (e.g., a mechanical actuator), heating or cooling a substance, adding a chemical, etc.

[0116]

[0143] In one implementation, the communication port 810 is connected to a network over which the computer system 1800 may receive network data useful in executing the methods and systems presented herein and in transmitting information and network configuration changes determined thereby. In other words, the communication port 810 connects the computer system 800 to one or more communication interface devices configured to transmit and / or receive information between the computing system 800 and other devices over one or more wired or wireless communication networks or connections. Examples of such networks or connections include, but are not limited to, Universal Serial Bus (USB), Ethernet, Wi-Fi, Bluetooth, Near Field Communication (NFC), Long Term Evolution (LTE), etc. One or more such communication interface devices may be utilized via communication port 1210 to communicate with one or more other machines, either directly, via a point-to-point communication path, via a wide area network (WAN) (e.g., the Internet), via a local area network (LAN), via a cellular (e.g., third generation (3G) or fourth generation (4G)) network, or via another communication means. Additionally, communication port 810 may be in communication with an antenna or other link for electromagnetic signal transmission and / or reception.

[0117]

[0144] In one exemplary implementation, the pulmonary health care data, air analysis, and software and other modules and services may be embodied by instructions stored on the data storage device 804 and / or memory device 806 and executed by the processor 802. The computer system 800 may be integrated with or otherwise form a part of the inhalation device 100.

[0118]

[0145] 8 is only one possible example of a computer system that may be employed or configured in accordance with aspects of the present disclosure. It will be appreciated that other non-transitory, tangible, computer-readable storage media that store computer-executable instructions may be utilized to implement the techniques of the present disclosure on a computing system.

[0119]

[0146] 9A-16K provide specific examples of various embodiments of the inhalation device 100. FIG. The description of these aspects is by way of example only and is not limiting.

[0147] Referring to Figures 9A-9C, in one implementation, the inhalation device 100 includes a handle 900, a housing 902 surrounding a mouthpiece 904, a cartridge mount 906 for receiving a disposable or reusable cartridge 908, a laminar flow element 910, and an opening 912 defined by the mouthpiece 904.

[0120]

[0148] 10 and 11 show cross-sectional and exploded views, respectively, of the inhalation device 100 shown in FIGS. 9A-9C. In one implementation, the inhalation device 100 includes a pressure sensor assembly 914, a pressure sensor electronics board 916, a superhydrophobic valve 918, a piezoelectric actuator 920, an aperture plate 922, a light source electronics board 924, one or more light sources 926 (e.g., LEDs), an aerosol tube 928 in communication with the mouthpiece 904, a power source 930, a power contact 932, a pressure sensor O-ring 934, a power mount 936, a removable handle cover 938, a controller 940, a manual dose button 942, a speaker 946, an audio chip 948, and a user device link 950. These components may be used to perform one or more of the operations described herein.

[0121]

[0149] 12A-12C, the cartridge 908 can include a guide 954 and a cartridge tag 952. The ejector assembly of the cartridge 908 can include a surface tension plate 956, an actuator 920, an ejector O-ring 960, and an aperture plate 922 that can have droplet forming apertures 958. As shown in FIG. 13, the droplet forming apertures 958 can be multiple sizes (e.g., 962 and 964) to generate different droplet sizes to target specific regions of the pulmonary airways.

[0122]

[0150] 14A-15C show various configurations of the pressure sensor assembly 914. FIG. In one implementation shown in FIG. 14A, the pressure sensor assembly 914 includes a first pressure sensor 1000 and a second pressure sensor 1002 to sense airflow by detecting a pressure difference across an airflow restriction inside the aerosol tube 928. FIG. 14B shows a pressure sensor assembly 914 with one pressure sensor 1002, where the restriction is a laminar flow screen 910, and the pressure is sensed as a difference between the pressure inside the tube 928 and outside the tube 928. The first pressure sensor 1000 and the second pressure sensor 1002 can be used for nebulization verification by detecting a pressure difference between the interior and exterior areas of the aerosol tube 928 as the airflow moves from the inlet 1004 to the output 1006. The pressure sensor assembly 914 can further coordinate a breathing cycle for the patient 104 to identify trigger points for activating nebulization during peak periods during the inhalation cycle.

[0123]

[0151] FIG. 14A shows a pressure sensor assembly 914 with one pressure sensor 1000 sensing the pressure inside the tube 928 and a second sensor 1002 sensing the atmospheric pressure outside the tube. This configuration allows for extremely low airflow internal resistance. Extremely low internal resistance for a droplet delivery device has great benefits. The device 100 is breath-actuated to nebulize and deliver the drug in the form of an aerosol, and the extremely low internal resistance to airflow gives the patient the opportunity for deep inhalation, thus allowing the aerosol particles to reach deep into the lung airways. The breath-actuated triggering mechanism for delivering the aerosol dosage further provides assurance for optimal delivery of the drug.

[0124]

[0152] 15A-15C show an example of a delta P sensor assembly 1100 of a pressure sensor assembly 914 having sensor electronics 916, a printed circuit board (PCB) 1102, a pressure sensor controller 1104, a sensor die 1108, a glob-top 1106, and holes 110. The assembly 1100 may further include a motherboard 1112 and an O-ring 1114. This example includes a one-port design and its assembly (15A) to a device board, with the sensor mounted on a main PCB or daughter board with an air connection through a hole in the PCB as shown in the manner in (FIG. 15B) or (FIG. 15C).

[0125]

[0153] Delta P sensor specifications may be, by way of example and not limitation, as follows: Pressure range; + / -500Pa range; Delta P measurement relative to ambient Absolute accuracy; 3% or better Repeatability: 3% or better FS resolution: 1% or better Digital or analog output; digital is preferred; I 2 C or SPI Power supply voltage: 3VDC+ / -5% offset, auto zero; after it is turned on; Storage temperature: -20~+60C; Operating temperature: 10~45C;

[0154] The sensor assembly 914 may be superior to conventional piezoresistive film sensors in terms of sensitivity, offset drift, and hysteresis at low differential pressures. These performance parameters allow for increased resolution and more accurate measurements at low pressures. These performance parameters are particularly important for children and elderly patients with low pulmonary output.

[0126]

[0155] In one implementation, the signal generated by the pressure sensor provides a trigger for activation of the nebulizer at or during the peak period of the patient's 104 inhalation (inhalation) cycle, as described herein, to ensure optimal deposition of the aerosol spray and delivery of the drug to the pulmonary airways.

[0127]

[0156] Additionally, image capture devices including, but not limited to, cameras, scanners, or other sensors, such as charge-coupled devices (CCDs), may be provided to detect and measure the emitted aerosol plume. These detectors, LEDs, delta P transducers, CCD devices all provide control signals to the controller 940, which may be communicated to the user device 204 via link 950, to monitor, sense, measure and control the release of fluid, as well as to report patient compliance, treatment time, dosage, and patient usage history, etc.

[0128]

[0157] 16A-16K, various exemplary circuit diagrams 1200-1220 are provided, by way of example only and not by way of limitation. The circuit diagrams include a power on / off circuit 1200, a power connector circuit 1202, a voltage power conditioning circuit 1204, a controller circuit 1206, a controller programming connector circuit 1208, a piezoelectric connector circuit 1210, a user switch with debounce circuit 1212, a piezoelectric driver circuit 1214, a pressure sensor circuit 1216, a light emitting diode indicator circuit 1218, and a buzzer driver circuit 1220. Variations to these circuits, as well as the addition of circuits, deletion of circuits, or other modifications to the circuits are contemplated.

[0129]

[0158] In this disclosure, the disclosed methods may be implemented as a set of instructions or device-readable software. Additionally, it is understood that the specific order or hierarchy of steps in the disclosed methods are examples of example approaches. Based on design preferences, it is understood that the specific order or hierarchy of steps in the methods may be rearranged while remaining within the disclosed subject matter. The accompanying method claims present elements of the various steps in an example order, and are not necessarily limited to the specific order or hierarchy presented.

[0130]

[0159] The described disclosure may be provided as a computer program product or software, which may include a non-transitory machine-readable medium having stored thereon instructions that may be used to program a computer system (or other electronic device) to perform a process according to the present disclosure. A machine-readable medium includes any mechanism for storing information in a form (e.g., software, processing application) readable by a machine (e.g., a computer). A machine-readable storage medium may include, but is not limited to, a magnetic storage medium, an optical storage medium, a magneto-optical storage medium, a read-only memory (ROM), a random access memory (RAM), an erasable programmable memory (e.g., EPROM and EEPROM), a flash memory, or other types of media suitable for storing electronic instructions.

[0131]

[0160] Although the present disclosure has been described with reference to various implementations, it will be understood that these implementations are exemplary and that the scope of the disclosure is not limited thereto. Many variations, modifications, additions, and improvements are possible. More generally, embodiments according to the present disclosure have been described in the context of specific implementations. Functions may be separated or combined in blocks differently or described using different terms in various embodiments of the present disclosure. These and other variations, modifications, additions, and improvements may fall within the scope of the present disclosure, as defined by the following claims.

Claims

1. 1. A system for monitoring the pulmonary health of a patient, comprising: one or more electronic inhalation devices for coordinating the capture of pulmonary health care data, each of said electronic inhalation devices comprising an inhalation tube, one or more airflow sensors, a memory, and a microprocessor; measuring and storing in memory a peak inspiratory flow achieved during inhalation by the patient, said measurement of peak inspiratory flow being generated based on a minimum pressure of airflow during inhalation; measuring and storing in memory a pulmonary output for the patient, the pulmonary output being determined by measuring a maximum flow achieved during exhalation; detecting and storing in memory the geographic location of said electronic inhalation device when in use, the time of day when in use, and any administered medication and dosage; an electronic inhalation device configured to 1. An air analyzer communicatively coupled to the electronic inhalation device, the air analyzer comprising at least one computing unit, the at least one computing unit comprising: generating a pulmonary health profile for the patient based at least in part on the measurements of peak inspiratory flow and the pulmonary output received from the electronic inhalation device; storing in a memory a pulmonary health profile, a geographic location, and a time of use of said electronic inhalation device; repeating the step of storing the pulmonary health profile, the geographic location, and the time of use of the electronic inhalation device a plurality of times at different times of day and at different geographic locations during use of the electronic inhalation device to obtain a set of disease condition occurrence events at different times of day and at different geographic locations; 1) determining, based on a set of occurrences of a disease condition, that the geographic location and the time of day when using the electronic inhalation device correspond to the time of day and the geographic location having a high occurrence of a disease condition; 2) the pulmonary health profile for the patient indicates an undesirable pulmonary health outcome; Generates a warning when the following two conditions are met: It is configured as follows: An air analyzer; a user device communicatively coupled to the air analyzer and comprising a display, the display configured to display an output of the pulmonary health profile received from the air analyzer and any warnings of a non-desired predicted geographic location or time of day; A system comprising:

2. The electronic inhalation device comprises: and further comprising one or more sensors for detecting a biomarker of patient health in the exhaled airflow; the at least one computing unit of the air analyzer is further configured to generate the lung health profile based on concentration values ​​of the biomarkers of subject health in the exhaled airflow; The biomarkers of patient health include nitric oxide, acetone, ammonia, H ２ S, or toluene; The system of claim 1 .

3. The system of claim 1 , wherein the at least one computing unit of the air analyzer is further configured to track changes in the patient's lung health profile over time.

4. The system of claim 1 , wherein the pulmonary health profile includes at least one of diagnostic data for a pulmonary condition or treatment data for a pulmonary condition.

5. the electronic inhalation device further comprising one or more environmental sensors configured to measure environmental data relating to one or more environmental conditions from one or more geographic locations within which the electronic inhalation device is disposed; the at least one computing unit of the air analyzer is further configured to associate the lung health profile with the environmental data. The system of claim 1 .

6. the one or more air flow sensors of the electronic inhalation device include a first sensor located near an air input port of the inhalation conduit in use and a second sensor located outside the air flow of the inhalation conduit in use; In use, the first sensor measures internal pressure and the second sensor measures ambient atmospheric pressure outside the intake pipe. The system of claim 1 .

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