阅读说明：本技术 智能带阀保持室 (Intelligent holding chamber with valve ) 是由 纳维坦·阿利佐蒂 史蒂芬·科斯特拉 丹·恩格尔布雷特 诺埃尔·古尔卡 阿兰娜·柯克纳 亚当 于 2017-05-19 设计创作，主要内容包括：一种药物输送系统,具有保持室,其能自定量吸入器输送药物剂量。保持室包括启动器检测器,流检测器和/或用于识别与保持室连接的定量吸入器的定量吸入器识别器,以及显示器。在另一实施例中,用于管理药物的用户界面包括药物输送装置,具有密封部和响应于与用户的接触的接触传感器的面罩部,以及与传感器通信以提供反馈的指示器。在另一实施例中,药物输送装置包括定义流通道的壳体和设置于流通道中且响应于流而在第一配置和第二配置之间可移动的阀,其中阀包括电活性聚合物,并响应于电刺激,在第一阻力条件和第二阻力条件之间是可重新配置的。(A drug delivery system has a holding chamber that is capable of delivering a dose of drug from a metered dose inhaler. The holding chamber comprises an initiator detector, a flow detector and/or a metered-dose inhaler identifier for identifying a metered-dose inhaler connected to the holding chamber, and a display. In another embodiment, a user interface for managing medication includes a medication delivery device, a mask portion having a sealing portion and a contact sensor responsive to contact with a user, and an indicator in communication with the sensor to provide feedback. In another embodiment, a drug delivery device includes a housing defining a flow channel and a valve disposed in the flow channel and movable between a first configuration and a second configuration in response to flow, wherein the valve includes an electroactive polymer and is reconfigurable between a first resistance condition and a second resistance condition in response to an electrical stimulus.)

1. A drug delivery system, comprising:

a holding chamber having an input end and an output end, the holding chamber comprising:

an actuation detector for detecting actuation of a metered-dose inhaler associated with the holding chamber;

a flow detector for detecting an inhalation flow through the holding chamber; and

and the feedback device is used for providing the delivery information for the user.

2. The drug delivery system of claim 1, further comprising:

a metered-dose inhaler identifier for identifying the type of metered-dose inhaler associated with the holding compartment.

3. The drug delivery system of claim 1, further comprising: an inhalation signal for signaling to a user that inhalation may be initiated.

4. The drug delivery system of claim 1, further comprising:

a timer, located between the start detector and the inhalation signal, for initializing the inhalation signal.

5. The drug delivery system of claim 1, further comprising:

a timer located between the start detector and the flow detector.

6. The drug delivery system of claim 1, further comprising a timer for measuring a breath hold duration of a user.

7. The drug delivery system of claim 1, wherein the holding chamber comprises an end piece releasably connected to the input end, wherein the end piece comprises the feedback device.

8. The drug delivery system of claim 1, wherein the holding chamber comprises a cannula releasably connected to a body portion of the holding chamber, wherein the cannula comprises the feedback device.

9. The drug delivery system of claim 1, wherein the holding chamber comprises:

a metered-dose inhaler insertion detector for detecting insertion of the metered-dose inhaler in the input end of the holding chamber.

10. The drug delivery system of claim 1, further comprising:

a breath hold detector for determining a duration of a breath hold of a user.

11. The drug delivery system of claim 10, wherein the breath hold detector comprises one or more of a carbon dioxide detector, a pressure sensor, a microphone, a humidity sensor, a temperature sensor, and/or a light curtain.

12. The drug delivery system of claim 1, further comprising:

an end-of-treatment detector for detecting an end of treatment of the user.

13. The drug delivery system of claim 1, further comprising a feedback device that exceeds maximum flow.

14. A drug delivery system, comprising:

a holding chamber having an input end and an output end;

a metered dose inhaler operably connected to the input end of the holding chamber; and

a metered-dose inhaler identifier associated with the holding compartment for identifying the metered-dose inhaler connected to the holding compartment.

15. The drug delivery system of claim 14, wherein the metered-dose inhaler identifier comprises a color sensing means for collecting color information from the metered-dose inhaler and/or an aerosol plume emitted by the metered-dose inhaler.

16. The drug delivery system of claim 14, wherein the metered-dose inhaler identifier comprises a mouth detection device for collecting information about the shape or length of the mouth of the metered-dose inhaler.

17. The drug delivery system of claim 14, wherein the metered dose inhaler identifier comprises an image processor and/or an RFID reader and the metered dose inhaler comprises a label.

18. The drug delivery system of claim 14, wherein the metered-dose inhaler identifier analyzes one or more of sound, temperature, color, infrared and/or ultraviolet spectrum, capacitance, and/or flow of an aerosol plume emitted from the metered-dose inhaler.

19. The drug delivery system of claim 14, wherein the metered dose inhaler identifier comprises: a force sensitive resistor for recording force upon actuation of the MDI.

20. The drug delivery system of claim 14, wherein the metered dose inhaler identifier comprises an infrared emitter and detector.

21. A drug delivery system, comprising:

a drug delivery device having an input end and an output end;

a mask connected to the output end, wherein the mask is movable along a longitudinal axis to a position engaging a user's face and configured to form a seal between the mask and the user's face;

a force sensor disposed between the face mask and the input of the drug delivery device, wherein the force sensor is responsive to a force applied to the face mask by the drug delivery device along a longitudinal axis; and

an indicator providing feedback to a user or caregiver regarding the amount of contact between the user's face and the mask and/or the amount of force applied to the mask by the drug delivery device.

22. The drug delivery system of claim 21, wherein the drug delivery device comprises a body portion defining the input end and a valve assembly connected to the body portion and defining the output end, wherein the face mask is connected to the valve assembly.

23. The drug delivery system of claim 22, wherein a sensor is disposed between the mask and the valve assembly.

24. The drug delivery system of claim 22, wherein the force sensor is disposed between the valve assembly and the body portion.

25. The drug delivery system of claim 21, wherein the mask comprises a contact sensor configured to sense engagement of the mask with the face of the user.

26. The drug delivery system of claim 25, wherein the contact sensors are coupled to a seal portion of the mask and are distributed around a perimeter of the mask.

27. The drug delivery system of claim 26, wherein the contact sensor comprises a plurality of spaced-apart contact sensors positioned around the perimeter of the mask.

28. The drug delivery system of claim 27, wherein the indicator comprises a plurality of indicators respectively associated with the plurality of contact sensors.

29. The drug delivery system of claim 28, wherein the plurality of indicators comprises a plurality of lights.

30. The drug delivery system of claim 26, wherein the contact sensor comprises a continuous strip extending around a seal of the mask.

31. The drug delivery system of claim 25, wherein the contact sensor monitors, senses and signals proper contact with the face of the user.

32. The drug delivery system of claim 21, wherein the indicator comprises a visual indicator.

33. The drug delivery system of claim 21, wherein the indicator comprises an audible indicator.

34. The drug delivery system of claim 21, wherein the indicator comprises a vibratory indicator.

35. The drug delivery system of claim 21, further comprising a controller for analyzing the output of the force sensor and estimating the quality of the seal.

36. The drug delivery system of claim 21, wherein the drug delivery device comprises one of a valved holding chamber, a nebulizer, or an oscillating positive expiratory pressure device.

37. The drug delivery system of claim 21, wherein the indicator provides feedback to the user or caregiver as to the desired seal when the force applied to the mask is between 1.5 pounds and 7 pounds.

38. The drug delivery system of claim 21, wherein the indicator is disposed on the drug delivery device.

39. A drug delivery system, comprising:

a drug delivery device having an input end and an output end;

a mask connected to the output end, wherein the mask is movable along a longitudinal axis to a position engaging a user's face and configured to form a seal between the mask and the user's face;

a force sensor disposed between the face mask and the input of the drug delivery device, wherein the force sensor is responsive to a force applied to the face mask by the drug delivery device along a longitudinal axis;

a contact sensor configured to sense engagement of the mask with the user's face; and the number of the first and second groups,

an indicator providing feedback to the user or caregiver regarding the amount of contact made between the user's face and the mask and/or the amount of force applied to the mask by the drug delivery device.

40. The drug delivery system of claim 39, wherein the drug delivery device comprises a body portion defining the input end and a valve assembly connected to the body portion and defining the output end, wherein the face mask is connected to the valve assembly.

41. The drug delivery system of claim 40, wherein a sensor is disposed between the mask and the valve assembly.

42. The drug delivery system of claim 40, wherein the force sensor is disposed between the valve assembly and the body portion.

43. The drug delivery system of claim 39, wherein the contact sensors are coupled to a seal portion of the mask and are distributed around a perimeter of the mask.

44. The drug delivery system of claim 39, wherein the indicator is disposed on the mask.

45. The drug delivery system of claim 39, wherein the indicator is disposed on the drug delivery device.

Technical Field

The present application relates to devices and systems used in the art of delivering pulmonary aerosols (aerosol) via Valved Holding Chambers (VHC) and Metered Dose Inhalers (MDI), and in particular to devices and systems for improving patient compliance with their medication regimen and providing feedback to the user, prescriber or payer regarding proper inhalation techniques and end of treatment.

Background

The VHC system and MDI system are commonly used to treat conditions such as asthma, Chronic Obstructive Pulmonary Disease (COPD) and cystic fibrosis. Patients experiencing these conditions may exhibit compliance with a medication or treatment regimen, use inadequate device dexterity, and/or fail to receive feedback of dose assurance. These types of problems may place additional cost burdens on the medical system, as well as less than optimal therapeutic results.

The regulatory nature of medication administration is often difficult to monitor, although this information is invaluable to medical and insurance personnel. Currently, there is no method of actively monitoring VHC usage by patients, and despite the recent advent of smart inhalers, most MDIs are still unable to autonomously monitor and communicate drug usage. Accordingly, there is a need to provide a VHC that can monitor drug usage and provide feedback to users, medical providers, and insurance personnel.

Disclosure of Invention

Upon inserting the MDI into the VHC, the system identifies the MDI inserted into the VHC. When the user performs practice breathing, the system monitors the flow rate and provides feedback to the user regarding his technique, including whether the user breathes too fast, or whether their breath hold is sufficient. During this exercise phase, the system can notify the user of the most appropriate time in his breathing cycle to activate the MDI.

Once the MDI is started, the system detects and records the start and the duration between the start and the first inhalation flow. This information is used to provide coordinated feedback after the current treatment and/or at the beginning of a subsequent treatment. At the end of the inhalation, a second timer measuring the duration of the breath-hold of the user may be started. This information can be used to provide further feedback before the next breath hold or before the next treatment.

After the MDI is activated, the system can determine when the user has received their full dose of medication. This can be done by measuring the flow rate and integrating the total volume delivered or by other means. At the end of the treatment, the user is notified and the system defaults to waiting for a second start of the MDI. If too much time passes without startup, the system will shut down. Additionally, in one embodiment, if the user removes the MDI, the program will terminate.

Different methods may be used to relay information and provide feedback to the user. LEDs, LED panels, 7-segment displays, LCD screens and/or OLED screens may be used to provide visual feedback. Auditory feedback with the option of the user deciding to mute at his or her discretion may also be used. Tactile feedback may also be used, for example, VHC vibrating when pulling excessive flow rates. The information may be displayed on a display screen, mobile device, remote computer, or other user interface using, for example, an app or website.

Different systems and devices improve patient compliance, improve device technology and provide dose assurance. These aspects, in turn, help reduce the cost of the medical system and provider (payer) by ensuring proper compliance. Furthermore, healthcare providers (prescribers) with reliable information about compliance and use can rely on patient specific data to make informed decisions about treatment regimens and changes. In turn, the patient receives the greatest benefit from treatment while also reducing self-payment costs.

The preceding paragraphs have been provided as a general introduction and are not intended to limit the scope of the claims below. The various preferred embodiments, together with further advantages, will be best understood by reference to the following detailed description taken in conjunction with the accompanying drawings.

Drawings

The figures illustrate various embodiments of drug delivery systems, their structural schematics/flow diagrams, methods of use, and their components.

Figure 1 is a flow diagram illustrating a feedback loop of patient compliance, treatment regimen and payer interaction.

FIG. 2 is a flow chart illustrating the use of an intelligent VHC device and a feedback loop.

FIG. 3 is a side view of an embodiment of an intelligent VHC.

FIG. 4 is a side view of another embodiment of an intelligent VHC.

Fig. 5A and 5B show a real image and a grayscale image of a medicine container.

Fig. 6 is an image showing the proper identification of the medication container shown in fig. 5A.

FIG. 7 is a side view of various alternative embodiments of the intelligent VHC.

FIG. 8 is a graph showing photodetector output versus time for MDI start-up (actuation).

FIG. 9 is a side view of another embodiment of an intelligent VHC.

FIG. 10 is a graph of output versus flow rate for different MDI specifications.

FIG. 11 is a schematic illustration of the different inputs/outputs involved in the use of an MDI.

FIG. 12 is a flow chart showing MDI usage and a feedback loop.

FIG. 13 is a side view of another embodiment of an intelligent VHC.

FIG. 14 is an end view of another embodiment of an intelligent VHC.

Fig. 15 is a graph showing the correlation between the valve opening and the flow rate.

FIG. 16 is a schematic diagram showing various controller inputs.

FIG. 17 is a flow chart showing MDI usage and a feedback loop.

FIG. 18 is a side view of another embodiment of an intelligent VHC.

FIG. 19 is a partial side view of another embodiment of an intelligent VHC.

FIG. 20 is MDI activated pressure sensor output versus time.

FIG. 21 is a graph showing pressure change versus time during MDI priming and inhalation.

FIG. 22 is a schematic diagram showing various controller inputs.

FIG. 23 is a flow chart showing MDI usage and a feedback loop.

FIG. 24 is a side view of another embodiment of an intelligent VHC.

Fig. 25 is a schematic diagram illustrating the recognition of an MDI by voice.

FIG. 26 is a graph showing amplitude versus time at different flow rates.

FIG. 27 is a schematic diagram showing various controller inputs.

FIG. 28 is a flow chart showing MDI usage and a feedback loop.

Fig. 29 is a schematic view of a drug delivery system using an embodiment.

Fig. 30 is a perspective view of an alternative embodiment of a mask configured with a contact sensor.

Fig. 31 is a schematic view of a mask and an enlarged cross-sectional view of a portion of the mask sealing rim.

Fig. 32 is a schematic diagram showing input and output of the controller.

Fig. 33 is a flow chart showing mask use.

FIG. 34 is a flow chart illustrating the use of a movable valve.

FIG. 35 is a cross-sectional view of an embodiment of a movable valve disposed in a flow channel of a drug delivery system.

FIG. 36 is an end view of an embodiment of the valve shown in FIG. 35.

FIG. 37 is a graph showing flow versus time for inhalation and exhalation cycles with and without an active valve.

FIG. 38 is a side view of an alternative embodiment of the intelligent VHC.

FIG. 39 is a plot of minimum plume temperature as a function of thermocouple for different MDI products.

FIG. 40 is a side view, partially in section, of an MDI applied to an embodiment VHC.

FIG. 41 is a side view, partially in section, of an MDI applied to another embodiment VHC.

FIG. 42 is an exemplary MDI initiated force versus displacement.

FIG. 43 is an end view of an embodiment of a back end component (backing) of a VHC.

FIG. 44 is a side view of the rear end assembly shown in FIG. 43.

FIGS. 45A and 45B are partial cross-sectional side views of an MDI located in an actuated position and an unactuated position relative to the intelligent VHC.

FIG. 46 is a partial cross-sectional view of one embodiment of a smart MDI.

FIG. 47 is a partial cross-sectional view of one embodiment of a smart MDI.

FIG. 48 is a partial cross-sectional view of one embodiment of a smart MDI.

FIG. 49 is a side view of an embodiment of a smart MDI.

FIG. 50 is a schematic diagram of a partial enlargement of the smart MDI shown in FIG. 49

FIGS. 51A-51C are different side views of an alternative VHC embodiment.

FIG. 52 is a side view, partially in section, of an embodiment of a VHC.

FIG. 53 is a side view, partially in section, of an embodiment of a VHC.

FIG. 54 is a partial cross-sectional side view of an embodiment of a VHC.

FIG. 55 is a graph of pressure versus flow for different MDI devices.

FIG. 56 is a side view of an embodiment of a VHC.

FIG. 57 is an enlarged partial side view of the VHC depicted in FIG. 56.

FIG. 58 is a side view of an embodiment of a VHC.

Figures 59A-59C are different views of a duckbill valve having a vibrating beam.

FIG. 60 is a side view, partially in section, of an embodiment of a flow rate sensor assembly.

FIG. 61 is a side view, partially in section, of an embodiment of a flow rate sensor assembly.

FIG. 62 is a side view, partially in section, of an embodiment of a flow rate sensor assembly.

FIG. 63 is a side view of an embodiment of a VHC.

FIG. 64 is a side view of another embodiment of a VHC.

FIG. 65 is a side view of another embodiment of a VHC.

FIGS. 66A-66C are different graphical displays with user indicia.

FIG. 67 is a schematic diagram illustrating communication between an intelligent VHC and a user interface.

FIG. 68 is a side view, partially in section, showing an MDI inserted into a VHC.

FIG. 69 is a side view, partially in section, of a VHC in a partially inserted position and a fully inserted position.

FIG. 70 is an end view of an embodiment of a VHC.

FIG. 71 is an end view of another embodiment of a VHC.

FIG. 72 is an end view of another embodiment of a VHC.

FIG. 73 is an end view of another embodiment of a VHC.

FIG. 74 is an end view of another embodiment of a VHC.

FIG. 75 is an MDI configured with conductive materials for closing an electrical loop in the VHC.

FIG. 76 is a side view of an MDI and VHC.

FIG. 77 is a view of a display of an MDI or VHC.

FIG. 78 is a side view of an embodiment of an intelligent VHC.

FIG. 79 is a perspective view of a valved holding chamber with an adapter having a display.

Fig. 80 is a perspective view of the adapter shown in fig. 79.

FIG. 81 is a perspective view of a valved holding chamber with a display in a back end assembly.

FIG. 82 is a perspective view of the rear end assembly shown in FIG. 81.

Fig. 83 is a schematic diagram showing a computer structure.

Fig. 84 is a schematic configuration diagram of a communication system.

FIG. 85 is a flow chart illustrating a method of use of an intelligent VHC and an MDI.

FIG. 86 is a diagram of an intelligent VHC and an MDI.

FIG. 87 is a side view of an embodiment of a movable valve.

Detailed Description

It should be understood that the term "plurality" herein means two or more. The term "coupled" means directly or indirectly connected, snapped in, or the like, e.g., connected to a mating component, and while may represent a permanent fixture or connection (or built-in), it does not necessarily represent a permanent connection, and may represent a mechanical or electrical connection. The terms "first", "second", etc. do not denote any particular elements, but rather denote the elements in a different numerical order, i.e., an element designated as "first" may instead be described as "second" in the following description, depending on the order in which they are described. It should be understood that "first" and "second" also do not mean that two elements or values are different, that is, the first element and the second element may be the same element but are given different names to distinguish the elements.

In the traditional patient/prescriber/payer model, the patient is prescribed a treatment and purchases the medication and/or treatment device. If the purchase is paid by the payer, there is typically no feedback to the payer whether the treatment was performed normally and as prescribed, except for subsequent requests for further treatment. Patients are often trained by prescribers on how to use medical devices and are complained of using the devices in daily life. At some point, the patient may track the prescription because of a change in status, prescription replenishment, or according to a set frequency. At this point, the prescriber needs to evaluate the effectiveness of the treatment and decide whether to modify or continue the treatment. If the prescriber decides to modify the treatment, a new prescription is given and the cycle repeats. Some of the technical challenges faced in improving compliance with treatment regimens, which in turn may increase tracking and diagnostic costs, include the challenges of effectively monitoring the functionality of the different treatment devices and the use of the devices, how to improve effective real-time feedback to the user and/or prescriber, and how to make real-time changes to the performance of the apparatus and/or the user's behavior/skills in some cases.

As shown in fig. 1 and 2, different intelligent devices and their associated feedback may be introduced to improve the effectiveness of the treatment regimen. In addition, patient-related data is provided to the prescriber for making informed decisions about treatment, including modification of treatment, and the payer may be assured that the patient has complied with the treatment regimen before paying another prescription.

As shown in fig. 3, the intelligent VHC of an exemplary embodiment includes a chamber housing 2 having walls defining an interior space extending along a longitudinal axis/suction flow path 6; a back end assembly (backspiece) 8 connected to the input end and the mouth of the chamber housing; and a valve assembly 12 connected to the output end of the chamber housing. The mouth assembly is releasably and removably connected to the chamber housing, for example, by a projection that fits within a recess. The mouth is configured with an inhalation valve 16 and/or an exhalation valve 18, the exhalation valve 18 providing the exhalation flow channel 13. Alternatively, the inhalation and exhalation valves may be placed on other components of the VHC. In various embodiments, the valve may be configured as part of an annular valve, with an inner periphery defining the inhalation valve 16 and an outer periphery defining the exhalation valve 18. In other embodiments, the inhalation valve is configured as a duckbill valve, which may also have an outer annular flange defining the exhalation valve. In other embodiments, the inhalation and exhalation valves may not be one piece, but rather are separately molded and disposed in the VHC. The rear end module 8 is configured with an opening 20, the opening 20 being shaped to receive a mouth portion 22 of an MDI activator (boot) 24. The actuator further comprises a conduit portion 26 defining a cavity for receiving a medicament container 28. The actuator also includes a support block defining a well for receiving a valve stem of the MDI. The well communicates with the bore to release the vaporized drug into the interior space of the chamber housing. For example and without limitation, U.S. patent nos. 6,557,549, 7,201,165, 7,360,537 and 8,550,067, the applicants of which are in agreement with the applicants of the present application, are all terradel International medicine (Trudell Medical International), and the entire contents of which are incorporated herein by reference, disclose different embodiments of VHC and MDI, including a mouth component, a chamber housing and a rear end component.

In an embodiment, VHC 3 is configured to correctly identify the MDI inserted in the VHC and correctly identify when MDI 5 is activated (activated) and, for example, as shown in fig. 12, provide feedback to the user regarding correct usage skills. For example, as shown in fig. 3 and 7, the VHC may have a blue LED30 connected to a wall of the chamber housing in the interior space 4 and a light detector 32 also disposed in the interior space 4, the light detector 32 being spaced apart from the LED 30. For example, the light detector 32 may be attached to the wall. The camera 35 may be coupled to the chamber housing 2, for example, adjacent the mouth assembly 12, or near the back end assembly 8. A flow detector, such as a flow sensor 34, is connected to the wall of the chamber housing and has an input port 36 and an output port 38 in communication with the interior space. A feedback device, such as a visual feedback indicator 40, for example, an LED or LED array, is provided on the back end assembly 8, although the feedback device may also be connected to the chamber housing or the mouth assembly.

As shown in fig. 79 and 80, the adapter 50 comprises a housing having a C-shaped interior region 52 that is matingly connectable with the chamber housing 2 by way of a snap fit. The adapter includes a feedback device configured as a display 54 visible to the user and may include a microcontroller 56 and a communication assembly. As shown in fig. 81 and 82, the back-end component includes a display 54 and/or a microcontroller 56. In each embodiment, the display 54 displays different information to the user and/or caregiver, such as the various feedback information disclosed herein. In different embodiments, microcontroller 56 may be implemented as a controller design as shown in FIG. 16, a microcontroller design as in FIG. 22 or 27, or a processor 502 with one or more components of a more complex computer 500 as shown in FIG. 83.

Communication and data processing

To achieve the above object, the apparatus, e.g., a VHC associated with an MDI, may be configured to perform one or more of the following operations: (1) correctly identifying the MDI used with the VHC; (2) correctly identifying when the MDI is activated; (3) monitoring and providing feedback to the user regarding proper use skills; and (4) providing the prescriber and/or the provider with patient-related data. As shown in fig. 2, 16, 65, 66A-66C, 67, 83, and 84, an aspect of an embodiment also relates to the processing of data. The VHC and/or MDI entered data may be transmitted to an external device such as a smartphone, tablet, personal computer, etc. If this external device is not available, the data may be stored internally in the VHC and/or MDI, in a data storage module or other memory, and transferred on the next synchronization between the VHC/MDI and the external device. The software may accompany the VHC/MDI to enable data transfer and analysis.

To more quickly and accurately process data generated from within the smart VHC and/or MDI and from, for example, one or more different sensors, the data may be wirelessly communicated with the smartphone, local computing device, and/or remote computing device to compile and process the raw sensor data.

In an embodiment, the smart VHC and/or MDI includes circuitry for sending real-time raw sensor data to a local device, such as a smartphone. The smartphone may display graphics or instructions to the user and execute processing software to compile and process the raw data. The smartphone may have software that filters and processes the raw sensor data and outputs the relevant state information contained in the raw sensor data to a display on the smartphone. Alternatively, the smartphone or other local computing device may use its local resources to access a remote database or server to obtain a processing program, or to forward raw sensor data for remote processing and compilation, and to receive processed and compiled sensor data from a remote server for display to the user or a caregiver with the user of the intelligent VHC.

In addition to simply presenting data, statistics, or instructions on a smartphone or other local computer in the vicinity of the intelligent VHC and/or MDI, the active operations associated with the intelligent VHC and/or MDI may also be actively managed and controlled. For example, if a smartphone or other local computer near the smart VHC and/or MDI determines that the sensor data indicates that the end of treatment has been reached or that further treatment is needed, the smartphone or other local computing device may communicate this information directly to the patient. Other variations are also contemplated, for example, a remote server communicating with a smartphone or directly with the smart VHC and/or MDI over a communications network so that information and instructions may be provided to the patient/user.

In other implementations, real-time data collected by the smart VHC and/or MDI and relayed by the smartphone to the remote server may trigger the remote server to track it and notify the physician or care-giver of questions about a particular course of treatment or patterns that develop over time based on a particular user's past courses of treatment. Based on the data from one or more sensors in the intelligent VHC and/or MDI, the remote server may generate an alert to send to the user, the user's physician or other caregiver in the form of text, mail or other electronic communication medium.

The intelligent VHC and/or the electronic circuits in the MDI, local computing device, and/or remote server described above (e.g., the controller design of fig. 16) may include some or all of the functionality of the computer 500 in communication with the network 526 and/or in direct communication with other computers. As shown in fig. 65, 66A-66C, 67, 76, 77, 83, and 84, the computer 500 may include a processor 502, a storage device 516, a display or other output device 510, an input device 512, and a network interface device 520, all connected by a bus 508. A battery 503 is coupled to and powers the computer. The computer may communicate with a network. The processor 502 may represent a central processing unit of any type of architecture, such as a Complex Instruction Set Computing (CISC), Reduced Instruction Set Computing (RISC), Very Long Instruction Word (VLIW), or hybrid architecture, although any suitable processor may be used. The processor 502 executes instructions and includes a portion of the computer 500 that controls the operation of the overall computer. Although not shown in fig. 83 and 84, the processor 502 typically includes a control unit that organizes data and programs in memory and passes data and other information between the various parts of the computer 500. The processor 502 receives input data from the input device 512, and the network 526 reads and stores instructions 524 (e.g., processor-executable code) and data in the main memory 504, such as Random Access Memory (RAM), static memory 506, such as Read Only Memory (ROM), and the storage device 516. The processor 502 may present the data to a user via an output device 510.

Although the computer 500 is shown to include only a single processor 502 and a single bus 508, embodiments of the present application are equally applicable to computers having multiple processors or computers having multiple buses, some or all of which perform different functions in different forms.

Storage 516 represents one or more mechanisms for storing data. For example, the storage device 516 may include a computer-readable medium 522, such as a ROM, RAM, non-transitory storage media, optical storage media, flash memory devices, and/or other machine-readable media, among others. In other embodiments, any other suitable type of storage device may be used. Although only a single storage device 516 is shown, multiple storage devices and multiple types of storage devices may be present. Further, although computer 500 is shown to contain storage 516, it may be located on other computers, such as servers.

Storage 516 may include a controller (not shown) and a computer-readable medium 522 having instructions 524 that are executable on processor 502 to perform the functions described previously, such as processing sensor data, displaying sensor data or instructions based on sensor data, controlling components of the intelligent VHC and/or MDI to change their operation, contacting a third party or other remote resource to provide updated information, or obtaining data from such remote resource. In another embodiment, some or all of these functions may be implemented in hardware instead of in a processor-based system. In one embodiment, the controller is a web browser, but in other embodiments, the controller may be a database system, file system, email system, media manager, image manager, etc., or may include any functionality that enables access to data items. The storage device 516 may also include other software and data (not shown), which is not necessary for an understanding of the present application.

Output device 510 is part of computer 500, which displays output to a user. The output device 510 may be a Liquid Crystal Display (LCD) as is well known in the computer hardware art. In other embodiments, output device 510 may be replaced by a gas or plasma flat panel display or a conventional cathode-ray tube (CRT) display. In other embodiments, any suitable display device may be used. Although only one output device 510 is shown, in other embodiments, any number of output devices of different types or the same type may be present. In one embodiment, output device 510 displays a user interface. The input device 512 may be a keyboard, mouse or other pointing device, trackball, touch pad, touch screen, keypad, microphone, voice recognition device, or any other device through which a user may input data to the computer 500 and operate the aforementioned user interface. Although only one input device 512 is shown, in another embodiment, any number and type of input devices may be present.

The network interface device 520 provides a connection from the computer 500 to a network 526 through any suitable communications protocol. The network interface device 520 transmits data to the network 526 or receives data from the network 526 via the wireless or wired transceiver 514. The transceiver 514 may be any of a number of known wireless or wired transmission systems that may be cellular, Radio Frequency (RF), Infrared (IR), or any other suitable type of system capable of communicating with the network 526 or other intelligent devices 102, the intelligent devices 102 having some or all of the features of the example computers of fig. 83 and 84. Bus 508 can represent one or more buses, such as USB, PCI, Industry Standard Architecture (ISA), X-bus, Extended Industry Standard Architecture (EISA), or any other suitable bus and/or bridge (also known as a bus controller).

Computer 500 may be implemented using any suitable hardware and/or software, such as a personal computer or other electronic computing device. The computer 500 may be a mobile computer, laptop, tablet or notebook computer, smart phone, personal digital assistant, pocket computer, kiosk, telephone, mainframe computer, these being examples of other possible configurations of the computer 500. The network 526 may be any suitable network and may support any protocol for communicating with the computer 500. In an embodiment, the network 526 may support wireless communications. In another embodiment, network 526 may support wired communications, such as through telephone lines or cables. In another embodiment, the network 526 may support the Ethernet IEEE (institute of Electrical and electronics Engineers) 802.3x specification. In another embodiment, the network 526 may be the Internet and may support Internet Protocol (IP). In another embodiment, the network 526 may be a local area network or a wide area network. In another embodiment, the network 526 may be a hotspot service provider network. In another embodiment, network 526 may be an intranet. In another embodiment, network 526 may be a General Packet Radio Service (GPRS) network. In another embodiment, the network 526 may be any cellular data network or cell-based wireless network technology. In another embodiment, the network 526 may be an IEEE 802.11 wireless network. In yet another embodiment, the network 526 may be any other network or combination of networks. Although only one network 526 is shown, in other embodiments, any number of networks of the same or different types may be used.

It should be understood that the various techniques herein may be implemented in hardware or software, and may also be implemented in combinations of these where appropriate. Thus, the methods and apparatus (or portions thereof) provided substantially herein may be embodied in the form of program code (i.e., instructions) embodied in tangible media, such as floppy diskettes, CD-ROMs, hard drives, or other machine-readable storage medium, wherein, when the program instructions are loaded into and executed by a device (e.g., a computer), the machine serves as a means for performing the substance of the present application. In the case of program code execution on programmable computers, the computing device can generally include a processor, a storage medium readable by the processor (including transitory and non-transitory memory and/or storage elements), at least one input device, and at least one output device. One or more programs that may implement or use the methods described in this application may, for example, be implemented using an API, reusable controls, or the like. Such programs may be implemented in a high level procedural or object oriented programming language to communicate with a computer system. However, the programs may also be implemented in component or machine language, if desired. In any case, the language may be a compiled language, and used in combination with hardware applications. Although in the illustrative embodiments, the teachings of the present application may be implemented by one or more stand-alone computer systems, it should be appreciated that they may be implemented in any other computing environment, such as a networked or distributed computing environment. Further, the substance of the present application may be implemented in a plurality of processing chips or devices, and the memory may be provided in a plurality of devices. The device may be a personal computer, a network server, a handheld device, or the like.

Correct technique of use

Providing feedback to the user regarding inhalation skills is one feature of VHC assisted drug delivery. In one embodiment, as shown in FIGS. 3 and 9, a flow detector, configured as a flow sensor 34, may be used to collect data and provide feedback regarding the trick. The flow sensor measures the flow rate at which the user inhales. Inhalation too quickly can cause a large portion of the drug to enter the throat rather than the lungs. Effective drug deposition in the lungs can be achieved by controlled inhalation. Further, the flow rate may be integrated over time to determine the volume of air inhaled, which may be used to provide an indication to the user when he has evacuated the interior space of the chamber housing and received the full dose. As shown in fig. 3 and 9, the flow sensor 34 includes a bypass passage 58 having an input port 36 and an output port 38 in communication with the interior space. The pressure differential between the proximal and distal openings defined by the input and output ports 36, 38 creates a small flow rate through the bypass channel. As shown in fig. 9, a thermal mass flow sensor 60 is used to measure the flow through the bypass channel, which is related to the inhalation flow rate. Flow sensor 34 and flow sensor 34' may be located anywhere as shown in FIG. 9. The flow sensor measures the flow without the need for a flow path or an interfering flow path provided in the inner space 4. In this way, the flow sensor does not interfere with the flow path of the aerosol medicament through the interior space. The flow rate information may be combined with MDI activation detection and MDI identification, as described in more detail below, to provide reliable insight into patient behavior and device usage.

As shown in fig. 12, the flow rate information is used in real time to provide feedback to the user about the duration of the exercise, e.g. by feedback means such as an indicator (visual, audible and/or tactile) or a display, or feedback as to whether the user has started inhalation, and/or whether the user needs to reduce the flow rate, e.g. when the maximum flow rate is exceeded. MDI start-up may also be used to provide feedback to the user to initiate start-up and/or to start inhalation. First, as shown in FIG. 19, a user 66 inserts the MDI into the back-end assembly. A touch switch 62 or other MDI insertion detector/sensor detects this insertion. When the MDI is inserted, the intelligent VHC actively looks for MDI initiation and/or inhalation flow detection. Based on feedback through a feedback device (e.g., an indicator or display), the user may activate the MDI, thereby dispersing the vaporized drug into the interior space, and an activation time stamp is recorded. Subsequently, the processor 502 looks for the inspiratory flow communicated by the flow sensor 34 and records the flow rate and time stamp of the active inspiration. The processor 502 also compares the flow rate to a stored preset flow rate, such as the maximum recommended flow rate, and provides feedback to the user whether the inhalation flow rate exceeds the preset flow rate. The processor then compares the volume of inhalation from the flow rate calculation with the volume of the interior space 4, thereby informing the user that the treatment is complete and that the dose has been administered correctly. Alternatively, the processor may inform the user that further inhalation is required to completely empty the interior space. Note that the user has the option of practicing using the device before treatment begins. In this case, no MDI is inserted. Instead, only the flow sensor is activated. The processor records the flow rate and provides feedback regarding the flow rate and informs the user that the exercise is complete.

As shown in fig. 14-17, the smart VHC of one embodiment includes a thin skin patch that includes a resistive strain gauge 68 mounted on the inhalation valve 16 to measure the geometry of the valve opening 70 during inhalation. The strain gauge may be applied to the valve by means of gluing or insert molding during injection molding retention of the valve. As shown in fig. 15, the size and duration of the opening of the valve 16 may be correlated to the inhalation flow rate to confirm that the inhalation is complete.

As shown in fig. 16, a controller, which may be disposed on or within the intelligent VHC of the various embodiments described herein, communicates with one or more sensors, switches or meters that track or control the operation of the intelligent VHC. The controller may save the collected data in memory for subsequent download to the receiving device, or may send the data to the receiving device in real-time. Further, the controller may perform some processing of collecting data from the sensors, or it may store or transmit raw data. An RF transmitter module and/or receiver module may be associated with a controller on the intelligent VHC to communicate with a remote handheld or fixed computing device in real-time or subsequently when the intelligent VHC is within communication range of a communication network with the remote handheld or fixed computing device. The controller may include one or more features of the computer system 500 shown in fig. 83. Further, one or more sensors, switches or gauges may be in wired or wireless communication with the controller.

To clearly illustrate other features of the intelligent VHC of the different embodiments, the controller circuitry is omitted, however, in one version of these embodiments, a controller or other processing unit is contemplated that is capable of managing at least routing or data storage from the intelligent VHC. In other implementations, the intelligent VHC may not have its own processor, and the various sensors, meters, and switches in certain embodiments may communicate wirelessly directly with a remote controller or other processing device, such as a handheld device or remote server. The data collected by the controller or other processing device may be compared to expected or preset values in the memory of the local controller or other remote location to provide a basis for feedback as to whether the desired effect or treatment was achieved. If the controller is more complex and includes many of the elements of the computer 500 shown in FIG. 83, the process may be entirely local to the intelligent device (intelligent VHC, MDI, etc.). In a more basic controller design, the numbers may also simply be dated/dated and saved locally or remotely for subsequent processing. In an embodiment, the data may also be locally or remotely stamped with a unique device or patient identifier.

Breath holding is also a specific step in promoting drug diffusion and optimizing drug deposition in the lungs. The user's breath-hold may be monitored using the methods described below, or the user may be encouraged, visually or audibly, to hold his breath without having to directly monitor the breath-hold.

1. Carbon dioxide detection

1.1. As shown in fig. 86, carbon dioxide is a by-product of cellular respiration, which can be expelled from the body by exhaled breath. Thus, the concentration of carbon dioxide in the exhaled breath is significantly higher than in the ambient air. Using the carbon dioxide sensor 76, the carbon dioxide concentration within the mouth and mask adapter portion of the VHC may be monitored, with higher concentrations identifying the exhalation phase of the user's breathing cycle. Combining this data with inhalation flow data or other forms of detecting user inhalation, breath hold duration may be determined and used to provide feedback to the user. The end of an inhalation may be determined, for example, by using a flow threshold or a pressure threshold. Once the inspiratory flow or pressure drops below this threshold, the breath-hold timer may start and not stop until a peak in carbon dioxide concentration is detected.

2. Pressure monitoring

2.1. As shown in fig. 18-20, a pressure sensor 78 may be placed within the mouth/mask adapter or chamber housing so that the inhalation and exhalation phases of the user's breathing cycle may be monitored. The inhalation pressure threshold and the exhalation pressure threshold are used in order to calculate the duration of the user's breath-hold. The breath-hold timer starts when the inhale pressure drops below the inhale threshold, and stops once exhalation begins and the exhale pressure threshold is exceeded. The pressure sensor 78 may be in communication with a computer 500 and a processor 502.

Furthermore, by assuming tidal volumes and calculating the number of inspired breaths, the device can provide information about when the chamber (chamber) is empty. The assumed tidal volume may be based on age and gender and may be selected during the establishment. Since the volume of the interior space 4 is known, the computer 500/processor 502 processes the positive pressure events to identify when the MDI has been activated, and then counts the number of negative pressure events representing inhalation until the chamber volume is reached. Each negative pressure event should be separated by a conventional breathing cycle, e.g., 2-5 seconds, because the volume of the chamber is evacuated for a limited total treatment time period. If this is satisfied, it is determined that the drug has been completely delivered. Otherwise, feedback is provided to the user to continue the inhalation and/or breathing cycle. The feedback may be audible, visual, or tactile/tactile (e.g., vibration), or a combination thereof, using the different indicators described elsewhere herein. This information may be recorded, stored and/or fed back, assuming additional training is required.

3. Microphone (CN)

3.1. Inhalation and exhalation air that passes through the VHC during use travels different paths. Due to the use of different flow paths, the flows through these paths will likely sound different from each other. As shown in the example in fig. 24, the microphone 82 may be used to listen for inhalations and exhalations and may be used to calculate breath-hold duration using a threshold method similar to that in example 1.1 and example 2.1.

Furthermore, during treatment, and upon activation of the MDI, the microphone records the sound of the air flow through the VHC and can be monitored and analyzed by the microprocessor based on the amount of turbulence recorded by the microphone. For example, as shown in fig. 26, the amplitude of the translated sound over a period of time is related to a particular flow rate or range of flow rates. By means of an indicator (visual, audible, tactile, etc.), the VHC may provide feedback to the user that the inhalation rate is too high, or exceeds a preset maximum flow rate. Other feedback may include information that the treatment is complete or that the data upload is complete. Once the treatment is complete, the system is reset and ready for the next MDI start.

As shown in fig. 58, a reed or array or series of reeds 84, for example, plastic or silicone, may be disposed adjacent to the microphone 82. The differential flow activates or creates a different acoustic output from the reed, which can be picked up and recorded by the microphone 82. As shown in fig. 59A-59C, a port through which a single reed 115 or bundle can pass is provided, as shown for a duckbill valve. Since the flap 88 of the valve opens or closes by different amounts, e.g., in response to flow velocity, the reed 115 acting as a vibrating string is made thinner or thicker so that it can generate different acoustic signals that can be picked up by the microphone 82. The microphone is in communication with the computer 500 and the processor 502.

4. Humidity sensor

4.1. As water vapor enters the lungs, air from the surrounding environment becomes saturated with water vapor. When this air is exhaled, it passes through the mouth and mask adapter where the humidity of the air can be analyzed. By continuously monitoring the humidity level with the mouth and the sensor 90 in the mask adapter as shown in fig. 86, the exhalation phase of the breathing cycle can be detected and used to determine the breath hold duration in a manner similar to example 1.1 and example 2.1. The humidity sensor 90 is in communication with a computer 500 and a processor 502.

5. Temperature sensor

5.1. When ambient air enters the body, it is warmed to body temperature. Air temperature may be monitored in the mouth and mask adapter using a temperature sensor 92 (see, e.g., fig. 86). When a sudden increase in temperature is observed, this may be interpreted as an exhalation from the user. Similar to the previous breath hold detection embodiments, combining the detection of the onset of exhalation with inhalation measurements (i.e., flow or pressure), breath hold duration may be calculated and fed back to the user for skill improvement. The temperature sensor 92 is in communication with a computer 500 and a processor 502.

6. Light curtain

6.1. As shown in fig. 63 and 86, the light curtain 94 or multiple light curtains may be used in conjunction with a resilient member 96 responsive to negative and positive pressures. During inhalation, the resilient member may be pulled out in a direction such that the light beam of one of the pair of light curtains is broken (or restored), which may be interpreted as an inhalation by the user. Instead, during exhalation, the resilient member is forced in the opposite direction, wherein the light beam of the second one of the light curtains is broken (or restored). This is interpreted as an outgoing call by the user. Using these measurements, the time that both light curtains are uncorrupted represents the breath-hold duration. Alternatively, a single light curtain may be used to detect exhalation by the user, and another method (e.g., inhalation such as a pressure threshold or an inhalation flow threshold) may be used to determine the end of inhalation.

6.2. In another embodiment, moisture in the exhaled breath of the user is sufficient to break the light curtain, which is used to detect exhalation without the elastic member.

End of treatment

When receiving aerosols from a valved holding chamber, especially infant and toddler mask products, one uncertainty is to know when the user has received all of the medication from the chamber. Premature removal of the chamber during use of the aerosol can result in low dose and excessive mask leakage. By monitoring the volume of aerosol in the chamber or air inhaled through the chamber, feedback can be given to the user as to the end of the treatment. This provides dose assurance for various aspects involved in the health of the patient.

1. Change in capacitance

1.1. Assuming that the aerosol has a different medium to that of air, the change in capacitance of the capacitance 106 as shown in fig. 43 and 44 can be used to detect when all of the aerosol is vacated from the chamber. Before aerosol activation, the baseline capacitance may be measured and treatment will not end until the capacitance returns to the baseline value or some similar value.

2. Light transmission/reflection

2.1. As shown in fig. 3 and 7, light source 30 and light detector 32 may be established in any direction with respect to the flow of light sources directed directly to the light detector or reflected from the surface to the light detector. When an aerosol is present, the light is scattered, diffused, refracted, absorbed, and reflected such that the amount of light returning to the light detector is reduced. When the baseline reading is reached, the treatment ends.

Flow detection

When the flow rate is high, aerosols deposit in the larynx and upper respiratory tract, causing side effects, and depriving the lungs of therapy. The intelligent VHC should have a feedback device or function that uses a flow detector to inform the user whether the preset maximum recommended flow rate is exceeded and allow the user to reduce his inhalation to an effective rate. The flow detectors of all embodiments described below, alone or in combination, may be used for this purpose, except to assist in determining the end of treatment. The end of the treatment is determined by integrating these flow rates over time until a threshold volume is reached, as shown in fig. 12. The threshold volume is selected such that all aerosol is inhaled from the chamber.

3. Pressure sensor

3.1 differential pressure across the valve

As shown in fig. 46, the selector valve, having a low hysteresis rate, is preferably linear so that its resistance is continuous. Subsequently, flow through the valve may be inferred based on the differential pressure across the valve.

3.2. Differential pressure across MDI

3.2.1 MDI actuator

The MDI identifier is for identifying the MDI for use with the chamber. Assuming this information is known, the resistance file (curve of pressure versus flow) of the MDI can be read from a predefined database and, as shown in fig. 47, the flow through the MDI itself can be calculated using differential pressure measurements to compare the pressure at the mouth of the MDI detected by the pressure sensor 78 with the atmospheric pressure.

3.2.2. Molded MDI adapter actuator (insert can)

Since most MDIs will have mutually different resistance profiles, the canister can be removed from the actuator and placed into a built-in container, or back end assembly, that is molded into the MDI adapter. This adapter will allow all MDI canisters to be inserted and allow aerosol to enter the chamber. The resistance to flow of the MDI adapter is then specifically designed for the requirements of the system, i.e. linear P0 curve, low hysteresis rate and continuous from part to part.

3.3. Differential through-hole in bypass

3.3.1. As shown in fig. 3, 9, 49 and 50, a bypass passage 60 exists in the interior of the chamber wall or mouth/mask adapter and this passage is in fluid communication with the aerosol chamber. During inhalation, some flow is drawn through this bypass channel and through the precisely sized orifice 110. The resistance to flow through this orifice can be fully qualitative and differential pressure measurements through orifice 110 using pressure sensor 78 can be used to calculate flow through the orifice and bypass channel. The flow rate through the chamber will be calibrated to the flow through the bypass channel so that the bypass flow measurement during use can represent the total flow through the VHC. The pressure sensor 78 is in communication with a computer 500 and a processor 502.

3.4. Venturi tube

3.4.1 venturi 112 uses local constriction of the flow path to accelerate the fluid as it passes. As the fluid velocity increases, its pressure drops relative to the pressure upstream of the less moving fluid that contracts. Differential pressure sensors can detect this difference and, using venturi geometry, the flow rate can be calculated.

Venturi tube 112 may be formed as part of chamber housing 2, part of mouth 12, or part of bypass flow path 60, as shown in fig. 51A-51C, respectively. The pressure sensor 78 is in communication with a computer 500 and a processor 502.

3.5. Pitot static tube

3.5.1. Pitot tube 114 comprises a tube closed at one end and is used to compare the pressure within the tube with the ambient fluid pressure. As the rapidly moving air enters the pitot tube 114, it stagnates within the tube and creates a pressure proportional to the initial velocity of the fluid flow.

As shown in fig. 52, a pitot tube may be fabricated or assembled onto the flapper 116 of the valved holding chamber to sample the fastest moving air during inhalation. With chamber geometry, this velocity can be converted into a flow velocity estimate. The pressure sensor 78 senses the pressure differential and communicates with a calculator 500 and a processor 502.

4. Sound-based method

For all sound-based methods, a second microphone may be used to detect ambient noise. This information may be used to reduce noise in signals processed by the microcontroller or other processor 502.

4.1. Based on quantity

4.1.1. Internal sound

Sound-producing turbulence is generated as air flows through the MDI and the valved holding chamber. At higher flow rates, more turbulence is generated and the sound is larger. While unfiltered volume-based approaches will be susceptible to ambient noise, monitoring the volume in the room can provide a way to estimate the flow rate.

The microphone 82 is placed in the interior space of the chamber housing, for example, in connection with an adapter or back end assembly (see, e.g., fig. 24), or along the chamber or at a baffle (see, e.g., fig. 59C). This same microphone may be used for MDI start-up detection.

4.1.2. Sound generation

The microphone was placed at a similar point as in example 4.1.1. As shown in fig. 58 and fig. 59A-59B, vibrating reed 115 or reed 84, edge tones or flow over open or closed tubes can be used to generate sound as flow passes. And this volume may be significantly greater than the volume present in the room itself. The microphone 82 is in communication with the computer 500 and the processor 502.

4.2. Quantities based on low-pass, high-pass and band-pass filters

As described in example 4.1.1, the quantity-based method is susceptible to false readings due to environmental noise. To reduce this risk, digital and/or analog filtering may be implemented so that the system effectively "listens" only to a particular frequency band. These filters will be selected so that the sound inherent in the room is heard or, in the case of sound generation, these frequencies are monitored.

4.3. Based on an algorithm

Whether these sounds are inherent to the product or generated by means of a reed or other sound generating source, the sound from the chamber at different flow rates is unique to the system. Different algorithms can be used to quantitatively compare the input microphone signal with a pre-recorded signal range from a defined flow rate within the device.

4.4. Time Of Flight (TOF) Of sound

As shown in fig. 64, TOF of sound in this case refers to the time it takes sound to travel from one sound transceiver 118 to another. Transceiver 1 (i.e., T1) is located downstream of transceiver 2 (i.e., T2), both of which may be located inside or outside the chamber. As the sound travels from T1 to T2, it is effectively slowed down due to the counter-travel with the air flow through the chamber. Conversely, when sound travels from 12 to Ii, it travels faster than normal due to moving with the flow. Knowing the angle 0 of the transceiver 118 or ultrasonic transducer relative to the flow direction and the TOF from 11 to 12 and 12 to T1, the average flow velocity and flow velocity can be estimated using the geometry of the chamber. Although sounds outside the human hearing range (>20kHz) are required, any frequency of sound is possible. The transceiver 118 is in communication with a calculator 500 and a processor 502.

4.5. Doppler device

Doppler ultrasound uses the frequency shift of the reflected wave relative to the transmitted wave to infer the velocity at which the reflector is moving. Using suspended aerosol particles as reflectors, the doppler principle can be used to determine the mean particle velocity and estimate the flow velocity. This method will only detect flow in the presence of aerosol, so it can also be used as other dose assurance means.

As shown in fig. 53, the ultrasonic transducer 118 may be placed in the baffle 116 with sound directed to the MDI adapter or back end assembly 8; is placed in the MDI adapter with the sound directed at the baffle or anywhere in between, as long as the sound generation is not perpendicular to the air flow. The transceiver/transducer 118 is in communication with a computer 500 and a processor 502.

5. Light-based method

5.1. Internal reflection in a valve with a crack

As shown in fig. 60, a light-emitting diode (LED) 122 or other light source and/or a light detector 124 that is sensitive to the wavelength of light from the LED are positioned within the valve 16, with both being directed toward a valve opening 126. The valve is of the type having an opening of variable size, wherein the size of the opening is dependent on the flow rate through the valve. Duckbill valves, cross valves and any die cut valves are preferred examples, but this list is not exclusive. As shown in fig. 56 and 57, the light detector 124 may be placed outside the valve.

During operation, the light source emits light inside/behind the valve 26, as shown in fig. 60, which in turn reflects some light back to the light detector, or as shown in fig. 56 and 57, which passes light to be received by the light detector. When the valve is closed, most of the light from the light source is reflected back to the light detector (internal) or not received by the light detector (external). When the valve is opened, more light can escape and therefore less light is reflected back to the light detector (inside) or otherwise received by the light detector (outside). By monitoring the signal from the light detector, the degree to which the valve is open and the flow through the valve can be estimated. The valve is designed in a way, using shape and color, to focus the reflected light on the light detector to a certain extent of its opening. The light detector 124 is in communication with the computer 500 and the processor 502.

A physical shield may be placed within the valve. The LEDs may have adjustable brightness such that the same baseline signal is achieved during an initial calibration phase by iteratively increasing the brightness of the LEDs with feedback from the light detector, or selecting wavelengths of light that are not readily absorbed by the drug being used. Although the wavelength of minimum absorption or reflection by the aerosol is preferred, any wavelength may be used in the present method. A high pass filter may also be implemented to remove signal contributions from DC power sources (flash or sunlight) as well as low power electro-optics, e.g., 60Hz (120Hz) light in north america and equivalent frequencies around the world.

Alternatively or in addition to high pass filtering, the brightness of the light source is variable at a particular frequency and using a frequency detection algorithm, the signal will be analyzed for flow. In this case, the amplitude of the frequency component of the signal matching the frequency of the light source will decrease and increase as the valve opens and closes, respectively.

5.2. Illumination in slit valve

5.2.1. External light source

As shown in fig. 61, the light source 122 is located outside the valve 16 of the type in the embodiment disclosed in section 5.1 and directed towards the valve 16, with the light detector 124 remaining inside the valve directed towards the light source. In this embodiment, the more the valve opening 126, the more light reaches the light detector. As in 5.1, a similar approach applies to this embodiment, including filtering and frequency coding and some 5.1s vulnerability to drug interference. The light detector 124 is in communication with the computer 500 and the processor 502.

5.2.2. Body heat (Infrared)

Similar to the embodiments disclosed in sections 5.1 and 5.2, and as shown in fig. 62, an infrared light detector 128 is located inside a valve 16 of the type described in sections 5.1 and 5.2. Similar to 5.2, when the valve 16 is opened, more light is allowed to reach the light detector 128. In this embodiment, the light detector is selected such that it is most sensitive to infrared wavelengths emitted by the human body. When the infrared opaque valve is opened, more infrared light from the user's mouth bar (mouth piece) or face (mask piece) enters and is absorbed by the light detector or photodiode. The light detector 128 is in communication with the computer 500 and the processor 502. The signal is analyzed by a microcontroller.

5.3. Oscillating body

As shown in fig. 63, the light source 122 and the light detector 124 face each other with an opaque body 96 therebetween.

The opaque body is free to move so that it can block light from the light source from reaching the detector at position 1 and allow light to reach the detector at position 2.

The opaque body is designed to oscillate when flow is present, and its oscillation is unique for different flow rates. The amplitude of these oscillations is such that position 1 and position 2 are reached. The oscillating body may be a reed made of silicone or plastic, a moving blade, a rotating blade, or a flapwise of loose or hard material, similar to a flag. This is not exclusive as any oscillating body is possible. The signal from the light detector is then continuously analyzed and the corresponding flow rate is inferred. The light detector 124 is in communication with the computer 500 and the processor 502.

6. Spring displacement

The following embodiments rely on the movement of a spring (linear or non-linear, either tension or compression) in response to suction pressure or suction flow rate. When the spring moves from one position to another, it brings or activates a series of sensing hardware:

6.1. hall effect

A magnet is placed on the movable end of the spring with the hall effect sensor in a fixed position. The hall effect sensors detect changes in the magnetic field as the magnet moves from one position to another, and this can be analyzed using various algorithms to determine flow.

6.2. Capacitor with a capacitor element

A charged plate is placed on the movable end of the spring with the oppositely charged plate in a fixed position, separated by air (the medium). As the charged plate on the spring moves, the capacitance changes and this can be detected using various hardware and software methods.

6.3. Reed switch

A magnet is placed on the moving end of the spring and a set or magnetic reed switch is placed along the length of the spring. When the spring is deflected and carries a magnet, different reed switches close, and by determining which switches are open and closed, the position and flow rate of the spring can be approximated.

6.4. Inductive sensor

A conductive plate is placed on the movable end of the spring, with an induction coil generated, and the electromagnetic field in close proximity. As the distance between the coil and the plate changes, the inductance of the system changes, which can be analyzed by software. This in turn can be used to estimate the position of the spring and thus the flow rate.

7. Needle wheel anemometer

7.1. The pinwheel is placed in the chamber such that its rotational speed varies with the flow rate. By rotating a contact switch, periodic opening of a light curtain or magnet, or a combination of magnetism and a hall effect sensor, the rotational speed of the pinwheel can be monitored and used to approximate the flow rate through the chamber.

8. Heating surface

8.1. Hot wire anemometer

By applying a constant voltage thereto, the wire or mesh is heated. As the air passes through the wire, it cools and its resistance drops. As the voltage remains constant, the current through the wire increases, which can be monitored by the electronics. The amount of current flowing through the wire can then be used to infer the flow rate.

8.2. Thin film flow sensor

This is the same principle as hot wire anemometers, except that it is not invasive. A sensor that heats the membrane is placed on a surface within the chamber and the amount of current flowing through the sensor is used to determine the flow rate.

9. Piezoelectric flexible sensor

9.1. Based on deflection

When the airflow comes into contact with the object, the object exerts a force on the air to change its direction around the object. At the same time, the air imparts the same amount of force, but in the opposite direction. Using this principle, a piezoelectric flexure sensor can be used so that when air strikes its surface, it is forced to deflect, and the amount of deflection will be proportional to the flow rate striking the sensor. Piezoelectric materials generate a voltage under strain, and thus strain can be detected and analyzed using various algorithms. Greater strain is an indication of higher flow rate.

9.2. Based on oscillations

When boundary layer separation occurs, air flowing around a blunt object may generate vortices at a specific frequency. This vortex shedding can cause vibration of the object itself and, if the object is made of a piezoelectric material, a voltage can be generated at a frequency that matches the frequency of the oscillating body. The signal can be analyzed and various algorithms used to infer the flow rate. Alternatively, to amplify the signal, various objects may be used that induce vortex shedding at different frequencies at the same flow rate. When the shedding frequency matches the resonant frequency of the object, a larger amplitude oscillation will be induced that is easier to detect and analyze.

10. Multi-stage contact switch

10.1. The different switches may be closed in discrete steps. A plurality of printed conductive paths may be printed onto the flexible surface and different switches closed at different positions of the resilient member. Based on which paths are closed and open, the position of the piece, and hence the flow rate, can be estimated.

11. Potentiometer blade

11.1. Using the force generated by the flow as described in example 9.1, the blade can be designed such that it adjusts the potentiometer when the flow is present. The biasing spring will cause the position of the vane to depend on the flow present. The resistance of the potentiometer may be continuously monitored and flow inferred based on the measurement.

MDI initiation detection

The detection of MDI activation is important information that can be used for dose assurance and for providing feedback to the user about optimizing his breathing skills. As described in various embodiments below, several characteristics of the MDI may be used and detected by the actuation detector to detect MDI actuation, including visual appearance of the aerosol plume, sound, temperature drop associated with rapid evaporation of the HEA propellant, its firing force, dielectric constant of the aerosol, displacement of the fire, pressure at actuation, or communication with the intelligent function of the MDI itself.

1. Light-based method

1.1. Optical transmission (AKA light curtain)

As shown in fig. 7 and 8, in one embodiment, the light source (e.g., blue LED)39 and the light detector (light detector) 32 are spaced apart and positioned such that the light source is directed to the detector with an air gap therebetween or such that light from the light source can be detected by the activation detector. Any wavelength in the visible spectrum and/or infrared spectrum may be used to detect MDI initiation. The air gap is large enough that when the MDI is activated, the aerosol plume is minimally impeded by the presence of the light source and detector. As the aerosol plume propagates between the light source and the detector, the amount of light reaching the detector from the light source will decrease as the aerosol scatters and reflects the light. The result is a sudden change in output from the detector, the signal of which can be analyzed by various software algorithms. In particular, the aerosol drug particles scatter, reflect and/or absorb blue light to varying degrees within the interior space of the chamber. The change in light is detected by a light detector, which transmits a signal to a processor. When no aerosol is present in the interior space, the photodetector records a baseline reading of the received light. When there is a start-up, the light detector receives less or more light due to light scattering/reflection/absorption. Based on these parameters, the intelligent VHC can accurately determine MDI initiation. The event may further be used to record a timestamp, and this information may be used for sticky tracking and monitoring. As shown in fig. 8, the output of the light detector over time shows a reliable indication of activation, as evidenced by the periodic spikes on the timeline.

The wavelength of the light source may be any wavelength and is ideally from the infrared bandwidth, so that the light is not visible and distracts the user. The sensitivity of the light detector should be such that it is most sensitive to the light emitted from the light source. The ideal light source has a wavelength in the infrared (wavelength 700nm to 1mm) or visible (wavelength 400nm to 700nm) spectrum and is in the form of an efficient light emitting diode.

An ideal photodetector has the highest sensitivity to the wavelength of the light source and may include a photodiode, phototransistor, or photoresistor (LSR).

1.2. Light reflection

The light source and light detector are oriented such that the detector will only receive light from the light source when a reflector or medium is present. When an aerosol plume is present, light from the light source is reflected, and at least a portion of the reflected light is absorbed by the detector. The light absorption peak at the detector results in a voltage change that can be analyzed by various software algorithms. The light source and detector should have the same properties as described in the light transmission embodiment.

1.3. Colour reflection

The white light source and the color sensor are oriented such that the color sensor receives light only after the white light is reflected off of the object or medium. When an aerosol plume is present, it reflects some wavelengths of light while absorbing other wavelengths. The combination of all reflected wavelengths will determine the color of the aerosol plume detectable by the color sensor. The sensor may detect sudden changes in light level and sudden changes in color that may be analyzed using various software algorithms to detect MDI activation.

1.4. Camera and image processing

Cameras and image processing tools are used in a wide range of applications, and identification of aerosol plumes may be one application. Various software algorithms may be used.

2. Sound-based method

As shown in fig. 24-28, the VHC or a back-end component 8 connected thereto is configured with a microphone 82 (activation detector), an audio interface, a visual feedback indicator 40, a microcontroller (which may be a processor 502), memory storage 504, limit switches, a bluetooth/Wi-Fi connection, and a battery 503, all of which are housed in the back-end component 8. The limit switch 62 detects the presence of the MDI, which triggers the electronic system to power up. The microphone and audio interface record the sound inside the interior room. When the MDI is activated, the entire sound wave that is activated is captured by the microphone 82 and stored in memory for analysis.

For all sound embodiments, a second microphone may be used to pick up ambient noise. The signal from the microphone may then be used for noise reduction purposes in the analyzed signal.

2.1. Microphone-simple volume threshold

The microphone is located near the mouth of the MDI and is at least partially isolated from sound from the external environment. During MDI startup, a relatively loud sound is generated as the drug flows out of the MDI orifice, and various software algorithms can be used to detect this volume peak.

2.2. Microphone-volume threshold with pre-filtering

A simple volume threshold method can be subject to false triggering due to any loud sounds from the environment that are not adequately damped by the acoustic insulation. To further reduce the risk of false triggers, a volume threshold may be combined with pre-filtering the input microphone signal.

The sound generated during the MDI start-up consists of various sound frequencies. Using a low pass, high pass or band pass filter, the microphone signal can be tuned such that only the frequencies associated with MDI activation are listened to. This limits the possibility of false triggering of loud sounds within the sound bandwidth of MDI activation.

The microphone is located near the mouth of the MDI and is at least partially isolated from sound from the external environment. The output signal of the microphone is passed through a series of resistors, capacitors and/or inductors that are carefully selected and arranged in a manner to construct a low pass filter and/or a high pass filter. After passing through these filters, the signal is analyzed by a microcontroller (fig. 28) or other processor 502 for volume spikes that can be detected using various algorithms. Frequency filtering may also be done digitally.

2.3. Microphone-target signal comparison (filtered and unfiltered)

Both methods (2.1. and 2.2.) are subject to false triggering due to loud ambient sounds. Instead of or in combination with a simple volume threshold, a quantitative comparison between the input sound and the predefined target may almost eliminate the risk of false triggering. Autocorrelation and minimization of root mean square are some algorithms based on the time domain that can be used for signal comparison, and two of these can be combined with the analog or digital filters described in 2.2, or no filtering at all. Frequency domain algorithms may also be used to compare the source and target.

3. Temperature variation method

3.1. Temperature sensor and direct contact evaporation

MDI typically contains a propellant, such as Hydrofluoroalkane (HFA), which has a low boiling point. During the start-up of the MDI, some of the propellant is able to escape the MDI in its liquid phase. When such liquid propellants are exposed to the external environment, they evaporate rapidly due to their low boiling point and the minimum vapor pressure of the propellant in the surrounding atmosphere. By evaporative cooling, the temperature drops rapidly in all materials with which the liquid propellant comes into contact.

As shown in fig. 38 and 39, one embodiment of the VHC and/or MDI is configured with one or more temperature sensors 140 (actuation detectors), e.g. connected to or embedded in the walls of the holding chamber, or provided in its inner space, e.g. on a suction valve or baffle at the output end of the chamber housing. The temperature sensor may be a temperature sensitive resistor, thermocouple, thermistor or infrared temperature sensor to detect rapid drops in temperature and subsequent increases in temperature. Alternatively, only a rapid drop in temperature may be sufficient. Such rapid temperature drops and/or re-increases may be detected using various software algorithms. In this embodiment, the temperature sensor is placed in the path of the aerosol plume so that a quantity of liquid propellant is deposited on its surface. Care was taken to avoid any substantial drug loss from the sensor being in the aerosol path. A sensor with minimal thermal mass is an ideal way to facilitate rapid detection of temperature changes. As shown in fig. 39, various minimum plume temperatures (MMPT) may be associated with various MDI formulations. The temperature data may then be input to a microcontroller or other processor 502 (not shown) to indicate and record MDI activation.

3.2. Temperature sensor and air temperature

3.1. Embodiments of (a) require the temperature sensor to be in the aerosol path during MDI start-up. Alternatively, a rapid drop in the air temperature can be monitored, since the evaporation of the propellant also leads to a decrease in the ambient air temperature. For example, as shown in fig. 38, the sensor 140 may be located outside of the interior space of the holding chamber, such as on an MDI. This would allow a non-invasive method of MDI start-up using temperature. The temperature sensor should be located close to the MDI, because the magnitude of the temperature drop decreases with increasing distance from the MDI. This is a result of the vaporization of most propellants before they propagate over long distances. Multiple temperature sensors placed along the chamber may also be used to evaluate the temperature or the distribution of temperature versus distance at different distances from the MDI to more reliably detect MDI activation.

3.3 temperature sensor on MDI

As shown in fig. 38, the propellant is not in phase equilibrium after start-up. This causes some of the liquid propellant to evaporate until saturation occurs and equilibrium is restored. The evaporation causes a drop in the temperature of the tank, which can be detected using a contact temperature sensor or any other sensor mentioned in example 3.1. This may be integrated into the MDI adapter or a counter may be added to the MDI canister having wireless communication functionality to communicate with the MDI adapter. The temperature data may then be input to a microcontroller or other processor 502 (not shown) to indicate and record MDI activation.

4. Force of launch

4.1. Local force peak detection

As shown in FIGS. 40-42, a Force Sensitive Resistor (FSR) or start detector located at the top or bottom of the MDI actuator may be used to determine the force measurement and detect the start of the MDI. As shown in fig. 42, when a force versus displacement of the canister in the actuator is observed, there may be a spike or other signal change at the point of actuation that can be detected using FSR and various algorithms. In addition to FSR, several types of force sensors may be used, including strain gauges, spring displacements, piezoelectric compliance sensors, and the like. As shown in fig. 40, the force sensor 160 is located on a support flange of the rear end assembly 8. In FIG. 41, the force sensor 160 is located on a cap 164, which cap 164 is connected to the rear end assembly by a tether 162 and is secured to the top of the container 28, where it is engaged by the user during actuation of the MDI. The force sensor 160 transmits signals to the computer 500 and the processor 502.

4.2. Threshold of force

Although the certainty is low with a simple force threshold, this approach can also be used instead of a peak detector.

5. Change in capacitance

5.1. One factor affecting the capacitance of the capacitor 106 is the dielectric constant of the material between the two charged surfaces. Assuming that the dielectric constant of the medicinal aerosol is different from that of air, the capacitance change of the integrated capacitor can be used to detect MDI activation. As shown in fig. 43 and 44, the capacitor will have an open air gap that is easily penetrated by aerosol from the MDI. The capacitor may be located at the output as shown in fig. 43, or at the input as shown in fig. 44. The change in capacitance is then monitored using an oscillating circuit or a charge/discharge circuit, and a sudden change in the frequency of the circuit will signal the MDI to start. This can be detected using various software algorithms. The capacitors are in communication with the computer 500 and the processor 502.

6. Displacement of the emission

6.1. Magnetic cap and reed switch

As shown in fig. 45A and 45B, the canister lid 170 is securely mounted on the MDI canister in a position similar to a dose counter and travels with the canister during actuation. The cover has magnetism by embedding a permanent magnet in its structure, and magnetic ink is printed thereon or made of a magnetic material. Within the MDI adapter is a hall effect sensor or reed switch 172. When the MDI canister is depressed to its actuated position, the reed switch closes, which is detected by the software. Using hall effect sensors, the steady state signal can be analyzed, which means that the MDI canister can be bottomed, or the change in X, and the starting point. The sensors are in communication with computer 500 and processor 502.

6.2. Conductive cap and inductor

Similarly to example 6.1, caps are sold with VHC. In this embodiment, the cap has electrical conductivity and is not necessarily magnetic. The oscillating electromagnetic field is generated by an inductor in the chamber that induces a current in the MDI canister lid. As the cap moves closer to the inductor during start-up, a detectable and analytical change in the inductance of the system occurs. Once a plateau in the signal is reached, indicating a canister bottoming, the start can be recorded by software.

7. Pressure detection

When the MDI is activated, its pressurized contents are forced out of the nozzle and into the VHC. As shown in fig. 18, the pressure waves associated therewith may be detected by a pressure sensor 78 placed in the room or near the mouth of the MDI itself. In particular, one or more pressure sensors 78 are disposed on or along an inner surface of a wall in the interior space of the chamber. As shown in fig. 20, the pressure sensor output versus time shows when a start-up occurs, as indicated by a spike.

As shown in fig. 46 and 47, the pressure sensor 78 may be provided at an input end or an output end of the holding chamber in the inner space. The sensor detects and records the differential pressure.

As shown in fig. 48, one or more flow passages 84 are provided adjacent to the support block 86, which has a drain hole 88. Ambient air is brought in through a flow channel that provides a flow path of known resistance. The pressure sensor 78 registers the pressure difference.

As shown in fig. 49 and 50, a restricting hole is formed in the bypass passage. The pressure drop across the restrictive orifice can be detected and recorded by a pressure sensor and then correlated to the flow rate. Various pressure sensors are in communication with the computer 500 and the processor 502.

8. Communication with a smart MDI

8.1 as shown in fig. 78, the MDI may be configured with a dose counter module 90 that has been activated for compliance monitoring purposes and captures dose activation times, counts and totals. Meanwhile, the VHC may be configured with a flow detection module 92 that captures inhalation times, durations, and counts, which communicate using, for example, bluetooth technology. Communications from these devices of the intelligent VHC or its applications can be used to detect and confirm MDI activations and tricks.

As shown in fig. 13, the activation of the MDI is detected by receiving a single from a transmitter 221 placed on top of the MDI canister. Once activated, the transmitter outputs a signal that is received by the intelligent VHC. For example, a piezoelectric disc mounted on the top of the canister, integrated into a dose counter connected to the container, or as a separate element, which when pressed to power the emitter generates sufficient voltage. Several types of transmitters/receivers are possible, including IR LEDs/photodiodes, RF Tx/Rx or tone generators/microphones. The system can also be used to identify the MDI type, depending on the type of Tx/Rx, using different RF frequencies for the controller inhaler/rescue inhaler.

MDI insertion

Providing feedback and confirmation to the user that the MDI has been properly inserted is a necessary function of the intelligent VHC. Additionally, depending on the method used, this function may control when the microcontroller or other processor 502 is in a sleep state, further extending the battery life of the device. For example, when the MDI is plugged in, the microcontroller wakes up the power supply and draws more current from the power supply to power its sensors, displays and communications. Once removed, the microcontroller returns to a low power consumption state.

1. Switch with a switch body

1.1. Limit/contact switch

In this embodiment, limit switches 62 (mechanical) or contact switches are placed in the back end assembly 8 in such a way that the switches close when the MDI is inserted, as shown in figure 19. When the MDI is inserted, the limit switch completes the circuit. The closing of this switch triggers an interrupt in the microcontroller or other processor 502 and allows it to operate in its fully operational state, at which point the user is notified by a visual or audio prompt that the MDI has been fully inserted. When the MDI is removed, the switch is opened, prompting the microcontroller to return to a low power consumption state. In one embodiment, the microcontroller may enter a sleep mode if the device is inactive for a predetermined period of time (e.g., about 30 to 120 seconds). The predetermined time period may be set/programmed by a user.

In addition to the touch switch, and as shown in fig. 11, a button may be used to turn the system on/off. Visual or audible indicators, such as lights and/or alarms, may be implemented using various LEDs, speakers, and tactile and/or visual displays/indicators.

1.2. Reed switch

Similar to example 1.1, and as shown in fig. 74, a portion 200 of the MDI is magnetized with magnetic ink, an electromagnet, or a permanent magnet. When the MDI is inserted, the reed switch 202 closes. As described in 1.1, the closing and opening of this switch has the same result for microcontroller operation and user feedback.

1.3. Conductive path

In this embodiment, as shown in FIG. 75, a portion of the MDI, such as the mouth, has conductive paths 204 that, when inserted into the MDI adapter, complete the circuitry 206 within the electronics of the MDI adapter. This circuit is used to provide feedback to the user and enable the full functionality of the microcontroller as described in 1.1.

2. Light curtain

2.1. As previously described, the light curtain may be used to determine the insertion of the MDI into the MDI adapter. In this embodiment, the LED and photodiode are positioned opposite each other through the MDI adapter opening. When no MDI is inserted, light from the LED can reach the photodiode. Once the MDI is inserted, the light transmission is interrupted, which can be detected by the microcontroller and used to provide audible or visual feedback to the user to ensure that the MDI is properly inserted.

3. Mouth shape detection

3.1. Strain gauge

As shown in fig. 70, strain is introduced in the MDI adapter or back end assembly as the material deforms to conform to the shape of the mouth of the MDI. The amount of strain may be measured using strain gauge 206. Monitoring the strain force of the MDI adapter may provide a means of detecting whether the MDI has been inserted into the MDI adapter. Once the strain reaches a certain threshold, the system may provide feedback to the user to confirm MDI insertion.

3.2. Force sensor Resistor (Force Sensitive Resistor, FSR)

As shown in fig. 72, the force sensitive resistor 208 may be placed on or within the MDI adapter or back end assembly 8. Once the MDI is inserted, the mouth of the MDI applies a force to the FSR that produces a voltage change that is evaluated by the microcontroller. From the signal from the FSR, the insertion of the MDI can be concluded and this information forwarded back to the user.

3.3. Linear action potentiometer

As shown in fig. 69 and 71, the linear action potentiometer 210 may be placed on or within an MDI adapter or back end assembly. Once the MDI is inserted, the potentiometer is shifted, which produces a voltage change that is evaluated by the microcontroller. Based on the signal from the potentiometer, insertion of the MDI can be concluded and this information forwarded back to the user.

3. Image processing

4.1. A camera or series of cameras may be used to determine the extent to which the MDI has been inserted into the MDI adapter. Various image processing algorithms may be used to determine this and once confirmed, this information may be forwarded back to the user.

Power and distribution problem identification

All embodiments require the use of electrical power to achieve the function. Various power sources may be used alone or in combination with other power sources. The sensors and feedback methods can receive power even on individual chamber components.

Power supply

1. Batteries (one or more batteries can be used each)

1.1. Permanent, disposable

The power supply may be such that: once the battery is depleted, the entire electronic device is discarded. The battery will be permanently enclosed within the electronics body, thereby restricting access without damaging the device.

1.2. Replaceable

The power supply may be such that: once the battery is depleted, the user can access the battery compartment and replace the depleted battery with a full battery. This is similar to the batteries of many children's toys or watches.

1.2. Rechargeable battery

The battery may be rechargeable so that once the battery is depleted, the user may simply charge the battery through a DC power jack, USB, or other method. Additionally, the battery may trickle charge throughout its life, which may extend its drain time. Trickle charging refers to charging the battery continuously or periodically with very little current. Separately, this type of charging would take a long time to fully charge a depleted battery, but it is useful to extend battery life, especially when continuously charged.

2. Photovoltaic cell

2.1. The photovoltaic cell generates a voltage in response to the light. This can be used to directly power the device, or to recharge the battery or super capacitor, depending on the power requirements of the sensor and function.

3. Rectifying antenna

3.1. Rectennas use ambient radio frequency energy from radio transmissions, mobile communications, Wi-Fi networks, etc. to induce small currents within the antenna that are rectified and managed in a manner that it can be used to trickle charge a rechargeable power source.

4. Shaking to charge

4.1. Integrating a freely moving magnet within the conductive coil would allow the system to generate a current in the conductive coil when the device is vibrated or the magnet is otherwise forced to move. The movement of the magnet induces a current in the coil that can be used to charge a battery or other power source.

Distribution of

Preferably, all electronic components are close to each other to make power distribution easier to manage. However, this may not be possible in view of the requirements of the device. In the case where some electronics are installed in the MDI adapter and others are installed towards the mouth or mask adapter, there are some power distribution strategies.

1. Conductive path along the body

1.1. This method uses only one power source (e.g., a battery) located in the mouth/mask adapter or MDI adapter, the power of which is transferred through the body to the other component. In each case, the contacts at both ends of the body ensure that power is reliably transmitted to the other components. The contacts are formed in a manner that still allows assembly and disassembly of the device for cleaning while providing a repeatable and secure connection on each component. These conductive paths are also used for data communication between the front-end hardware and the back-end microcontroller.

1.1.1 conductive resin

The conductive resin may be used to mold the conductive vias directly into the body assembly. This would be accomplished by a two-shot or insert molding manufacturing method.

1.1.2 conductive inks

The conductive ink may be used to form the conductive path and may be pad printed or screen printed onto the body.

1.1.3 Flexible electronics and adhesive

A flexible low profile line may be used and the lines may be secured to the body by use of an adhesive.

2. Double batteries for wireless communication

2.1. The hardware at the mouth/mask adapter end of the VHC may be powered by a power source (e.g., a battery) that is completely separate from the power source at the MDI adapter end of the VHC. Each end of the chamber may require its own microcontroller or other processor 502 to process inputs and outputs located at those respective ends. In this case, the two microcontrollers are likely to need to communicate to share data. This may be done via bluetooth or other means.

MDI identification

The identification of the MDI provides assurance to the patient, prescriber and payer that an approved medication regimen is also being complied with. In addition, it can be used to alert the patient whether the wrong medication has been inserted into the chamber, which can help prevent overdosing and underdosing of a particular medication. The following identification methods may be used alone or in combination to confirm the MDI.

For example, and as shown in FIG. 13, the photodiode 222 and color detector sensor 224 or MDI identifier may be disposed on the exterior surface of the chamber housing wall, or on the rear end assembly, and toward the MDI, including the actuator activator and container. A unique tag 226 is attached to each MDI, or a unique rescue tag may be attached to the rescue MDI and a unique controller tag attached to the controller MDI. A sensor 224 (e.g., a color detector sensor) detects the presence of the label to identify each particular MDI or to identify each MDI by category, such as rescue or controller. The labels may be configured with different colors, barcodes, magnetism, surface characteristics, such as reflection/absorption, etc.

Color sensing of MDI actuators

1.1. Colour of mouth

As shown in FIG. 68, the MDFs have a variety of different colors, some having two colors to distinguish the mouth from the handle. Color sensing may be used to help identify an MDI inserted into an MDI adapter by obtaining a specific color code reading (e.g., RGB, CMYK, la). When the MDI is inserted into the adapter, color sensing hardware or sensors 224(MDI identifiers) are triggered to collect color information from the mouth of the MDI. The color codes are then analyzed by the software and compared to the MDI database and their respective color codes. Various algorithms may be used to make the comparison and use the closest match for the MDI identity. Alternatively, the MDI activator color code may be used as an input to a multi-factor algorithm that uses several inputs to identify the MDI.

1.2. Color of handle

As shown in fig. 68, similar to mouth color sensing, but instead of providing a color sensor 224 to obtain a mouth color code, it is provided to analyze the color of the handle portion of the MDI actuator.

1.3. Mouth color and handle color

The combination of 1.1 and 1.2 helps to distinguish between two-color MDI actuators.

2. Color sensing of aerosol plume

2.1. There are many specifications in all MDIs, which may be reflected in different color codes of the aerosol plume. Color sensing hardware is placed near the mouth of the MDI activator within the MDI adapter and during MDI activation, the color code of the aerosol plume is collected and compared to a database of various MDIs. Various comparison algorithms may be used, with the closest match being used for MDI identification. Alternatively, the aerosol color code may be used as an input to a multi-factor algorithm that uses several inputs to identify the MDI.

3. Mouth shape detection

3.1 Force-Sensitive Resistors (Force Sensitive Resistors, FSR)

As shown in fig. 72, the FSR 208 is placed in the MDI adapter so that during MDI insertion, the resistor is compressed in that particular direction by an amount proportional to the size of the MDI mouth, causing its signal to change accordingly. The resistance value is compared to the MDI in the database. Various comparison algorithms may be used, with the closest match being used for MDI identification. Alternatively, the resistance value may be used as an input to a multi-factor algorithm that uses several inputs to identify the MDI.

3.2 Strain gauge

As shown in fig. 70, the MDI adapter port is intentionally undersized so that it must stretch when inserted into the MDI. The total strain detected by the strain gauges 208 and the locations of high and low strain may be analyzed and compared to a database of different MDIs and their strain values to help identify the MDI.

3.3. As shown in fig. 69 and 71, and the linear action potentiometer 210, similar to the FSR method, is adjusted by linear motion according to the size of the MDI mouth in a particular direction. The resistance values collected by the system at the time of MDI insertion are compared to the values stored in the database for the various MDIs. These potentiometers have a biasing spring to return to their original position when the MDI is removed.

4. Length of mouth

4.1. Tactile or sliding potentiometer

The length of the mouth portion of the MDI may be used as a distinguishing factor.

After full insertion of the MDI adapter, the length of the mouth may be measured by tactile or sliding potentiometer and compared to various lengths stored in the system database, as shown in fig. 69.

5. Resistance to flow

5.1. Resistance to flow

As shown in fig. 54 and 55, the flow through the chamber may be monitored by various sensors, as disclosed herein. This flow may be used to help identify the MDI. Using this flow information in combination with data from the differential pressure sensor 78, the pressure at the mouth of the MDI is compared to atmospheric pressure, and a plot of pressure versus flow for the MDI can be collected. Comparing this curve with the curves in the MDI database, a match can be found which can identify the MDI. Alternatively, the resistance distribution may be used as an input to a multi-factor algorithm.

6. MDI Sound at specific flow Rate

As shown in fig. 24-28, the audio interface includes an equalizer circuit (e.g., 7-band) that divides the audio spectrum into seven frequency bands, including, for example, but not limited to, 63Hz, 160Hz, 400Hz, 1kHz, 2.5kHz, 6.25kHz, and 16 kHz. These seven frequencies are peak detected and multiplexed to the output to provide a representation of the amplitude of each band. The microcontroller processes these bands to average them to a single amplitude (dB) versus time signal (fig. 25). The unique sounds produced by the different frequency bands MDF may then be compared to stored known sounds in a memory or cloud database. Using normalized correlation, the input sound can be compared to a reference sound with higher certainty. The activation sound is captured and stored at the MDI activation and the comparison and determination can be processed after the treatment to free up processing power for other VHC tasks during or during the treatment depending on the available processing power. If the process is fast enough, the MDI activation can be analyzed in real time and feedback provided as to whether the MDI nozzle or support block is clogged or partially clogged due to the low or insufficient sound produced. The feedback may also include information as to whether the MDI needs to be shaken and/or primed, or checked for sufficient remaining dose counting.

6.1. A database may be generated containing the frequency spectrum or dominant frequency of all MDIs at a particular flow rate. In use, when this flow rate is reached, sound is sampled by the microphone and compared to a sound profile stored in the system database. Various algorithms may be used to make this comparison.

7. MDI Sound at Start

7.1. A database may be generated containing the frequency spectrum or dominant frequency of all MDI initiating sounds. When a start-up occurs, the recorded sounds are quantitatively compared to sounds stored in the system database and the closest match is determined.

8. MDI sound at knock

8.1. A database may be generated that contains the frequency spectrum or dominant frequency of all MDI sounds at the time of tapping or hammering. Upon insertion into the MDI adapter, the mechanical hammer is triggered so that it strikes the MDI in the mouth region. The sound produced depends on the shape, volume, stiffness of the MDI actuator and its fit to the MDI adapter. This sound can then be quantitatively compared to the sounds in the system database.

9. Image processing

9.1 reading tags

Text recognition software is used to "read" the text on the MDI actuators and/or MDI canisters. For example, and as shown in FIG. 4, a camera 35 or other image sensor (MDI identifier) is mounted on the chamber housing, for example, adjacent to or anywhere in between its inputs or outputs. The image sensor may also be connected to a mouth assembly or a back end assembly. The camera or image sensor captures an image of the MDI including various textual information presented on the label 240 connected to the container and/or the actuating member. Image processing algorithms and/or machine learning techniques may be used to extract textual information, unique shapes and/or unique features that reveal the type and identity of the MDI associated with the VHC. The captured image may further be stored in memory and compared to different types of MDFs in a database to narrow the selection. As shown in fig. 5A, 5B and 6, the camera or image sensor captures an image of the MDI and converts it to a grayscale image 242 as shown in fig. 5B. The processor then extracts a plurality of templates (e.g., three) from the captured grayscale image and compares the templates/images to the images stored in the database. Referring to label 244, the processor correctly identifies the MDI, as shown in figure 6.

9.2. Combining colour, shape

The digital image or series of digital images is analyzed for color and shape and compared to the color and shape of the various MDIs in the database.

9.3. Feature identification

The image kernel may be used to scan the image for similarity to the kernel itself. For example, a kernel in the form of a GSK tag may be used to identify GSK triggers by calculating the correlation product for each location of the kernel on the image and checking if the correlation coefficient exceeds a certain threshold indicating a good match.

10. Spectroscopic drug ID

10.1 Single wavelength Infrared/ultraviolet

Infrared and ultraviolet spectroscopy are methods used to determine the chemical structure and composition of a sample. All chemicals absorb infrared and ultraviolet radiation to some extent and, depending on the bonds present in their chemical structure, will absorb some wavelengths of light more than others. Using a light source of controlled wavelength, the absorption of a drug at that particular wavelength can be analyzed by shining light through the aerosol onto a light detector. This absorbency can then be compared to values in the MDI database.

10.2 Multi-wavelength Infrared/ultraviolet

Similar to 10.1, except that multiple wavelengths may be used.

11. Force of launch

11.1. Using a Force Sensitive Resistor (FSR), the force at the start of the MDI can be determined. This would need to be combined with MDI start-up detection, as described herein. Once MDI activation is detected, the force is recorded and compared to values stored in the MDI database.

12. Temperature of Aerosol (Aerosol/air temperature or contact Evaporation)

12.1. Single point

The temperature may be monitored at a fixed distance from the MDI, and using the temperature detected during the start-up of the MDI, this information may be compared to the temperatures stored in the system MDI database. Although the same propellant line (HEA 134a or HFA 227) was used for all MDIs, the temperature difference of the aerosol was seen at a fixed distance from the MDI due to the different pharmaceutical formulations.

12.2. Temperature and distance

Further to example 12.1, several temperature sensors may be used at a fixed distance from the MDI to collect the temperature profile during the start-up of the MDI. This temperature profile can be used and compared to a configuration file in the system database.

13. RFID on MDI from vendors

13.1. As shown in fig. 73, a Radio Frequency Identification (RFID) tag or label 252 may be adhered or molded to the MDI of the manufacturer or supplier of the medication. In this case, it is possible to read the RFID tag on the MDI with the RFID reader 250 within the MDI adapter or connected to the backend component 8 or other component of the VHC.

14. RFID on dose counter (Integrated or OEM)

14.1. Similar to example 13.1, the RFID tag may be integrated into an integrated module or dose counter module, and these may be read with an RFID reader integrated with the chamber.

15. Label placed on MDI by user

15.1 RFID

Similar to example 13.1 and example 14.1, the RFID tag can be read from an MDI. In this embodiment, the RFID is presented in the form of a sticker, adhesive patch, or other form placed on the MDI by the user.

15.2 Bar code (ID and 2D)

Similar to example 15.1, except that a bar code can be used instead of RFID. The chamber then includes a bar code scanner instead of an RFID reader.

16. Accessing patient drug lists on the cloud

16.1. Bluetooth/Wi-Fi access

The user's digital medical records may be accessed over the internet and their MDI medication order may be used to help identify the MDI used with the VHC. Additionally, to ensure security, the healthcare provider or payer may initialize the user's ' profile ' and select their MDI drugs, which will then be transmitted to the VHC via bluetooth or Wi-Fi.

17. Communication with an intelligent inhaler

17.1. Bluetooth communication/Wi-Fi communication

Smart inhalers have been used to track compliance of MDIs. Communication with these inhalers will enable the VHC to directly identify the MDI being used. This may be done via bluetooth or Wi-Fi communication.

18. User manual selection

18.1 Manual selection

As shown in fig. 19, the user input buttons 260, for example, have different colors, shapes or markings. The user 66 will press an appropriate button, for example, blue in relation to the rescue MDI, or red in relation to the controller MDI. Pressing the combination of these two buttons will convey the MDI combination being used. Each button may also have a visual indicator, such as a light, that illuminates or remains illuminated when pressed for a preset period of time (or until the treatment is complete). If an error indication is displayed, it provides a user with indicia to restart. A single button may also be used, where a button press is associated with one of the rescue MDI or the controller MDI and no button press is associated with the other type of MDI. In viewing the patient usage data, the prescriber will know which type of medication is associated with each of the rescue MDF and the controller MDF. Additionally, the user may enter medication information through an application on the computer, such as in a user profile setting. The user may share the recorded medication activity with the prescriber and/or the payer.

The user may be provided with the option of manually selecting the MDI that is in progress. This may be done at each dose, or the user may specify a list of medications at the time of receipt of the smart room. For users with only one prescription medication, the latter approach may help in determining to identify the MDI used each time, while for users with multiple medications this will be used to briefly list possible MDI candidates, which then requires the system to use the apparatus described in other embodiments for further identification.

19. Capacitance/dielectric constant detection

19.1. Dielectric constant detection

The two oppositely charged features are separated by an air gap forming an open capacitor. Upon actuation of the MDI, the air gap is permeated by the aerosol. Assuming that the aerosols have dielectric constants different from each other, the capacitance change of the open capacitor can be measured and the capacitance value can be matched to the capacitance value in a database of known aerosols and used to identify the MDI.

Resonance frequency of MDI

20.1. A sound generator is located within the VHC to generate a series of frequencies in a scanning manner. When the sound generator generates the resonant frequency of the MDI, a volume spike may occur that is detectable by the microphone.

Infrared reflection of MDI actuators

21.1. Infrared "signatures" may be generated for various MDIs using Infrared (IR) emitters and IR detectors. The IR emitters and detectors and their locations may be the same as the white LEDs and color sensors discussed above and shown in the figures. The IR radiation is directed at the mouth and/or handle portion of the MDI actuator and the amount of radiation absorbed/reflected is used to identify the MDI. In particular, in this embodiment, the amount of radiation reflected is detected by an IR detector and this value is compared with the values present in the pre-recorded MDI database. The material, shape and surface finish of the MDI actuators all play a role in the amount of IR radiation reflected. A single wavelength IR LED/detector may be used, or several IR LEDs/detectors with different IR wavelengths may be used.

Mask force and seal feedback

The face mask 600 is often used when delivering respiratory medicaments to a user. For example, the mask may be connected to the mouth assembly 12 or output end of the VHC 3. To maximize drug delivery, it is important to ensure that a proper seal is formed between the mask and the user's face 602. An appropriate seal may be determined by measuring the force applied to the mask, VHC or other delivery device (e.g., nebulizer or OPEP device), or by recording contact between the mask and the user's face.

In one embodiment, as shown in fig. 29, a drug delivery system comprises a drug delivery device, such as a VHC, having an input 10 and an output 14. The mask 600 is connected to the output. The mask and delivery device are movable along the longitudinal axis 6 to a position engaging the face 602 of the user. The force sensor 604 is arranged between the face mask 600 and the input 10 of the drug delivery device. For example, the force sensor 604 may be mounted between the mask 600 and the valve assembly 12 (e.g., mouth assembly), or between the valve assembly 12 and the chamber housing 2. The force sensor 604 may be a load cell that converts mechanical deformation or displacement into an electrical signal via a strain gauge, or a piezoelectric sensor that converts a change in force into an electrical change via the piezoelectric effect. The force sensor transmits signals to the computer 500 and processor 502, which may be mounted on the back end assembly 8, for example. The VHC microcontroller monitors the applied force and provides feedback to the user or caregiver operating the delivery device to increase, decrease or maintain the applied force. For example, the force required to achieve the desired seal may be between 1.5 and 7 pounds. The feedback to the user includes an indicator, whether a visual indicator 40 (e.g., an LED), an audible indicator (speaker), or a vibratory indicator. The force sensor 604 is responsive to a force applied to the mask along the longitudinal axis by the drug delivery device. The indicators each provide feedback to the user as to the amount of force applied to the mask, whether too little or too much, and/or not uniform around the perimeter.

In another embodiment, as shown in fig. 30 and 31, contact sensors 608 and 610 may be integrated into mask 600 to monitor, sense and signal proper contact of the user's face around the perimeter of the mask. For example, the mask is configured with a seal portion 612 adapted to engage the face 602 of the user. The seal portion 612 may include a turned-in C-shaped lip terminating in a free end 615. One or more sensors 608 are connected to the seal, wherein the force sensors are responsive to a force applied to the seal edge. In one embodiment, as shown in fig. 30 and 31, a plurality of sensors are embedded in the seal and distributed in spaced apart relation around the perimeter of the mask or the length of the seal. In an alternative embodiment, as shown in FIG. 30, the sensor 610 comprises a continuous strip extending around the sealed edge.

As shown in fig. 30 and 31, the indicator 616 is in communication with the sensor and is adapted to provide feedback to the user as to the amount of force applied to the sealing edge or whether contact has been made with the user's face. For example, the indicator may comprise a visual indicator, an audible indicator, or a vibratory indicator. In one embodiment, the visual indicator includes a plurality of lights 616 (e.g., LEDs) distributed and spaced along the perimeter of the sealing rim or mask. In one embodiment, a plurality of visual indicators are associated with the plurality of sensors, respectively, and are directly connected to the plurality of sensors.

In operation, and as shown in fig. 32 and 33, a user or caregiver applies a force to the mask 600, engages the user's face 602 with the mask's sealing edge 612, senses the force applied to the mask, or alternatively, makes contact at a particular location on the sealing edge, and provides feedback to the user regarding the applied force and/or contact via an indicator 616. The user/caregiver can then adjust the force applied to the mask. In one embodiment, the feedback would be the illumination of a light 616 that is connected to the contact sensor 608 and the contact sensor 610 that detects contact, and the light would not illuminate if no contact is detected. Similarly, portions of the indicator lights may illuminate when a different force sensor has detected that sufficient force has been applied and lights not along the mask portion do not illuminate when the applied force is insufficient. In other embodiments, the lights may be illuminated in a different color, or turned off, if the applied force is excessive.

Once activated, a controller (which may be implemented to include one or more computer 500 elements, such as processor 502 (fig. 83)) may analyze the output of the force sensor or contact sensor and estimate the quality of the seal. Combining the measurement of the applied force and the measurement of the contact with the user's face allows the device to provide information on whether a sufficient seal is formed.

Movable valve

When using various drug delivery devices, such as VHC, slow inhalation (max <30L/min) followed by breath holding, the deposition of the drug in the lungs can be significantly improved. Although various hearing aids are available to provide feedback to the user that the inhalation rate is too high, they are passive and do not control the rate. Thus, it may be misinterpreted or confused with positive feedback (e.g., rapid inhalation to make the whistle sound good, rather than the intended feedback of the sound should be avoided).

As shown in fig. 34-37, one embodiment of the valve 700 actively adjusts the resistance to opening or closing during inhalation (or exhalation) in order to actively control the inhalation or exhalation rate. The system may also provide feedback to the user that the valve is actively controlling the flow so that the user can adjust the flow rate.

The valve may be configured in various forms, including an annular valve as shown in fig. 35 and 36, as a duckbill valve 720 as shown in fig. 87, or as other valves having movable, bendable, or deformable features. The annular valve includes a central opening 702 and an annular flange 704, the annular flange 704 being bent or deformed outwardly such that the flange is lifted from a valve seat 706, thereby allowing flow through the opening 702. The duckbill valve 720 has a pair of opposing flaps 722 that open to form an opening in response to flow therethrough. The valve may be made of Liquid Silicone Rubber (LSR).

The actuator portion 730 is applied to or embedded in the valve. For example, the actuator portion may be made of an electroactive polymer (EAP). When stimulated by an electric field, the LSR portion becomes stiffer and resists opening. In one embodiment, the annular flange 704 of the valve is configured with a plurality of EAP strips 732 (four shown). Other configurations, including more or fewer strips, or differently shaped portions, are also suitable. In another embodiment, at least one tab 722, and in one embodiment two tabs, of the duckbill valve 720 is configured with an embedded electroactive polymer actuator portion 730, such as a strip. It should be understood that the actuator portion or EAP feature may also be applied to the exhalation portion 731 of the exhaust valve or valve.

The VHC or other drug delivery device has a housing 2 and a housing 12 defining a flow channel 701. Valves 700 and 720 are disposed in the flow channels. The valve is movable between a first configuration and a second configuration, e.g., opened and closed (fully or partially) in response to flow through the flow channel. The flow may be inhaled or exhaled. In response to a stimulus, such as an electrical stimulus, the valve may be reconfigured between a first condition and a second condition. For example, the first and second conditions are first and second stiffnesses, or resistance to bending and/or deformation. The valve has a first resistance to movement, such as bending or deformation, between the first configuration and the second configuration when the valve is in the first condition, and a second resistance to movement between the first configuration and the second configuration when the valve is in the second condition, wherein the first resistance is less than the second resistance. Actuator 708 applies an electrical stimulus.

In operation, a flow is generated through the flow channel of the housing, for example by inhalation or exhalation by the patient. In response to flow through the flow channels, the flow causes the valves 700 and 720 to move between the first configuration and the second configuration. Based on the flow rates calculated by the various sensors and methods described elsewhere in this application, the actuator 708 may be instructed to apply a stimulus (e.g., electricity) to the valve as shown in fig. 34. In response to the stimulus, the valve is reconfigured from the first condition to a second condition. When the valve is reconfigured to the second condition, e.g., greater resistance to bending or deformation occurs, the flow through the passageway is altered, e.g., restricted or increased, so that the opening formed by the valve, or the opening between the valve and the valve seat, is restricted or kept smaller.

As shown in fig. 37, the valve may be actively managed such that the sensed and detected flow rate through the valve as described above does not exceed a predetermined threshold, such as 30L/min.

In any of the above embodiments of the smart device, the controller or other processing element in communication with or controlling the sensor, meter or switch may be integrated into the smart device itself, disposed on or remote from the smart device itself. It should be understood that various sensors, meters, or switches may be used for multiple functions, and may be used in various combinations, all of which are in communication with a controller or other processing element. Additionally, for any of the intelligent devices described above, some or all of the data collected by the sensors, switches or meters, as well as feedback provided to the user of the device, may be sent to a remotely located caregiver at the same time. Remotely located caregivers or monitoring facilities may intervene to provide further advice or information during treatment. Alternatively, the data and feedback sent to the caregiver or monitoring facility in parallel with the user may be stored remotely for later evaluation by a medical professional. Parallel transmission to the remote information source, including sensing data and any feedback, may also prevent problems tampering with or damaging the data stored on the smart device itself.

In various embodiments of the smart devices described herein, the battery or other power source for any of the controller circuitry, sensors, meters, and switches may be rechargeable or removable. To minimize battery drain, some sensors may be configured for a predetermined sampling frequency rather than a continuous measurement mode. Also, the circuitry on the smart device may only activate when a particular event is detected, and may automatically shut down after a predetermined period of time from the initial touch initiation or after sensing an idle period of the device.

Although the present application has been described with reference to preferred embodiments, workers skilled in the art will recognize that changes may be made in form and detail without departing from the spirit and scope of the invention. It is, therefore, intended that the foregoing detailed description be regarded as illustrative rather than limiting, and that it is the appended claims, including all equivalents thereof, which are intended to define the scope of the invention.