JP2021194273A - Nebulizer - Google Patents

Abstract

To provide a technique capable of enhancing efficiency of inhaling a medicinal solution.SOLUTION: A nebulizer according to one aspect of the invention includes: an atomization part for atomizing a medicinal solution in accordance with a supplied drive voltage; a detecting part for detecting timing of breathing of a user who inhales the medicinal solution atomized in the atomization part; and a control part which controls the drive voltage supplied to the atomization part based on a detected result by the detecting part. For example, the control part controls the drive voltage supplied to the atomization part while the user takes a breath in to be higher than the drive voltage supplied to the atomization part while the user takes a breath out.SELECTED DRAWING: Figure 1

Description

The present invention relates to a nebulizer.

Conventionally, as a medical device for atomizing a drug solution for asthma treatment and sending it to the bronchi and lungs, the user can inhale the atomized drug solution by atomizing the drug solution in the bottle by vibrating the horn oscillator. Such a nebulizer is known (see, for example, Patent Documents 1 and 2).

Japanese Unexamined Patent Publication No. 2019-076243 Japanese Unexamined Patent Publication No. 2019-051217

However, in the prior art, there is a problem that the efficiency of inhalation of the chemical solution is low because the amount of the chemical solution atomized per hour is constant.

For example, since the drug solution is not inhaled by the user during the period when the user is exhaling, most of the drug solution atomized during that period is discharged or reliquefied in the nebulizer without being inhaled by the user. Therefore, the chemical solution and the electric power for atomizing the chemical solution are wasted, and the chemical solution cannot be inhaled efficiently. Further, Patent Documents 1 and 2 do not disclose means for solving such a problem.

The present invention, on the one hand, has been made in view of such circumstances, and an object of the present invention is to provide a technique capable of improving the efficiency of inhalation of a drug solution.

The present invention adopts the following configuration in order to solve the above problems.

That is, the nebulizer according to one aspect of the present invention detects the atomizing unit that atomizes the chemical solution according to the supplied drive voltage and the breathing timing of the user who inhales the chemical solution atomized by the atomizing unit. It includes a detection unit and a control unit that controls a drive voltage supplied to the atomization unit based on the detection result by the detection unit.

In the above configuration, by controlling the drive voltage supplied to the atomizing unit based on the detection result of the user's breathing timing, the user breathes from the amount of the chemical solution atomized during the period when the user is exhaling. It is possible to increase the amount of chemical solution that atomizes during the period of inhalation. Therefore, it is possible to suppress the consumption of the chemical solution and the electric power during the period when the user is exhaling, and to atomize a sufficient amount of the chemical solution during the period when the user is inhaling. Therefore, the efficiency of inhalation of the drug solution can be improved.

In the nebulizer according to the one aspect, the control unit receives, for example, a drive voltage supplied to the atomization unit during the period when the user is inhaling, and the atomization unit during the period when the user is exhaling. It may be controlled to be higher than the drive voltage supplied to the.

In the nebulizer according to the one aspect, the control unit does not supply a drive voltage to the atomization unit during the period when the user is exhaling, and the atomization unit is used during the period when the user is inhaling. Control may be performed to supply the drive voltage to the unit.

In the nebulizer according to the one aspect, the detection unit detects the respiration intensity, and the control unit controls the height of the drive voltage supplied to the atomization unit based on the respiration intensity. May be good. According to this configuration, the strength of the user's breathing is detected in addition to the timing of the user's breathing, and the height of the drive voltage supplied to the atomization unit is controlled based on the strength of the user's breathing to control the chemical solution. The efficiency of inhalation can be improved. In addition, since it is possible to atomize an appropriate amount of the drug solution according to the respiratory condition of the user, it becomes easier for the user to inhale the drug solution.

In the nebulizer according to the one aspect, the atomizing unit has, for example, a vibrator that vibrates according to the supplied drive voltage, the chemical solution is atomized by the vibration of the vibrator, and the control unit vibrates. The drive voltage may be supplied to the child.

In the nebulizer according to the one aspect, for example, a suction port for the user to inhale the drug solution atomized by the atomizing portion, and a suction port provided inside the suction port, which is rotated by an air flow accompanying the breathing of the user. A rotating body may be provided, and the detection unit may detect the timing of the respiration based on the rotation of the rotating body.

In the nebulizer according to the one aspect, the control unit may predict the timing of the breath and start supplying the driving voltage to the atomization unit before the user starts inhaling. As a result, atomization of the drug solution is started before the user starts inhaling, and at the timing when the user starts inhaling, a certain amount of the drug solution is atomized, and the efficiency of inhaling the drug solution can be improved. ..

In the nebulizer according to the one aspect, the height of the drive voltage supplied to the atomization unit may be controlled based on the result of predicting the timing of the respiration. This makes it possible to atomize the drug solution according to the strength of the user's breathing within the user's breathing cycle and improve the efficiency of inhalation of the drug solution.

In the nebulizer according to the one aspect, the control unit may predict the timing of the breath and stop supplying the drive voltage to the atomization unit before the user finishes inhaling. As a result, it is possible to suppress atomization of the chemical solution that is not inhaled by the user and improve the efficiency of inhalation of the chemical solution.

According to the present invention, it is possible to provide a technique capable of improving the efficiency of inhalation of a drug solution.

It is a figure which shows the structure of the nebulizer 100 which is an example of an embodiment. It is a front view which shows the appearance of a nebulizer 100. It is a side view which shows the appearance of a nebulizer 100. It is a figure which shows an example of wearing an inhalation mask to a nebulizer 100. It is sectional drawing which shows an example of the structure of the respiration detection part 120. It is sectional drawing which shows the other example of the structure of the respiration detection part 120. It is sectional drawing which shows still another example of the structure of the respiration detection part 120. It is a figure which shows an example of the control of the drive voltage by the control unit 130. It is a figure which shows another example of the control of the drive voltage by the control unit 130. It is a figure which shows an example of the control of atomization of a drug solution according to a respiratory cycle.

Hereinafter, embodiments according to one aspect of the present invention will be described with reference to the drawings.

(Embodiment)
<Structure of Nebulizer 100, which is an example of the embodiment>
FIG. 1 is a diagram showing a configuration of a nebulizer 100, which is an example of an embodiment. As shown in FIG. 1, the nebulizer 100 includes a power supply 101, an atomization unit 110, a respiration detection unit 120, and a control unit 130. The user 10 is a user of the nebulizer 100, that is, a person (for example, a patient) who inhales the drug solution atomized by the atomizing unit 110.

The power supply 101 supplies electric power to the control unit 130. For example, the power source 101 may be a power source such as a dry battery, or may be a power source that receives power from an external household power source or the like of the nebulizer 100 via a power cable or the like.

The atomizing unit 110 atomizes the chemical solution according to the drive voltage supplied from the control unit 130. For example, the atomizing unit 110 includes a chemical solution bottle 111, a horn oscillator 112, and a mesh 113.

The chemical solution bottle 111 is a container containing a liquid chemical solution that has not been atomized. The chemical solution bottle 111 supplies the chemical solution to the gap between the vibrating surface of the horn oscillator 112 and the mesh 113.

The horn oscillator 112 is an ultrasonic oscillator that vibrates according to the drive voltage supplied from the control unit 130, and has a horn for amplifying the vibration and a vibration surface. The vibration of the horn oscillator 112 is amplified by the horn and transmitted to the vibrating surface. When the vibrating surface of the horn oscillator 112 vibrates, the chemical solution supplied to the gap between the vibrating surface of the horn oscillator 112 and the mesh 113 passes through the mesh 113.

The mesh 113 atomizes the passing chemical solution and ejects the atomized chemical solution. The user 10 can inhale the atomized drug solution by inhaling.

The respiration detection unit 120 detects the respiration timing of the user 10. The detection of the breathing timing by the breathing detection unit 120 is at least one of the timing at which the user 10 inhales and the timing at which the user 10 exhales. In this example, a case where the breathing detection unit 120 detects both the timing at which the user 10 inhales and the timing at which the user 10 exhales will be described.

In addition, the respiratory detection unit 120 may further detect the respiratory intensity of the user 10. The breathing intensity of the user 10 is the strength with which the user 10 inhales and the strength with which the user 10 exhales. The specific configuration of the respiration detection unit 120 will be described later (see, for example, FIGS. 5 and 6). The respiration detection unit 120 outputs the detection result to the control unit 130.

The control unit 130 supplies a drive voltage to the atomization unit 110 by using the electric power supplied from the power supply 101. This drive voltage is, for example, an AC voltage. In this example, the drive voltage supplied by the control unit 130 to the atomization unit 110 is applied to the horn oscillator 112 of the atomization unit 110. The higher the drive voltage applied to the horn oscillator 112, the larger the amount of the chemical solution atomized per hour.

Further, the control unit 130 controls the drive voltage supplied to the atomization unit 110 based on the detection result output from the breathing detection unit 120. For example, the control unit 130 makes the drive voltage supplied to the atomization unit 110 higher during the period when the user 10 is inhaling than the drive voltage supplied to the atomization unit 110 during the period when the user 10 is exhaling. Take control.

In this control, the drive voltage supplied to the atomizing unit 110 during the period when the user 10 is exhaling is set to 0 [V], and the driving voltage supplied to the atomizing unit 110 during the period when the user 10 is inhaling is set to 0 [V]. Includes control to be greater than 0 [V]. That is, the control unit 130 does not supply the drive voltage to the atomization unit 110 during the period when the user 10 is exhaling, and does not supply the drive voltage to the atomization unit 110 during the period when the user 10 is inhaling. May be done.

Further, this control is based on the average value of the drive voltage supplied to the atomizing unit 110 during the period when the user 10 is exhaling, and the drive voltage supplied to the atomizing unit 110 during the period when the user 10 is inhaling. It also includes control to increase the average value. That is, even if the drive voltage supplied for a part of the period during which the user 10 is exhaling is equal to or higher than the drive voltage supplied for a part of the period during which the user 10 is inhaling, the user 10 It suffices if the average value of the drive voltage supplied during the period in which the user 10 is inhaling is higher than the average value of the drive voltage supplied during the period of exhalation.

The control unit 130 is realized by, for example, a processor and a memory that operate in cooperation. The processor is, for example, a processor such as a CPU (Central Processing Unit) or an MPU (Micro Processing Unit). The processor functions as a control unit 130 by reading and executing a program stored in the memory. Note that this processor may be a combination of a plurality of processors.

The memory is realized by a RAM (Random Access Memory), a ROM (Read Only Memory), a flash memory, or the like. The memory stores a program executed by the processor, data used by the processor, and the like.

In this way, the nebulizer 100 controls the drive voltage supplied to the atomizing unit 110 based on the detection result of the breathing timing of the user 10, so that the atomizing unit 110 is in the period when the user 10 is exhaling. It is possible to make the drive voltage supplied to the atomizing unit 110 higher than the drive voltage supplied to the atomizing unit 110 during the period when the user 10 is inhaling.

As a result, the amount of the chemical solution atomized during the period when the user 10 is inhaling is larger than the amount of the chemical solution atomized during the period when the user 10 is exhaling. Therefore, it is possible to suppress the consumption of the chemical solution and the electric power during the period when the user 10 is exhaling, and to atomize a sufficient amount of the chemical solution during the period when the user 10 is inhaling. As described above, according to the nebulizer 100, the efficiency of inhalation of the drug solution can be improved.

<Appearance of Nebulizer 100>
FIG. 2 is a front view showing the appearance of the nebulizer 100. FIG. 3 is a side view showing the appearance of the nebulizer 100. FIG. 4 is a diagram showing an example of attaching an inhalation mask to the nebulizer 100. As shown in FIGS. 2 and 3, the nebulizer 100 includes a main body portion 140, a bottle storage portion 150, and a suction port 160.

The main body unit 140 has a power supply unit 141 and a power supply button 142. Further, the control unit 130 and the horn oscillator 112 shown in FIG. 1 are provided inside, for example, the main body unit 140.

The power supply unit 141 is provided with the power supply 101 shown in FIG. In the example shown in FIGS. 2 and 3, the power supply 101 has a power cord 141a (see FIG. 3), and receives power from an external household power supply or the like of the nebulizer 100 via the power cord 141a. The power supply unit 141 may be removable from the main body unit 140, and in that case, a dry battery or the like may be inserted into the main body unit 140.

The power button 142 is an operation unit for starting atomization of the chemical solution. For example, when the user 10 presses the power button 142, the control unit 130 starts supplying and controlling the drive voltage to the atomization unit 110. When a certain period of time has elapsed after the power button 142 is pressed, the control unit 130 ends the supply and control of the drive voltage to the atomization unit 110.

The bottle storage portion 150 has a base portion 151, a lid portion 152, a hinge 153, and a hook 154. The base portion 151 is a member fixed to the main body portion 140. Further, the base portion 151 may be detachable from the main body portion 140. The chemical solution bottle 111 shown in FIG. 1 is provided inside, for example, the base 151.

The lid portion 152 is connected to the base portion 151 via a hinge 153 and is rotatable with respect to the base portion 151 about the lid portion 152. The chemical solution bottle 111 can be opened and closed by rotating the lid portion 152. The hook 154 is provided on the lid portion 152, and is a portion operated by the user 10 to rotate the lid portion 152 to open and close the bottle storage portion 150.

When the bottle storage unit 150 is opened, it becomes possible to fill the chemical solution of the chemical solution bottle 111 in the bottle storage unit 150. Further, when the bottle storage unit 150 is opened, the mesh 113 shown in FIG. 1 can be installed on the chemical solution supply port in the chemical solution bottle 111. When the bottle storage unit 150 is closed, the chemical solution of the chemical solution bottle 111 is supplied to the gap between the horn oscillator 112 and the mesh 113.

The suction port 160 is a member for the user 10 to inhale the atomized chemical solution, and is a cylindrical member in the example shown in FIGS. 2 and 3. The suction port 160 has a first end portion 161, a second end portion 162, and a detection portion accommodating portion 163. The first end portion 161 has one opening of a cylindrical suction port 160 and is detachably fixed to the bottle storage portion 150. The second end 162 has the other opening of the cylindrical suction port 160.

The second end 162 is provided with a connection interface with the mouth and nose of the user 10, such as an inhalation mask, a mouthpiece, or a nosepiece. FIG. 4 shows an example in which the suction mask 41 is attached to the second end portion 162. It should be noted that the user 10 may directly inhale the atomized chemical solution from the second end portion 162 without providing these connection interfaces at the second end portion 162.

By closing the bottle storage unit 150 and vibrating the horn oscillator 112 in a state where the chemical solution of the chemical solution bottle 111 is supplied to the gap between the horn oscillator 112 and the mesh 113, the chemical solution is atomized via the mesh 113. To become. As a result, when the user 10 inhales from the side of the second end portion 162, the atomized chemical solution is inhaled into the mouth or nose of the user 10 through the inhalation port 160.

The detection unit storage unit 163 is a storage unit provided for providing the breathing detection unit 120 shown in FIG. 1 in the suction port 160. The breathing detection unit 120 detects the breathing timing of the user 10 by detecting the airflow passing through the suction port 160. A configuration example of the respiration detection unit 120 provided by using the detection unit storage unit 163 will be described later (see, for example, FIGS. 5 and 6).

<Structure of breathing detection unit 120>
FIG. 5 is a cross-sectional view showing an example of the configuration of the respiration detection unit 120. FIG. 5 shows a state in which the portion of the detection unit accommodating portion 163 of the suction port 160 is cut by a cut surface perpendicular to the axial direction (depth direction of FIG. 5) of the cylindrical suction port 160. As shown in FIG. 5, the respiration detection unit 120 includes an impeller 121, a generator 122, a lead wire 123, and a detection circuit 124.

The impeller 121 is a rotating body provided inside the cylindrical suction port 160 so that the rotation axis is parallel to the axial direction of the suction port 160. Further, the impeller 121 has a rotation shaft fixed to the inner wall of the suction port 160 by four arms, and can rotate inside the suction port 160 about the axial direction of the suction port 160.

The impeller 121 has three blades having an oblique surface with respect to the axial direction of the suction port 160, and the impeller 121 rotates when these blades receive an air flow in the axial direction of the suction port 160. .. Therefore, when an air flow is generated in the suction port 160 with the breathing of the user 10, the impeller 121 rotates at a speed corresponding to the strength of the air flow. Further, the rotation direction of the impeller 121 differs depending on the direction of the air flow in the suction port 160, that is, whether the user is inhaling or exhaling.

The generator 122 converts the rotation of the impeller 121 into an electric signal, and outputs the converted electric signal to the detection circuit 124 via the conducting wire 123. For example, the electric signal output by the generator 122 is a signal having a voltage proportional to the rotation speed of the impeller 121. Further, this electric signal may be a voltage signal whose polarity (positive or negative) changes according to the rotation of the impeller 121.

The detection circuit 124 detects the breathing timing and intensity of the user 10 based on the electric signal output from the generator 122. Further, the detection circuit 124 is connected to the control unit 130 provided in the main body unit 140 by a wiring (not shown), and outputs the detection result to the control unit 130.

In this example, the detection unit storage unit 163 is provided in a part of the cylindrical suction port 160, and the detection circuit 124 is housed in the detection unit storage unit 163. However, if the detection circuit 124 is sufficiently small and the influence on the air flow in the suction port 160 is small, the detection unit storage unit 163 is installed in the cylindrical suction port 160 without providing the detection unit storage unit 163. It may be provided.

In FIG. 5, the configuration in which the impeller 121 is provided so that the central axis of the suction port 160 and the rotation axis of the impeller 121 substantially coincide with each other has been described. However, the central axis of the suction port 160 and the rotation axis of the impeller 121 have been described. The impeller 121 may be provided so as to be misaligned. Further, the size, shape, number, and the like of the blades of the impeller 121 are not limited to the example shown in FIG. 5, and various deformations are possible.

For example, in the example shown in FIG. 5, the blades of the impeller 121 may be shortened and the rotation axis of the impeller 121 may be located near the detection circuit 124. As a result, the respiration of the user 10 can be detected while suppressing the influence on the air flow in the suction port 160. Further, it may be designed so that a part of the rotation range of the blades of the impeller 121 enters the detection unit storage unit 163.

FIG. 6 is a cross-sectional view showing another example of the configuration of the respiration detection unit 120. FIG. 6 shows a state in which the suction port 160 is cut by a cut surface parallel to the axial direction of the cylindrical suction port 160. As shown in FIG. 6, the respiration detection unit 120 may have a cup-shaped rotating body 125 instead of the impeller 121 in the configuration shown in FIG.

The wind cup type rotating body 125 has four wind cups in the example of FIG. 6, and is a rotating body that rotates by receiving an air flow perpendicular to the rotation axis. In this case, the cup-shaped rotating body 125 is provided so that the rotating shaft of the cup-shaped rotating body 125 is perpendicular to the axial direction of the suction port 160. The generator 122 converts the rotation of the cup-shaped rotating body 125 into an electric signal, and outputs the converted electric signal to the detection circuit 124 via the conducting wire 123.

In FIG. 6, the configuration in which the cup-shaped rotating body 125 is provided near the central axis of the suction port 160 has been described, but the cup-shaped rotating body 125 may be provided at a position different from the central axis of the suction port 160. good. Further, the size, shape, number, and the like of the cup-shaped rotating body 125 are not limited to the example shown in FIG. 6, and various deformations are possible.

For example, in the example shown in FIG. 5, the air cup may be shortened and the rotation axis of the air cup type rotating body 125 may be located near the detection circuit 124. As a result, the respiration of the user 10 can be detected while suppressing the influence on the air flow in the suction port 160. Further, it may be designed so that a part of the rotation range of the cup of the wind cup type rotating body 125 enters the detection unit storage unit 163.

Since the cup-shaped rotating body 125 can detect only one-way airflow, two cup-shaped rotating bodies with the directions of the cups reversed in order to detect bidirectional airflow using the cup-shaped rotating body 125. 125 may be provided.

FIG. 7 is a cross-sectional view showing still another example of the configuration of the respiration detection unit 120. FIG. 6 shows a state in which the suction port 160 is cut by a cut surface parallel to the axial direction of the cylindrical suction port 160. As shown in FIG. 7, the respiration detection unit 120 may have a heater 126 and a temperature measuring sensor 127, 128 instead of the impeller 121, the generator 122, and the conducting wire 123 shown in FIG.

The heater 126 and the temperature measuring sensors 127 and 128 are arranged on a membrane parallel to the central axis of the suction port 160. Further, temperature measuring sensors 127 and 128 are provided at each position symmetrical with respect to the heater 126 in the direction of the central axis of the suction port 160.

The heater 126 generates heat depending on the supplied voltage. The resistance value of the temperature measurement sensor 127 changes depending on the temperature of the temperature measurement sensor 127. Similarly, the resistance value of the temperature measuring sensor 128 changes depending on the temperature of the temperature measuring sensor 128. Each of the heater 126 and the resistance temperature sensors 127 and 128 is, for example, a platinum thin film formed on the membrane.

The detection circuit 124 is electrically connected to the heater 126 and the temperature measuring sensors 127 and 128, supplies a voltage to the heater 126, and detects the resistance values of the temperature measuring sensors 127 and 128. The difference between the resistance values of the temperature measuring sensors 127 and 128 is proportional to the flow velocity of the air flow in the suction port 160. Therefore, the detection circuit 124 can detect the direction and strength of the air flow in the suction port 160 by calculating the difference between the resistance values of the temperature measuring sensors 127 and 128.

<Control of drive voltage by control unit 130>
FIG. 8 is a diagram showing an example of control of the drive voltage by the control unit 130. The respiration detection unit 120 detects the flow rate of the airflow in the suction port 160 (for example, the volumetric flow rate per minute [liter / minute]) accompanying the respiration of the user 10 as the respiration of the user 10.

The positive or negative of the flow rate indicates the direction of the air flow in the suction port 160, that is, whether the user 10 is inhaling or exhaling. In the example of FIG. 8, the positive flow rate is the flow rate of the airflow from the first end 161 to the second end 162 of the suction port 160, that is, the airflow in the suction port 160 when the user 10 is inhaling. Intake) flow rate is shown. The negative flow rate indicates the flow rate of the airflow from the second end 162 to the first end 161 at the suction port 160, that is, the flow rate of the airflow (exhalation) in the suction port 160 when the user 10 is exhaling. ..

For example, in the configuration shown in FIGS. 5 and 6, the detection circuit 124 stores the correspondence information between the electric signal output from the generator 122 and the flow rate of the airflow in the suction port 160, and stores the generator. By converting the electric signal output from 122 by this corresponding information, the flow rate of the airflow in the suction port 160 is detected. Alternatively, the detection circuit 124 may detect the voltage of the electric signal output from the generator 122 as it is as the flow rate of the air flow in the suction port 160.

The flow rate detection result 71 is an example of a time change of the detection result of the flow rate of the air flow in the suction port 160 by the breathing detection unit 120. In the example of FIG. 8, the user 10 repeats breathing at a constant cycle. The respiration detection unit 120 outputs, for example, the flow rate detection result 71 to the control unit 130, and the control unit 130 controls the drive voltage supplied to the atomization unit 110 based on the flow rate detection result 71.

For example, the control unit 130 stores the correspondence information between the flow rate of the air flow in the suction port 160 and the drive voltage supplied to the atomization unit 110. Then, the control unit 130 derives the drive voltage to be supplied to the atomization unit 110 based on the flow rate of the air flow in the suction port 160 indicated by the flow rate detection result 71 and the corresponding information, and atomizes the derived drive voltage. It is supplied to the unit 110.

The drive voltage 72 is an example of a time change of the drive voltage supplied by the control unit 130 to the atomization unit 110. While the drive voltage is being supplied to the atomizing unit 110, the chemical solution supplied from the chemical solution bottle 111 is vaporized. The amount of the chemical solution atomized per hour increases as the drive voltage supplied to the atomizing unit 110 increases.

In the example of FIG. 8, the control unit 130 atomizes the drive voltage proportional to the flow rate in the suction port 160 during the period when the flow rate in the suction port 160 is positive, that is, during the period when the user 10 is inhaling. Supply to 110. Further, the control unit 130 does not supply the drive voltage to the atomization unit 110 during the period when the flow rate in the suction port 160 is negative, that is, during the period when the user 10 is exhaling.

That is, the control unit 130 supplies the drive voltage to the atomization unit 110 in synchronization with the intake air of the user 10. As a result, a sufficient amount of the chemical solution can be atomized during the period when the user 10 is inhaling, and the consumption of the chemical solution and the electric power can be suppressed during the period when the user 10 is exhaling. Therefore, the efficiency of inhalation of the drug solution can be improved.

FIG. 9 is a diagram showing another example of control of the drive voltage by the control unit 130. The respiratory intensity of the user 10 depends on the health condition of the user 10 and the like. For example, when a seizure due to asthma or the like occurs in the user 10, as shown in the flow rate detection result 71 of FIG. 9, the respiration of the user 10 becomes weak as a whole. Then, in such a situation, the amount of the drug solution that can be inhaled by the user 10 is reduced.

As described above, the control unit 130 supplies the atomization unit 110 with a drive voltage proportional to the flow rate in the suction port 160 during the period when the user 10 is inhaling. As a result, for example, when the user 10 has a seizure, the drive voltage supplied to the atomization unit 110 is also lowered, as shown in the drive voltage 72 of FIG. Therefore, it is possible to suppress atomization of the chemical solution in excess of the amount that can be inhaled by the user 10, and to suppress consumption of the chemical solution and electric power.

On the other hand, when the user 10 does not have a seizure or the like and the user 10 breathes strongly (normal time), the drive voltage supplied to the atomizing unit 110 is as shown in the drive voltage 72 of FIG. , Higher than the example in FIG. As a result, a sufficient amount of the drug solution can be atomized with respect to the amount that can be inhaled by the user 10.

In this way, the nebulizer 100 detects the breathing intensity of the user 10 in addition to the breathing timing of the user 10, and determines the height of the drive voltage supplied to the atomizing unit 110 based on the breathing intensity of the user 10. By controlling, the efficiency of inhalation of the drug solution can be improved.

In addition, since it is possible to atomize an appropriate amount of the drug solution according to the respiratory state of the user 10, the user 10 can easily inhale the drug solution. For example, it is possible to prevent the user 10 from having difficulty inhaling the drug solution due to atomization of a large amount of the drug solution even though the user 10 has a weak breath and cannot inhale a large amount of the drug solution. Further, it is possible to prevent the user 10 from having difficulty inhaling the drug solution because a sufficient amount of the drug solution is not atomized even though the user 10 has strong breathing and the user 10 can inhale a large amount of the drug solution.

(Modification 1)
In the example shown in FIGS. 8 and 9, the control unit 130 has described the configuration in which the drive voltage is supplied to the atomization unit 110 only during the period when the user 10 is inhaling, but the configuration is not limited to such a configuration. .. That is, the control unit 130 may supply the drive voltage to the atomization unit 110 during the period when the user 10 is exhaling. In this case, the control unit 130 lowers the drive voltage supplied by the user 10 during the period when the user 10 is exhaling to be lower than the drive voltage supplied by the control unit 130 during the period when the user 10 is inhaling. As a result, the consumption of the chemical solution and the electric power can be suppressed during the period when the user 10 is exhaling, and a sufficient amount of the chemical solution can be atomized during the period when the user 10 is inhaling. Therefore, the efficiency of inhalation of the drug solution can be improved.

(Modification 2)
The drive voltage supplied by the control unit 130 is not limited to the drive voltage proportional to the flow rate in the suction port 160, and may be a constant drive voltage. For example, the control unit 130 supplies the drive voltage V1 to the atomization unit 110 while the user 10 is inhaling. Further, the control unit 130 supplies the drive voltage V2 (0 <V2 <V1) to the atomization unit 110 or does not supply the drive voltage to the atomization unit 110 during the period when the user 10 is exhaling.

(Modification 3)
The control unit 130 does not supply the drive voltage to the atomizing unit 110 during the entire period during which the user 10 is inhaling, but is a part of the period during which the user 10 is inhaling (for example, when the user starts inhaling). The drive voltage may be supplied to the atomizing unit 110 only for a short time from).

(Modification example 4)
The breathing detection unit 120 has described a configuration in which the user 10 detects both the timing at which the user 10 inhales and the timing at which the user 10 exhales, but the configuration is not limited to such a configuration. For example, the breathing detection unit 120 may detect only the timing at which the user 10 inhales. In this case, the respiration detection unit 120 detects the air flow from the first end portion 161 to the second end portion 162 in the suction port 160, and from the second end portion 162 to the first end portion 161 in the suction port 160. No heading airflow is detected. Also in this case, as shown in FIGS. 8 and 9, it is possible to control to supply the drive voltage to the atomizing unit 110 only during the period when the user 10 is inhaling. Further, the control unit 130 may determine a period other than the period during which the user 10 is inhaling as a period during which the user is exhaling.

Further, the breathing detection unit 120 may detect only the timing at which the user 10 exhales. In this case, the respiration detection unit 120 detects the airflow from the second end portion 162 in the suction port 160 toward the first end portion 161 and moves from the first end portion 161 to the second end portion 162 in the suction port 160. No heading airflow is detected. In this case as well, the control unit 130 may determine a period other than the period during which the user 10 is exhaling as a period during which the user is inhaling. For example, the control unit 130 atomizes for a certain period of time (for example, several seconds) after a certain period of time (for example, a time of 0 seconds or more and 1 second or less) elapses after the period in which the user 10 is exhaling ends. A drive voltage may be supplied to the unit 110.

(Modification 5)
Although the configuration in which the drive voltage is immediately supplied to the atomization unit 110 according to the respiration of the user 10 detected by the respiration detection unit 120 has been described, the configuration is not limited to such a configuration. For example, the control unit 130 predicts the future breathing timing of the user 10 based on the periodically detected breathing timing of the user 10, and supplies the driving voltage to the atomizing unit 110 at the predicted timing. You may do it. Further, for example, the control unit 130 includes a phase synchronization circuit that outputs a drive voltage synchronized with the periodic flow rate detection result 71 output from the breath detection unit 120, and atomizes the drive voltage generated by this phase synchronization circuit. It may be supplied to the conversion unit 110. This makes it possible to improve the followability of the atomization of the drug solution to the respiration of the user 10.

FIG. 10 is a diagram showing an example of control of atomization of a drug solution according to a respiratory cycle. The breathing cycle 90 shown in FIG. 10 is the breathing cycle of the user 10.

For example, the control unit 130 identifies the respiration cycle 90 of the user 10 based on the timing of a plurality of respirations of the user 10 periodically detected by the respiration detection unit 120. The identification of the respiratory cycle 90 includes, for example, identification of the length of one cycle of the respiratory cycle 90, identification of the ratio of the period of exhalation to the period of inspiration (for example, 2: 1) in the respiratory cycle 90, and the identification of the respiratory cycle 90. Includes phase identification.

Then, the control unit 130 supplies a drive voltage to the atomization unit 110 based on the specified breathing cycle 90. For example, the control unit 130 starts supplying the drive voltage to the atomization unit 110 at a timing 91 slightly earlier than the timing when the user 10 starts inhaling. As a result, atomization of the chemical solution is started at the timing 91, and at the timing when the user 10 starts inhaling, the chemical solution is atomized to some extent, and the efficiency of inhalation of the chemical solution can be improved.

Further, the control unit 130 identifies the timing 92 at which the user 10 has the strongest inhaling force in the breathing cycle 90, and controls the timing 92 so that the drive voltage supplied to the atomization unit 110 becomes maximum. You may. As a result, the atomization density of the chemical solution is maximized at the timing 92, and the atomization density of the chemical solution can be set to the atomization density according to the force of the user 10 to inhale. In this way, the control unit 130 may control the height of the drive voltage supplied to the atomization unit 110 based on the result of predicting the breathing timing of the user 10. Thereby, the drug solution can be atomized according to the breathing intensity of the user 10 in the breathing cycle of the user 10, and the efficiency of inhalation of the drug solution can be improved.

Further, the control unit 130 stops the supply of the drive voltage to the atomization unit 110 at a timing 93 slightly earlier than the timing when the user 10 finishes inhaling. As a result, the atomization of the chemical solution is stopped at the timing 93, the atomization of the chemical solution that is not inhaled by the user 10 can be suppressed, and the efficiency of inhalation of the chemical solution can be improved.

In this way, the control unit 130 may specify the cycle of exhalation and inspiration (respiratory cycle 90) and control the amount of atomization of the drug solution at the optimum timing. This makes it possible to improve the efficiency of inhalation of the drug solution.

(Modification 6)
The breathing detection unit 120 has a rotating body (impeller 121 or a wind cup type rotating body 125) inside the suction port 160, and detects breathing based on the rotation of the rotating body, a heater 126, and a temperature measuring sensor. Although the configuration for detecting respiration using 127 and 128 has been described, the configuration is not limited to such a configuration. For example, the respiration detection unit 120 may have a microphone that converts the respiration sound of the user 10 into an electric signal, and may be configured to detect respiration based on the electric signal obtained by the microphone.

Alternatively, the respiration detection unit 120 may have, for example, a pressure sensor that detects a change in pressure near the body surface due to the respiration of the user 10, and may be configured to detect respiration based on the detection result by the pressure sensor. Alternatively, the respiration detection unit 120 may have, for example, an acceleration sensor that detects the movement of the body surface due to the respiration of the user 10, and may be configured to detect respiration based on the detection result by the acceleration sensor. Alternatively, the respiration detection unit 120 has, for example, an image pickup device that captures the body surface of the user 10, and is configured to detect respiration based on the movement of the body surface of the user 10 indicated by the image captured by the image pickup device. May be good.

10 User 41 Inhalation mask 71 Flow detection result 72 Drive voltage 90 Respiratory cycle 91-93 Timing 100 Nebulizer 101 Power supply 110 Atomizer 111 Chemical solution bottle 112 Horn oscillator 113 Mesh 120 Respiratory detection unit 121 Impeller 122 Generator 123 Lead wire 124 detection Circuit 125 Cup type rotating body 126 Heater 127, 128 Temperature measurement sensor 130 Control unit 140 Main body 141 Power supply 141a Power cord 142 Power button 150 Bottle storage 151 Base 152 Lid 153 Hinge 154 Hook 160 Suction port 161 1st end Part 162 Second end part 163 Detection part Storage part

Claims (9)

An atomizer that atomizes the chemical solution according to the supplied drive voltage,
A detection unit that detects the breathing timing of the user who inhales the drug solution atomized by the atomization unit, and a detection unit.
A control unit that controls the drive voltage supplied to the atomization unit based on the detection result by the detection unit.
A nebulizer equipped with. The nebulizer according to claim 1.
The control unit controls the drive voltage supplied to the atomization unit during the period when the user is inhaling to be higher than the drive voltage supplied to the atomization unit during the period when the user is exhaling. conduct,
Nebulizer. The nebulizer according to claim 2.
The control unit controls not to supply the drive voltage to the atomization unit during the period when the user is exhaling, but to supply the drive voltage to the atomization unit during the period when the user is inhaling. ,
Nebulizer. The nebulizer according to any one of claims 1 to 3.
The detection unit detects the intensity of the respiration and
The control unit controls the height of the drive voltage supplied to the atomization unit based on the intensity of the respiration.
Nebulizer. The nebulizer according to any one of claims 1 to 4.
The atomizing unit has a vibrator that vibrates according to the supplied drive voltage, and the chemical solution is atomized by the vibration of the vibrator.
The control unit supplies the driving voltage to the vibrator.
Nebulizer. The nebulizer according to any one of claims 1 to 5.
An inhalation port for the user to inhale the chemical solution atomized by the atomizing portion, and
A rotating body provided inside the suction port and rotated by the air flow accompanying the user's breathing, and
Equipped with
The detection unit detects the timing of the respiration based on the rotation of the rotating body.
Nebulizer. The nebulizer according to any one of claims 1 to 6.
The control unit predicts the timing of the breath and starts supplying the drive voltage to the atomization unit before the user starts inhaling.
Nebulizer. The nebulizer according to any one of claims 1 to 7.
The control unit controls the height of the drive voltage supplied to the atomization unit based on the result of predicting the timing of the respiration.
Nebulizer. The nebulizer according to any one of claims 1 to 8.
The control unit predicts the timing of the breath and stops supplying the drive voltage to the atomization unit before the user finishes inhaling.
Nebulizer.

Images