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WO2018176632A1 - Atomiseur et système de surveillance de dosage de médicament inhalé - Google Patents

Atomiseur et système de surveillance de dosage de médicament inhalé Download PDF

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Publication number
WO2018176632A1
WO2018176632A1 PCT/CN2017/088091 CN2017088091W WO2018176632A1 WO 2018176632 A1 WO2018176632 A1 WO 2018176632A1 CN 2017088091 W CN2017088091 W CN 2017088091W WO 2018176632 A1 WO2018176632 A1 WO 2018176632A1
Authority
WO
WIPO (PCT)
Prior art keywords
airflow
atomizer
user
electrode
polymer film
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/CN2017/088091
Other languages
English (en)
Chinese (zh)
Inventor
徐传毅
钟强
赵豪
刁海丰
崔婧
程驰
孙晓雅
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Nazhiyuan Technology Tangshan Co Ltd
Original Assignee
Nazhiyuan Technology Tangshan Co Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from CN201710208190.XA external-priority patent/CN107402048B/zh
Priority claimed from CN201710211423.1A external-priority patent/CN108525082B/zh
Application filed by Nazhiyuan Technology Tangshan Co Ltd filed Critical Nazhiyuan Technology Tangshan Co Ltd
Publication of WO2018176632A1 publication Critical patent/WO2018176632A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • A61M11/00—Sprayers or atomisers specially adapted for therapeutic purposes
    • A61M11/06—Sprayers or atomisers specially adapted for therapeutic purposes of the injector type
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Definitions

  • the invention relates to the technical field of sensors, in particular to an atomizer and a drug absorption monitoring system with a drug absorption monitoring function.
  • atomizers to atomize water-soluble drugs into tiny mist particles to inhale patients to alleviate the pain.
  • the types and functions of the atomizers in the prior art are various.
  • the commonly used atomizers include ultrasonic atomizers, compressed air atomizers and mesh atomizers.
  • ultrasonic atomizers include ultrasonic atomizers, compressed air atomizers and mesh atomizers.
  • most of the above atomizers only It can control the amount of atomized liquid, but it can't monitor the user's inhaled dose sensitively and accurately. Monitoring the user's inhaled dose is especially important for the treatment of the disease.
  • the prior art lacks an atomizer capable of sensitively and accurately monitoring the user's drug absorption information and a corresponding drug absorption monitoring system.
  • the object of the present invention is to provide a nebulizer and a drug absorption monitoring system with a drug absorption monitoring function, which is used to solve the prior art that the atomizer cannot be sensitive and accurate. The problem of user drug absorption information is monitored.
  • the present invention provides an atomizer having a drug absorption monitoring function, the atomizer comprising: a liquid storage component, a nozzle airflow monitoring component, and an atomizer body; wherein
  • liquid storage component connected to the atomizer body for storing the liquid medicine to be atomized and sprayed
  • the nozzle airflow monitoring component is connected to the liquid storage component for outputting the airflow pressure electrical signal according to the airflow generated by the user inhaling or exhaling, and injecting the liquid medicine atomized by the atomizer body into the mouth and nose of the user;
  • the atomizer body is electrically connected to the nozzle airflow monitoring component for atomizing and spraying the liquid medicine stored in the liquid storage component, and analyzing and calculating the user inhaling dose according to the airflow pressure electrical signal output by the nozzle airflow monitoring component. Get user drug information.
  • the invention also provides a drug absorption monitoring system, comprising: the above-mentioned atomizer with a drug absorption monitoring function and a terminal device; wherein
  • the terminal device is connected to the atomizer with the drug absorption monitoring function by wired communication or wireless communication, and is used for storing and displaying the user drug absorption information calculated by the atomizer with the drug absorption monitoring function, and transmitting A control command for controlling an atomizer having a drug absorption monitoring function.
  • the invention also provides a drug absorption monitoring system, comprising: the above-mentioned atomizer with drug absorption monitoring function and a large database service platform; wherein
  • the large database service platform is connected to the atomizer with the drug absorption monitoring function by wired communication or wireless communication, and is used for receiving and storing the user drug absorption information calculated by the atomizer with the drug absorption monitoring function.
  • the received user drug absorption information is compared with the user drug absorption information in the large database service platform to obtain user analysis information, and the user analysis information is sent to the atomizer.
  • the atomizer and the drug absorption monitoring system with the drug absorption monitoring function provided by the nozzle airflow monitoring component monitor the airflow generated by the user's inhalation or exhalation, and can infiltrate the drug and absorb the drug sensitively and accurately.
  • the user's drug absorption information such as time and drug absorption times are monitored, and the user's drug absorption information is monitored.
  • the atomizer and the drug absorption monitoring system with the drug absorption monitoring function provided by the invention not only have high sensitivity and high accuracy, but also have the advantages of simple structure, simple manufacturing process, low cost and large-scale industrial production.
  • Figure 1a is a functional junction of the first embodiment of the atomizer with the drug absorption monitoring function provided by the present invention Block diagram
  • FIG. 1b is a schematic structural view of a first embodiment of an atomizer with a drug absorption monitoring function according to the present invention
  • 1c is a schematic structural view of a liquid storage component in the first embodiment of the atomizer with a drug absorption monitoring function according to the present invention
  • 1d is a functional block diagram of a signal pre-processing module in the first embodiment of the atomizer with the drug absorption monitoring function provided by the present invention
  • FIG. 2a is a schematic perspective structural view of an airflow sensor example 1 in the first embodiment of the atomizer with the drug absorption monitoring function provided by the present invention
  • 2b is a cross-sectional structural view showing an example 1 of the air flow sensor in the first embodiment of the atomizer with the drug absorption monitoring function provided by the present invention
  • 2c is a schematic structural view of an example 2 of the airflow sensor in the first embodiment of the atomizer with the drug absorption monitoring function provided by the present invention
  • 2d is a schematic structural view of an example 3 of the airflow sensor in the first embodiment of the atomizer with the drug absorption monitoring function provided by the present invention
  • 2 e is an exploded structural view showing an example 4 of the air flow sensor in the first embodiment of the atomizer with the drug absorption monitoring function provided by the present invention
  • 2f is a schematic view showing the assembled structure of the airflow sensor example 4 in the first embodiment of the atomizer with the drug absorption monitoring function provided by the present invention
  • 2g is a schematic structural view of a diaphragm of a first polymer film according to an example 4 of the gas flow sensor in the first embodiment of the atomizer with the drug absorption monitoring function provided by the present invention
  • 2h is a schematic view showing the friction between the first polymer film and the electrode after the assembly of the first polymer film of the fourth embodiment of the gas flow sensor with the drug absorption monitoring function provided in the first embodiment of the present invention
  • FIG. 3 is a functional block diagram of a second embodiment of an atomizer having a drug absorption monitoring function according to the present invention.
  • FIG. 4 is a functional block diagram of a third embodiment of an atomizer having a drug absorption monitoring function according to the present invention.
  • FIG. 5 is a functional block diagram of a drug absorption monitoring system using the atomizer with the drug absorption monitoring function provided by the present invention shown in FIG. 4;
  • Fig. 6 is a block diagram showing another functional configuration of a drug absorption amount monitoring system using the atomizer having the drug absorption amount monitoring function provided by the present invention shown in Fig. 4.
  • the invention provides an atomizer having a drug absorption monitoring function, the atomizer comprising: a liquid storage component, a nozzle airflow monitoring component and an atomizer body; wherein the liquid storage component is connected to the atomizer body, The liquid medicine for storing the atomized spray; the nozzle airflow monitoring component is connected to the liquid storage component for outputting the airflow pressure electric signal according to the airflow generated by the user inhaling or exhaling, and is atomized after passing through the atomizer body.
  • the liquid medicine is sprayed into the nose and mouth of the user; the atomizer body is electrically connected to the nozzle airflow monitoring component for atomizing the liquid medicine stored in the liquid storage component, and detecting the airflow output by the component according to the nozzle airflow.
  • the pressure electric signal analyzes and calculates the inhaled dose of the user, and obtains the user's drug taking information.
  • FIG. 1a is a functional block diagram of a first embodiment of an atomizer with a drug absorption monitoring function according to the present invention
  • FIG. 1b is a schematic structural view of a first embodiment of an atomizer with a drug absorption monitoring function according to the present invention.
  • the atomizer includes a liquid storage component 110, a nozzle airflow monitoring component 120, and an atomizer body 130.
  • the liquid storage component 110 is disposed on the atomizer body 130, and is connected to the atomizer body 130.
  • the liquid storage component 110 is sealingly connected with the atomizer body 130 for storing the liquid medicine to be atomized and sprayed;
  • the nozzle airflow monitoring component 120 is disposed on the liquid storage component 110, and is connected to the liquid storage component 110 for outputting the airflow pressure electrical signal according to the airflow generated by the user's inhalation or exhalation, and will be atomized after passing through the atomizer body 130.
  • the liquid medicine is sprayed into the nose and mouth of the user; the atomizer body 130 is electrically connected to the nozzle airflow monitoring component 120 for atomizing the liquid medicine stored in the liquid storage component 110, and is sprayed according to the nozzle airflow monitoring component 120.
  • the output airflow pressure electric signal analyzes and calculates the user's inhaled dose, and obtains the user's drug absorption information.
  • the liquid storage component 110 includes a cover body and a receiving cavity.
  • the cover body and the receiving cavity are connected by a flip cover, and the cover body can be opened or closed, and the cover body is provided with a snap mechanism for sealingly engaging the cover body and the receiving cavity.
  • the cavity is used for storing the liquid medicine to be atomized and sprayed, and the receiving cavity is provided with an atomizing port and a liquid outlet, and the atomizing port is connected with the atomizer body 130, and the liquid outlet is connected to the nozzle airflow monitoring component 120.
  • the atomizer body 130 atomizes the liquid medicine stored in the accommodating cavity through the atomizing port on the accommodating cavity, and ejects into the inside of the nozzle airflow monitoring part 120 through the liquid outlet on the accommodating cavity, and then ejects to the user. In the mouth and nose.
  • the structure of the liquid storage component can be as shown in FIG. 1c.
  • the liquid storage component 110 includes a cover body 111 and a receiving cavity 112.
  • the atomizing port 113 is respectively connected to the middle portion of the bottom surface of the receiving cavity 112, and the atomizing port 113 is connected to the atomizer body 130 and the air flow channel 114 respectively; the upper portion of the side wall of the receiving cavity 112 is provided with the liquid outlet 115.
  • the liquid outlet 115 is connected to the nozzle airflow monitoring unit 120.
  • a liquid suction pipe 116 is disposed at a position adjacent to the air flow passage 114 in the accommodation cavity 112, and a barrier 117 is further disposed at an air outlet adjacent to the air flow passage 114.
  • the liquid suction pipe 116 is configured to suck the liquid medicine stored in the accommodating cavity 112, and the compressed air generated by the atomizer main body 130 flows in from the atomizing port 113, and flows into the accommodating cavity 112 through the air flow passage 114, and the compressed air passes through
  • the generated negative pressure drives the liquid medicine in the liquid suction pipe 116 to be sprayed onto the obstacle 117, and splashes around the high-speed impact to make the liquid droplets become misty particles.
  • the liquid port 115 is ejected.
  • the nozzle airflow monitoring component 120 includes a nozzle body (not shown) and an airflow sensor (not shown).
  • the nozzle body is disposed on the liquid storage component 110, and is connected to the liquid storage component 110.
  • the nozzle body can adopt the atomizer nozzle of the prior art, for example, the nozzle of the cylindrical cylindrical structure as shown in FIG. 1b.
  • the air flow sensor is disposed inside the nozzle body, and is used for converting the pressure of the airflow generated by the user's inhalation or exhalation on the airflow sensor into the airflow pressure electric signal output. .
  • the air flow sensor may be a friction power generation air flow sensor and/or a piezoelectric power generation air flow sensor, that is, the air flow sensor may be an air flow sensor fabricated by using a friction generator and/or a piezoelectric generator. Personnel can choose according to actual needs, which is not limited here.
  • an air flow sensor may be disposed inside the nozzle body, or a plurality of air flow sensors may be disposed.
  • the advantage of providing an air flow sensor inside the nozzle body is that the structure is simple and easy to implement, and the atomizer with the drug absorption monitoring function is more simple in structure;
  • the advantage of the internal airflow sensor is that the pressure of the airflow generated by the user's inhalation or exhalation can be induced in different directions, so that the atomizer with the drug absorption monitoring function is more sensitive and the monitoring result is obtained. more precise.
  • the air flow sensor when an air flow sensor is disposed inside the nozzle body, the air flow sensor is electrically connected to the atomizer body 130, and the airflow pressure electrical signal output by the airflow sensor is pre-processed by the atomizer body 130 to be calculated and calculated by the user.
  • the user draws information such as a dose; when a plurality of airflow sensors are disposed inside the nozzle body, the plurality of airflow sensors may be electrically connected to the atomizer body 130, respectively, and the plurality of airflow sensors correspond to the plurality of airflow pressures outputted
  • the electrical signals are respectively subjected to pre-treatment analysis by the atomizer main body 130 to calculate user inhalation information such as the user's inhaled dose.
  • connection between the plurality of airflow sensors and between the plurality of airflow sensors and the atomizer body 130 can be performed by a person skilled in the art according to actual conditions.
  • the connection relationship is set, and the present invention does not limit this.
  • a plurality of air flow sensors may be disposed inside the nozzle body in a longitudinal direction along the longitudinal direction of the nozzle body; or, a plurality of air flow sensors may be disposed The interior of the nozzle body is disposed along the lateral direction of the nozzle body, in a tangent arrangement, or other type of arrangement. It should be noted that when a plurality of air flow sensors are disposed inside the nozzle body, those skilled in the art can set the arrangement of the plurality of air flow sensors disposed inside the nozzle body according to actual conditions, and the present invention No restrictions.
  • the atomizer body 130 further includes: an atomizing component 131, a signal preprocessing module 132, a central control module 133, and a power supply module 134.
  • the atomizing component 131 is connected to the liquid storage component 110 for atomizing the liquid medicine stored in the liquid storage component 110
  • the signal pretreatment module 132 is electrically connected to the airflow sensor in the nozzle airflow monitoring component 120.
  • the airflow pressure electrical signal outputted by the airflow sensor in the nozzle airflow monitoring component 120 is preprocessed;
  • the central control module 133 is electrically connected to the atomizing component 131 and the signal preprocessing module 132, respectively, for controlling the atomizing component 131 to store the liquid.
  • the liquid medicine in the component 110 is atomized, and the air pressure electric signal pre-processed by the signal pre-processing module 132 is analyzed, and the user inhaled drug amount is analyzed and calculated to obtain user drug-absorbing information;
  • the power supply module 134 is electrically connected to the central control module 133. Used to provide power to the central control module 133.
  • the central control module 133 utilizes the electrical energy provided by the power supply module 134 for atomization.
  • Component 131 and signal pre-processing module 132 are powered.
  • the user's drug absorption information includes: the user inhaled the dose, the user's drug taking time, the number of times the user takes the drug, and the time interval between two adjacent drugs, and the like.
  • the atomizing member 131 is a member capable of realizing the atomization and post-injection function of the liquid medicine stored in the liquid storage member 110 in the prior art, and can be selected by a person skilled in the art as needed, and is not limited herein.
  • the number of the signal pre-processing modules 132 may be one or more, and may be selected by a person skilled in the art as needed, which is not limited herein. However, it should be noted that the number of signal pre-processing modules 132 should be the same as the number of airflow sensors in the nozzle airflow monitoring component 120 such that the signal pre-processing module 132 can correspond to the airflow sensors in the nozzle airflow monitoring component 120. Electrical connection.
  • the number of signal preprocessing modules 132 in the atomizer body 130 is only one, and the signal preprocessing module 132 respectively
  • the airflow sensor is electrically connected to the central control module 133 in the atomizer body 130; if a plurality of airflow sensors are disposed inside the nozzle body in the nozzle airflow monitoring component 120, the signal preprocessing module 132 in the atomizer body 130
  • the number of the plurality of airflow sensors disposed in the nozzle body of the nozzle airflow monitoring component 120 is the same as that of the plurality of airflow sensors, and the plurality of signal preprocessing modules 132 are electrically connected to the plurality of airflow sensors in one-to-one correspondence.
  • the plurality of signal pre-processing modules 132 are also electrically connected to the central control module 133 in the atomizer body 130, for example, if two air flow sensors are disposed inside the nozzle body in the nozzle airflow monitoring component 120, the fog
  • the number of signal pre-processing modules 132 in the main body 130 and the internal setting of the nozzle body in the nozzle airflow monitoring unit 120 The number of the flow sensors is the same, and is also two, and the input ends of the two signal pre-processing modules 132 are electrically connected to the output ends of the two air flow sensors respectively, and at the same time, the two signal pre-processing modules 132 The output ends are electrically connected to the different signal input terminals of the central control module 133 in the atomizer body 130, respectively.
  • the signal pre-processing module 132 may include a rectification module 1321, a filtering module 1322, an amplification module 1323, and an analog-to-digital conversion module 1324.
  • the rectifier module 1321 is electrically connected to the airflow sensor in the nozzle airflow monitoring component 120 for outputting the airflow sensor.
  • the airflow pressure electrical signal is rectified;
  • the filtering module 1322 is electrically connected to the rectifier module 1321, and is configured to filter the rectified airflow pressure electrical signal to filter out interference clutter;
  • the amplification module 1323 is electrically connected to the filtering module 1322.
  • the method is used for amplifying the filtered airflow pressure electrical 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 The converted digital airflow pressure electrical signal is output to the central control module 133.
  • the above-mentioned modules ie, the rectification module 1321, the filtering module 1322, the amplification module 1323, and the analog-to-digital conversion module 1324
  • the airflow pressure electrical signal output by the airflow sensor in the nozzle airflow monitoring component 120 does not need to be rectified, and the rectifier module 1321 can be omitted.
  • the airflow sensor in the nozzle airflow monitoring component 120 can distinguish between the airflow pressure electrical signals obtained by the pressure conversion of the airflow generated by the user's inhalation or exhalation.
  • the airflow sensor in the nozzle airflow monitoring component 120 is further configured to: convert the pressure exerted by the user's inhaled airflow on the airflow sensor into an inspiratory airflow pressure electrical signal output; and apply the airflow generated by the user's exhalation to the airflow.
  • the pressure on the sensor is converted to an expiratory flow pressure electrical signal output.
  • the inspiratory flow pressure electrical signal is a positive airflow pressure electrical signal
  • the expiratory flow pressure electrical electrical signal is a negative airflow pressure electrical signal.
  • the signal pre-processing module 132 is further configured to: pre-process the inspiratory flow pressure electrical signal and the expiratory flow pressure electrical signal output by the airflow sensor.
  • the central control module 133 is internally provided with a timer and a counter, and the central control module 133 is further configured to: when receiving the inspiratory airflow pressure electrical signal preprocessed by the signal preprocessing module 132, start a timer to perform timing; When the exhalation airflow pressure electric signal preprocessed by the signal pre-processing module 132 is received, the timing is stopped, the timing time is obtained, and the counter is started to count, and the number of times of user suction is obtained.
  • the structural schematic diagram of the first embodiment of the atomizer with the drug absorption monitoring function shown in FIG. 1b is only a schematic structure, and the atomizer with the drug absorption monitoring function provided by the invention is provided. It can also be applied to the atomizer of other structures in the prior art, and the application can be applied according to actual needs by a person skilled in the art, which is not limited herein.
  • the structural schematic diagram of the liquid storage component in the first embodiment of the atomizer having the drug absorption monitoring function shown in FIG. 1c is only a schematic one. A person skilled in the art can specifically set the structure of the liquid storage component according to actual needs, which is not limited herein.
  • Examples 1 to 4 are friction generating type air flow sensors.
  • the airflow sensor includes a housing 211, a diaphragm assembly 212, and an electrode assembly 213.
  • the inside of the outer casing 211 is formed with an accommodating chamber.
  • the side wall of the outer casing 211 is formed with an air inlet 2111.
  • the bottom wall is formed with an air outlet 2112, and the air inlet 2111 and the air outlet 2112 respectively and the accommodating chamber Connected to form an air flow path, such that a flow generated by a user inhaling or exhaling passes through the air flow path; both ends of the diaphragm assembly 212 are fixedly disposed in the accommodating chamber inside the outer casing 211, and respectively and the electrode assembly A vibration gap is formed between the 213 and the bottom wall of the outer casing 211.
  • the diaphragm assembly 212 reciprocates between the electrode assembly 213 and the bottom wall of the outer casing 211 under the driving of the airflow inside the housing chamber; the electrode assembly 213 is The signal output end of the air flow sensor is located in the accommodating chamber inside the outer casing 211, opposite to the diaphragm assembly 212, and the reciprocating vibrating diaphragm assembly 212 and the electrode assembly 213 and/or the bottom wall of the outer casing 211 rub against each other to generate an air flow.
  • the electric signal is pressurized and output by the electrode assembly 213.
  • the diaphragm assembly 212 is a flexible component, and the shape is preferably an elongated shape.
  • the elongated diaphragm assembly 212 is located in the accommodating chamber inside the outer casing 211, and the two ends are fixedly disposed.
  • a diaphragm ring 2113, a first washer 2114, and a second washer 2115 are disposed in the accommodating chamber inside the outer casing 211.
  • the diaphragm ring 2113 is annular, and the two ends of the diaphragm assembly 212 are respectively fixedly disposed on the diaphragm ring 2113, and an air flow passage is formed between the side of the diaphragm assembly 212 and the diaphragm ring 2113.
  • the diaphragm assembly 212 on the diaphragm ring 2113 can reciprocate between the electrode assembly 213 and the bottom wall of the housing 211, driven by the airflow inside the chamber.
  • the first washer 2114 is a notched ring between the diaphragm ring 2113 and the electrode assembly 213 to form a vibration gap between the diaphragm assembly 212 and the electrode assembly 213;
  • the second washer 2115 is also a notched ring, located at The diaphragm ring 2113 is spaced between the diaphragm wall 212 and the bottom wall of the outer casing 211 to form a vibration gap between the diaphragm assembly 212 and the bottom wall of the outer casing 211.
  • the air flow 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 the bottom wall of the outer casing 211, respectively.
  • the diaphragm assembly 212 reciprocates between the friction film assembly and the bottom wall of the outer casing 211 to frictionally generate a gas flow pressure electrical signal in contact with the bottom surface of the friction film assembly and/or the outer casing 211.
  • the air flow sensor includes a shielding case 221, an insulating layer 222 disposed on a part or all of the inner surface of the shielding case 221, and at least one sensing unit.
  • the shielding shell 221 is provided with at least two vents 2211, and the airflow generated by the user inhaling or exhaling passes between the vents 2211; specifically, a vent is opened in the middle of the left and right sides of the shielding shell 221 2211, the airflow can enter from one of the vents 2211 and out of the other vent 2211.
  • the sensing unit comprises: at least one fixed layer and one free layer; at least one fixed layer is fixed on the shielding shell 221; the free layer has a fixing portion and a friction portion; the fixing portion of the free layer and at least one fixed layer or The shield case 221 is fixedly coupled; the free layer is rubbed against the at least one fixed layer and/or the shield case 221 by the friction portion.
  • At least one of the fixed layers is a signal output end of the air flow sensor, or at least one of the fixed layer and the shield case 221 is a signal output end of the air flow sensor.
  • FIG. 2c is a schematic structural diagram of a second embodiment of the airflow sensor including a sensing unit, the sensing unit includes: a fixed layer and a free layer 2231.
  • the intake direction of the airflow is parallel to the plane of the fixed layer in the airflow sensor.
  • the fixing layer is fixed below the inside of the shield case 221 .
  • the fixed layer is a polymer polymer insulating layer 2233 having an electrode 2232 plated on one side thereof, and the insulating layer 222 is disposed between a surface on which the polymer polymer insulating layer 2233 is plated with the electrode 2232 and the inner surface of the shield case 221.
  • the fixing portion of the free layer 2231 is fixedly connected to the polymer insulating layer 2233 through the spacer 2234, and the free layer 2231 is rubbed against the side surface of the polymer insulating layer 2233 and the shielding case 221 by the non-plating electrode 2232 through the friction portion.
  • the electrode 2232 and the shield case 221 are signal output ends of the air flow sensor.
  • the airflow sensor includes: a housing 231, The electrode 232 and the first polymer film 233 are disposed inside the casing 231.
  • the housing 231 has a hollow structure, and is internally provided with an electrode 232 and a first polymer film 233.
  • the central axes of the casing 231, the electrodes 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 outer casing or a non-metallic insulating outer casing.
  • the housing 231 further includes a first end face 2311 and a second end face 2312 that are oppositely disposed.
  • the first end surface 2311 is provided with at least one air inlet hole for supplying airflow
  • the second end surface 2312 is provided with at least one air outlet for supplying airflow.
  • at least one of the first end surface 2311 and the second end surface 2312 may be integrally disposed on the housing 231 to better protect the internal structure of the air flow sensor; or, the first end surface 2311 and the second end surface At least one of the end faces of the 2312 may also be detachably disposed on the housing 231 to facilitate replacement, disassembly, and the like of the housing 231 by the user.
  • the electrode 232 is disposed inside the casing 231 and disposed along the central axis of the casing 231.
  • the surface thereof may be provided as a metal electrode layer or as a non-metal electrode layer.
  • the inside of the electrode 232 may be a solid structure or a hollow structure.
  • the inside of the electrode 232 is a hollow structure so as to form an air flow passage between the electrode 232 and the first polymer film 233, and/or an air flow passage is formed inside the electrode 232, and at the same time, the electrode 232 of the hollow structure is more weighty.
  • the electrode 232 is further provided with a through hole communicating with the inside and the outside to increase the airflow in the airflow passage and improve the friction effect.
  • the first polymer film 233 is a tubular film that is sleeved outside 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. When the airflow passes through the air inlet hole, the airflow drives the diaphragm to vibrate through the airflow channel.
  • Each of the diaphragms has a fixed end integrally connected to the first polymer film 233 and a free end that can rub against the electrode 232 under the action of the air flow.
  • the fixed end of each diaphragm is disposed on a side close to the air inlet hole
  • the free end of each diaphragm is disposed on a side close to the air outlet hole, and the arrangement is used to ensure that when the airflow is blown from the air inlet hole At this time, the airflow is blown in from the direction of the fixed end of each diaphragm, so that a good friction effect can be achieved (the inventors found in the experiment that when the airflow is blown from the direction of the fixed end of the diaphragm, the vibration-starting effect of the free end of the diaphragm And the friction effect is better).
  • the electrode 232 serves as a signal output terminal of the air flow sensor.
  • the first polymer film 233 and the electrode 232 are separated by a preset distance, and the preset The distance is used to form a gas flow path between the electrode 232 and the first polymer film 233, and the space is also used to provide a sufficient vibration space for the diaphragm on the first polymer film 233.
  • the preset distance is controlled to be between 0.01 and 2.0 mm. In the case where no airflow flows in, the diaphragm on the first polymer film 233 and the surface of the electrode 232 are not rubbed, and no induced charge is generated; when the airflow flows in from the air inlet hole on the first end face 2311, the airflow is generated.
  • the eddy current causes the free end of the diaphragm to vibrate, and the free end of the vibration generates contact with the surface of the electrode 232 at a corresponding frequency, that is, the diaphragm and the surface of the electrode 232 are rubbed, thereby generating an induced charge on the electrode 232.
  • the electrode 232 is used as a signal output end of the air flow sensor, and the electrode 232 is provided with a wire connected to the electrode, and the induced charge on the surface of the electrode 232 is output as an induced electrical signal through the wire.
  • the electrode 232 can form a current loop together with the grounding point in the external circuit, thereby realizing the electrical signal output in a single electrode manner.
  • the electrical signal includes an electrical signal parameter related to a voltage value, a frequency value and the like.
  • the larger the flow velocity of the airflow the higher the vibration frequency of the diaphragm, and the larger the output voltage value and the frequency value.
  • the inventors further found from the measured values that the flow velocity is proportional to the voltage value V and the frequency f, that is, the specific voltage value or frequency value corresponds to a certain flow velocity value, and therefore, the output voltage value is obtained.
  • the frequency value can be further calculated to obtain the flow rate and flow rate of the airflow.
  • FIG. 2e to 2h respectively show the structural schematic diagram of the fourth example of the airflow sensor in the first embodiment of the atomizer with the drug absorption monitoring function provided by the present invention from different angles.
  • 2e is a schematic exploded view showing an example 4 of the airflow sensor in the first embodiment of the atomizer having the drug absorption monitoring function provided by the present invention
  • FIG. 2f is a view showing the drug absorption monitoring function provided by the present invention.
  • the air flow sensor includes a housing 241, and a first polymer film 243, a support structure 244, and an electrode 242 which are sequentially disposed inside the housing 241.
  • the support structure 244 is disposed outside the electrode 242, and the first polymer film 243 is sleeved on the outside of the electrode 242 and the support structure 244, and A diaphragm 2431 is further provided on the first polymer film 243.
  • the housing 241 is first introduced.
  • the shape of the housing 241 may be a cylindrical shape, a prismatic shape, a truncated cone shape, and a prismatic shape, wherein the shape of the housing 241 is preferably cylindrical.
  • the housing 241 may be a metal housing or a non-metallic insulating housing.
  • the housing 241 further includes a first end surface 2411 and a second end surface 2412. The first end surface 2411 is provided with at least one air inlet hole for the airflow to flow therein, and the second end surface 2412 is provided with at least one air outlet hole for the airflow.
  • the number of the air inlet holes and the air outlet holes may be plural, and the shape may be a mesh air hole or a hole shape air hole.
  • FIG. 2f is a schematic view of the assembled structure corresponding to the exploded structure diagram of FIG. 2e.
  • the airflow flows from the air inlet hole on the first end surface 2411, wherein the air intake
  • the number of holes is plural, and the shape is a hole-shaped air hole.
  • the shape and the number of the air outlet holes on the first end surface 2411 and the air outlet holes on the second end surface 2412 can be set by a person skilled in the art according to actual conditions, which is not limited in the present invention.
  • the housing 241 is internally provided with an electrode 242 and a first polymer film 243, wherein the positional relationship of the three is specifically that the central axes of the housing 241, the electrode 242 and the first polymer film 243 are on the same straight line, and
  • 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. That is, there is a certain gap between the casing 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 specifically described.
  • the electrode 242 will be described.
  • the electrode 242 is disposed along the central axis direction of the housing 241.
  • the shape of the electrode 242 may be a cylindrical shape, a prism shape, a truncated cone shape, and a prismatic shape; wherein, in order to increase the friction area of the electrode 242
  • the shape of the electrode 242 is a prismatic shape or a prismatic shape in which the side surface is flat.
  • the electrode 242 is in the shape of a hollow triangular prism.
  • the electrode 242 can be either a solid structure or a hollow structure.
  • the inside of the electrode 242 is a hollow structure so as to form an air flow passage between the electrode 242 and the first polymer film 243, and/or an air flow passage is formed inside the electrode 242, and at the same time, the electrode 242 of the hollow structure is more weighty. Small, so that the whole of the air flow sensor is more light; more preferably, the electrode 242 is further provided with a through hole communicating with the inner and outer portions, thereby increasing the airflow in the air flow passage, thereby further improving the friction. effect.
  • the shape of the first polymer film 243 may be various shapes such as a hollow cylindrical shape, a hollow prism shape, a hollow truncated cone shape, and a hollow prism shape;
  • the first polymer film 243 has a hollow prism shape or a hollow prism shape having a side surface, and the shapes of the first polymer film 243 and the electrode 242 are maintained. match.
  • the first polymer film 243 has a hollow cylindrical shape; and if the shape of the electrode 242 is a triangular prism, the first polymer film 243 corresponds to a hollow triangular prism. Wait.
  • the first polymer film is matched in shape to the electrode.
  • the electrode 242 has a triangular prism shape, and the shape of the first polymer film 243 is also a hollow triangular prism shape.
  • the inner diameter of the first polymer film 243 is larger than that of the electrode 242.
  • the outer diameter of the housing 241 is larger than the outer diameter of the first polymer film 243 so as to form a gap between the housing 241 and the first polymer film 243 and between the first polymer film 243 and the electrode 242. .
  • the inner diameter of the upper surface of the first polymer film 243 is larger than the electrode.
  • the outer diameter of the upper surface of the 242, and the inner diameter of the upper surface of the housing 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 surface of the electrode 242
  • the inner diameter of the lower surface of the casing 241 is larger than the outer diameter of the lower surface of the first polymer film 243 so as to be between the casing 241 and the first polymer film 243, and the first polymer film 243 and the electrode.
  • a gap is formed between 242.
  • the first polymer film 243 is hollow, that is, the first polymer film 243 is a hollow structure that is penetrated at both ends.
  • the upper and lower surfaces of the first polymer film 243 means: the first polymer film 243
  • the two sides are respectively defined on the first end surface 2411 and the second end surface 2412 of the housing 241.
  • the electrode 242 is hollow, the upper and lower surfaces of the electrode 242 have similar meanings.
  • the first polymer film 243 has a plurality of side surfaces
  • at least one diaphragm 2431 is further formed on each side surface of the first polymer film 243, as shown in FIG. 2g
  • the first polymer Two diaphragms 2431 are formed on each side surface of the film.
  • the number of the diaphragms 2431 on each side surface of the first polymer film is not limited to two, and may be one or plural, and the specific number thereof is determined by a person skilled in the art according to actual conditions. The setting is made, and the present invention does not limit this.
  • the diaphragm 2431 is specifically configured to: after the airflow passes through the air inlet hole, the airflow enters the airflow channel to drive the diaphragm 2431 to vibrate.
  • the air flow channel may be implemented in various manners, for example, may be formed between the electrode 242 and the first polymer film 243, or may be formed inside the electrode 242, or may be simultaneously at the electrode 242 and the first polymer. Airflow channels are formed between the membranes 243 and inside the electrodes 242.
  • the air flow channel is formed in a gap between the electrode 242 and the first polymer film 243; in the second implementation, in addition to the electrode 242 and the first polymer film 243
  • a gas flow path may be further formed inside the electrode 242.
  • a plurality of inner and outer communication through holes may be provided inside the electrode 242, or the inside of the electrode 242 may be a hollow structure or the like. Etc.
  • the provision of an air flow passage inside the electrode 242 can be more advantageous for the accelerated flow of the air flow, thereby achieving a more desirable friction effect.
  • Those skilled in the art can flexibly set the above air flow passages as needed.
  • each diaphragm 2431 on the first polymer film 243 has a fixed end integrally connected to the first polymer film 2431 and a free end which can be rubbed against the electrode by the air flow.
  • the fixed end of the diaphragm 2431 is disposed on a side close to the air inlet hole, and the free end of the diaphragm 2431 is disposed on a side close to the air outlet hole, and the arrangement is used to ensure that when the airflow is blown from the air inlet hole, The air flow is blown in from the direction of the fixed end of each diaphragm, so that a good friction effect can be achieved.
  • the diaphragm 2431 is a diaphragm that is pre-cut from the first polymer film 243 to form a predetermined shape, and accordingly, the vacant portion formed on the first polymer film 243 after the diaphragm 2431 is cut can be The airflow is improved to improve the friction effect.
  • the free end of the diaphragm 2431 can reciprocate under the action of the airflow, that is, the diaphragm 2431 generates a corresponding frequency vibration in the vacant portion under the driving force of the airflow.
  • the vibration can cause the free end of the diaphragm 2431 to rub against the surface of the electrode 242, thereby achieving the effect that the diaphragm 2431 generates friction under the action of the air force.
  • those skilled in the art can also design the structure of the diaphragm 2431 as a structure capable of fully utilizing inertia to achieve continuous vibration according to actual experimental conditions.
  • the design of the diaphragm 2431 has a free end slightly larger than the diaphragm 2431.
  • the diaphragm 2431 in the vibration will continuously vibrate under the action of inertia, the inertia Simultaneously acting on the diaphragm 2431 at the same time as the air flow acts, the vibration effect of the diaphragm 2431 is further increased, so that the friction effect can be further improved.
  • a plurality of diaphragms of a predetermined shape may be fixedly disposed on the first polymer film 243.
  • the specific arrangement of the diaphragm 2431 is not limited in the present invention. As long as it can achieve the contact friction effect.
  • the shape of the diaphragm 2431 may be a rectangle, a triangle, a polygon, a fan, or the like, and the length of the diaphragm 2431 can be adaptively set by a person skilled in the art according to the shape of the diaphragm to avoid the diaphragm being too long or too long. A short diaphragm vibration is unstable or cannot be oscillated.
  • the number of the diaphragms 2431 is plural, the plurality of diaphragms are disposed on the first polymer film 243 in an array manner, and the first polymer film 243 is hollow prismatic in order to enhance the friction effect.
  • one or a plurality of diaphragms may be respectively disposed on each side surface of the first prismatic polymer film 243.
  • the first polymer film is in the shape of a hollow triangular prism
  • the diaphragm 2431 is a plurality of rectangular diaphragms respectively disposed on the respective side surfaces of the first polymer film
  • the rectangular diaphragm has one side and the other
  • a polymer film is connected to form a fixed end of the rectangular diaphragm; the remaining three sides are separated to form a free end of the rectangular diaphragm.
  • the number of the diaphragms may be plural, and the diaphragms in Fig. 2g are arranged in an array on the first polymer film 243.
  • the first polymer film 243 and the electrode 242 are spaced apart by a predetermined distance, which is used to provide sufficient vibration space for the diaphragm on the first polymer film 243.
  • the preset distance can be controlled between 0.01-2.0 mm.
  • the preset distance may be implemented in the following two manners: in the first implementation, the two ends of the electrode 242 are respectively fixed on the first end surface 2411 of the housing 241 and the inner wall of the second end surface 2412.
  • the two ends of the first polymer film 243 are also respectively fixed on the inner walls of the first end surface 2411 and the second end surface 2412 of the housing 241 to maintain the space between the fixed housing 241 and the first polymer film 243.
  • the separation is performed, and the predetermined distance between the electrode 242 after the fixation and the first polymer film 243 is present.
  • This method is particularly suitable for a scene in which the first polymer film 243 is hard.
  • at least one support structure 244 is further disposed between the electrode 242 and the first polymer film 243.
  • the support structure 244 is for forming a gap between the electrode 242 and the first polymer film 243 such that the free end of the diaphragm on the first polymer film 243 is in contact with the electrode 242.
  • the support structure 244 can be integrated On the side surface of the electrode 242 opposite to the first polymer film 243 or on the side surface opposite to the first polymer film 243 and the electrode 242, the first polymer film 243 is prevented from being caused by the support structure 244 due to dropping or the like. The surface is continuously contacted on the electrode 242, so that the desired friction effect cannot be achieved.
  • the support structure 244 can be configured as a detachable structure to facilitate the user to disassemble and replace the support structure 244.
  • the thickness of the support structure 244 is preferably between 0.01 and 2.0 mm, and those skilled in the art may also provide a plurality of sets of support structures 244 of different thicknesses, so that the user can select support structures 244 of different thickness according to different actual conditions. Disassemble and replace.
  • the number of the support structures 244 may be one or plural. When the number of the support structures 244 is plural, each adjacent two support structures 244 are spaced apart from each other by a predetermined distance. Wherein, the preset distance can ensure that the respective diaphragms are respectively disposed between each adjacent two support structures 244.
  • a corresponding diaphragm is disposed in a portion of the first polymer film 243 that is not in contact with the support structure 244, and the diaphragm can generate vibration under the action of the airflow, and the vibration process is not affected by the support structure 244.
  • the support structure 244 can ensure effective separation between the first polymer film 243 and the electrode 242, preventing the two friction interfaces from being effectively separated after contact, thereby improving the friction effect.
  • the above two implementations can be used alone or in combination.
  • the electrode 242 and the first polymer film 243 are usually made of a material having opposite polarity (for example, an electrode) It is made of a material that is easy to lose electrons, and the first polymer film is generally made of a material that is easy to obtain electrons.
  • the first The diaphragm on the polymer film 243 is adsorbed on the surface of the electrode 242.
  • the diaphragm 2431 vibrates up and down under the action of the airflow, and a rapid contact separation occurs between the diaphragm 242 and the electrode 242, that is, the diaphragm 2431 rubs against the surface of the electrode 242 to generate an induced charge.
  • the induced charge flows out of the electrode 242 to output a corresponding electrical signal.
  • the electrode 242 forms a current loop together with the grounding point in the external circuit, thereby realizing the electrical signal output in a single electrode manner.
  • the airflow sensor of the above structure mainly relies on the contact friction between the first polymer film and the electrode to generate electricity.
  • those skilled in the art can also make various modifications and deformations to the internal structure of the airflow sensor:
  • the electrode 242 therein can be further realized by the following two schemes:
  • the electrode 242 includes only a single metal electrode layer. Accordingly, the free end of each diaphragm on the first polymer film 243 can be rubbed against the metal electrode layer in the electrode 242 by the air flow. Wherein, since the metal is more likely to lose electrons due to friction with the polymer, the surface of the electrode 242 is set as a metal electrode layer, and the metal electrode and the high molecular polymer (ie, the first polymer film 243) are rubbed, which can effectively enhance Inductive charge generation and increased sensitivity of the output electrical signal.
  • the polarity of the electrode 242 is opposite to that of the first polymer film 243, the electrode 242 is extremely susceptible to electrons, and the first polymer film 243 is easily electron-accepting. That is, the metal electrode layer is extremely susceptible to electrons, and the first polymer film is extremely easy to obtain electrons.
  • the second embodiment is different from the single layer structure in the first embodiment.
  • the electrode in the second embodiment is a composite structure.
  • the electrode 242 further includes: a metal electrode layer and a second polymer film disposed outside the metal electrode layer. The free end of the diaphragm can be rubbed against the second polymer film in the electrode 242 by the air flow.
  • a second polymer film is further disposed on the metal electrode layer of the electrode 242.
  • a second polymer film may be further coated on the metal electrode layer of the electrode 242.
  • each diaphragm on the first polymer film 243 is rubbed by the air current and the second polymer film in the electrode 242 to generate an induced charge, that is, through the polymer (the first polymer film).
  • the friction between the polymer and the polymer (second polymer film) generates an induced charge and outputs an electric signal through the metal electrode layer inside the second polymer film, thereby achieving a friction effect similar to that of the above-described first embodiment.
  • the material of the metal electrode layer may specifically be a metal or an alloy, wherein the metal may be gold, silver, platinum, palladium, aluminum, nickel, copper, titanium, chromium, tin, iron, manganese. , Molybdenum, tungsten or vanadium; alloys may be aluminum alloys, titanium alloys, magnesium alloys, niobium alloys, copper alloys, zinc alloys, manganese alloys, nickel alloys, lead alloys, tin alloys, cadmium alloys, niobium alloys, indium alloys, gallium alloys , tungsten alloy, molybdenum alloy, niobium alloy or niobium alloy.
  • the metal may be gold, silver, platinum, palladium, aluminum, nickel, copper, titanium, chromium, tin, iron, manganese. , Molybdenum, tungsten or vanadium
  • alloys may be aluminum alloys, titanium alloys, magnesium alloys, niobium alloy
  • the material of the metal electrode layer may be further selected from non-metallic conductive materials such as indium tin oxide, graphene, and silver nanowire film.
  • the material of the first polymer film and the second polymer film is selected from the group consisting of polyimide film, aniline formaldehyde resin film, polyoxymethylene film, ethyl cellulose film, polyamide film, melamine formaldehyde film, polyethylene glycol butyl Acid ester film, cellulose film, cellulose acetate film, polyethylene adipate film, poly( diallyl phthalate film), fiber (recycled) 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, polyparaphenylene Ethylene glycol dicarboxylate film
  • the materials of the first polymer film and the second polymer film may be the same or different. However, if the two layers of polymer film are made of the same material, the amount of charge that causes triboelectric charging is small. Therefore, it is preferable that the material of the first polymer film and the second polymer film are different.
  • the corresponding scheme is as follows: If the electrode 242 adopts the structure in the first scheme, that is, the outer layer of the electrode 242 includes only a single metal electrode layer, The support structure 244 is correspondingly disposed on the outer side of the metal electrode layer of the electrode 242; if the electrode 242 adopts the structure in the second embodiment, that is, the second polymer film layer is further disposed on the metal electrode layer of the outer layer of the electrode 242, The support structure 244 mentioned above corresponds to the outer side of the second polymer film layer disposed in the electrode 242.
  • the surface of the electrode 242 may be further disposed such that the surface of the electrode 242 is formed into a planar shape or a rough spot shape.
  • the planar electrode is an electrode whose surface is a smooth plane, and the electrostatic adsorption force of the induced charge generated by the friction of the planar electrode is small, that is, the adsorption force of the generated electrostatic adsorption diaphragm is small, so under the action of the airflow, when When the diaphragm on the first polymer film 243 is rubbed against the electrode 242 whose surface is provided in a planar shape, the problem that the vibration of the diaphragm is unstable due to the large electrostatic force generated by the friction can be overcome; the rough spot electrode is An electrode with a certain roughness on the surface, due to its The large roughness surface generates a large amount of induced charges when rubbed, so that when the diaphragm on the first polymer film 243
  • the rough dot electrode can be realized by grinding the surface of the electrode 242 or providing a concave-convex structure, wherein the concave-convex structure can be a semi-circular, stripe-shaped, cubic-shaped, quadrangular pyramid, or cylindrical rule. Concave structure of shape or other irregular shape.
  • each of the foregoing two solutions may be further divided into two implementation manners: in the first implementation manner, only the electrode 242 may be used as the signal output end; in the second implementation manner, The signal output is formed by the electrode 242 and the other output electrode.
  • the housing 241 can be provided as a metal housing such that the housing 241 serves as another signal output of the air flow sensor. That is, when the housing 241 is a metal housing, the housing 241 may be provided as another output electrode.
  • the housing 241 constitutes one of the output electrodes of the air flow sensor. When the distance between the housing 241 and the first polymer film 243 is set, the distance between the two is set within a preset distance, for example.
  • the diaphragm on the first polymer film 243 is vibrated up and down by the air current, the diaphragm is not only the electrode surface of the electrode 242.
  • the friction is generated, and further friction may be generated with the inner surface of the housing 241 to generate a corresponding induced charge on the inner surface of the housing 241, and the housing 241 at this time may serve as another signal output other than the electrode 242. end.
  • the material of the housing 241 may be set as a metal, or may be provided as a material other than metal; or the housing 241 may be further configured as a two-layer structure, that is, The inner structure of the casing 241 is set to a metal, and then a polymer film material or the like is disposed in addition to the above metal.
  • the present invention does not limit the material and structure of the housing 241.
  • only one signal output terminal is disposed, that is, the electrode 242 is the only signal output terminal; and in the second implementation manner of the first scheme and the second scheme, There are two signal outputs, namely an electrode 242 and a housing 241.
  • the electrode 242 when only one signal output terminal is provided, that is, 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; when two signal output terminals are set, When the electrode 242 and the casing 241 are selected as the signal output ends, a current loop is formed due to a potential difference between the electrode layers 242 and the casing 241.
  • those skilled in the art may further add an intervening film layer or an intervening electrode layer between the second polymer film and the first polymer film, thereby further increasing the friction interface. Quantity, improve friction.
  • the present invention does not limit the specific number and implementation manner of the friction interface, and those skilled in the art can flexibly set the form of the friction interface as long as the effect of friction power generation can be achieved.
  • the flow rate and flow rate of the airflow are obtained by processing the corresponding values contained in the electrical signal.
  • the electrical signal includes an electrical signal parameter related to a voltage value, a frequency value and the like. According to the measurement by the inventors, the larger the flow velocity of the airflow, the higher the vibration frequency of the diaphragm, and the greater the voltage value and frequency of the output.
  • the flow rate and flow rate of the airflow can be further calculated by obtaining the output voltage value, the frequency value, and the measured time length, thereby achieving the purpose of measuring the flow rate and flow rate of the airflow.
  • Table 1 shows the sample output electric signal parameter table measured under different air flow rates, and the specific sample parameters in items 1 and 2 are different, so at the same air flow rate The measured values are also different.
  • an optional parameter information of the measurement sample is as follows: the sample casing is a metal casing, the diameter is 6.0 mm, the distance between the diaphragm and the electrode (ie, the step height of the electrode tripod) is 1.0 mm, and the diaphragm thickness is 4-6 um.
  • the diaphragm is rectangular, with a length of 3.50 mm and a width of 1.0 mm.
  • the airflow sensor provided in the example 4 is realized by the principle of friction power generation, which not only has the advantages of being light and easy to carry, but also has the advantages of low production cost, simple manufacturing process, strong implementation and easy assembly.
  • the working process of the airflow sensor provided by the present invention by further providing a diaphragm on the first polymer film, the free end of the diaphragm is utilized to generate vibration under the action of the airflow, thereby generating a friction effect, and the diaphragm is in the vibration process.
  • the inertia generated in the friction increases the friction effect in the friction generation process, and obtains more accurate and effective induction signals by setting various modes of friction generation schemes, which improves the signal sensitivity and improves the accuracy of the operation of the airflow sensor.
  • the electrical signals output by the electrodes in Examples 1 to 4 are the airflow pressure electrical signals mentioned in the present invention.
  • the electrical signals output by the electrodes in the first to fourth examples are the inspiratory flow pressure electrical signals mentioned in the present invention;
  • the electrical signals output by the electrodes in Examples 1 to 4 are the expiratory flow pressure electrical signals mentioned in the present invention.
  • FIG. 3 is a block diagram showing the functional structure of the second embodiment of the atomizer with the drug absorption monitoring function provided by the present invention.
  • the atomizer having the drug absorption monitoring function of the second embodiment is different from the atomizer having the drug absorption monitoring function of the first embodiment in that the atomizer body 130 includes the atomizing member 131.
  • a wireless transceiver module 135 and an interactive function module 136 are also included.
  • the wireless transceiver module 135 is electrically connected to the central control module 133, and is configured to send the user suction information calculated by the central control module 133 to the preset receiving device by wireless communication, so as to preset the doctor and the receiving device side. Or the custodian view, wherein the preset receiving device can 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 for transmitting a user interaction command to the central control module 136, where The user interaction instruction includes at least one of the following: an open command, a close command, a user information initialization command, and a user medication information setting instruction.
  • the opening or closing instruction is used to control the opening or closing of the central control module 133 to control the opening or closing of the monitoring process;
  • the user information initialization instruction is used to clear or establish the monitored user drug absorption information.
  • the user drug absorption information setting instruction is used to control the monitoring type or monitoring mode of the user's drug absorption information.
  • the user can select to monitor the user's inhaled drug amount, the user drug taking time, and the user drug taking time through the interaction function module 136.
  • One or more of the user's drug-taking information such as the number of times the user takes the drug and the interval between two adjacent drugs, to increase the flexibility and selectivity of the monitoring information.
  • the identification function of the user may be preset through the interactive function module 136 to facilitate continuous monitoring of the same user. For other descriptions, refer to the description in Embodiment 1, and details are not described herein again.
  • an air flow sensor is disposed inside the nozzle body in the nozzle airflow monitoring component, and a signal pre-processing module electrically connected to the airflow sensor is disposed in the atomizer body.
  • the user can control the power supply module to communicate with the central control module through the interactive function module, so that the central control module starts working; and the user can also set the user drug absorption information to be monitored through the interactive function module. If the interactive function module is not disposed in the main body of the atomizer (as shown in the first embodiment), the work starts according to the preset user drug absorption information.
  • an air flow sensor disposed inside the nozzle body in the nozzle airflow monitoring component senses the pressure exerted on the airflow generated by the user's inhalation, and converts the pressure acting thereon into the corresponding inhalation.
  • the airflow pressure electrical signal is output to a signal pre-processing module electrically connected to the airflow sensor, and the signal pre-processing module outputs the inspiratory flow pressure of the airflow sensor
  • the electrical signal is preconditioned.
  • the central control module starts the timer set in the central control module when receiving the inspiratory airflow pressure electric signal preprocessed by the signal preprocessing module, and the central control module analyzes and calculates the inspiratory flow pressure electrical signal.
  • the peak value is obtained, and the flow rate and flow rate of the airflow generated by the user's inhalation are calculated according to the obtained peak value analysis of the inspiratory airflow pressure electric signal, and then the user inhaled dose Y1 per unit time during the first inhalation of the user is calculated and calculated. .
  • an air flow sensor disposed inside the nozzle body in the nozzle airflow monitoring component senses the pressure exerted on the airflow generated by the user's exhalation, and converts the pressure acting thereon to the corresponding exhalation.
  • the airflow pressure electrical signal is output to a signal pre-processing module electrically connected to the airflow sensor, and the signal pre-processing module pre-processes the expiratory airflow pressure electrical signal output by the airflow sensor.
  • the central control module When receiving the exhalation airflow pressure electric signal preprocessed by the signal preprocessing module, the central control module stops the timer set in the central control module to obtain the first timing time X1 (ie, the first inhalation of the user) Time), then clear the timer set in the central control module; at the same time, start the counter set in the central control module to count, get the first dose C1.
  • the first timing time X1 ie, the first inhalation of the user
  • an airflow sensor is also provided with an initial state electrical signal similar to the expiratory flow pressure electrical signal output by the airflow sensor when the user exhales, that is, the airflow sensor output when the user exhales.
  • the expiratory flow pressure electrical signal has the same direction as the initial state electrical signal, and therefore, the working principle and the above-mentioned airflow generated by the user's exhalation act on an airflow sensor disposed inside the nozzle body in the nozzle airflow monitoring component. The principle is the same and will not be described here.
  • the central control module determines whether the inspiratory flow pressure electrical signal preprocessed by the signal preprocessing module is received again within the preset time interval.
  • the preset time interval may be set by a person skilled in the art according to actual needs, which is not limited herein.
  • the preset time interval can be 1 s. If it is determined that the inspiratory airflow pressure electric signal preprocessed by the signal preprocessing module is received again within the preset time interval, the user inhales for the second time, and at this time, the central control module starts the timer setting of its internal setting.
  • the central control module analyzes and calculates the peak value of the inspiratory flow pressure electrical signal, and calculates the flow rate and flow rate of the airflow generated by the user's inhalation according to the obtained peak analysis of the inspiratory flow pressure electrical signal. Then analyze and calculate the unit time when the user inhales for the second time. The user inhaled the dose Y2.
  • the central control module receives the expiratory airflow pressure electrical signal preprocessed by the signal preprocessing module, the central control module stops the timer set by its internal timer, and obtains the second timing time X2 (ie, the user inhales for the second time) After the time), the timer set inside the central control module is cleared.
  • the central control module starts the counter of its internal setting and counts up to obtain the second number of times of suction C2.
  • the central control module determines whether the inspiratory flow pressure electrical signal preprocessed by the signal pre-processing module can also be received within the preset time interval. If yes, the central control module starts the timer set by its internal setting again, and repeats the above process; if not, the central control module analyzes and calculates the total user drug taking time X, and the total user drug intake number C is C2 (ie 2 The total user inhales the dose S, thereby obtaining the user's drug taking time information, the user's drug taking times information, and the user's inhaled drug amount information.
  • X X1 + X2
  • S X1 ⁇ Y1 + X2 ⁇ Y2.
  • the peak value of the inspiratory flow pressure electric signal output by an air flow sensor disposed inside the nozzle body in the nozzle airflow monitoring part when inhaling by the user and the flow rate and flow rate of the airflow generated by the user inhaling and the unit time is one-to-one correspondence.
  • the correspondence between the peak value of the inspiratory flow pressure electric signal output by an air flow sensor disposed inside the nozzle body in the nozzle airflow monitoring component and the flow rate and flow rate of the airflow generated by the user inhaling and the user can be preset by the manufacturer who produces the atomizer having the drug absorption monitoring function.
  • the inside of the nozzle body in the nozzle airflow monitoring component is provided with a plurality of airflow sensors
  • the atomizer body is provided with a plurality of signal preprocessing modules
  • the plurality of signal preprocessing modules and the nozzle airflow monitoring component The number of the plurality of airflow sensors disposed in the nozzle body is the same, and the plurality of signal pre-processing modules are electrically connected to the plurality of airflow sensors in one-to-one correspondence, and the plurality of signal pre-processing modules are also respectively associated with the atomizer body
  • the central control module is electrically connected.
  • the user can control the power supply module to communicate with the central control module through the interactive function module, so that the central control module starts working; and the user can also set the user drug absorption information to be monitored through the interactive function module. If the interactive function module is not disposed in the main body of the atomizer (as shown in the first embodiment), the work starts according to the preset user drug absorption information.
  • the plurality of airflows When the user inhales, the plurality of airflows disposed inside the nozzle body in the nozzle airflow monitoring component
  • the sensor senses the pressure exerted by the airflow generated by the user's inhalation, and converts the pressure acting thereon into a corresponding inspiratory flow pressure electrical signal output to the one that is electrically connected to the plurality of airflow sensors in one-to-one correspondence
  • the signal pre-processing module preprocesses the inspiratory flow pressure electrical signals output by the plurality of airflow sensors by the plurality of signal pre-processing modules.
  • the central control module receives the plurality of inspiratory flow pressure electrical signals, the central control module initiates the internal setting timing according to the first inspiratory flow pressure electrical signal received in the plurality of inspiratory flow pressure electrical signals.
  • the central control module separately analyzes and calculates the peak value of the plurality of inspiratory flow pressure electrical signals, adds the peaks of the plurality of inspiratory flow pressure electrical signals to obtain an average value, and obtains the final inspiratory flow.
  • the peak value of the pressure electric signal thereby calculating the flow rate and flow rate of the airflow generated by the user's inhalation according to the peak analysis of the obtained final inspiratory flow pressure electrical signal, and then analyzing and calculating the user's first inhalation time per unit time Inhaled dose Y1.
  • the above-described air flow sensor that outputs the first inspiratory flow pressure electric signal is referred to as the air flow sensor A.
  • the plurality of airflow sensors disposed inside the nozzle body in the nozzle airflow monitoring component sense the pressure exerted on the airflow generated by the user's exhalation, and convert the pressure acting thereon into a corresponding call.
  • the gas flow pressure electric signal is output to the plurality of signal pre-processing modules electrically connected to the plurality of air flow sensors in one-to-one correspondence, and the plurality of signal pre-processing modules perform the expiratory flow pressure electric signals output by the plurality of air flow sensors Pretreatment.
  • the central control module will stop the timer set by its internal airflow pressure electric signal according to the airflow sensor A, and obtain the first timing time X1 (that is, the time for the user to inhale for the first time), and then The timer set in the central control module is cleared.
  • the counter set in the central control module is started to count, and the first dose C1 is obtained.
  • the airflow sensor A also outputs an airflow sensor A when exhaling with the user in order to return to the initial state.
  • the output expiratory airflow pressure electrical signal is similar to the initial state electrical signal, that is, the expiratory airflow pressure electrical signal output by the airflow sensor A when the user exhales is in the same direction as the initial state electrical signal, therefore, the working principle and the above are The airflow generated by the user's exhalation works the same on the airflow sensor A, and will not be described here.
  • the central control module determines whether the inspiratory flow pressure electrical signal output by the airflow sensor A when the pre-processed user inhales is received again in the preset time interval.
  • the preset time interval may be set by a person skilled in the art according to actual needs, which is not limited herein.
  • preset time interval Can be 1s. If it is judged that the inspiratory airflow pressure electric signal output by the airflow sensor A is received again during the preset time interval, the user inhales for the second time, at this time, the central control module starts the timer setting of its internal setting.
  • the central control module also receives the inspiratory flow pressure electrical signals corresponding to the output of the other airflow sensors after the pre-processing, and at this time, the central control module separately analyzes and calculates the plurality of inspiratory airflows corresponding to the output of all the airflow sensors.
  • the peak value of the pressure electric signal is added to obtain the average value of the pressure signals of all the inspiratory gas flow signals, and the average value of the final inspiratory gas flow pressure electric signal is obtained, thereby obtaining the electric signal according to the obtained final inspiratory gas flow pressure.
  • the peak analysis calculates the flow rate and flow rate of the airflow generated by the user's inhalation, and then analyzes and calculates the user's inhaled dose Y2 per unit time when the user inhales for the second time.
  • the central control module receives the expiratory airflow pressure electric signal output by the airflow sensor A when the pre-processed user exhales, the central control module stops the timer set by its internal setting, and obtains the second timing time X2 (ie, the user After the second inhalation time, the timer set inside the central control module is cleared. At the same time, the central control module starts the counter counting of its internal setting to obtain the second sampling frequency C2.
  • the central control module determines whether the inspiratory flow pressure electrical signal output by the airflow sensor A when the pre-processed user inhales is still received in the preset time interval. If yes, the central control module starts its internal setting timer again to repeat the above process; if not, the central control module analyzes and calculates the total user drug intake time X, and the total user drug intake number C is C2 (ie 2 times), the total user inhales the dose S, thereby obtaining the user's drug taking time information, the user's drug taking times information, and the user's inhaled drug amount information.
  • X X1 + X2
  • S X1 ⁇ Y1 + X2 ⁇ Y2.
  • the average value obtained by adding the peaks of the inspiratory flow pressure electric signals outputted by the plurality of airflow sensors provided inside the nozzle body in the nozzle airflow monitoring member when inhaling by the user is generated by the user's inhalation.
  • the flow rate and flow rate of the airflow and the user's inhaled dose Y per unit time are one-to-one correspondence.
  • the average value obtained by adding the peaks of the inspiratory flow pressure electrical signals outputted by the plurality of airflow sensors provided inside the nozzle body in the nozzle airflow monitoring component when inhaling by the user and the flow velocity of the airflow generated by the user inhaling can be pre-set by the manufacturer who produces the atomizer with the drug absorption monitoring function. set.
  • the frictional power flow sensor outputs a pressure electric signal with the intake air flow (eg, positive Pulse electrical signal) the opposite of the expiratory flow pressure electrical signal (such as the negative impulse electrical signal) or the initial state electrical signal (such as the negative impulse telecommunications No.) Therefore, in order to accurately monitor the user's inhalation time, thereby accurately monitoring the user's inhaled dose, this requires an expiratory flow pressure electrical signal that acts on the frictional-generation airflow sensor by the airflow generated by the user's exhalation. Or the frictional power type airflow sensor monitors the initial state electrical signal outputted in order to return to the initial state, thereby determining the end time of the user to complete an inhalation.
  • a pressure electric signal with the intake air flow eg, positive Pulse electrical signal
  • the opposite of the expiratory flow pressure electrical signal such as the negative impulse electrical signal
  • the initial state electrical signal such as the negative impulse telecommunications No.
  • FIG. 4 is a functional block diagram of a third embodiment of an atomizer with a drug absorption monitoring function according to the present invention.
  • the atomizer having the drug absorption monitoring function of the third embodiment is different from the atomizer having the drug absorption monitoring function of the second embodiment in that the atomizer body 130 further includes a display module 137 and Alarm module 138.
  • the display module 137 is electrically connected to the central control module 133 for displaying the user drug absorption information obtained by the central control module 133.
  • the central control module 133 is further configured to: issue an alarm control signal according to the obtained user drug absorption information; and the alarm module 138 It is electrically connected to the central control module 133 for alerting according to an alarm control signal sent by the central control module 133.
  • the central control module 133 sends an alarm control signal according to the obtained user drug absorption information, when the user inhaled dose exceeds the preset dose threshold and/or the user ingests the number of times exceeds the preset dose threshold, the alarm module 138 generates an alarm control signal according to the The alarm control signal gives an alarm prompt to prompt the user to stop taking the medicine.
  • the alarm module 138 sends an alarm control signal according to the obtained user drug absorption information, when the user inhaled dose exceeds the preset dose threshold and/or the user ingests the number of times exceeds the preset dose threshold, the alarm module 138 generates an alarm control signal according to the The alarm control signal gives an alarm prompt to prompt the user to stop taking the medicine.
  • the wireless transceiver module 135, the interactive function module 136, the display module 137, and the alarm module 138 in the second embodiment and the third embodiment may be selected according to the design of a person skilled in the art, which is not limited herein. For example: if you do not need to communicate with a preset receiving device or By communicating with the preset receiving device by using a wired connection, the wireless transceiver module 135 can be omitted; if the atomizer is not required to be manually controlled, the interactive function module 136 can be omitted; if the user's drug absorption information is not required to be displayed, The display module 137 is omitted; if the alarm function is not required, the alarm module 138 can be omitted.
  • FIG. 5 is a functional block diagram of a drug absorption monitoring system using the atomizer with the drug absorption monitoring function provided by the present invention shown in FIG. 4.
  • the drug absorption monitoring system includes an atomizer 510 having a drug absorption monitoring function and a terminal device 520.
  • the atomizer 510 having the drug absorption monitoring function is the atomizer with the drug absorption monitoring function shown in FIG. 4; the terminal device 520 is wirelessly communicated with the atomizer 510 having the drug absorption monitoring function.
  • the mode is connected to store and display the atomizer 510 having the drug absorption monitoring function to analyze the calculated user drug absorption information, and/or to transmit a control command for controlling the atomizer 510 having the drug absorption amount monitoring function.
  • the terminal device 520 is connected to the wireless transceiver module 135 in the atomizer 510 having the drug absorption monitoring function in a wireless communication manner, and is configured to receive the central control module 133 sent by the wireless transceiver module 135.
  • the calculated user medication information is analyzed, and/or a control command for controlling the central control module 133 is sent to the wireless transceiver module 135.
  • the control instructions may include an open command for turning on the operation of the central control module 133 and a termination command for terminating the operation of the central control module 133.
  • the terminal device 520 can be a device such as a mobile phone or a computer, and can complete the statistics of the total user drug taking time, the total user drug intake times, and the total user inhaled drug amount, etc., by designing a specific application program therein.
  • the work of the information can be selected by a person skilled in the art as needed, and is not limited herein.
  • Fig. 6 is a block diagram showing another functional configuration of a drug absorption amount monitoring system using the atomizer having the drug absorption amount monitoring function provided by the present invention shown in Fig. 4. As shown in FIG. 6, the difference between the drug absorption monitoring system shown in FIG. 6 and the drug absorption monitoring system shown in FIG. 5 is that the drug absorption monitoring system shown in FIG. 6 further includes a large database service platform 630.
  • the terminal device 520 is further configured to: send the received user drug absorption information to the large database service platform 630; the large database service platform 630 and the terminal device 520 are connected in a wireless communication manner, and are used for receiving and storing the terminal device 520 to send
  • the user drug absorption information analyzes and compares the received user drug absorption information with the user drug absorption information in the large database service platform 630, obtains user analysis information, and transmits the user analysis information to the terminal device 520 for the terminal device.
  • 520 side doctors and / or guardians to view or reference, so that doctors and / Or the guardian can get a deeper understanding of the user's condition.
  • the drug absorption monitoring system provided by the present invention may also include the terminal device 520, but only the large database service platform 630, and then first passes through the central control module 133 in the atomizer 510 having the drug absorption monitoring function.
  • the analysis completes the calculation of the total user drug taking time, the total user inhaling times, and the total user inhaled drug amount, and the like, and obtains the user's drug inhaling information, and then sends the user's drug inhaling information through the wireless transceiver module 135.
  • the large database service platform 630 is analyzed and compared to obtain user analysis information, and finally the user analysis information is sent to the central control module 133 through the wireless transceiver module 135, so that the central control module 133 controls the display module 137 to display user analysis information for the doctor. And/or guardian review or reference to enable doctors and/or guardians to gain a deeper understanding of the user's condition.
  • the drug absorption monitoring system shown in FIG. 5 and FIG. 6 can not only adopt the atomizer with the drug absorption monitoring function of the third embodiment, but also adopt the drug absorption method of the first embodiment or the second embodiment.
  • the atomizer of the volume monitoring function can be selected by a person skilled in the art as needed, and is not limited herein.
  • connection mode of the atomizer 510 having the drug absorption monitoring function and the terminal device 520 or the large database service platform 630 can be connected not only by wireless communication but also directly.
  • the wired communication mode is connected, and when connected by wired communication, the corresponding wireless communication device can be omitted, for example, the wireless transceiver module 135 in the atomizer 510 having the drug absorption monitoring function.
  • the atomizer and the drug absorption monitoring system with the drug absorption monitoring function provided by the nozzle airflow monitoring component monitor the airflow generated by the user's inhalation or exhalation, and can infiltrate the drug and absorb the drug sensitively and accurately.
  • the user's drug absorption information such as time and drug absorption times are monitored, and the user's drug absorption information is monitored.
  • the atomizer and the drug absorption monitoring system with the drug absorption monitoring function provided by the invention not only have high sensitivity and high accuracy, but also have the advantages of simple structure, simple manufacturing process, low cost and large-scale industrial production.
  • the various modules and circuits mentioned in the present invention are circuits implemented by hardware.
  • the central control module may include a microcontroller or a micro control chip
  • the rectifier module may include a rectifier circuit
  • the filter module may include a comparison circuit to amplify
  • the module may include an amplification circuit or the like
  • the analog to digital conversion module may include an analog to digital converter or the like.

Landscapes

  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Veterinary Medicine (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Biomedical Technology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Anesthesiology (AREA)
  • Pulmonology (AREA)
  • Bioinformatics & Cheminformatics (AREA)
  • General Physics & Mathematics (AREA)
  • Physics & Mathematics (AREA)
  • Fluid Mechanics (AREA)
  • Biophysics (AREA)
  • Electrochemistry (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Chemical & Material Sciences (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

L'invention concerne un atomiseur doté d'une fonction de surveillance du dosage d'un médicament inhalé et un système de surveillance du dosage d'un médicament inhalé. L'atomiseur comprend un élément de stockage (110) de liquide, un élément de surveillance (120) d'écoulement d'air dans une buse, et un corps (130) d'atomiseur, l'élément de stockage (110) de liquide étant relié au corps (130) d'atomiseur et étant utilisé pour stocker un médicament liquide destiné à être atomisé et injecté; l'élément de surveillance (120) d'écoulement d'air dans une buse est relié à l'élément de stockage (110) de liquide et est utilisé pour délivrer un signal électrique de pression d'écoulement d'air en fonction d'un écoulement d'air généré par l'inspiration ou l'expiration d'un utilisateur, et injecter le médicament liquide atomisé par le corps (130) d'atomiseur dans la bouche et le nez de l'utilisateur; le corps (130) d'atomiseur est électriquement connecté à l'élément de surveillance (120) d'écoulement d'air dans une buse et est utilisé pour atomiser et injecter le médicament liquide stocké dans l'élément de stockage (110) de liquide, et analyser et calculer un dosage de médicament inhalé par l'utilisateur en fonction du signal électrique de pression d'écoulement d'air délivré par l'élément de surveillance (120) d'écoulement d'air dans une buse de façon à obtenir des informations sur un médicament inhalé par l'utilisateur.
PCT/CN2017/088091 2017-03-31 2017-06-13 Atomiseur et système de surveillance de dosage de médicament inhalé Ceased WO2018176632A1 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
CN201710208190.XA CN107402048B (zh) 2017-03-31 2017-03-31 气体流量传感器
CN201710211423.1A CN108525082B (zh) 2017-03-31 2017-03-31 具有吸药量监测功能的雾化器及吸药量监测系统
CN201710211423.1 2017-03-31
CN201710208190.X 2017-03-31

Publications (1)

Publication Number Publication Date
WO2018176632A1 true WO2018176632A1 (fr) 2018-10-04

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