CN207591050U

CN207591050U - With the atomizer for inhaling dose monitoring function and inhale dose monitoring system

Info

Publication number: CN207591050U
Application number: CN201720336008.4U
Authority: CN
Inventors: 徐传毅; 钟强
Original assignee: Nazhiyuan Technology Tangshan Co Ltd
Current assignee: Nazhiyuan Technology Tangshan Co Ltd
Priority date: 2017-03-31
Filing date: 2017-03-31
Publication date: 2018-07-10
Anticipated expiration: 2027-03-31

Abstract

There is the atomizer for inhaling dose monitoring function and suction dose monitoring system the utility model discloses a kind of, wherein, which includes：Liquid storage component, nozzle air current monitoring component and nebulizer body；Wherein, liquid storage component is connected with nebulizer body, for storing the liquid of injection to be atomized；Nozzle air current monitoring component is connected with liquid storage component, for the air-flow output gas flow electric pressure signal according to user's air-breathing or generation of exhaling, and will be in the mouth and nose of the medical liquid spraying after nebulizer body is atomized to user；Nebulizer body is electrically connected with nozzle air current monitoring component, and for will be sprayed after the medical liquid atomizing being stored in liquid storage component, and the stream pressure electric signal exported according to nozzle air current monitoring component, analysis calculate user and suck dose, obtain user and inhale medicine information.It is provided by the utility model to have the atomizer for inhaling dose monitoring function and suction dose monitoring system sensitive, monitor user suction medicine information.

Description

Atomizer with medicine suction amount monitoring function and medicine suction amount monitoring system

Technical Field

The utility model relates to a sensor technical field, concretely relates to atomizer and inhale medicine volume monitoring system with inhale medicine volume monitoring function.

Background

Due to the continuous warming of global climate, the continuous aggravation of environmental pollution, the sudden cold and warming of climate during season change and other factors, the number of global respiratory diseases is continuously increased, and the normal life of people is seriously influenced.

At present, in order to adapt to various complicated treatment conditions and meet the high quality requirements of modern people on life, people usually use an atomizer to atomize water-soluble medicines into tiny fog particles to be inhaled by patients to relieve pains. The atomizers in the prior art are various in types and functions, and common atomizers include ultrasonic atomizers, compressed air atomizers and mesh atomizers, but most of the atomizers can only control the atomized liquid medicine amount, but cannot sensitively and accurately monitor the user inhalation amount, and the monitoring of the user inhalation amount is particularly important for treating the state of an illness.

Therefore, the prior art lacks an atomizer and a corresponding drug inhalation amount monitoring system, which can sensitively and accurately monitor the drug inhalation information of the user.

SUMMERY OF THE UTILITY MODEL

The utility model discloses an invention purpose is to prior art's defect, provides an atomizer and inhale medicine volume monitoring system with inhale medicine volume monitoring function for solve among the prior art problem that the user inhales medicine information can't be monitored out sensitively, accurately to the atomizer.

The utility model provides an atomizer with inhale medicine volume monitor function, this atomizer includes: the atomizer comprises a liquid storage part, a nozzle airflow monitoring part and an atomizer main body; wherein,

the liquid storage part is connected with the atomizer main body and is used for storing liquid medicine to be atomized and sprayed;

the nozzle airflow monitoring part is connected with the liquid storage part and used for outputting airflow pressure electric signals according to airflow generated by inhalation or exhalation of a user and spraying the liquid medicine atomized by the atomizer main body to the mouth and nose of the user;

the atomizer main body is electrically connected with the nozzle airflow monitoring part and used for atomizing the liquid medicine stored in the liquid storage part and then spraying the liquid medicine, and analyzing and calculating the medicine inhalation amount of a user according to the airflow pressure electric signal output by the nozzle airflow monitoring part to obtain the medicine inhalation information of the user.

Further, the liquid storage part includes: a cover and a receiving cavity;

the cover body is provided with a buckle mechanism which is used for hermetically buckling the cover body and the accommodating cavity;

the holding cavity is provided with an atomization port and a liquid outlet, the atomization port is connected with the atomizer main body, and the liquid outlet is connected with the nozzle airflow monitoring part.

Further, the nozzle airflow monitoring part includes: a nozzle body and an airflow sensor;

the nozzle body is connected with the liquid storage part;

and the air flow sensor is arranged in the nozzle body and used for converting the pressure of the air flow generated by inhalation or exhalation of the user and acting on the air flow sensor into an air flow pressure electric signal for output.

Further, the nebulizer body includes: the device comprises an atomization component, a signal preprocessing module, a central control module and a power supply module;

the atomization component is connected with the liquid storage component and is used for atomizing and then spraying the liquid medicine stored in the liquid storage component;

the signal preprocessing module is electrically connected with the airflow sensor in the nozzle airflow monitoring component and is used for preprocessing the airflow pressure electric signal output by the airflow sensor in the nozzle airflow monitoring component;

the central control module is respectively electrically connected with the atomization component and the signal preprocessing module and is used for controlling the atomization component to atomize the liquid medicine in the liquid storage component and analyzing and calculating the medicine inhalation amount of the user according to the airflow pressure electric signal preprocessed by the signal preprocessing module to obtain the medicine inhalation information of the user;

and the power supply module is electrically connected with the central control module and is used for providing electric energy.

Further, the nebulizer body further includes: a wireless transceiver module and/or an interactive function module;

the wireless transceiving module is electrically connected with the central control module and is used for sending the user drug absorption information obtained by the analysis and calculation of the central control module to the preset receiving equipment in a wireless communication mode;

the interactive function module is electrically connected with the central control module and is used for sending a user interactive instruction to the central control module;

wherein the user interaction instruction comprises at least one of: the system comprises an opening instruction, a closing instruction, a user information initialization instruction and a user medicine sucking information setting instruction.

Further, the nebulizer body further includes: a display module and/or an alarm module;

the display module is electrically connected with the central control module and is used for displaying the medicine suction information of the user obtained by the central control module;

the central control module is further configured to: sending an alarm control signal according to the user medicine suction information obtained by analysis and calculation;

and the alarm module is electrically connected with the central control module and is used for carrying out alarm prompt according to the alarm control signal sent by the central control module.

Further, the airflow sensor is further configured to: converting the pressure of the airflow generated by the inhalation of the user on the airflow sensor into an inhalation airflow pressure electric signal for output; converting the pressure of the airflow generated by the exhalation of the user on the airflow sensor into an exhalation airflow pressure electric signal for output;

the signal preprocessing module is further configured to: preprocessing an inspiratory airflow pressure electric signal and an expiratory airflow pressure electric signal output by an airflow sensor;

a timer and a counter are arranged in the central control module;

the central control module is further configured to: starting a timer to time when an electric signal of the pressure of the air suction flow preprocessed by the signal preprocessing module is received; and when the expiratory airflow pressure electric signal preprocessed by the signal preprocessing module is received, stopping the timer to obtain timing time, and starting the counter to count to obtain the medicine suction times of the user.

The utility model also provides a inhale medicine volume monitoring system, include: the atomizer with the function of monitoring the medicine sucking amount and the terminal equipment are provided; wherein,

and the terminal equipment is connected with the atomizer with the medicine suction amount monitoring function in a wired communication or wireless communication mode, and is used for storing and displaying the user medicine suction information obtained by analyzing and calculating the atomizer with the medicine suction amount monitoring function and sending a control instruction for controlling the atomizer with the medicine suction amount monitoring function.

Furthermore, the medicine suction amount monitoring system also comprises a large database service platform; wherein,

the terminal device is further configured to: sending the received medicine suction information of the user to a big database service platform;

the big database service platform is connected with the terminal equipment in a wired communication or wireless communication mode and used for receiving and storing the user medicine suction information sent by the terminal equipment, analyzing and comparing the received user medicine suction information with the user medicine suction information in the big database service platform to obtain user analysis information, and sending the user analysis information to the terminal equipment.

The utility model also provides a inhale medicine volume monitoring system, include: the atomizer with the function of monitoring the medicine suction amount and the large database service platform are arranged; wherein,

the large database service platform is connected with the atomizer with the medicine suction amount monitoring function in a wired communication or wireless communication mode and used for receiving and storing the user medicine suction information obtained by analyzing and calculating the atomizer with the medicine suction amount monitoring function, analyzing and comparing the received user medicine suction information with the user medicine suction information in the large database service platform to obtain user analysis information, and sending the user analysis information to the atomizer.

The utility model provides an atomizer and inhale medicine volume monitoring system with inhale medicine volume monitor function inhales or exhales the air current that produces through nozzle air current monitoring part monitoring user, can monitor user's inhaled medicine volume, inhale medicine time, inhale medicine number of times etc. and inhale medicine information sensitively, accurately, has realized the monitoring to user's inhaled medicine information. Additionally, the utility model provides an atomizer and inhale medicine volume monitoring system with inhale medicine volume monitoring function not only sensitivity and rate of accuracy are high, still have structure and simple, the low cost of manufacture technology simultaneously, are fit for large-scale industrial production's advantage.

Drawings

Fig. 1a is a functional structure block diagram of a first embodiment of an atomizer with a function of monitoring drug absorption amount provided by the present invention;

FIG. 1b is a schematic structural diagram of a first embodiment of an atomizer with a function of monitoring an amount of inhaled medicine according to the present invention;

fig. 1c is a schematic structural diagram of a liquid storage component in a first embodiment of an atomizer with a function of monitoring drug absorption amount according to the present invention;

fig. 1d is a functional structure block diagram of a signal preprocessing module in a first embodiment of the nebulizer with a function of monitoring the amount of inhaled medicine provided by the present invention;

fig. 2a is a schematic perspective view of a first airflow sensor in a first embodiment of an atomizer with a function of monitoring drug absorption amount according to the present invention;

fig. 2b is a schematic cross-sectional view of a first exemplary airflow sensor in a first embodiment of an atomizer with a function of monitoring an amount of inhaled medicine according to the present invention;

fig. 2c is a schematic structural diagram of a second exemplary airflow sensor in the first embodiment of the nebulizer with a function of monitoring the amount of inhaled medicine provided by the present invention;

fig. 2d is a schematic structural diagram of a third exemplary airflow sensor in the first embodiment of the nebulizer with a function of monitoring the amount of inhaled medicine provided by the present invention;

fig. 2e is an exploded schematic view of a fourth exemplary airflow sensor in a first embodiment of the nebulizer with an inhalation monitoring function according to the present invention;

fig. 2f is a schematic diagram of an assembled structure of a fourth example of the airflow sensor in the first embodiment of the nebulizer with a function of monitoring the amount of inhaled medicine according to the present invention;

fig. 2g is a schematic diagram of a diaphragm structure of a first polymer film of an air flow sensor in the first embodiment of the atomizer with a function of monitoring drug absorption amount according to the present invention;

fig. 2h is a schematic diagram of friction between the diaphragm and the electrode after the first polymer film of the airflow sensor in the first embodiment of the nebulizer with a function of monitoring drug absorption amount is assembled with the electrode;

FIG. 3 is a functional block diagram of a second embodiment of an atomizer with a function of monitoring the amount of inhaled medicine provided by the present invention;

fig. 4 is a functional structure block diagram of a third embodiment of the atomizer with a function of monitoring the amount of inhaled medicine provided by the present invention;

fig. 5 is a functional block diagram of a medicine inhalation monitoring system using the atomizer with medicine inhalation monitoring function shown in fig. 4;

fig. 6 is another functional structure block diagram of a medicine inhalation monitoring system using the atomizer with medicine inhalation monitoring function shown in fig. 4.

Detailed Description

The present invention will be described in detail with reference to the following embodiments in order to fully understand the objects, features and functions of the present invention, but the present invention is not limited thereto.

The utility model provides an atomizer with inhale medicine volume monitor function, this atomizer includes: the atomizer comprises a liquid storage part, a nozzle airflow monitoring part and an atomizer main body; the liquid storage part is connected with the atomizer main body and is used for storing liquid medicine to be atomized and sprayed; the nozzle airflow monitoring part is connected with the liquid storage part and used for outputting airflow pressure electric signals according to airflow generated by inhalation or exhalation of a user and spraying the liquid medicine atomized by the atomizer main body to the mouth and nose of the user; the atomizer main body is electrically connected with the nozzle airflow monitoring part and used for atomizing the liquid medicine stored in the liquid storage part and then spraying the liquid medicine, and analyzing and calculating the medicine inhalation amount of a user according to the airflow pressure electric signal output by the nozzle airflow monitoring part to obtain the medicine inhalation information of the user.

Fig. 1a is the functional structure block diagram of the first atomizer embodiment with function of monitoring drug absorption amount provided by the utility model, and fig. 1b is the structure schematic diagram of the first atomizer embodiment with function of monitoring drug absorption amount provided by the utility model. As shown in fig. 1a and 1b, the atomizer includes: a reservoir component 110, a nozzle flow monitoring component 120, and a nebulizer body 130. The liquid storage part 110 is arranged on the atomizer main body 130, is connected with the atomizer main body 130, and specifically, the liquid storage part 110 is hermetically connected with the atomizer main body 130 and is used for storing liquid medicine to be atomized and sprayed; the nozzle airflow monitoring part 120 is arranged on the liquid storage part 110, is connected with the liquid storage part 110, and is used for outputting airflow pressure electric signals according to airflow generated by inhalation or exhalation of a user and spraying the liquid medicine atomized by the atomizer main body 130 to the mouth and nose of the user; the nebulizer body 130 is electrically connected to the nozzle airflow monitoring part 120, and is configured to atomize the liquid medicine stored in the liquid storage part 110 and then spray the atomized liquid medicine, and analyze and calculate the amount of medicine inhaled by the user according to the airflow pressure electrical signal output by the nozzle airflow monitoring part 120, so as to obtain the medicine inhalation information of the user.

Optionally, the reservoir component 110 includes: a cover and a receiving cavity. Specifically, the cover body and the accommodating cavity are connected in a flip type mode, the cover body can be opened or closed, a buckle mechanism is arranged on the cover body, and the buckle mechanism is used for enabling the cover body and the accommodating cavity to be buckled in a sealing mode. When adding or pouring out the liquid medicine, only the buckle mechanism on the cover body needs to be opened, so that the cover body can be opened; when the liquid medicine is not added or poured out, only the buckle mechanism on the cover body needs to be closed, so that the cover body can be closed and is in sealed buckling with the containing cavity. The accommodating cavity is used for storing liquid medicine to be atomized and sprayed, an atomizing opening and a liquid outlet are formed in the accommodating cavity, the atomizing opening is connected with the atomizer main body 130, and the liquid outlet is connected with the nozzle airflow monitoring part 120. The atomizer body 130 atomizes the liquid medicine stored in the accommodating cavity through the atomizing port on the accommodating cavity, and sprays the liquid medicine into the nozzle airflow monitoring part 120 through the liquid outlet on the accommodating cavity, and then sprays the liquid medicine into the mouth and nose of the user.

Taking the atomizer body 130 as a compressed air atomizer as an example, the schematic structural diagram of the liquid storage component can be shown in fig. 1c, and with reference to fig. 1b and 1c, the liquid storage component 110 includes a cover 111 and a receiving cavity 112. Wherein, the middle part of the bottom surface of the accommodating cavity 112 is provided with an atomizing port 113, and the atomizing port 113 is respectively connected with the atomizer main body 130 and the airflow channel 114; an outlet 115 is formed in an upper portion of a side wall of the accommodation cavity 112, and the outlet 115 is connected to the nozzle airflow monitoring part 120. A pipette 116 is disposed within the receiving cavity 112 adjacent the airflow passage 114 and a barrier 117 is disposed adjacent the air outlet of the airflow passage 114. The liquid suction pipe 116 is used for sucking the liquid medicine stored in the accommodating cavity 112, the compressed air generated by the atomizer body 130 flows in from the atomizing opening 113 and flows into the accommodating cavity 112 through the air flow passage 114, the compressed air forms high-speed air flow when passing through a fine air outlet of the air flow passage 114, the generated negative pressure drives the liquid medicine in the liquid suction pipe 116 to be sprayed onto the obstacle 117 together, and liquid drops are splashed to the periphery under high-speed impact to be changed into mist particles to be sprayed out from the liquid outlet 115.

Optionally, the nozzle airflow monitoring part 120 includes: a nozzle body (not shown) and an airflow sensor (not shown). Wherein, the nozzle body sets up on liquid storage part 110, and it links to each other with liquid storage part 110, and the nozzle body can adopt the atomizer nozzle among the prior art, for example: the nozzle with a cylindrical structure shown in fig. 2b can be selected by those skilled in the art according to actual needs, and is not limited herein; the air flow sensor is arranged in the nozzle body and used for converting the pressure of air flow generated by inhalation or exhalation of a user, which acts on the air flow sensor, into an air flow pressure electric signal for output.

The airflow sensor may be a friction power generation type airflow sensor and/or a piezoelectric power generation type airflow sensor, that is, the airflow sensor may be an airflow sensor manufactured by using a friction generator and/or a piezoelectric generator, and a person skilled in the art may select the airflow sensor according to actual needs, which is not limited herein.

In addition, one air flow sensor may be provided inside the nozzle body, or a plurality of air flow sensors may be provided. The air flow sensor is arranged in the nozzle body, so that the structure is simple, the realization is easy, and the atomizer with the function of monitoring the medicine suction amount is simpler and more convenient in structure; the advantage that sets up a plurality of air current sensors in the inside of nozzle body lies in can inducting the pressure that the air current that the user breathed in or exhale the production was used on it in the equidirectional response, makes this atomizer with inhale medicine volume monitor function more sensitive, monitoring result more accurate.

When an airflow sensor is arranged in the nozzle body, the airflow sensor is electrically connected with the atomizer main body 130, and an airflow pressure electric signal output by the airflow sensor is preprocessed by the atomizer main body 130 and then is analyzed and calculated to obtain user medicine suction information such as the user medicine suction amount; when a plurality of airflow sensors are arranged in the nozzle body, the airflow sensors can be respectively and electrically connected with the atomizer main body 130, and a plurality of airflow pressure electric signals correspondingly output by the airflow sensors are respectively subjected to preprocessing of the atomizer main body 130 and then analyzed and calculated to obtain user medicine suction information such as user medicine suction amount. It should be noted that, when the plurality of airflow sensors are disposed inside the nozzle body, a person skilled in the art can set the connection relationship between the plurality of airflow sensors and the atomizer main body 130 according to actual conditions, and the present invention is not limited thereto.

Further, when a plurality of air flow sensors are provided inside the nozzle body, the plurality of air flow sensors may be provided inside the nozzle body in a longitudinally overlapping manner along the longitudinal direction of the nozzle body; alternatively, the plurality of air flow sensors may be disposed inside the nozzle body in a tangential arrangement or other type of arrangement along a lateral direction of the nozzle body. It should be noted that, when a plurality of airflow sensors are disposed inside the nozzle body, a person skilled in the art can set the arrangement of the plurality of airflow sensors disposed inside the nozzle body according to actual conditions, and the present invention is not limited thereto.

Optionally, the nebulizer body 130 further comprises: the atomization component 131, the signal preprocessing module 132, the central control module 133 and the power supply module 134. The atomization component 131 is connected with the liquid storage component 110 and is used for atomizing and spraying the liquid medicine stored in the liquid storage component 110; the signal preprocessing module 132 is electrically connected to the air flow sensor in the nozzle air flow monitoring component 120, and is configured to preprocess the air flow pressure electrical signal output by the air flow sensor in the nozzle air flow monitoring component 120; the central control module 133 is electrically connected to the atomizing component 131 and the signal preprocessing module 132, and is configured to control the atomizing component 131 to atomize the liquid medicine in the liquid storage component 110, and analyze and calculate the amount of medicine inhaled by the user according to the electric signal of the air pressure preprocessed by the signal preprocessing module 132, so as to obtain medicine inhalation information of the user; the power supply module 134 is electrically connected to the central control module 133 for supplying power to the central control module 133. The central control module 133 supplies power to the atomizing part 131 and the signal preprocessing module 132 by using the power supplied from the power supply module 134. Wherein, the user drug inhalation information comprises: the user medicine suction information comprises the user medicine suction amount, the user medicine suction time, the user medicine suction times, the time interval between two adjacent times of medicine suction and the like.

The atomizing part 131 is a part that can atomize the liquid medicine stored in the liquid storage part 110 and spray the atomized liquid medicine in the prior art, and can be selected by those skilled in the art as needed, and is not limited herein.

The number of the signal preprocessing modules 132 may be one or more, and those skilled in the art can select the number according to needs, which is not limited herein. However, it should be noted that the number of signal preprocessing modules 132 should be the same as the number of air flow sensors in the nozzle air flow monitoring section 120, so that the signal preprocessing modules 132 can be electrically connected to the air flow sensors in the nozzle air flow monitoring section 120 in a one-to-one correspondence.

Specifically, if one air flow sensor is disposed inside the nozzle body in the nozzle air flow monitoring part 120, the number of the signal preprocessing modules 132 in the nebulizer main body 130 is only one, and the signal preprocessing modules 132 are electrically connected to the air flow sensor and the central control module 133 in the nebulizer main body 130, respectively; if a plurality of airflow sensors are disposed inside the nozzle body of the nozzle airflow monitoring component 120, the number of the signal preprocessing modules 132 in the nebulizer main body 130 is the same as or more than the number of the airflow sensors disposed inside the nozzle body of the nozzle airflow monitoring component 120, and the signal preprocessing modules 132 are respectively electrically connected to the airflow sensors in a one-to-one correspondence, and meanwhile, the signal preprocessing modules 132 are also respectively electrically connected to the central control module 133 in the nebulizer main body 130, for example: if the inside of the nozzle body in the nozzle airflow monitoring part 120 is provided with 2 airflow sensors, the number of the signal preprocessing modules 132 in the atomizer main body 130 is the same as the number of the 2 airflow sensors arranged inside the nozzle body in the nozzle airflow monitoring part 120, and is also 2, and the input ends of the 2 signal preprocessing modules 132 are respectively electrically connected with the output ends of the 2 airflow sensors in a one-to-one correspondence manner, and meanwhile, the output ends of the 2 signal preprocessing modules 132 are respectively electrically connected with different signal input ends of the central control module 133 in the atomizer main body 130 in a one-to-one correspondence manner.

Further, as shown in fig. 1d, the signal preprocessing module 132 may include: a rectifying module 1321, a filtering module 1322, an amplifying module 1323 and an analog-to-digital conversion module 1324. The rectification module 1321 is electrically connected to the airflow sensor in the nozzle airflow monitoring component 120, and is configured to rectify an airflow pressure electrical signal output by the airflow sensor; the filtering module 1322 is electrically connected with the rectifying module 1321, and is configured to filter the rectified airflow pressure electrical signal to filter interference noise; the amplifying module 1323 is electrically connected with the filtering module 1322 and is used for amplifying the filtered airflow pressure electric signal; the analog-to-digital conversion module 1324 is electrically connected to the amplification module 1323, and is configured to convert the analog airflow pressure electrical signal output by the amplification module 1323 into a digital airflow pressure electrical signal and output the converted digital airflow pressure electrical signal to the central control module 133. It should be noted that the above modules (i.e., the rectifying module 1321, the filtering module 1322, the amplifying module 1323 and the analog-to-digital converting module 1324) may be selected according to the needs of those skilled in the art, and are not limited herein. For example, the flow pressure electrical signal output by the flow sensor in the nozzle flow monitoring unit 120 does not need to be rectified, and the rectifying module 1321 may be omitted.

Further, the air flow sensor in the nozzle air flow monitoring section 120 may distinguish between the air flow pressure electrical signals converted from the pressure on which the air flow generated by the inhalation or exhalation of the user acts. Specifically, the air flow sensor in the nozzle air flow monitoring component 120 is further configured to: converting the pressure of the airflow generated by the inhalation of the user on the airflow sensor into an inhalation airflow pressure electric signal for output; the pressure of the airflow generated by the exhalation of the user acting on the airflow sensor is converted into an exhalation airflow pressure electric signal to be output. For example, the inspiratory airflow pressure electrical signal is a positive airflow pressure electrical signal, and the expiratory airflow pressure electrical signal is a negative airflow pressure electrical signal. In this case, the signal preprocessing module 132 is further configured to: and preprocessing the inspiratory airflow pressure electric signal and the expiratory airflow pressure electric signal output by the airflow sensor.

Optionally, a timer and a counter are disposed inside the central control module 133, and the central control module 133 is further configured to: when receiving the electrical signal of the pressure of the inspiratory air flow preprocessed by the signal preprocessing module 132, starting a timer to time; when the expiratory airflow pressure electric signal preprocessed by the signal preprocessing module 132 is received, the timer is stopped to obtain timing time, and the counter is started to count to obtain the medicine suction times of the user.

It should be understood that the schematic structural diagram of the first embodiment of the atomizer with a drug absorption amount monitoring function shown in fig. 1b is only an illustrative one, and the atomizer with a drug absorption amount monitoring function provided by the present invention can also be applied to atomizers of other structures in the prior art, and those skilled in the art can apply the present invention according to actual needs, and the present invention is not limited herein. In addition, the schematic structural diagram of the liquid storage part in the first embodiment of the nebulizer with a function of monitoring a drug absorption amount shown in fig. 1c is only a schematic structure, and a person skilled in the art can specifically set the structure of the liquid storage part according to actual needs, and the structure is not limited here.

For convenience of understanding, the air flow sensor in the first embodiment of the nebulizer having a function of monitoring a drug absorption amount provided by the present invention is described in detail by way of example one to example four. Among them, the first to fourth examples are a friction power generation type airflow sensor.

Example 1

Fig. 2a and fig. 2b are a schematic perspective structure diagram and a schematic cross-sectional structure diagram of a first airflow sensor in a first embodiment of an atomizer with a drug absorption amount monitoring function according to the present invention. As shown in fig. 2a and 2b, the airflow sensor includes: a housing 211, a diaphragm assembly 212, and an electrode assembly 213. An accommodating chamber is formed inside the housing 211, an air inlet 2111 is formed on the side wall of the housing 211, an air outlet 2112 is formed on the bottom wall of the housing 211, and the air inlet 2111 and the air outlet 2112 are respectively connected with the accommodating chamber to form an air flow passage, so that air flow generated by inhalation or exhalation of a user passes through the air flow passage; two ends of the diaphragm assembly 212 are fixedly arranged in the accommodating chamber inside the housing 211, and a vibration gap is formed between the diaphragm assembly 212 and the electrode assembly 213 and the bottom wall of the housing 211 respectively, and the diaphragm assembly 212 vibrates reciprocally relative to the electrode assembly 213 and the bottom wall of the housing 211 under the driving of the airflow inside the accommodating chamber; the electrode assembly 213 is a signal output end of the airflow sensor, is located in the accommodating chamber inside the housing 211, and is disposed opposite to the diaphragm assembly 212, and the reciprocally vibrating diaphragm assembly 212 and the electrode assembly 213 and/or the bottom wall of the housing 211 rub against each other to generate an airflow pressure electrical signal, which is output by the electrode assembly 213.

The diaphragm assembly 212 is a flexible assembly, preferably in a strip shape, and the strip-shaped diaphragm assembly 212 is located in the accommodating chamber inside the housing 211, and two ends of the strip-shaped diaphragm assembly are fixedly disposed. Specifically, a diaphragm ring 2113, a first washer 2114 and a second washer 2115 are disposed in the accommodating chamber inside the housing 211. Wherein, vibrating diaphragm ring 2113 is annular, and the both ends of vibrating diaphragm subassembly 212 are fixed respectively and are set up on vibrating diaphragm ring 2113, and are formed with the air current passageway between the side of vibrating diaphragm subassembly 212 and vibrating diaphragm ring 2113, and under the drive of the inside air current of holding chamber, vibrating diaphragm subassembly 212 can be on vibrating diaphragm ring 2113 for electrode subassembly 213 and the diapire reciprocating vibration of shell 211. The first gasket 2114 is in a ring shape with a notch and is positioned between the diaphragm ring 2113 and the electrode assembly 213, so that a vibration gap is formed between the diaphragm assembly 212 and the electrode assembly 213; second washer 2115 is also in the form of a notched ring and is positioned between diaphragm ring 2113 and the bottom wall of housing 211, such that a vibration gap is formed between diaphragm assembly 212 and the bottom wall of housing 211.

Optionally, the airflow sensor may further include a friction film assembly disposed on a lower surface of the electrode assembly 213, and the diaphragm assembly 212 forms a vibration gap with the friction film assembly and a bottom wall of the housing 211, respectively, and the diaphragm assembly 212 may vibrate reciprocally with respect to the friction film assembly and the bottom wall of the housing 211 under the driving of the airflow inside the accommodating chamber to contact and rub the friction film assembly and/or the bottom wall of the housing 211 to generate an airflow pressure electrical signal.

Example two

Fig. 2c is a schematic structural diagram of a second exemplary airflow sensor in the first embodiment of the nebulizer with an inhalation monitoring function according to the present invention. As shown in fig. 2c, the airflow sensor includes: a shield case 221, an insulating layer 222 provided on a part or all of an inner side surface of the shield case 221, and at least one sensing unit. Wherein, the shielding case 221 is provided with at least two air vents 2211, and the air flow generated by the inhalation or exhalation of the user passes through the air vents 2211; specifically, one air vent 2211 is disposed in the middle of the left and right sides of the shielding shell 221, and the air flow can enter from one air vent 2211 and flow out from the other air vent 2211. The sensing unit includes: at least one pinned layer and a free layer; at least one fixed layer is fixedly arranged on the shielding shell 221; the free layer is provided with a fixed part and a friction part; the fixed part of the free layer is fixedly connected with at least one fixed layer or shielding shell 221; the free layer is rubbed with at least one of the fixed layer and/or the shield shell 221 by the rubbing part. At least one fixed layer is a signal output end of the airflow sensor, or at least one fixed layer and the shielding shell 221 are signal output ends of the airflow sensor.

Wherein, fig. 2c only schematically shows a schematic structural diagram of an embodiment of the airflow sensor, which includes a sensing unit, the sensing unit includes: a fixed layer and a free layer 2231. At this time, the air inlet direction of the air flow is parallel to the plane of the fixed layer in the air flow sensor. Specifically, the fixing layer is fixed below the inside of the shield case 221. The fixed layer is a high molecular polymer insulating layer 2233 with one side surface plated with an electrode 2232, and the insulating layer 222 is disposed between the one side surface plated with the electrode 2232 of the high molecular polymer insulating layer 2233 and the inner side surface of the shielding shell 221. The fixed portion of the free layer 2231 is fixedly connected to the polymer insulating layer 2233 through a spacer 2234, the free layer 2231 rubs against the surface of the polymer insulating layer 2233 on the side not coated with the electrode 2232 and/or the shielding case 221 through a friction portion, and the electrode 2232 and the shielding case 221 are signal output terminals of the airflow sensor.

Example three

Fig. 2d is a schematic structural diagram of an airflow sensor in the first embodiment of the nebulizer with an inhalation monitoring function according to the present invention. As shown in fig. 2d, the airflow sensor includes: a case 231, an electrode 232 disposed inside the case 231, and a first polymer film 233. The housing 231 is a hollow structure, and the electrode 232 and the first polymer film 233 are sleeved inside the housing. The central axes of the housing 231, the electrode 232 and the first polymer film 233 are located on the same straight line, and the surfaces of the three are separated from each other. The housing 231 may be a metal case or a non-metal insulating case. Structurally, housing 231 further includes first and second oppositely disposed end faces 2311 and 2312. The first end face 2311 is provided with at least one air inlet hole for air to flow in, and the second end face 2312 is provided with at least one air outlet hole for air to flow out. Specifically, at least one of the first end face 2311 and the second end face 2312 may be integrally provided on the housing 231, thereby better protecting the internal structure of the airflow sensor; alternatively, at least one of the first end surface 2311 and the second end surface 2312 may be detachably disposed on the housing 231, so as to facilitate replacement, detachment, and the like of the housing 231 by a user.

The electrode 232 is disposed inside the case 231 along the central axis direction of the case 231, and the surface thereof may be a metal electrode layer or a non-metal electrode layer. The electrode 232 may have a solid structure or a hollow structure. Preferably, the electrode 232 has a hollow structure inside, so that a gas flow channel is formed between the electrode 232 and the first polymer film 233, and/or a gas flow channel is formed inside the electrode 232, and at the same time, the electrode 232 with the hollow structure has a smaller weight, so that the whole gas flow sensor is lighter; more preferably, a through hole is further formed on the electrode 232 to increase the size of the air flow in the air flow channel and improve the friction effect. The first polymer film 233 is a cylindrical film covering the electrode 232, and the shape of the first polymer film 233 matches the shape of the electrode 232. The first polymer film 233 is further provided with at least one diaphragm, and when the air flow passes through the air inlet hole, the air flow drives the diaphragm to vibrate through the air flow channel. Each diaphragm has a fixed end integrally connected with the first polymer film 233 and a free end capable of rubbing against the electrode 232 under the driving of the airflow. Wherein, the stiff end setting of every vibrating diaphragm is in the one side that is close to the inlet port, and the free end setting of every vibrating diaphragm is in the one side that is close to the venthole, and this kind of setting mode is used for guaranteeing that the air current blows in from the inlet port time, and the air current blows in from the direction of the stiff end of every vibrating diaphragm to can realize better friction effect (inventor discovers in the experiment, when the air current blows in from the direction of vibrating diaphragm stiff end, the effect of shaking and the friction effect of vibrating diaphragm free end are all preferred). And, the electrode 232 serves as a signal output terminal of the air flow sensor.

Specifically, the first polymer film 233 is spaced from the electrode 232 by a predetermined distance, which is used to form an airflow channel between the electrode 232 and the first polymer film 233, and at the same time, the distance is also used to provide a sufficient vibration space for the diaphragm on the first polymer film 233. In specific implementation, the preset distance is controlled to be 0.01-2.0 mm. Under the condition that no airflow flows in, no friction is generated between the diaphragm on the first polymer film 233 and the surface of the electrode 232, and no induced charge is generated; when the airflow flows in from the air inlet hole on the first end face 2311, the free end of the vibrating diaphragm is vibrated by the vortex generated by the airflow, and the vibrating free end is in contact separation with the surface of the electrode 232 at a corresponding frequency, that is, the vibrating diaphragm is in friction with the surface of the electrode 232, so that induced charges are generated on the electrode 232. The electrode 232 is used as a signal output end of the airflow sensor, and a lead connected to the electrode 232 is disposed on the electrode 232, so that the induced charges on the surface of the electrode 232 are output as an induced electrical signal through the lead. The electrode 232 and a grounding point in an external circuit can jointly form a current loop, so that the electric signal output is realized in a single electrode mode. The electrical signal includes electrical signal parameters related to a voltage value, a frequency value, and the like. The inventor has found that the larger the flow velocity of the air flow is, the higher the vibration frequency of the diaphragm is, and the larger the output voltage value and frequency value are. Furthermore, the inventor further finds that, from the measured values, the airflow velocity is in a direct relation with the voltage value V and the frequency f, that is, a specific voltage value or frequency value corresponds to a certain airflow velocity value, so that the flow velocity and the flow rate of the airflow can be further obtained by calculating by obtaining the output voltage value and frequency value.

Example four

Fig. 2e to fig. 2h respectively show the schematic structural diagram of the fourth example of the airflow sensor in the first embodiment of the nebulizer with a function of monitoring the amount of inhaled medicine provided by the present invention from different angles. Wherein, fig. 2e shows the utility model provides an air current sensor example four decomposition structure schematic diagram in the atomizer embodiment one with inhale medicine volume monitor function, fig. 2f shows the utility model provides an air current sensor example four's in the atomizer embodiment one with inhale medicine volume monitor function structure schematic diagram after the equipment, fig. 2g shows the utility model provides an air current sensor example four's in the atomizer embodiment one with inhale medicine volume monitor function vibrating diaphragm structure schematic diagram, fig. 2h shows the utility model provides an air current sensor example four's in the atomizer embodiment one with inhale medicine volume monitor function vibrating diaphragm and electrode assembly between the friction schematic diagram of an organic whole back vibrating diaphragm and electrode. As shown in fig. 2e to 2h, the airflow sensor includes: a case 241, and a first polymer film 243, a support structure 244, and an electrode 242 sequentially provided inside the case 241. The supporting structure 244 is disposed outside the electrode 242, the first polymer film 243 is disposed outside the electrode 242 and the supporting structure 244, and a diaphragm 2431 is further disposed on the first polymer film 243.

Specifically, the case 241 will be described first. In terms of shape, the shape of the case 241 may be a hollow case having a shape such as a cylindrical shape, a prismatic shape, a circular truncated cone shape, or a truncated pyramid shape, and the shape of the case 241 is preferably a cylindrical shape. The housing 241 may be a metal housing or a non-metal insulating housing. Structurally, the housing 241 further includes a first end face 2411 and a second end face 2412. Wherein, the first end face 2411 is provided with at least one air inlet hole for air flow to flow in; the second end face 2412 is provided with at least one air outlet hole for air to flow out. The air inlet holes and the air outlet holes can be multiple in number and can be net-shaped air holes or hole-shaped air holes. As shown in fig. 2f, fig. 2f is an assembled structural schematic view corresponding to the exploded structural schematic view in fig. 2e, and as can be seen from fig. 2f, the air flow flows in from the air inlet holes on the first end face 2411, wherein the number of the air inlet holes is plural, and the air inlet holes are in the shape of hole-shaped air holes. Here, it is to be noted that the shapes and the numbers of the air holes on the first end face 2411 and the air holes on the second end face 2412 may be set by those skilled in the art according to practical situations, and the present invention is not limited thereto.

The casing 241 is internally sleeved with an electrode 242 and a first polymer film 243, wherein the positional relationship among the three is as follows: the central axes of the casing 241, the electrode 242 and the first polymer film 243 are located on the same straight line, the inner diameter of the first polymer film 243 is larger than the outer diameter of the electrode 242, and the inner diameter of the casing 241 is larger than the outer diameter of the first polymer film 243. Namely: a certain gap is formed between the case 241 and the first polymer film 243, and between the first polymer film 243 and the electrode 242.

The electrode 242 and the first polymer film 243 will be described in detail. The electrodes 242 will be described first. Specifically, the electrode 242 is disposed along the central axis direction of the housing 241, and the shape of the electrode 242 may be a cylindrical shape, a prismatic shape, a circular truncated cone shape, a truncated pyramid shape, or the like; in order to increase the frictional area of the electrode 242, the electrode 242 preferably has a prismatic or truncated pyramid shape whose side surface is flat. For example, as shown in fig. 2h, the electrode 242 shown in fig. 2h has a hollow triangular prism shape. Structurally, the electrode 242 may be either a solid structure or a hollow structure. Preferably, the interior of the electrode 242 is a hollow structure, so that a gas flow channel is formed between the electrode 242 and the first polymer film 243, and/or a gas flow channel is formed inside the electrode 242, and at the same time, the weight of the electrode 242 with the hollow structure is smaller, so that the whole gas flow sensor is lighter; more preferably, a through hole is further formed on the electrode 242 to communicate with the inside and the outside, so as to increase the size of the air flow in the air flow passage, thereby further improving the friction effect.

Next, the first polymer film 243 will be described. Specifically, the shape of the first polymer film 243 may be various shapes such as a hollow cylindrical shape, a hollow prismatic shape, a hollow circular truncated cone shape, and a hollow truncated cone shape in accordance with the shape of the electrode 242; in order to increase the contact area between the first polymer film 243 and the electrode 242 during rubbing, the first polymer film 243 preferably has a hollow prism shape or a hollow truncated pyramid shape having a side surface, and the shapes of the first polymer film 243 and the electrode 242 are preferably matched. That is, if the electrode 242 has a cylindrical shape, the first polymer film 243 has a hollow cylindrical shape; if the electrode 242 has a triangular prism shape, the first polymer film 243 has a hollow triangular prism shape. For example, as shown in fig. 2h, the first polymer thin film shown in fig. 2h matches the shape of the electrode, and in fig. 2h, if the electrode 242 has a triangular prism shape, the shape of the first polymer thin film 243 corresponds to a hollow triangular prism shape.

Specifically, when the shapes of the case 241 and the electrode 242 are cylindrical or prismatic, and the shape of the first polymer film 243 is hollow cylindrical or hollow prismatic, the inner diameter of the first polymer film 243 is larger than the outer diameter of the electrode 242, and the inner diameter of the case 241 is larger than the outer diameter of the first polymer film 243, so that a gap is formed between the case 241 and the first polymer film 243, and between the first polymer film 243 and the electrode 242. When the casing 241 and the electrode 242 are in the shape of a circular truncated cone or a truncated pyramid and the first polymer film 243 is in the shape of a hollow circular truncated cone or a hollow truncated pyramid, the inner diameter of the upper surface of the first polymer film 243 is larger than the outer diameter of the upper surface of the electrode 242, and the inner diameter of the upper surface of the casing 241 is larger than the outer diameter of the upper surface of the first polymer film 243; the inner diameter of the lower surface of the first polymer film 243 is larger than the outer diameter of the lower surface of the electrode 242, and the inner diameter of the lower surface of the case 241 is larger than the outer diameter of the lower surface of the first polymer film 243, so that a gap is formed between the case 241 and the first polymer film 243 and between the first polymer film 243 and the electrode 242. The first polymer film 243 is hollow, that is, the first polymer film 243 has a hollow structure with two ends penetrating through, and in the above description, the upper and lower surfaces of the first polymer film 243 refer to: the first polymer film 243 has two sides respectively defined on the first end face 2411 and the second end face 2412 of the case 241. Similarly, when the electrode 242 is hollow, the upper and lower surfaces of the electrode 242 are similarly defined.

Structurally, when the first polymer film 243 has a plurality of side surfaces, at least one diaphragm 2431 is further disposed on each side surface of the first polymer film 243, as shown in fig. 2g, and two diaphragms 2431 are disposed on each side surface of the first polymer film in fig. 2 g. Of course, it is understood that, in the implementation, the number of the vibrating membranes 2431 on each side surface of the first polymer film is not limited to two, and may be one, or may be multiple, and the specific number is set by a person skilled in the art according to the actual situation, and the present invention is not limited to this. Wherein, the diaphragm 2431 is specifically configured to: after the air flow passes through the air inlet hole, the air flow enters the air flow channel to drive the diaphragm 2431 to vibrate. However, the gas flow channel may be implemented in various ways, for example, the gas flow channel may be formed between the electrode 242 and the first polymer film 243, may be formed inside the electrode 242, or may be formed between the electrode 242 and the first polymer film 243 and inside the electrode 242 at the same time. Specifically, in the first implementation, the gas flow channel is formed in the gap between the electrode 242 and the first polymer film 243; in the second implementation manner, besides forming the gas flow channel in the gap between the electrode 242 and the first polymer film 243, the gas flow channel may be further formed inside the electrode 242, for example, a plurality of through holes communicating inside and outside are provided inside the electrode 242, or the inside of the electrode 242 is provided with a hollow structure, etc., in short, providing the gas flow channel inside the electrode 242 can be more beneficial to the accelerated flow of the gas flow, thereby achieving a more desirable friction effect. The above-mentioned airflow channels can be flexibly arranged as required by those skilled in the art.

Next, the structure of the diaphragm 2431 will be described. The structure of the diaphragm 2431 is specifically as follows: each of the diaphragms 2431 on the first polymer film 243 has a fixed end integrally connected with the first polymer film 2431 and a free end capable of rubbing against the electrode under the driving of the airflow. Wherein, vibrating diaphragm 2431's stiff end setting is in the one side that is close to the inlet port, and vibrating diaphragm 2431's free end setting is in the one side that is close to the venthole, and this kind of setting mode is used for guaranteeing when the air current blows in from the inlet port, and the air current blows in from the direction of the stiff end of every vibrating diaphragm to can realize better friction effect. Preferably, the diaphragm 2431 may be a diaphragm that is cut from the first polymer film 243 in advance to form a preset shape, and accordingly, a vacant portion formed on the first polymer film 243 after the diaphragm 2431 is cut can better enter and exit an air flow, so as to improve a friction effect; moreover, the free end of the diaphragm 2431 can reciprocate under the drive of the airflow, that is: the vibrating diaphragm 2431 is driven by the airflow acting force to generate vibration with corresponding frequency at the above-mentioned vacant part, and the vibration can make the free end of the vibrating diaphragm 2431 generate friction with the surface of the electrode 242, so as to realize the effect that the vibrating diaphragm 2431 generates friction under the driving of the airflow acting force. Furthermore, a person skilled in the art can design the structure of the vibrating diaphragm 2431 to be a structure capable of achieving continuous vibration by fully utilizing inertia according to practical experimental conditions, for example, the size of the free end of the vibrating diaphragm 2431 is designed to be slightly larger than the size of the fixed end of the vibrating diaphragm 2431, so that after the free end of the vibrating diaphragm 2431 is vibrated by the airflow acting force, the vibrating diaphragm 2431 in vibration can continuously vibrate under the inertia effect, and the inertia effect and the airflow effect act on the vibrating diaphragm 2431 at the same time, so that the vibration effect of the vibrating diaphragm 2431 is further increased, and the friction effect can be further improved. Of course, in other embodiments of the present invention, a plurality of vibrating diaphragms with preset shapes may be fixed on the first polymer film 243, and here, the present invention does not limit the specific setting mode of the vibrating diaphragm 2431, as long as the contact friction effect can be achieved. The shape of the diaphragm 2431 may be rectangular, triangular, polygonal, or fan-shaped, and the length of the diaphragm 2431 may be adaptively set by a person skilled in the art according to the shape of the diaphragm, so as to avoid the unstable vibration or the inability to start vibration of the diaphragm due to too long or too short length of the diaphragm. When the number of the diaphragms 2431 is plural, the plural diaphragms are arranged on the first polymer film 243 in an array manner, and when the first polymer film 243 is in a hollow prism shape, one or more diaphragms may be arranged on each side surface of the hollow prism-shaped first polymer film 243 to improve the friction effect. As shown in fig. 2g, the first polymer film shown in fig. 2g is a hollow triangular prism, the vibrating diaphragm 2431 is a plurality of rectangular vibrating diaphragms respectively disposed on each side surface of the first polymer film, and one side of each rectangular vibrating diaphragm is connected to the first polymer film, so as to form a fixed end of the rectangular vibrating diaphragm; the remaining three sides are separated to form the free end of the rectangular diaphragm. Moreover, as can be seen from fig. 2g, the number of the diaphragms may be multiple, and the diaphragms in fig. 2g are arranged on the first polymer film in an array manner.

Specifically, in order to facilitate the rubbing, the first polymer film 243 is spaced apart from the electrode 242 by a predetermined distance, and the predetermined distance is used to provide a sufficient vibration space for the diaphragm on the first polymer film 243. In specific implementation, the preset distance can be controlled to be between 0.01 and 2.0 mm. Specifically, the preset distance may be implemented in the following two ways: in the first implementation manner, both ends of the electrode 242 are respectively fixed to the inner walls of the first end face 2411 and the second end face 2412 of the casing 241, and both ends of the first polymer film 243 are also respectively fixed to the inner walls of the first end face 2411 and the second end face 2412 of the casing 241, so that the casing 241 and the first polymer film 243 are kept separated after being fixed, and the preset distance exists between the electrode 242 and the first polymer film 243 after being fixed. In the second implementation manner, in order to prevent the middle portion of the first polymer film 243 and the electrode 242 from contacting each other and being unable to be effectively separated, there are further provided between the electrode 242 and the first polymer film 243: and at least one supporting structure 244, wherein the supporting structure 244 is used for forming a gap between the electrode 242 and the first polymer film 243, so that the free end of the diaphragm on the first polymer film 243 is contacted and separated with the electrode 242. In a specific implementation, when the supporting structure 244 is provided, the supporting structure 244 may be integrally provided on the side surface of the electrode 242 opposite to the first polymer film 243 or on the side surface of the first polymer film 243 opposite to the electrode 242, so as to prevent one surface of the first polymer film 243 from continuously contacting the electrode 242 due to the falling off of the supporting structure 244 and the like, and further, a more ideal friction effect cannot be achieved; alternatively, the support structure 244 may be configured to be removable to facilitate removal and replacement of the support structure 244 by a user. Wherein, the thickness of the supporting structure 244 is preferably between 0.01 mm and 2.0mm, and those skilled in the art can also set a plurality of groups of supporting structures 244 with different thicknesses, so that the user can select the supporting structures 244 with different thicknesses to disassemble and replace according to different situations in practice. The number of the supporting structures 244 may be one or more. When the number of the support structures 244 is plural, every adjacent two support structures 244 are spaced apart from each other by a predetermined distance. Wherein the predetermined distance ensures that each diaphragm is disposed between each adjacent two of the support structures 244. Namely: a corresponding diaphragm is disposed at a portion of the first polymer film 243 not in contact with the support structure 244, and the diaphragm can vibrate under the driving action of the airflow, and the vibration process of the diaphragm is not affected by the support structure 244. In short, the support structure 244 can ensure effective separation between the first polymer film 243 and the electrode 242, so as to prevent two friction interfaces from being separated after contacting, thereby improving the friction effect. The two implementations described above can be used either alone or in combination.

After the structure of the airflow sensor is described, the operation principle of the airflow sensor is described as follows:

when no airflow flows in, no friction is generated between the electrode 242 and the first polymer film 243, so no induced charge is generated; the electrodes 242 and the first polymer thin film 243 are usually made of materials with opposite polarities (for example, the electrodes are usually made of materials with volatile electrons, and the first polymer thin film is usually made of materials with readily available electrons), and at this time, the predetermined distance between the electrodes 242 and the first polymer thin film 243 is small, so that the diaphragm on the first polymer thin film 243 is adsorbed on the surface of the electrodes 242. When the airflow flows in from the air inlet hole on the first end surface of the casing 241, the vortex generated by the airflow vibrates the free end of the diaphragm, and the vibrating free end makes contact and separation with the surface of the electrode 242 at a corresponding frequency, that is, the diaphragm on the first polymer film 243 makes friction with the surface of the electrode 242, so that the diaphragm and the electrode 242 generate corresponding induced charges. In specific implementation, as shown in fig. 2h, fig. 2h is a schematic diagram of friction between a diaphragm and an electrode on a first polymer film. Wherein, the electrode 242 in fig. 2h is disposed inside the first polymer film 243, and there is a certain preset distance between the electrode 242 and the first polymer film 243, when the airflow flows in, the vibrating diaphragm 2431 vibrates up and down under the driving of the airflow, and the electrode 242 is in rapid contact separation, that is, the surface of the vibrating diaphragm 2431 and the surface of the electrode 242 generate friction, so as to generate induced charges, and the induced charges flow out from the electrode 242, so as to output corresponding electrical signals. The electrode 242 and a grounding point in an external circuit together form a current loop, so that the electric signal output is realized in a single electrode manner.

In addition, the airflow sensor with the structure mainly generates electricity by means of contact friction between the first polymer film and the electrode, and in the concrete implementation, a person skilled in the art can make various changes and deformations to the internal structure of the airflow sensor:

for example, the electrodes 242 can be further implemented by the following two schemes:

the first scheme is as follows: the electrode 242 includes only a single metal electrode layer, and accordingly, the free end of each diaphragm on the first polymer film 243 can rub against the metal electrode layer in the electrode 242 under the driving of the airflow. Because metal and high molecular polymer rub each other, the metal is more likely to lose electrons, so that the surface of the electrode 242 is set as a metal electrode layer, and the metal electrode and the high molecular polymer (i.e., the first high molecular film 243) rub each other, which can effectively enhance the generation of induced charges and increase the sensitivity of the output electrical signal. Here, the polarity of the electrode 242 is opposite to that of the first polymer thin film 243, so that the electrode 242 is very likely to lose electrons, and the first polymer thin film 243 is likely to obtain electrons. Namely: the metal electrode layer is easy to lose electrons, and the first polymer film is easy to obtain electrons.

Scheme II: unlike the single-layer structure in the first embodiment, the electrode in the second embodiment is a composite structure, and specifically, the electrode 242 further includes: the metal electrode layer and the second polymer film disposed outside the metal electrode layer, the free end of each vibrating diaphragm can rub against the second polymer film in the electrode 242 under the driving of the airflow. Specifically, in the present embodiment, a second polymer film is further disposed on the metal electrode layer of the electrode 242, for example, a second polymer film may be further coated on the metal electrode layer of the electrode 242, so that the free end of each vibrating diaphragm on the first polymer film 243 is rubbed with the second polymer film in the electrode 242 under the driving of the airflow to generate induced charges, that is, the induced charges are generated by the friction between the polymer (the first polymer film) and the polymer (the second polymer film), and an electrical signal is output through the metal electrode layer inside the second polymer film, thereby achieving a friction effect similar to that of the above embodiment.

Specifically, in the first or second aspect, the material of the metal electrode layer may be metal or alloy, where the metal may be gold, silver, platinum, palladium, aluminum, nickel, copper, titanium, chromium, tin, iron, manganese, molybdenum, tungsten, or vanadium; the alloy may be an aluminum alloy, a titanium alloy, a magnesium alloy, a beryllium alloy, a copper alloy, a zinc alloy, a manganese alloy, a nickel alloy, a lead alloy, a tin alloy, a cadmium alloy, a bismuth alloy, an indium alloy, a gallium alloy, a tungsten alloy, a molybdenum alloy, a niobium alloy, or a tantalum alloy. In addition, the material of the metal electrode layer may be further selected from non-metal conductive materials such as indium tin oxide, graphene, silver nanowire film, and the like. The material of the first polymer film and the second polymer film is selected from polyimide film, aniline formaldehyde resin film, polyformaldehyde film, ethyl cellulose film, polyamide film, melamine formaldehyde film, polyethylene glycol succinate film, cellulose acetate film, polyethylene adipate film, polydiallyl phthalate film, fiber (regenerated) sponge film, polyurethane elastomer film, styrene-propylene copolymer film, styrene-butadiene copolymer film, rayon film, polymethyl film, methacrylate film, polyvinyl alcohol film, polyester film, polyisobutylene film, polyurethane flexible sponge film, polyethylene terephthalate film, polyvinyl butyral film, formaldehyde phenol film, chloroprene rubber film, butadiene-propylene copolymer film, polyethylene terephthalate film, polyvinyl butyral film, formaldehyde-phenol film, chloroprene rubber film, butadiene-propylene copolymer film, polyethylene terephthalate film, polyethylene, One of a natural rubber film, a polyacrylonitrile film, an acrylonitrile-vinyl chloride film and a polyethylene propylene glycol carbonate film. In principle, the first polymer film and the second polymer film may be made of the same material or different materials. However, if the two polymer films are made of the same material, the amount of triboelectric charge is small. Therefore, the first polymer film and the second polymer film are preferably made of different materials.

Accordingly, with respect to the above-mentioned arrangement of the support structure 244, the corresponding solution is as follows: if the electrode 242 adopts the structure in the first scheme, that is: the outer layer of the electrode 242 only includes a single metal electrode layer, and the above-mentioned support structure 244 is correspondingly disposed outside the metal electrode layer of the electrode 242; if the electrode 242 adopts the structure in scheme two, that is: the metal electrode layer of the outer layer of the electrode 242 is further provided with a second polymer film layer, and the above-mentioned support structure 244 is correspondingly provided on the outer side of the second polymer film layer in the electrode 242.

Further, in the above two embodiments, in order to increase the friction effect, the surface of the electrode 242 may be further provided so that the surface of the electrode 242 is formed in a planar shape or in a rough dot shape. The planar electrode is an electrode with a smooth planar surface, and because the electrostatic adsorption force of induced charges generated by the friction of the planar electrode is small, that is, the adsorption force of the generated electrostatic adsorption diaphragm is small, under the action of the airflow, when the diaphragm on the first polymer film 243 is rubbed with the electrode 242 with a planar surface, the problem of unstable vibration of the diaphragm caused by the large electrostatic force generated by the friction can be overcome; the rough point-like electrode is an electrode with a certain roughness on the surface, and the surface with larger roughness can generate more induced charges during friction, so that when the vibrating diaphragm on the first polymer film 243 and the electrode 242 with the rough point-like surface are rubbed, the friction resistance can be increased on the surface of the rough point-like electrode, the induced charges generated by friction are increased, the output electric signal is increased, and the sensitivity of electric signal output is improved. The rough dot-shaped electrode may be formed by polishing the surface of the electrode 242 or by providing a concave-convex structure, wherein the concave-convex structure may be a concave-convex structure having a regular shape such as a semicircular shape, a stripe shape, a cubic shape, a quadrangular pyramid shape, or a cylindrical shape, or other irregular shapes.

In addition, each of the two schemes can be further divided into two implementation manners: in a first implementation, only the electrode 242 may serve as a signal output terminal; in a second implementation, the electrode 242 and another output electrode may jointly form a signal output terminal, for example, the housing 241 may be provided as a metal housing, so that the housing 241 serves as another signal output terminal of the airflow sensor. That is, when the case 241 is a metal case, the case 241 may be provided as another output electrode. Specifically, the casing 241 constitutes an output electrode in the airflow sensor, and when the distance between the casing 241 and the first polymer film 243 is set, the distance between the casing 241 and the first polymer film 243 is set within a preset distance range, for example, the distance between the casing 241 and the first polymer film 243 may be set between 0.01 mm and 2.0mm, so that when the diaphragm on the first polymer film 243 is driven by the airflow to vibrate up and down, the diaphragm not only rubs against the electrode surface of the electrode 242, but also rubs against the inner surface of the casing 241, so as to generate corresponding induced charges on the inner surface of the casing 241, and the casing 241 at this time may serve as another signal output terminal except the electrode 242. Here, the material of the case 241 may be metal, or may be a material having conductivity other than metal; alternatively, the housing 241 may be further configured as a two-layer structure, that is: a layer of structure inside the casing 241 may be made of metal, and then a layer of polymer film material may be provided outside the metal. Here, the present invention is not limited to the material and structure of the case 241 as long as the case 241 can be used as another signal output terminal.

In the first implementation manner of the first and second schemes, only one signal output terminal is provided, that is, the electrode 242 serves as the only signal output terminal; in the second implementation manner of the first and second embodiments, two signal output terminals, namely the electrode 242 and the housing 241, are provided. When only one signal output terminal is provided, i.e. the electrode 242 is selected as the only signal output terminal, the electrode 242 and the grounding point in the external circuit form a current loop together; when two signal output terminals are provided, that is, the electrode 242 and the case 241 are selected as the signal output terminals, a current loop is formed due to a potential difference between the two electrode layers of the electrode 242 and the case 241.

In addition, on the basis of any implementation manner of the second scheme, a person skilled in the art can further add an intermediate thin film layer or an intermediate electrode layer between the second polymer film and the first polymer film, so that the number of friction interfaces is further increased, and the friction effect is improved. In a word, the utility model discloses do not restrict friction interface's specific quantity and implementation, the form that technical personnel in the field can set up friction interface in a flexible way as long as can realize friction power generation's effect.

Finally, a conversion relation between the electric signal output by the airflow sensor and the flow speed of the airflow inside the sensor is introduced:

after acquiring the electric signal output by the signal output end, the flow speed and the flow rate of the airflow are acquired by processing corresponding values contained in the electric signal. The electrical signal includes electrical signal parameters related to a voltage value, a frequency value, and the like. The inventor has found that the larger the airflow velocity of the airflow, the higher the vibration frequency of the diaphragm, and the larger the output voltage value and frequency. Furthermore, the inventor further finds that, from the measured values, the air flow velocity is in a direct proportion relationship with the voltage value V and the frequency f, that is, the air flow velocity is in a linear relationship with the voltage value V and the air flow velocity is in a linear relationship with the frequency f, so that the air flow velocity and the air flow can be further calculated by obtaining the output voltage value, the output frequency value and the measurement time length, and the purpose of measuring the air flow velocity and the air flow can be achieved. The specific experimental data of the above measurement are shown in table 1, table 1 is a table of parameters of the output electrical signals of the samples measured at different flow rates of the gas flow, and the parameters of the specific samples in item 1 and item 2 are different, so that the measured values at the same flow rate of the gas flow are different. As can be seen from table 1, the relationship between the flow rate of the gas flow and the voltage value V, and the flow rate of the gas flow and the frequency f in table 1 are approximately linear. The data in table 1 do not show a strict linear relationship due to the influence of the multiple parameters on the measurement result and due to the existence of experimental errors, but it is obvious that the voltage value and the frequency value are correspondingly increased as the airflow speed is increased in item 1 or item 2. Wherein, one optional parameter information of the measurement sample is as follows: the sample shell is metal casing, and the diameter is 6.0mm, and the interval (being electrode tripod step height) of vibrating diaphragm and electrode is 1.0mm, and vibrating diaphragm thickness is 4 ~ 6um, and the vibrating diaphragm is the rectangle, and length is 3.50mm, and the width is 1.0 mm.

TABLE 1

Therefore, the utility model provides an airflow sensor utilizes the friction power generation principle to realize, not only has light portable advantage, makes low cost, preparation simple process moreover, has the characteristics that the implementation is strong, easy equipment. And simultaneously, the utility model provides an in the working process of airflow sensor, through further setting up the vibrating diaphragm on first polymer film, make full use of vibrating diaphragm free end produces vibration and then produces the friction effect under the air current effect to and the inertia effect that the vibrating diaphragm produced in the vibration process increases the friction effect among the friction electricity generation process, and obtain more accurate and effectual sensing signal through the friction electricity generation scheme that sets up multiple mode, signal sensitivity has been promoted, the accuracy of airflow sensor work has also been improved simultaneously.

It should be understood that when the airflow generated by the respiration of the user acts on the airflow sensor in the above examples one to four, the electrical signal output by the electrode in the examples one to four is the airflow pressure electrical signal mentioned in the present invention. Specifically, when the airflow generated by the inhalation of the user acts on the airflow sensor in the first to fourth examples, the electrical signals output by the electrodes in the first to fourth examples are the inhalation airflow pressure electrical signals mentioned in the present invention; when the airflow generated by the exhalation of the user acts on the airflow sensor in the first to fourth examples, the electrical signal output by the electrode in the first to fourth examples is the exhalation airflow pressure electrical signal mentioned in the present invention.

Fig. 3 is a functional structure block diagram of a second embodiment of the nebulizer with an inhalation monitoring function according to the present invention. As shown in fig. 3, the nebulizer with an inhaled medicine amount monitoring function according to the second embodiment differs from the nebulizer with an inhaled medicine amount monitoring function according to the first embodiment in that: the atomizer body 130 includes a wireless transceiver module 135 and an interactive function module 136, in addition to the atomization component 131, the signal preprocessing module 132, the central control module 133 and the power supply module 134. The wireless transceiver module 135 is electrically connected to the central control module 133, and is configured to send the user medication intake information analyzed and calculated by the central control module 133 to a preset receiving device in a wireless communication manner, so that a doctor and/or a guardian on the preset receiving device side can check the information, where the preset receiving device may be a terminal device and/or a large database service platform; the interactive function module 136 is electrically connected to the central control module 133, and is configured to send a user interactive instruction to the central control module 136, where the user interactive instruction includes at least one of the following: the system comprises an opening instruction, a closing instruction, a user information initialization instruction and a user medicine sucking information setting instruction.

Specifically, the on or off command is used to control the central control module 133 to be turned on or off, so as to control the monitoring process to be turned on or off; the user information initialization instruction is used for clearing the monitored user medicine suction information or establishing new user medicine suction information monitoring data; the user drug inhalation information setting instruction is used for controlling the monitoring type or monitoring mode of the user drug inhalation information, for example, the user can select and monitor one or more of the user drug inhalation information such as the user drug inhalation amount, the user drug inhalation time, the user drug inhalation times, the time interval between two adjacent times of drug inhalation and the like through the interactive function module 136, so that the flexibility and the selectivity of the monitoring information are increased. In addition, the interactive function module 136 may also preset identification information of the user, so as to facilitate continuous monitoring of the same user. Other descriptions can refer to the description in the first embodiment, and are not repeated herein.

The following describes in detail the specific working principles of the first and second embodiments of the atomizer with a function of monitoring the amount of inhaled medicine provided by the present invention. For convenience of explanation, the following description will be given by taking three user inhalation information, i.e., monitoring user inhalation time, user inhalation frequency, and user inhalation amount, as an example.

In the first case: an air flow sensor is arranged inside a nozzle body in the nozzle air flow monitoring component, and a signal preprocessing module electrically connected with the air flow sensor is arranged in the atomizer main body.

In the second embodiment, the user can control the power supply module to be communicated with the central control module through the interactive function module, so that the central control module starts to work; and the user can also set the user medicine suction information to be monitored through the interactive function module. If the interaction function module is not arranged in the atomizer main body (as shown in the first embodiment), the operation is started according to the preset medicine suction information of the user.

When a user inhales, an airflow sensor arranged in the nozzle body in the nozzle airflow monitoring part senses the pressure acted on the airflow generated by the inhalation of the user, converts the pressure acted on the airflow sensor into a corresponding inhalation airflow pressure electric signal and outputs the inhalation airflow pressure electric signal to a signal preprocessing module correspondingly and electrically connected with the airflow sensor, and the signal preprocessing module preprocesses the inhalation airflow pressure electric signal output by the airflow sensor. When the central control module receives the inspiratory airflow pressure electric signal preprocessed by the signal preprocessing module, a timer arranged in the central control module is started to time, and meanwhile, the central control module analyzes and calculates the peak value of the inspiratory airflow pressure electric signal, so that the flow speed and the flow of airflow generated by inspiration of a user are calculated according to the obtained peak value of the inspiratory airflow pressure electric signal, and the medicine amount Y1 inhaled by the user in unit time when the user inhales for the first time is further analyzed and calculated.

When a user exhales, an air flow sensor arranged inside a nozzle body in the nozzle air flow monitoring component senses the pressure acted on the nozzle body by the air flow generated by the exhalation of the user, converts the pressure acted on the air flow sensor into a corresponding exhalation air flow pressure electric signal and outputs the exhalation air flow pressure electric signal to a signal preprocessing module which is correspondingly and electrically connected with the air flow sensor, and the exhalation air flow pressure electric signal output by the air flow sensor is preprocessed by the signal preprocessing module. When the central control module receives the expiratory airflow pressure electric signal preprocessed by the signal preprocessing module, stopping timing by a timer arranged in the central control module to obtain first timing time X1 (namely the time for the user to inhale for the first time), and then resetting the timer arranged in the central control module; meanwhile, a counter arranged in the central control module is started to count, and the first medicine suction frequency C1 is obtained. In addition, if the user does not have an exhalation process, that is, the airflow generated by the inhalation or exhalation of the user does not act on an airflow sensor arranged inside the nozzle body in the nozzle airflow monitoring part, in order to recover to the initial state, the airflow sensor arranged inside the nozzle body in the nozzle airflow monitoring part also outputs an initial state electrical signal similar to the exhalation airflow pressure electrical signal output by the airflow sensor when the user exhales, that is, the direction of the exhalation airflow pressure electrical signal output by the airflow sensor when the user exhales is the same as that of the initial state electrical signal, therefore, the working principle of the airflow monitoring part is the same as that of the airflow generated by the exhalation of the user acting on the airflow sensor arranged inside the nozzle body in the nozzle airflow monitoring part, and details are not repeated herein.

The central control module judges whether the electric signal of the pressure of the suction airflow preprocessed by the signal preprocessing module is received again in a preset time interval. Wherein, a person skilled in the art can set the preset time interval according to actual needs, and the preset time interval is not limited herein. For example, the preset time interval may be 1 s. If the electric signal of the pressure of the inspiratory air flow preprocessed by the signal preprocessing module is judged to be received again in the preset time interval, the second inspiration of the user is indicated, at the moment, the central control module starts a timer arranged in the central control module to time, and simultaneously, the central control module analyzes and calculates the peak value of the electric signal of the pressure of the inspiratory air flow, so that the flow speed and the flow of the air flow generated by the current inspiration of the user are calculated according to the analysis of the obtained peak value of the electric signal of the pressure of the inspiratory air flow, and the medicine amount Y2 inhaled by the user in unit time when the user inhales for the second time is further calculated through analysis. When the central control module receives the expiratory airflow pressure electric signal preprocessed by the signal preprocessing module, the central control module stops a timer arranged in the central control module from timing to obtain second timing time X2 (namely the time for the user to inhale for the second time), and then the timer arranged in the central control module is reset; meanwhile, the central control module starts a counter arranged in the central control module to count up, and a second medicine suction frequency C2 is obtained.

The central control module can judge whether the electrical signal of the pressure of the suction airflow preprocessed by the signal preprocessing module can be received within a preset time interval. If yes, the central control module starts the timer arranged in the central control module again to time, and the process is repeated; if not, the central control module analyzes and calculates the total user medicine suction time X, the total user medicine suction times C is C2 (namely 2 times), and the total user medicine suction quantity S, so that the user medicine suction time information, the user medicine suction times information and the user medicine suction quantity information are obtained. Wherein, X is 1+ X2, and S is 1 × Y1+ X2 × Y2.

It should be noted that, when a user inhales, the peak value of the inspiratory air pressure electric signal output by an air flow sensor arranged in the nozzle air flow monitoring part inside the nozzle body corresponds to the flow velocity and flow rate of the air flow generated by the inhalation of the user and the medicine amount Y inhaled by the user in unit time. When a user inhales, the corresponding relation between the peak value of an inspiratory air flow pressure electric signal output by an air flow sensor arranged in the nozzle body of the nozzle air flow monitoring component and the flow rate and the flow quantity of the air flow generated by the inspiration of the user and the corresponding relation between the flow rate and the flow quantity of the air flow generated by the inspiration of the user and the amount Y of the medicine inhaled by the user in unit time can be preset by a manufacturer for producing the atomizer with the function of monitoring the medicine inhalation quantity.

In the second case: the inside of the nozzle body in the nozzle airflow monitoring part is provided with a plurality of airflow sensors, a plurality of signal preprocessing modules are arranged in the atomizer main body, the number of the airflow sensors arranged in the plurality of signal preprocessing modules and the inside of the nozzle body in the nozzle airflow monitoring part is the same, the plurality of signal preprocessing modules are electrically connected with the plurality of airflow sensors in a one-to-one correspondence manner, and meanwhile, the plurality of signal preprocessing modules are also electrically connected with the central control module in the atomizer main body respectively.

When a user inhales, a plurality of airflow sensors arranged inside a nozzle body in the nozzle airflow monitoring part sense the pressure acted on the nozzle body by airflow generated by the inhalation of the user, the pressure acted on the nozzle body is converted into corresponding inhalation airflow pressure electric signals to be output to the plurality of signal preprocessing modules which are electrically connected with the plurality of airflow sensors in a one-to-one correspondence mode, and the inhalation airflow pressure electric signals output by the plurality of airflow sensors are preprocessed by the plurality of signal preprocessing modules. When the central control module receives the plurality of inspiratory airflow pressure electric signals, the central control module starts a timer arranged in the central control module to time according to a first inspiratory airflow pressure electric signal received in the plurality of inspiratory airflow pressure electric signals, simultaneously, the central control module analyzes and calculates peak values of the plurality of inspiratory airflow pressure electric signals respectively, the peak values of the plurality of inspiratory airflow pressure electric signals are added to obtain an average value, and a final peak value of the inspiratory airflow pressure electric signal is obtained, so that the flow speed and the flow of airflow generated by inspiration of a user are calculated according to the obtained final peak value of the inspiratory airflow pressure electric signal, and the amount of medicine Y1 inhaled by the user in unit time during the first inspiration of the user is further analyzed and calculated. For convenience of description hereinafter, the airflow sensor that outputs the first electrical signal of the inspiratory airflow pressure will be referred to as an airflow sensor a.

When a user exhales, a plurality of air flow sensors arranged inside a nozzle body in the nozzle air flow monitoring component sense the pressure acted on the nozzle body by the air flow generated by the exhalation of the user, the pressure acted on the nozzle body is converted into corresponding exhalation air flow pressure electric signals to be output to the plurality of signal preprocessing modules which are electrically connected with the plurality of air flow sensors in a one-to-one correspondence mode, and the exhalation air flow pressure electric signals output by the plurality of air flow sensors are preprocessed by the plurality of signal preprocessing modules. At this time, the central control module still stops the timer arranged in the central control module from timing according to the expiratory airflow pressure electric signal output by the airflow sensor a to obtain first timing time X1 (namely the time for the user to inhale for the first time), and then clears the timer arranged in the central control module; meanwhile, a counter arranged in the central control module is started to count, and the first medicine suction frequency C1 is obtained. In addition, if the user does not have an exhalation process, that is, no airflow generated by the user inhaling or exhaling acts on the airflow sensor a, the airflow sensor a may also output an initial state electrical signal similar to the expiratory airflow pressure electrical signal output by the airflow sensor a when the user exhales, that is, the expiratory airflow pressure electrical signal output by the airflow sensor a when the user exhales has the same direction as the initial state electrical signal, and therefore, the working principle of the airflow sensor a is the same as the working principle of the airflow generated by the user exhaling acting on the airflow sensor a, and the detailed description is omitted here.

The central control module judges whether the preprocessed inhalation airflow pressure electric signals output by the airflow sensor A when the user inhales are received again in the preset time interval. Wherein, a person skilled in the art can set the preset time interval according to actual needs, and the preset time interval is not limited herein. For example, the preset time interval may be 1 s. If the electric signal of the inspiratory air flow pressure output by the air flow sensor A when the user inhales is judged to be received again in the preset time interval, which indicates that the user inhales for the second time, at the moment, the central control module starts a timer arranged in the central control module to time, meanwhile, the central control module also receives the preprocessed electric signals of the air flow pressure output by other air flow sensors correspondingly, at the moment, the central control module analyzes and calculates the peak values of a plurality of electric signals of the air flow pressure output by all the air flow sensors correspondingly respectively, adds the received peak values of all the electric signals of the air flow pressure to calculate the average value, obtains the final peak value of the electric signals of the air flow pressure, therefore, the flow speed and the flow of the airflow generated by the inhalation of the user are calculated according to the peak value analysis of the final inhalation airflow pressure electric signal, and the inhalation dosage Y2 of the user in unit time when the user inhales for the second time is further calculated through analysis. When the central control module receives the preprocessed expiratory airflow pressure electric signal output by the airflow sensor A during expiration of the user, the central control module stops timing of a timer arranged in the central control module to obtain second timing time X2 (namely the time for the user to inhale for the second time), and then the timer arranged in the central control module is cleared; meanwhile, the central control module starts a counter arranged in the central control module to count up, and a second medicine suction frequency C2 is obtained.

The central control module judges whether the preprocessed inhalation airflow pressure electric signals output by the airflow sensor A when the user inhales can be received within a preset time interval. If yes, the central control module starts the timer arranged in the central control module again to time, and the process is repeated; if not, the central control module analyzes and calculates the total user medicine suction time X, the total user medicine suction times C is C2 (namely 2 times), and the total user medicine suction quantity S, so that the user medicine suction time information, the user medicine suction times information and the user medicine suction quantity information are obtained. Wherein, X is 1+ X2, and S is 1 × Y1+ X2 × Y2.

It should be noted that the average value obtained by adding the peak values of the inspiratory air pressure electric signals output by the plurality of air flow sensors provided inside the nozzle body in the nozzle air flow monitoring part when the user inhales corresponds to the flow velocity and flow rate of the air flow generated by the inhalation of the user and the amount of medicine Y inhaled by the user per unit time. The correspondence between the average value obtained by adding the peak values of the inspiratory air flow pressure electric signals output by the plurality of air flow sensors arranged in the nozzle body of the nozzle air flow monitoring part when the user inhales and the flow rate and the flow quantity of the air flow generated by the inhalation of the user and the correspondence between the flow rate and the flow quantity of the air flow generated by the inhalation of the user and the amount Y of the medicine inhaled by the user in unit time can be preset by a manufacturer for producing the atomizer with the function of monitoring the medicine inhalation amount.

Further, it should be noted that, in the above two cases, when the airflow generated by the inhalation of the user acts on a friction-electric airflow sensor, the inhalation airflow pressure electrical signal output by the friction-electric airflow sensor will gradually increase with the gradual increase of the airflow pressure exerted thereon, but when the inhalation airflow pressure exerted on the friction-electric airflow sensor reaches a steady state (e.g. the inhalation airflow pressure exerted on the friction-electric airflow sensor is constant), the inhalation airflow pressure electrical signal output by the friction-electric airflow sensor will gradually decrease until it returns to the original state (e.g. the inhalation airflow pressure electrical signal returns to 0), and will continuously remain in the original state; when the expiratory airflow pressure applied to the friction-generation-type airflow sensor by the airflow generated by the exhalation of the user or the airflow pressure applied to the friction-generation-type airflow sensor is zero, the above-mentioned original state is changed, and at this time, the triboelectric airflow sensor outputs an expiratory airflow pressure electrical signal (e.g., a negative-going pulse electrical signal) or an initial-state electrical signal (e.g., a negative-going pulse electrical signal) that is opposite to an inspiratory airflow pressure electrical signal (e.g., a positive-going pulse electrical signal), and thus, in order to accurately monitor the time at which a user inhales, therefore, the inhaled medicine quantity of the user is accurately monitored, and the expiratory airflow pressure electric signal generated by the expiration of the user and acted on the friction power generation type airflow sensor or the initial state electric signal output by the friction power generation type airflow sensor to restore to the initial state is monitored, so that the termination time of finishing one inhalation of the user is determined.

Fig. 4 is a functional structure block diagram of a third embodiment of the atomizer with a function of monitoring the amount of inhaled medicine provided by the present invention. As shown in fig. 4, the nebulizer with an inhaled medicine amount monitoring function of the third embodiment differs from the nebulizer with an inhaled medicine amount monitoring function of the second embodiment in that: the nebulizer body 130 also includes a display module 137 and an alarm module 138. The display module 137 is electrically connected to the central control module 133, and is configured to display the medicine inhalation information of the user, which is obtained by the central control module 133; the central control module 133 is further configured to: sending an alarm control signal according to the obtained medicine suction information of the user; the alarm module 138 is electrically connected to the central control module 133, and is configured to perform an alarm prompt according to an alarm control signal sent by the central control module 133. For example, when the central control module 133 obtains that the amount of medicine inhaled by the user exceeds a preset medicine amount threshold and/or the number of times of medicine inhalation by the user exceeds a preset medicine inhalation number threshold according to the obtained medicine inhalation information of the user, an alarm control signal is sent, and the alarm module 138 gives an alarm according to the alarm control signal to prompt the user to stop medicine inhalation. The other descriptions can refer to the descriptions in the second embodiment, and are not repeated herein.

It should be understood that the wireless transceiver module 135, the interactive function module 136, the display module 137 and the alarm module 138 in the second and third embodiments may be selected according to the design of those skilled in the art, and are not limited herein. For example: if the communication with the preset receiving device is not required or the communication with the preset receiving device is performed in a wired connection manner, the wireless transceiving module 135 may be omitted; if manual control of the nebulizer is not required, the interaction function module 136 may be omitted; if the user inhalation information does not need to be displayed, the display module 137 may be omitted; the alarm module 138 may be omitted if the alarm function is not required.

Fig. 5 is a functional block diagram of a medicine inhalation monitoring system using the atomizer with medicine inhalation monitoring function shown in fig. 4. As shown in fig. 5, the inhalation amount monitoring system includes: a nebulizer 510 having a function of monitoring the amount of inhaled medicine, and a terminal device 520. Wherein, the nebulizer 510 with a drug inhalation amount monitoring function is the nebulizer with a drug inhalation amount monitoring function shown in fig. 4; the terminal device 520 is connected with the nebulizer 510 with a drug inhalation amount monitoring function in a wireless communication manner, and is configured to receive and display the user drug inhalation information calculated and analyzed by the nebulizer 510 with a drug inhalation amount monitoring function, and/or send a control instruction for controlling the nebulizer 510 with a drug inhalation amount monitoring function.

Specifically, as shown in fig. 5, the terminal device 520 is connected to the wireless transceiver module 135 in the nebulizer 510 with a function of monitoring the amount of inhaled medicine in a wireless communication manner, and is configured to receive the user inhaled medicine information analyzed and calculated by the central control module 133 and sent by the wireless transceiver module 135, and/or send a control instruction for controlling the central control module 133 to the wireless transceiver module 135. Specifically, the control instructions may include: an opening instruction for opening the operation of the central control module 133 and a termination instruction for terminating the operation of the central control module 133. The terminal device 520 may be a mobile phone, a computer, or other devices, and may complete the work of counting the user inhalation information, such as the total user inhalation time, the total user inhalation times, and the total user inhalation amount, by designing a specific application program therein, and a person skilled in the art may select the information as needed, which is not limited herein.

Fig. 6 is another functional structure block diagram of a medicine inhalation monitoring system using the atomizer with medicine inhalation monitoring function shown in fig. 4. As shown in fig. 6, the inhalation amount monitoring system shown in fig. 6 differs from the inhalation amount monitoring system shown in fig. 5 in that: the drug intake monitoring system shown in fig. 6 also includes a large database service platform 630. Wherein the terminal device 520 is further configured to: sending the received user drug absorption information to the big database service platform 630; the big database service platform 630 is connected with the terminal device 520 in a wireless communication manner, and is configured to receive and store the user drug absorption information sent by the terminal device 520, analyze and compare the received user drug absorption information with the user drug absorption information in the big database service platform 630 to obtain user analysis information, and send the user analysis information to the terminal device 520, so that a doctor and/or a guardian at the terminal device 520 side can check or refer to the user analysis information, and the doctor and/or the guardian can further understand the illness state of the user.

In addition, the medicine suction amount monitoring system provided by the utility model does not include the terminal device 520, but only comprises the big database service platform 630, then, the central control module 133 in the nebulizer 510 with the drug inhalation amount monitoring function completes the work of analyzing and calculating the drug inhalation information of the user, such as the total drug inhalation time of the user, the total drug inhalation times of the user, the total drug inhalation amount of the user, and the like, to obtain the drug inhalation information of the user, then the user drug absorption information is sent to the big database service platform 630 through the wireless transceiver module 135 for analysis and comparison to obtain user analysis information, finally the user analysis information is sent to the central control module 133 through the wireless transceiver module 135, thereby enabling the central control module 133 to control the display module 137 to display the user analysis information for the doctor and/or the guardian to view or refer, so that the doctor and/or the guardian can understand the condition of the user more deeply.

It should be understood that the inhalation amount monitoring system shown in fig. 5 and 6 can be used not only in the nebulizer with an inhalation amount monitoring function according to the third embodiment, but also in the nebulizer with an inhalation amount monitoring function according to the first embodiment or the second embodiment, and those skilled in the art can select the monitoring system according to needs, and the monitoring system is not limited herein.

In addition, in all the above inhalation amount monitoring systems, the connection mode of the nebulizer 510 with inhalation amount monitoring function to the terminal device 520 or to the large database service platform 630 may be not only connected by wireless communication, but also directly connected by wired communication, and when connected by wired communication, the corresponding wireless communication device may be omitted, for example: a wireless transceiver module 135 in a nebulizer 510 with a drug inhalation amount monitoring function.

The utility model discloses in various modules, circuit that mention are the circuit that is realized by hardware, for example, central control module can include microcontroller or little control chip, and rectifier module can include rectifier circuit, and filter module can include comparison circuit, and amplifier module can include amplifier circuit etc. and analog-to-digital conversion module can include analog-to-digital converter etc.. Although some modules and circuits are integrated with software, the invention protects hardware circuits which integrate corresponding functions of the software, not only the software itself.

It will be appreciated by those skilled in the art that the arrangement of devices shown in the figures or embodiments is merely schematic and representative of a logical arrangement. Where modules shown as separate components may or may not be physically separate, components shown as modules may or may not be physical modules.

Finally, it is noted that: the above list is only the concrete implementation example of the present invention, and of course those skilled in the art can make modifications and variations to the present invention, and if these modifications and variations fall within the scope of the claims of the present invention and their equivalent technology, they should be considered as the protection scope of the present invention.

Claims

1. A nebulizer having a drug-inhalation amount monitoring function, comprising: the atomizer comprises a liquid storage part, a nozzle airflow monitoring part and an atomizer main body; wherein,

2. The nebulizer with a drug inhalation amount monitoring function according to claim 1, wherein said liquid storage part comprises: a cover and a receiving cavity;

the cover body is provided with a buckling mechanism which is used for enabling the cover body and the accommodating cavity to be buckled in a sealing mode;

the containing cavity is provided with an atomization port and a liquid outlet, the atomization port is connected with the atomizer main body, and the liquid outlet is connected with the nozzle airflow monitoring part.

3. The nebulizer with a medicine-inhalation-amount monitoring function according to claim 1, wherein the nozzle-airflow monitoring section comprises: a nozzle body and an airflow sensor;

the nozzle body is connected with the liquid storage part;

the air flow sensor is arranged in the nozzle body and used for converting the pressure of air flow generated by inhalation or exhalation of a user and acting on the air flow sensor into an air flow pressure electric signal and outputting the air flow pressure electric signal.

4. The nebulizer with a medicine-inhalation-amount monitoring function according to claim 3, wherein the nebulizer body comprises: the device comprises an atomization component, a signal preprocessing module, a central control module and a power supply module;

5. The nebulizer with a medicine-inhalation-amount monitoring function according to claim 4, wherein the nebulizer body further comprises: a wireless transceiver module and/or an interactive function module;

the wireless transceiving module is electrically connected with the central control module and is used for sending the user medicine suction information obtained by analyzing and calculating by the central control module to preset receiving equipment in a wireless communication mode;

wherein the user interaction instructions comprise at least one of: the system comprises an opening instruction, a closing instruction, a user information initialization instruction and a user medicine sucking information setting instruction.

6. The nebulizer with a function of monitoring an amount of inhaled medicine according to claim 4 or 5, wherein the nebulizer body further comprises: a display module and/or an alarm module;

the central control module is further configured to: sending an alarm control signal according to the user medicine suction information obtained by analyzing and calculating;

and the alarm module is electrically connected with the central control module and used for giving an alarm according to the alarm control signal sent by the central control module.

7. The nebulizer with inhalation amount monitoring function of claim 4, wherein said air flow sensor is further configured to: converting the pressure of the airflow generated by the inhalation of the user on the airflow sensor into an inhalation airflow pressure electric signal for output; converting the pressure of the airflow generated by the exhalation of the user on the airflow sensor into an exhalation airflow pressure electric signal for output;

the signal pre-processing module is further configured to: preprocessing an inspiratory airflow pressure electric signal and an expiratory airflow pressure electric signal output by the airflow sensor;

a timer and a counter are arranged in the central control module;

the central control module is further configured to: starting the timer to time when receiving the electric signal of the pressure of the air flow after the pretreatment of the signal pretreatment module; and when the expiratory airflow pressure electric signal preprocessed by the signal preprocessing module is received, stopping the timer to obtain timing time, and starting the counter to count to obtain the medicine suction times of the user.

8. An inhalation quantity monitoring system, comprising: the nebulizer having a function of monitoring an amount of inhaled medicine and the terminal device according to any one of claims 1 to 7; wherein,

the terminal equipment is connected with the atomizer with the medicine suction amount monitoring function in a wired communication or wireless communication mode, and is used for storing and displaying the user medicine suction information obtained by analyzing and calculating the atomizer with the medicine suction amount monitoring function and sending a control instruction for controlling the atomizer with the medicine suction amount monitoring function.

9. The drug intake monitoring system of claim 8, further comprising a big database service platform; wherein,

the terminal device is further configured to: sending the received user drug absorption information to the big database service platform;

10. An inhalation quantity monitoring system, comprising: a nebulizer with inhalation monitoring and big database service platform according to any one of claims 1 to 7; wherein,

the big database service platform is connected with the atomizer with the medicine suction amount monitoring function in a wired communication or wireless communication mode and used for receiving and storing the user medicine suction information obtained by analyzing and calculating the atomizer with the medicine suction amount monitoring function, analyzing and comparing the received user medicine suction information with the user medicine suction information in the big database service platform to obtain user analysis information, and sending the user analysis information to the atomizer.