JP2018000271A - Inhalation device and inhalation state presentation system - Google Patents

Abstract

To easily learn a method for inhaling dry powder. An inhaler includes a detection unit and a transmission unit. A detection part detects the flow velocity of the air which flows in from the inlet of a pipe | tube and flows out to the exit of a pipe | tube by the negative pressure by human respiration. The transmission unit transmits information based on the flow velocity detected by the detection unit. [Selection] Figure 1

Description

  The present invention relates to an inhaler and an inhalation state presentation system.

  Conventionally, a dry powder inhaler for introducing a dry powder such as a drug into the human body is known (for example, Patent Document 1).

JP-T-2002-524107

However, there is a problem that it is difficult to learn a method for inhaling dry powder, and inhalation by an appropriate method may not be performed.
An object of the present invention is to provide an inhaler and an inhalation state presentation system that can facilitate the learning of a method for inhaling a dry powder.

  In one embodiment of the present invention, a detection unit that detects a flow rate of air that flows in from an inlet of a tube and flows out to the outlet of the tube due to negative pressure due to human breathing, and transmits information based on the flow rate detected by the detection unit An inhaler including the transmitter.

  In the inhaler according to one aspect of the present invention, the detection unit includes a sound generation unit and a sound collection unit, and the sound generation unit has a sound having an attribute according to the flow velocity of the air flowing from the inlet. The sound collection unit collects the sound produced by the sound production unit, and the detection unit detects the flow velocity based on the attribute of the sound collected by the sound collection unit. .

  In the inhaler according to one aspect of the present invention, the information transmitted by the transmission unit is information indicating the flow velocity detected by the detection unit.

  Moreover, in the inhaler of one embodiment of the present invention, the frequency band of the sound is outside the human audible range.

  The inhalation device according to one aspect of the present invention includes a charge suppression unit that suppresses electrostatic charge in a region of the tube through which the air passes.

  In the inhaler of one embodiment of the present invention, the tube is configured by a plurality of members being detachably combined.

  The inhalation device according to one aspect of the present invention further includes an inclination detection unit that detects the inclination of the tube based on the flow velocity detected by the detection unit and inclination information indicating the inclination of the tube with respect to a horizontal axis. The transmitting unit further transmits information based on the tilt information detected by the tilt detecting unit.

  The inhalation device according to one aspect of the present invention further includes a respiration frequency determination unit that determines the number of times the human has breathed based on the flow velocity detected by the detection unit, and the transmission unit further includes the respiration The respiratory frequency information indicating the frequency determined by the frequency determination unit is transmitted.

  The inhalation device according to one aspect of the present invention further includes a breathing timing determination unit that determines a timing at which the person breathes based on the flow velocity detected by the detection unit, and the transmission unit further includes the breathing Respiration timing information indicating the respiration timing determined by the timing determination unit is transmitted.

  One aspect of the present invention is an inhalation state presentation system including an inhaler and a display device that displays information based on the flow velocity output from the communication unit.

  According to the present invention, it is possible to provide an inhaler and an inhalation state presentation system that can facilitate the learning of a method for inhaling dry powder.

It is a figure which shows an example of the external appearance structure of an inhalation state presentation system. It is a figure which shows an example of the relationship between the chemical | medical agent sprayed from an inhaler, and the flow of the air which flows through an inhaler. It is a figure which shows an example of a function structure of an inhalation state presentation system. It is a figure which shows an example of the characteristic of a sound generation part. It is a flowchart which shows an example of operation | movement of an inhaler. It is a figure which shows an example of the screen which displays the information based on the flow velocity which a display part and a portable terminal display. It is a figure showing an example of composition of an inhalation device concerning an embodiment. It is a figure which shows an example of the division | segmentation form of the inhalation device which concerns on embodiment. It is a figure which shows an example of a function structure of an inhalation state presentation system. It is a figure which shows an example of the flow velocity information which a display part and a portable terminal display. It is a figure which shows an example of the inclination which an inclination detection part at the time of respiration detects.

[First Embodiment]
[External configuration of inhalation state presentation system 1]
The inhalation state presentation system according to the first embodiment will be described below with reference to the drawings.
With reference to FIG.1 and FIG.2, the external appearance structure of the inhalation state presentation system 1 which concerns on 1st Embodiment is demonstrated.
FIG. 1 is a diagram illustrating an example of an external configuration of the inhalation state presentation system 1. The inhalation state presentation system 1 includes an inhaler 10 and a display unit 11.
The inhaler 10 includes a detection unit 12, an inlet unit 13, an outlet unit 14, and a transmission unit 104. The inhaler 10 is coupled to the nebulizer 3. The nebulizer 3 is, for example, a pressurized metered dose inhaler (pMDI; pressurized Metered Dose Inhaler). The nebulizer 3 sprays the medicine into the tube of the inhaler 10 according to human operation.
The detection unit 12 detects the flow velocity of air that flows into the suction pipe from the inlet 13 and flows out to the outlet 14 due to negative pressure due to human respiration.
In the following, when it is necessary to indicate the positional relationship of each part, an explanation is given using an XYZ three-dimensional orthogonal coordinate system. In the XYZ orthogonal coordinate system, the X axis is an axis parallel to the direction in which the sprayer 3 sprays the medicine. The Z-axis is an axis parallel to the vertically upward direction when the inhaler 10 is in use. The Y axis is an axis orthogonal to the X axis and the Z axis. The positional relationship between each shaft and each part of the inhaler 10 shown here is an example, and the present invention is not limited to this. The suction pipe axis of the suction device 10 is arranged parallel to the X axis. That is, in this example, the direction of the axis of the inhalation tube of the inhaler 10 is parallel to the direction in which the nebulizer 3 sprays the medicine.

The transmission unit 104 transmits information based on the flow velocity detected by the detection unit 12.
The display unit 11 acquires and displays information based on the flow velocity transmitted from the transmission unit 104.
The mobile terminal 2 includes a receiving unit 204 and a mobile terminal display unit 211. The receiving unit 204 acquires information based on the flow rate transmitted from the transmitting unit 104. The mobile terminal 2 displays information based on the flow rate acquired by the reception unit 204 on the mobile terminal display unit 211.
Details of each piece of information shown here will be described later.

FIG. 2 is a diagram illustrating an example of the relationship between the medicine MF sprayed from the sprayer 3 and the air flow AF flowing through the inhaler 10.
The medicine MF sprayed from the nebulizer 3 into the suction pipe of the inhaler 10 is diffused from the negative side of the X axis toward the positive side of the X axis in the suction pipe. The drug MF diffused in the inhalation tube stays in the inhaler 10. When suctioned by human breathing with the outlet 14 held by a human mouth, negative pressure is generated in the suction pipe. The air outside the suction pipe flows into the suction pipe from the inlet 13 due to the negative pressure generated by the human suction. The air that has flowed into the suction pipe flows out from the outlet portion 14 due to negative pressure generated by human suction. At this time, an air flow AF from the inlet portion 13 toward the outlet portion 14 is generated in the inhaler 10. The drug MF in the suction pipe moves to the outlet portion 14 by the air flow AF. The drug MF that has moved to the outlet 14 is sucked into the human mouth by the air flow AF2 from the outlet 14 toward the human mouth. At this time, if the flow velocity or flow rate of the air flow AF satisfies a predetermined condition, the drug MF efficiently reaches the human lung.

  By the way, it may be difficult for a human to understand whether or not the flow rate and flow rate of the air flow AF in the inhalation tube satisfy a predetermined condition for the drug MF to efficiently reach the human lung. . Therefore, the inhalation state presentation system 1 of the present embodiment indicates whether or not the medicine MF satisfies a predetermined condition for efficiently reaching the human lung by presenting the flow rate and flow rate of the air flow AF. Provides information for judgment. Hereinafter, a specific functional configuration of the inhalation state presentation system 1 will be described.

[Functional configuration of inhalation state presentation system 1]
Next, an example of a functional configuration of the inhalation state presentation system 1 will be described with reference to FIG.
FIG. 3 is a diagram illustrating an example of a functional configuration of the inhalation state presentation system 1.
The inhalation state presentation system 1 includes an inhalation device 10 and a display unit 11.
The inhaler 10 includes a detection unit 12 and a transmission unit 104.

The detection unit 12 includes a sound generation unit 101, a sound collection unit 102, and a calculation unit 100.
The sound generation unit 101 generates a sound having an attribute corresponding to the flow velocity of air flowing from the inlet unit 13. Here, the attribute according to the air flow rate includes a volume according to the air flow rate and a frequency according to the air flow rate. In this example, the sound generation unit 101 generates a sound S having a magnitude corresponding to the air flow rate. In addition, the frequency of the sound S generated by the sound generation unit 101 can be set to a frequency outside the human audible range.
The sound collection unit 102 collects the sound S generated by the sound generation unit 101. The sound collection unit 102 outputs the collected sound S as volume information SV. Here, the volume information SV is information indicating the loudness of the sound collected by the sound collection unit 102. That is, the sound collection unit 102 outputs information indicating the magnitude of the collected sound S and volume information SV.

The calculation unit 100 includes a CPU (Central Processing Unit), and includes a flow velocity calculation unit 103 as its functional unit.
The flow velocity calculation unit 103 acquires the volume information SV output from the sound collection unit 102. The flow velocity calculation unit 103 calculates flow velocity information SFD based on the volume information SV. Here, the relationship between the volume information SV and the flow velocity information SFD will be described with reference to FIG.
FIG. 4 is a diagram illustrating an example of characteristics of the sound generation unit 101. As described above, the sound generation unit 101 generates a sound having a volume corresponding to the flow velocity AF of the air in the suction pipe. The sound collection unit 102 outputs volume information SV according to the volume of the collected sound. Here, the magnitude of the sound collected by the sound collection unit 102 corresponds to the flow velocity AF of the air in the suction pipe.
The flow velocity calculation unit 103 calculates the flow velocity information SFD based on the volume information SV and the relationship between the volume information SV and the flow velocity information SFD illustrated in FIG. The flow velocity calculation unit 103 outputs the calculated flow velocity information SFD.
As an example, when the sound collection unit 102 outputs the volume information SV1, the flow velocity calculation unit 103 calculates the flow velocity information SFD1 based on the volume information SV1 and the relationship between the volume information SV and the flow velocity information SFD illustrated in FIG. .
That is, the detection unit 12 detects the flow velocity of air that flows in from the inlet of the suction pipe and flows out to the outlet of the suction pipe due to negative pressure due to human breathing.
When the inhaler 10 includes a storage unit (not shown), the flow velocity calculation unit 103 may store the calculated flow velocity information SFD in this storage unit.

The transmission unit 104 acquires the flow rate information SFD calculated by the flow rate calculation unit 103. The transmission unit 104 transmits information. The information transmitted by the transmission unit 104 is information indicating the flow velocity detected by the detection unit 12. Here, the information indicating the flow velocity detected by the detection unit 12 is, for example, the flow velocity information SFD. That is, the transmission unit 104 transmits the acquired flow velocity information SFD. The transmission unit 104 includes, for example, a digital input / output port such as a USB, an Ethernet (registered trademark) port, an infrared communication port, a Bluetooth (registered trademark) port, and the like, and includes other components including the display unit 11 and the portable terminal 2. Communicate with the device. In the following description, the transmission unit 104 converts the flow velocity information SFD into a radio signal and transmits the converted radio signal. Note that the transmission unit 104, the display unit 11, and the portable terminal 2 may be connected by wire. In this case, the transmission unit 104 transmits the acquired flow velocity information SFD as an electrical signal.
The display unit 11 and the mobile terminal 2 receive the flow rate information SFD. The display unit 11 and the mobile terminal 2 generate and display an image based on the received flow velocity information SFD. The display unit 11 and the mobile terminal 2 may store the received flow velocity information SFD in storage units (not shown) provided in the display unit 11 and the detection unit 12 respectively.

[Outline of operation of inhaler 10]
Next, the outline of the operation of the inhaler 10 will be described with reference to FIG.
FIG. 5 is a flowchart showing an example of the operation of the inhaler 10.
The sound generation unit 101 generates a sound S having a volume corresponding to the flow velocity of air generated by the negative pressure due to human breathing (step S110). The sound collection unit 102 collects the sound S generated by the sound generation unit 101 (step S120). The sound collection unit 102 outputs volume information SV based on the collected sound S. The flow velocity calculation unit 103 calculates the flow velocity information SFD based on the volume information SV (Step S130). The flow velocity calculation unit 103 outputs the calculated flow velocity information SFD. The transmission unit 104 acquires the flow velocity information SFD. The transmission unit 104 transmits the acquired flow velocity information SFD (step S140).

Next, an example of a screen displayed on the display unit 11 or the mobile terminal 2 will be described with reference to FIG.
FIG. 6 is a diagram illustrating an example of a screen that displays information based on the flow velocity displayed on the display unit 11 or the mobile terminal 2.
FIG. 6 is a graph in which time is plotted on the horizontal axis and the flow velocity of air generated by negative pressure due to human respiration is plotted on the vertical axis. The display unit 11 or the portable terminal 2 stores a flow rate suitable for inhaling the medicine MF as the threshold Th1. The flow rate suitable for inhaling the medicine MF means that the display unit 11 or the portable terminal 2 draws a line L1 at a flow rate corresponding to the threshold Th1. The display unit 11 or the portable terminal 2 renders the flow velocity information SFD received together with the line L1 according to the time when it is acquired. The display unit 11 or the mobile terminal 2 may draw the portion where the flow velocity exceeding the threshold Th1 is detected with a color different from the color of the portion where the flow velocity below the threshold Th1 is detected.
In addition, when the inhaler 10 includes a storage unit, the threshold Th1 may be stored in this storage unit. In this case, the transmission unit 104 of the inhaler 10 transmits the flow rate information SFD and the threshold value Th1 to the display unit 11 or the mobile terminal 2.

  As described above, the inhalation state presentation system 1 generates the sound generation unit 101 that generates sound with an attribute corresponding to the flow rate, and the flow rate calculation unit 103 that calculates the flow rate based on the sound attribute generated by the sound generation unit 101. With. Thereby, the inhaler 10 detects the flow velocity of the air that flows in from the inlet portion 13 and flows out to the outlet portion 14 due to negative pressure due to human breathing. Therefore, according to the inhaler 10, the flow rate of air when a human inhales the medicine MF in the inhalation tube can be presented to a patient who is inhaling, a medical worker who gives guidance on an aspiration method, and the like.

  The inhaler 10 includes a transmission unit 104. The inhaler 10 outputs flow velocity information SFD as information based on the detected flow velocity to other devices such as the display unit 11 and the portable terminal 2. Thereby, even if the inhaler 10 does not have a display function, it is possible to present the air flow rate when the human inhales the medicine MF in the inhalation tube. That is, the inhaler 10 can be manufactured at a lower cost compared to the case where the self-device has a display function. In addition, devices such as the display unit 11 and the mobile terminal 2 display the flow velocity information SFD. Thereby, the flow rate suitable for the medicine MF to reach the back of the human lung can be displayed. Furthermore, the display unit 11 and the mobile terminal 2 may be configured to record a history of inhaling the medicine MF based on the flow rate information SFD. In this case, a medical staff in charge of a patient who inhales the medicine MF can refer to the inhalation history and perform guidance and treatment of the patient. The medical staff can determine whether the patient appropriately inhales the medicine MF based on the flow rate information SFD, and can use it for guidance of a breathing method suitable for inhalation of the medicine MF.

In the above description, the sound generation unit 101 has been described as a whistle whose sound volume (volume) changes according to the flow velocity of air flowing from the inlet unit 13. The sound generation unit 101 may use a whistle whose frequency characteristics change according to the flow velocity of air. In this case, the flow velocity calculation unit 103 may calculate the flow velocity based on the frequency of the sound S collected by the sound collection unit 102.
In the above description, the sound S generated by the sound generation unit 101 is the sound S in a frequency band outside the human audible range, but is not essential. When the sound generation unit 101 generates a sound S in a frequency band outside the human audible range, the sound S cannot be heard by the human, so that noise during inhalation can be suppressed. Moreover, even when the inhaling human being is old, the inhaler 10 can be used without feeling a sense of avoidance from the embarrassment of sounding during inhalation due to the sound S in the frequency band outside the audible range. Moreover, since the sound is attenuated at a shorter distance as the frequency band of the sound S is higher, the interference of the sound S between the plurality of inhalation devices 10 can be suppressed.

[Second Embodiment]
Next, with reference to FIG.7 and FIG.8, the structure of the inhaler 10a which concerns on 2nd Embodiment is demonstrated. In addition, about the structure and operation | movement same as 1st Embodiment, the same code | symbol is attached | subjected and the description is abbreviate | omitted.
FIG. 7 is a diagram illustrating an example of the configuration of the inhaler 10a according to the second embodiment.
FIG. 8 is a diagram illustrating an example of a division form of the inhaler 10a according to the second embodiment.
The inhaler 10a includes a charge suppression unit ES. The charging suppression unit ES suppresses electrostatic charging in a region through which air passes.

  The inhaler 10a is configured by a plurality of members being detachably combined with each other. As an example, the inhaler 10a is configured in combination so as to be detachable in the Z direction in an XYZ orthogonal coordinate system. Specifically, the inhaler 10a is divided at the locations indicated by the dividing unit C1 and the dividing unit C2. In this case, the inhaler 10a is divided into three parts: a part 10_1, a part 10_2, and a part 10_3. The component 10_1 is connected to the sprayer 3. The component 10_1 includes a detection unit 12, an entrance unit 13, a transmission unit 104, and the like. The component 10_3 includes a valve 15 and an outlet portion 14.

Next, as shown in FIG. 8, the inhaler 10a may be configured to be detachable in parallel with the X axis in the XYZ orthogonal coordinate system. Specifically, the inhaler 10a is divided at the location indicated by the dividing unit C3. In this case, it is divided into two parts, a part 10_4 and a part 10_5. The component 10_4 includes a detection unit 12, an entrance unit 13, a transmission unit 104, and the like.
Further, the inhaler 10a may be configured by combining only a part of the tube so as to be detachable. Specifically, the inhaler 10a may be divided at a location indicated by the dividing unit C4. In this case, the component 10_6 can be removed from the inhaler 10a. The component 10_6 includes a detection unit 12, an entrance unit 13, a transmission unit 104, and the like. Note that the above-described division unit C1 to division unit C4 are merely examples, and the parts and division directions that can be divided are not limited thereto.

  Returning to FIG. 7, the inhaler 10 a has a spray area FA where a large amount of the sprayed medicine MF stays and a non-spray area NFA. The medicine MF sprayed from the sprayer 3 is sprayed mainly on the spray area FA. Specifically, the spray area FA is an area inside a part of the part 10_2 and the part 10_3. The lines dividing the spray area FA and the non-spray area NFA are defined as a boundary line FAL1 and a boundary line FAL2. The detection unit 12 and the transmission unit 104 included in the inhaler 10a are arranged in the non-spray area NFA. The non-spray area NFA is a position where the medicine MF sprayed from the sprayer 3 is difficult to directly hit. Specifically, the non-spray area NFA is an area inside the part 10_1. In this example, the non-spray area NFA is an area on the sprayer 3 side of the boundary line FAL1 and the boundary line FAL2. Note that the non-spray area NFA may be different for each spray shape determined by a spray port (not shown) attached to the sprayer 3.

  As described above, the inhaler 10a includes the charging suppression unit ES. Thereby, it can suppress that the chemical | medical agent MF adheres to the wall surface inside a pipe | tube by static electricity. The inhaler 10a is configured by a plurality of members being detachably combined with each other. Thereby, the inhaler 10a can be divided. Since the inhaler 10a can be divided, it can be easily cleaned. Further, when the inhaler 10a is broken or when the spraying distance of the sprayer 3 is changed, it is possible to cope with it by replacing only a part of the tube. The inhaler 10a includes a detection unit 12 and a transmission unit 104 in the non-spray area NFA. Thereby, when the inhaler 10a is washed with water, for example, a portion that may be washed with water and a portion where inconvenience occurs due to washing with water can be divided. That is, the maintenance work of the inhaler 10a can be reduced.

[Third Embodiment]
Next, an example of a functional configuration of the inhalation state presentation system 1a according to the third embodiment will be described with reference to FIG. In addition, about the structure and operation | movement same as 1st Embodiment and 2nd Embodiment, the same code | symbol is attached | subjected and the description is abbreviate | omitted.
FIG. 9 is a diagram illustrating an example of a functional configuration of the inhalation state presentation system 1a.
The inhalation state presentation system 1a includes an inhaler 10b and a display unit 11a.
The inhaler 10b includes a sound generation unit 101, a sound collection unit 102, a calculation unit 100a, an inclination sensor 109, and a transmission unit 104a.
The calculation unit 100a includes a CPU (Central Processing Unit), a flow rate calculation unit 103, a respiration number determination unit 105, a respiration timing determination unit 106, a counting unit 107, and a respiration inclination detection unit. 108 as a functional unit thereof.

The respiration frequency determination unit 105 determines the number of times the human has respired based on the flow velocity detected by the detection unit 12. The breathing number determination unit 105 acquires the volume information SV from the sound collection unit 102. The respiration frequency determination unit 105 outputs the respiration frequency determined based on the acquired volume information SV as the respiration frequency information CT.
The breathing timing determination unit 106 determines the timing at which a human breathes based on the flow velocity detected by the detection unit 12. The breathing timing determination unit 106 acquires volume information SV from the sound collection unit 102. The respiration timing determination unit 106 determines the respiration timing as the respiration timing information BT based on the acquired volume information SV. The respiration timing determination unit 106 outputs the determined respiration timing information BT.

  The counting unit 107 determines the number of uses of the medicine MF inhaled by a human based on the flow rate detected by the detection unit 12. The counting unit 107 acquires volume information SV from the sound collection unit 102. The counting unit 107 determines the use frequency of the medicine MF inhaled by a human as the use frequency SET based on the acquired volume information SV.

The tilt sensor 109 measures the tilt of the inhaler 10b with respect to the horizontal axis, and outputs the measured information as tilt information SD.
The respiration inclination detection unit 108 (an example of the inclination detection unit) detects the inclination of the tube based on the flow velocity detected by the detection unit 12 and the inclination information SD indicating the inclination of the tube with respect to the horizontal axis. The respiration inclination detection unit 108 acquires inclination information SD from the inclination sensor 109. The respiration inclination detection unit 108 acquires the volume information SV from the sound collection unit 102. The respiration inclination detector 108 outputs inclination information SD.

  The transmission unit 104 a acquires the flow rate information SFD from the flow rate calculation unit 103 and transmits it. The transmission unit 104a acquires the respiratory rate information CT from the respiratory rate determination unit 105 and transmits it. The transmission unit 104a acquires the respiratory timing information BT from the respiratory timing determination unit 106 and transmits it. The transmission unit 104a acquires the use count SET from the counting unit 107 and transmits it. The transmission unit 104a acquires the inclination information SD from the respiratory inclination detection unit 108 and transmits it.

  The display unit 11a and the mobile terminal 2a receive the flow rate information SFD from the transmission unit 104a. The display unit 11a and the mobile terminal 2a display the received flow velocity information SFD. The display unit 11a and the portable terminal 2a receive the respiration frequency information CT from the transmission unit 104a. The display unit 11a and the portable terminal 2a display the received respiratory frequency information CT. The display unit 11a and the mobile terminal 2a receive the respiration timing information BT from the transmission unit 104a. The display unit 11a and the portable terminal 2a display the received respiratory timing information BT. The display unit 11a and the mobile terminal 2a receive the usage count SET from the transmission unit 104a. The display unit 11a and the mobile terminal 2a display the received use count SET. The display unit 11a and the mobile terminal 2a receive the tilt information SD from the transmission unit 104a. The display unit 11a and the mobile terminal 2a display the received tilt information SD.

Next, an example of the operation of the inhalation state presentation system 1a according to the third embodiment will be described with reference to FIG.
FIG. 10 is a diagram illustrating an example of the flow velocity information SFD displayed by the display unit 11a and the mobile terminal 2a. FIG. 10 is a graph in which time is plotted on the horizontal axis and flow velocity information SFD is plotted on the vertical axis. FIG. 10 includes waveforms from the flow velocity information SFD1 to the flow velocity information SFDn. Here, n is an integer of 1 or more.

Specifically, the respiration count determination unit 105 determines that the change in the flow velocity information SFD1 from time T20 to time T21 is the first respiration Br1. When determining that the change in the flow velocity information SFD1 is respiration, the respiration frequency determination unit 105 adds 1 to the respiration frequency information CT. Further, the respiration count determination unit 105 determines that the change in the flow velocity information SFD2 from time T22 to time T24 is the second respiration Br2. When determining that the change in the flow velocity information SFD2 is respiration, the respiration frequency determination unit 105 adds 1 to the respiration frequency information CT. The respiration count determination unit 105 determines that the change in the flow velocity information SFDn from time T2n to time T2n + 2 is the nth respiration Brn. When determining that the change in the flow velocity information SFDn is respiration, the respiration frequency determination unit 105 adds 1 to the respiration frequency information CT.
Note that although the breath number determination unit 105 has been described so far as counting the number of breaths based on both the time of inspiration and the time of expiration in human breathing, the present invention is not limited to this. The respiration frequency determination unit 105 may count the respiration frequency based on only the time of inspiration of human respiration. Specifically, as shown in FIG. The first breathing Br1 is determined from T220 to time T221, the second breathing Br2 from time T222 to time T223, and the nth breathing Brn from time T22n to time T22n + 1. May be.

  Further, the respiration frequency determination unit 105 may store a respiration frequency suitable for each medicine MF in advance. The respiration frequency determination unit 105 may output a respiration frequency suitable for each medicine MF to the transmission unit 104a. The transmission unit 104 a transmits the number of breaths suitable for each medicine MF acquired from the breathing number determination unit 105. The display unit 11a and the mobile terminal 2a may display the number of breaths suitable for each medicine MF. Moreover, you may output a sound according to the frequency | count of respiration from the speaker (not shown) with which the display part 11a and the portable terminal 2a are provided. The human breathes based on the number of breaths presented by the display unit 11a and the portable terminal 2a. Note that the number of breaths suitable for each drug MF may be stored in the storage unit (not shown), the display unit 11a, and the portable terminal 2a included in the detection unit 12.

  The respiration timing determination unit 106 determines that the human has inhaled the drug MF while detecting the flow velocity information SFD. The breathing timing determination unit 106 determines that the human has exhaled while the flow rate information SFD is not detected. Specifically, the breathing timing determination unit 106 determines that the human has inhaled the drug MF from time T20 to time T21 as shown in FIG. The breathing timing determination unit 106 determines that the person has exhaled from time T21 to time T22. Similarly, the breathing timing determination unit 106 determines that the human has inhaled the drug MF between time T22 and time T23 and between time T2n and time T2n + 1. The breathing timing determination unit 106 determines that the person has exhaled between time T23 and time T24 and between time T2n + 1 and time T2n + 2.

  In addition, in the respiratory timing determination unit 106, information indicating a respiratory timing suitable for each medicine MF may be stored in advance. Here, the information indicating the breathing timing includes information indicating when to breathe, information indicating a time zone of inspiration of breathing, and information indicating a time zone of expiration. The respiration timing determination unit 106 outputs a respiration timing suitable for each drug MF to the transmission unit 104a. The transmission unit 104a transmits a breathing timing suitable for each medicine MF. The display unit 11a and the portable terminal 2a may display a breathing timing suitable for each medicine MF. Moreover, you may output a sound according to a respiration timing from the speaker (not shown) with which the display part 11a and the portable terminal 2a are provided. The human breathes based on the breathing timing presented by the display unit 11a and the portable terminal 2a. Note that the respiration timing suitable for each medicine MF may be stored in the storage unit (not shown), the display unit 11a, and the mobile terminal 2a included in the detection unit 12.

Here, there are cases where the number of inhalation sets of drug MF per day is prescribed as a plurality of sets. For example, it may be prescribed to inhale 3 sets per day such as morning, noon and evening. In this case, the counting unit 107 counts the number of inhalation sets of the drug MF per day.
In addition, the number of inhalations of the drug MF per inhalation set may be multiple. For example, it may be prescribed to be inhaled three times in the morning, three times in the day, and three times in the evening. In this case, the counting unit 107 counts how many breaths the medicine MF is inhaled per inhalation set.
Specifically, the counting unit 107 counts the number of inhalations per inhalation set SET1 for the inhalation set SET1 shown in FIG. The counting unit 107 stores the counted number of inhalations per inhalation set SET1 as the cumulative number of inhalations. The counting unit 107 outputs the cumulative number of inhalations to the transmission unit 104a. The transmission unit 104a outputs the acquired cumulative number of inhalations to the display unit 11a and the mobile terminal 2a.
The counting unit 107 may count the cumulative value of the number of inhalation sets per day or the cumulative value of the number of inhalations per time.

Next, the respiration inclination detecting unit 108 will be described with reference to FIG.
FIG. 11 is a diagram illustrating an example of an inclination detected by the respiration inclination detection unit 108.
The center line BL of the inhaler 10b shown in FIG. 11 is in a state inclined by an angle θ in the Z-axis direction with respect to the horizontal line HL. The inclination sensor 109 detects the inclination of the angle θ. If a person who has added the inhaler 10b inhales the drug MF while the inhaler 10b is tilted, the prescribed amount of the drug MF may not reach the target organ such as the lung. Therefore, the inhaler 10b detects the angle θ and displays the angle θ suitable for inhalation on the display unit 11a and the portable terminal 2a.

  As described above, the inhaler 10b includes the respiratory frequency determination unit 105. As a result, the number of breaths can be determined. The inhaler 10b can determine whether a human has inhaled the drug MF a specified number of times. The inhaler 10b includes a respiratory timing determination unit 106. Thereby, the inhaler 10b can determine whether or not the medicine MF has been inhaled at an appropriate timing of breathing. Further, the inhaler 10b can teach suitable breathing timing, and can save time and effort taught by a medical worker. The inhaler 10b includes a counting unit 107. Thereby, the inhaler 10b can count how many times the human has inhaled the medicine MF. That is, the medical staff can know whether the medicine MF is taken a prescribed number of times based on the number of times of use SET, and can be used for treatment. The inhaler 10b includes a breathing inclination detector 108. Thereby, the human using the inhaler 10b can know the posture suitable for the medicine MF. Further, a person using the inhaler 10b can inhale the drug MF in a suitable posture, and reach the intended location of the drug MF, thereby enhancing the therapeutic effect.

  The embodiment of the present invention has been described in detail with reference to the drawings. However, the specific configuration is not limited to this embodiment, and appropriate modifications may be made without departing from the spirit of the present invention. it can.

  Note that a program for realizing the functions of arbitrary components in the inhaler 10, the inhaler 10a, and the inhaler 10b described above is recorded (stored) in a computer-readable recording medium (storage medium). The program may be read by a computer system and executed. The “computer system” here includes an operating system (OS) or hardware such as peripheral devices. The “computer-readable recording medium” means a portable medium such as a flexible disk, a magneto-optical disk, a ROM (Read Only Memory), a CD (Compact Disc) -ROM, or a hard disk built in a computer system. Refers to the device. Further, the “computer-readable recording medium” refers to a volatile memory (RAM: Random Access) in a computer system that becomes a server or a client when a program is transmitted via a network such as the Internet or a communication line such as a telephone line. Memory that holds a program for a certain period of time, such as Memory).

The program may be transmitted from a computer system storing the program in a storage device or the like to another computer system via a transmission medium or by a transmission wave in the transmission medium. Here, the “transmission medium” for transmitting the program refers to a medium having a function of transmitting information, such as a network (communication network) such as the Internet or a communication line (communication line) such as a telephone line.
Further, the above program may be for realizing a part of the functions described above. Further, the above program may be a so-called difference file (difference program) that can realize the above-described functions in combination with a program already recorded in the computer system.

  DESCRIPTION OF SYMBOLS 1, 1a, 1b ... Inhalation state presentation system 2, 2a ... Portable terminal, 3 ... Nebulizer, 10, 10a, 10b ... Inhalation device, 11, 11a ... Display part (display device), 12 ... Detection part, 13 ... Inlet Part (inlet of pipe), 14 ... outlet part (exit of pipe), 100, 100a ... calculating part, 101 ... sounding part, 102 ... sound collecting part, 103 ... flow velocity calculating part, 104, 104a ... transmitting part, 105 ... Respiration frequency determination unit 106. Respiration timing determination unit 107 107 Counting unit 108 Respiratory inclination detection unit 109 Inclination sensor

Claims (10)

A detection unit that detects the flow velocity of air flowing in from the inlet of the tube and flowing out to the outlet of the tube due to negative pressure due to human breathing;
An inhaler comprising: a transmission unit that transmits information based on the flow velocity detected by the detection unit. The detection unit includes a sound generation unit and a sound collection unit,
The sound generation unit generates a sound having an attribute according to the flow velocity of the air flowing from the inlet,
The sound collection unit collects the sound produced by the sound generation unit,
The inhaler according to claim 1, wherein the detection unit detects the flow velocity based on the attribute of the sound collected by the sound collection unit. The inhaler according to claim 1 or 2, wherein the information transmitted by the transmission unit is information indicating the flow velocity detected by the detection unit. The inhaler according to claim 2 or 3, wherein the frequency band of the sound is outside a human audible range. The inhaler according to any one of claims 1 to 4, further comprising: a charge suppression unit that suppresses electrostatic charge in a region of the tube through which the air passes. The inhaler according to any one of claims 1 to 5, wherein the tube is configured by a plurality of members being detachably combined with each other. Further comprising an inclination detection unit for detecting the inclination of the tube based on the flow velocity detected by the detection unit and inclination information indicating the inclination of the tube with respect to a horizontal axis;
The inhaler according to any one of claims 1 to 6, wherein the transmission unit further transmits information based on the inclination information detected by the inclination detection unit. Based on the flow velocity detected by the detection unit, further comprising a breathing number determination unit that determines the number of times the human breathed,
The inhaler according to any one of claims 1 to 7, wherein the transmission unit further transmits respiration frequency information indicating the number of times determined by the respiration frequency determination unit. Further comprising a breathing timing determination unit for determining the timing of breathing based on the flow velocity detected by the detection unit;
The inhaler according to any one of claims 1 to 8, wherein the transmission unit further transmits respiration timing information indicating the respiration timing determined by the respiration timing determination unit. Inhalation device according to any one of claims 1 to 9,
An inhalation state presentation system comprising: a display device that displays information based on the flow velocity transmitted by the transmission unit.

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