CN219206933U - Humidity sensor and system for detecting urine humidity or detecting dehydration of exhale of intelligent paper diaper - Google Patents
Humidity sensor and system for detecting urine humidity or detecting dehydration of exhale of intelligent paper diaper Download PDFInfo
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Abstract
The utility model discloses a humidity sensor and a system for detecting urine wetness or exhaling and dehydrating of an intelligent paper diaper, which belong to the technical field of humidity sensors and application thereof and comprise a flexible conductive layer, a flexible dielectric layer, a flexible spacer layer and a functional structure layer which are sequentially overlapped; the functional structure layer comprises a metal substrate and a sensitive layer, the sensitive layer is arranged on the outer surface of the metal substrate facing the flexible spacing layer, the functional structure layer is provided with a through hole, and the through hole penetrates through the outer surface of the functional structure layer facing the flexible spacing layer and the outer surface of the functional structure layer opposite to the flexible spacing layer. The utility model utilizes the mechanical vibration generated by sound to drive the flexible wearable humidity sensor to work, thereby realizing the conversion of sound energy into humidity sensing electric signals.
Description
Technical Field
The utility model relates to a humidity sensor and application thereof, in particular to a humidity sensor and a system for detecting urine wetness or exhaling and dehydrating of an intelligent paper diaper.
Background
With the development of flexible electronics, various intelligent wearable systems, such as smart watches, smart glasses, or smart bracelets, have been proposed.
The intelligent paper diaper is worn on a baby or a nursed person after integrating a flexible sensor and a data processing/transmitting unit on the paper diaper, and is used for monitoring urination and transmitting information to a mobile terminal or a cloud terminal. The health condition of the nursed person can be known in real time by the nursed person. The intelligent diaper for detecting the urine wet state of a baby or an adult in the current market mainly comprises a prompt lamp (used for information reminding), a humidity sensor (used for urine wet information acquisition), a data processor (used for information processing) and a diaper, wherein the prompt lamp sends data received from the urine wet sensor and the data processor to a mobile phone APP through Wi-Fi, and a nursing staff is informed of replacing the diaper for the baby or the cared person.
In the aspect of human expiration detection, research finds that the gas exhaled by the human is closely related to the physiological state of the body, and the relative humidity in the exhaled gas can be used as an index for accurately judging the dehydration condition of a patient or an athlete. However, in the clinical medical field, the breath detection is mainly sleep breathing condition monitoring, and different sensors and electrodes are required to be placed on multiple places of the body of a subject, so that the influence on sleep is caused, and therefore, the actual breathing condition may not be reflected. For example, a wearable respiration monitoring chest belt combines the respiration frequency with information such as heart rate and blood oxygen saturation, and an indirect respiration monitoring method is utilized to respond to the respiration state by changing the stress of the chest or abdomen fluctuation during respiration.
The sensing principle of the humidity sensor adopted is mainly as follows: the common characteristics of the intelligent sensing systems are that the intelligent sensing systems are additionally provided with batteries for supplying power, so that the system volume is increased, and the portability and the comfort are reduced.
In recent years, various self-powered sensing devices have been developed for use in smart wearable systems for detecting certain physiological information of the human body. The system integrates a sensor and a self-powered unit, such as a nano-generator. A small amount of mechanical energy can be harvested in the environment for operation and can be operated without any external power supply. Such self-powered sensing systems are small and easy to integrate, and in published academic papers and patents, many self-powered active gas sensors and biosensors have been developed, the working principle of which can be briefly described as the coupling of energy conversion to the sensing process. Taking the piezoelectric/gas sensing coupling effect as an example, under the condition of applying body movement deformation or finger pressing, the piezoelectric output of the device depends on environmental parameters (such as gas atmosphere or biochemical molecules), and can be used as a power source of a sensor and a sensing signal. However, for infants and patients, the deformation by applying body movement is not suitable because the body itself does not move or the frequency and intensity of the motion are low.
Accordingly, embodiments of the present utility model provide a flexible wearable humidity sensor that utilizes acoustic actuation, which may be embedded in applications such as a diaper or a mask for detecting the relative humidity of the diaper and the person's exhale.
Disclosure of Invention
The utility model aims at: a sound-driven flexible wearable humidity sensor and a system for detecting urine wetness or expiratory dehydration of an intelligent diaper are provided.
The utility model is realized by the following technical scheme:
a sound-driven flexible wearable humidity sensor comprises a flexible conductive layer, a flexible dielectric layer, a flexible spacer layer and a functional structure layer which are overlapped in sequence; the functional structure layer comprises a metal substrate and a sensitive layer, the sensitive layer is arranged on the outer surface of the metal substrate facing the flexible spacing layer, the functional structure layer is provided with a through hole, and the through hole penetrates through the outer surface of the functional structure layer facing the flexible spacing layer and the outer surface of the functional structure layer opposite to the flexible spacing layer.
The flexible dielectric layer is a polyvinylidene fluoride film, a perfluoroethylene propylene film, a vinylidene chloride acrylonitrile copolymer film, a polytetrafluoroethylene film, a polyvinyl chloride film or a polytrifluoroethylene film.
The flexible dielectric layer is provided with nano-microstructures at least towards that outer surface of the flexible spacer layer.
The metal substrate is a flexible metal net or a flexible metal foil.
The flexible metal net is a gold metal net, a silver metal net, a platinum metal net, a palladium metal net, a copper metal net, a titanium metal net or a chromium metal net, or the flexible metal net is an alloy metal net of a plurality of metals in gold, silver, platinum, palladium, copper, titanium and chromium.
The flexible metal foil is a gold metal foil, a silver metal foil, a platinum metal foil, a palladium metal foil, a copper metal foil, a titanium metal foil or a chromium metal foil, or the flexible metal net is an alloy metal foil of a plurality of metals in gold, silver, platinum, palladium, copper, titanium and chromium.
The sensitive layer is ZnO nanowire and WO 3 Nanowires, snO 2 Nanowires, baTiO 3 Film, znWO 4 Nanowires, znSnO 3 The nano-wire, the element doped ZnO nano-wire, the graphene film layer with the surface modified by functionalization, and the carbon nano-tube or polyaniline film layer with the surface modified by functionalization.
The flexible spacer layer is a flexible insulating layer.
The flexible conductive layer is a gold metal layer, a silver metal layer, a platinum metal layer, a palladium metal layer, a copper metal layer, a titanium metal layer or a chromium metal layer, or the flexible conductive layer is a conductive film.
A system for diaper wetness detection or breath dehydration detection of a smart pant diaper comprising:
the flexible wearable humidity sensor is used for converting the relative humidity of the paper diaper or the expired air into an electric signal under the driving of sound;
a data processing circuit for amplifying, voltage converting, level shifting and low pass filtering the electrical signal;
and the wireless emission display module is used for converting the electric signals subjected to amplification, voltage conversion, level shift and low-pass filtering into relative humidity signals of paper diapers or human exhalations and displaying the relative humidity signals.
Compared with the prior art, the utility model has the following beneficial technical effects:
the utility model provides a sound-driven flexible wearable humidity sensor, which utilizes mechanical vibration generated by sound to drive the flexible wearable humidity sensor to work so as to convert sound energy into humidity sensing electric signals. The utility model can reduce the complexity of the system, improve the flexibility of the sensing system and is more beneficial to the application of the wearable intelligent equipment; the repeated utilization of the detection system can be realized, and the cost of the wearable intelligent device is reduced, so that the feasibility of market popularization is improved.
Drawings
FIG. 1 is a flow chart of the operational mode of the sound-driven flexible wearable humidity sensor of the present utility model;
FIG. 2 is a schematic illustration of two exemplary configurations of the acoustically driven flexible wearable humidity sensor of this utility model;
in fig. 3, fig. 3 (a) is an SEM image of the etched PTFE film; FIG. 3 (b) is a PANI/copper mesh SEM image; FIG. 3 (c) SEM image of zinc oxide nanowire growth on porous titanium foil;
FIG. 4 is a graph of humidity sensing performance of a flexible wearable humidity sensor of PTFE/PANI/metal mesh construction; wherein fig. 4 (a) is a graph of electrical output as a function of relative humidity; FIG. 4 (b) is a graph of the relationship between relative humidity and sensor response; FIG. 4 (c) is a diagram of the detection limit of the sensor; FIG. 4 (d) is a repetitive graph of the sensor; FIG. 4 (e) a humidity sensing performance graph driven by a child song "little stars"; FIG. 4 (f) shows humidity sensing performance driven by popular songs from the desert river dance hall;
FIG. 5 is a graph of humidity sensing performance of a flexible wearable humidity sensor of PTFE/ZnO/metal foil construction; wherein, FIG. 5 (a) is a graph of the stable output characteristics of the sensor under specific acoustic wave driving; FIG. 5 (b) sensor electrical output plot at different relative humidities; FIG. 5 (c) is a graph of relative humidity versus voltage versus relative humidity versus response; FIG. 5 (d) is a repetitive graph of the sensor; FIG. 5 (e) a reversibility diagram of the sensor;
FIG. 5 (f) is a graph of sensing performance at high humidity; FIG. 5 (g) is a graph of high relative humidity versus voltage and response; FIG. 5 (h) graph of changes in relative humidity in room for 24 hours; FIG. 5 (i) is a graph showing changes in sensor output voltage for 24 hours in a room relative to humidity;
FIG. 6 is a circuit diagram of a system for detecting diaper wetness or detecting dehydration by exhalation of a smart diaper according to the present utility model;
FIG. 7 is a graph showing the sensing performance of a flexible wearable humidity sensor with three diaper embedded PTFE/PANI/metal mesh structures;
fig. 8 is a graph of relative humidity change before and after exercise for subject 1 (male) and subject 2 (female) wearing a flexible wearable humidity sensor of PTFE/ZnO/metal foil structure.
The meaning of the reference numerals is as follows:
1. flexible conductive layer 2, flexible dielectric layer 3, flexible spacer layer 4, functional structure layer.
Detailed Description
All the features disclosed in this specification, or the steps of all methods or processes disclosed, except for the mutually exclusive features and/or steps, may be combined in any combination, unless specifically stated otherwise, with other equivalents or alternatives having a similar purpose, i.e., each feature is one embodiment of a series of equivalents or similar features, unless specifically stated otherwise.
Referring to fig. 1 and 2, the utility model designs a sound-driven flexible wearable humidity sensor which can be embedded into a paper diaper or a face mask and can be repeatedly used, two layers of the humidity sensor, namely a flexible dielectric layer 2 and a functional structural layer 4, generate vibration (resonance effect) under the driving of sound or music acceptable to infants, patients and athletes, generate electric output through a triboelectric effect, the output current is reduced along with the increase of humidity, and the humidity sensor can be used for monitoring relative humidity information of urine trousers or human exhalations, and the sensing information is uploaded through a data processing circuit and a wireless transmitting display module. Specifically, the flexible dielectric layer 2 generates negative charges after friction with the functional structural layer 4; the functional structural layer 4 comprises a sensitive layer, which can be made of a material that is sensitive to humidity and generates positive charges after friction with the flexible dielectric layer 2, for example, znO or polyaniline is adopted, that is, the sensitive layer can be a ZnO nanowire or polyaniline film layer, and the functional structural layer 4 is used for generating positive charges and humidity induction.
The flexible wearable humidity sensor can be used for converting the relative humidity of the baby diaper into an electric signal under the driving of sound. The data processing circuit is used for amplifying, voltage converting, level shifting and low-pass filtering the electric signals. The wireless emission display module is used for converting the electric signals subjected to amplification, voltage conversion, level shift and low-pass filtering into relative humidity signals of paper diapers or people exhales and displaying the relative humidity signals.
Referring to fig. 2, an acoustically-driven flexible wearable humidity sensor in accordance with one of many embodiments of the present utility model includes a flexible conductive layer 1, a flexible dielectric layer 2, a flexible spacer layer 3, and a functional structural layer 4. The flexible conductive layer 1, the flexible dielectric layer 2, the flexible spacer layer 3 and the functional structural layer 4 are overlapped in sequence. The functional structure layer 4 comprises a metal substrate and a sensitive layer arranged on the outer surface of the metal substrate facing the flexible spacer layer, i.e. the sensitive layer is arranged between the flexible spacer layer 3 and the metal substrate. The functional structural layer 4 is provided with through holes penetrating through the outer surface of the functional structural layer 4 facing the flexible spacer layer 3 and the outer surface of the functional structural layer 4 opposite the flexible spacer layer 3.
The flexible dielectric layer 2 may be a polyvinylidene fluoride film, a perfluoroethylene propylene film, a vinylidene chloride acrylonitrile copolymer film, a polytetrafluoroethylene film, a polyvinyl chloride film, or a polytrifluoroethylene film. The polyvinylidene fluoride film is a film made of polyvinylidene fluoride, and other films are the same.
At least that outer surface of the flexible dielectric layer 2 facing the flexible spacer layer is provided with nano-microstructures.
The metal substrate may be a flexible metal mesh or a flexible metal foil.
The flexible metal mesh may be a gold metal mesh, a silver metal mesh, a platinum metal mesh, a palladium metal mesh, a copper metal mesh, a titanium metal mesh, or a chromium metal mesh, or the flexible metal mesh may be an alloy metal mesh of a plurality of metals of gold, silver, platinum, palladium, copper, titanium, and chromium. The gold wire mesh is a wire mesh made of gold, and other wire meshes are the same.
The flexible metal foil can be a gold metal foil, a silver metal foil, a platinum metal foil, a palladium metal foil, a copper metal foil, a titanium metal foil or a chromium metal foil, or the flexible metal mesh can be an alloy metal foil of a plurality of metals in gold, silver, platinum, palladium, copper, titanium and chromium. Gold foil is a metal foil made of gold, other metal foils, and so on.
The sensitive layer can be a ZnO nanowire or a polyaniline film layer. The sensitive layer may also be WO 3 Nanowires, snO 2 Nanowires, baTiO 3 Film, znWO 4 Nanowires, znSnO 3 Nanowires, element doped ZnO nanowires, surface functionalized modified graphene film layers, surface functionalized modified carbon nanotubes and the like.
The flexible spacer layer 5 may be a flexible insulating layer, for example, made of one or more of a variety of non-conductive materials such as rubber, polymers, springs, etc.
The flexible conductive layer 1 is specifically a gold metal layer, a silver metal layer, a platinum metal layer, a palladium metal layer, a copper metal layer, a titanium metal layer or a chromium metal layer, or the flexible conductive layer 1 may be a conductive film.
The utility model takes a flexible wearable humidity sensor formed by Polytetrafluoroethylene (PTFE)/Polyaniline (PANI)/metal mesh and a flexible wearable humidity sensor formed by PTFE/zinc oxide (ZnO)/porous titanium foil as examples, and the flexible wearable humidity sensor driven by sound is simply introduced. It will be appreciated by those skilled in the art that the flexible dielectric layer 2 is not limited to PTFE films, the sensing layer of the functional structure layer 4 is not limited to PANI films or ZnO nanowires, but may be other polymers and piezoelectric semiconductors, etc.
Taking PTFE/PANI/metal mesh humidity sensor and PTFE/ZnO/porous titanium foil humidity sensor as examples, the manufacturing method of the sound-driven flexible wearable humidity sensor is briefly described, and comprises the following steps:
when the metal substrate is a flexible metal net (for example, the metal substrate is a copper net), the flexible metal net is cleaned by deionized water and ethanol, surface impurities are removed, and the metal net is dried for 15 minutes at 60 ℃; then, the PANI derivative is deposited on a copper mesh by an electrochemical polymerization method, namely, 0.01 mole of aniline, 0.01 mole of sodium dodecyl benzene sulfonate and 50 milliliters of deionized water are used for preparing a growth solution; the electrochemical polymerization process adopts a three-electrode system, wherein a working electrode adopts a platinum sheet, a reference electrode adopts an Ag/AgCl electrode, and a counter electrode adopts a platinum wire; polymerizing PANI for 200 seconds by using an electrochemical workstation under the conditions of 1.2V and 0.05V/second, and then cleaning with deionized water, so that a PANI derivative film layer is deposited on the outer surface of the metal substrate and is used as a sensitive layer; drying in a drying oven at 60 ℃ for 10 minutes to obtain a functional structural layer 4;
when the metal substrate is flexible metal foil (for example, titanium foil is adopted), firstly, a hot press is used for flattening titanium foil with the thickness of 0.1 mm and the thickness of 40 mm by 40 mm, and a plurality of through holes with the diameter of 1 mm are arranged on the titanium foil, so that the propagation of sound waves and the immersion of water molecules are facilitated; ultrasonically cleaning the porous titanium foil by using ethanol and deionized water, and drying at 60 ℃; 2 g of zinc nitrate hexahydrate powder is taken and dissolved in 152 ml of deionized water, and then 8 ml of ammonia water is slowly dripped into the solution and stirred until the solution is clear; transferring to a high-pressure reaction kettle, and keeping at 90 ℃ for 24 hours, so that ZnO nanowires are generated on the outer surface of the metal substrate, wherein the ZnO nanowires are used as sensitive layers;
and 4, placing the product in a drying oven at 60 ℃ for 30 minutes after the step 3 is finished, and obtaining the flexible wearable humidity sensor.
The PTFE film after oxygen plasma etching has a rough surface, which is beneficial to increasing the contact area and improving the triboelectric output. As shown in fig. 3 (a), 3 (b) and 3 (c), PANI generated by electrochemical reaction was also confirmed to be attached to the copper mesh, and ZnO nanowires obtained by hydrothermal method were also confirmed to be vertically grown on the surface of the porous titanium foil.
Fig. 4 shows the humidity sensing performance of the flexible wearable humidity sensor of PTFE/PANI/copper mesh structure. Where FIG. 4 (a) is a graph of electrical output change with changes in relative humidity, with sound waves maintained at 325Hz and 118dB, and with 50%, 60%, 70%, 80% and 90% relative humidity, respectively, the sensor output currents are 0.78, 0.66, 0.46, 0.36 and 0.28 nanoamperes, respectively, with output decreasing with increasing relative humidity. Experimental results show that the flexible wearable humidity sensor can actively monitor the relative humidity under the drive of sound waves, and no external power supply is needed. Sensor response R for detecting relative humidity i Is defined by formula (1).
In the formula (1), I 0 And I t The outputs of initial relative humidity and experimental relative humidity, respectively. The response of the device was 15.4%, 41%, 53.8% and 64.1% when the relative humidity varied between 50% and 90%, respectively, as shown in fig. 4 (b). The result shows that the flexible wearable humidity sensor has higher sensitivity and can realize real-time monitoring of relative humidity.
The detection limits of such humidity sensors were further studied by the examples of the present utility model, and it can be seen from fig. 4 (c) that the current outputs at 48% and 50% relative humidity are very similar, and the currents at 90% and 93% relative humidity are very similar, and therefore the flexible wearable humidity sensor of the present utility model has a relative humidity detection range of about 50% to 90%. As the relative humidity increases from 50% to 90%, the output decreases from 0.78 to 0.28 nanoamps. When the relative humidity was restored to 50%, the output was restored to 0.76 nanoamperes. The repeatability study shows that the flexible wearable humidity sensor of the utility model has good stability and repeatability, as shown in fig. 4 (d). Fig. 4 (e) and 4 (f) are the operation of the flexible wearable humidity sensor of the present utility model driven by music, playing child songs (small stars) and chinese popular songs (desert river dance) as music driving sources, and decreasing the sensor output driven by small stars from 0.24 to 0.17 nanoamperes and the flexible wearable humidity sensor output driven by desert river dance from 0.68 to 0.59 nanoamperes as the relative humidity increases from 70% to 80%. The results show that the flexible wearable humidity sensor of the present utility model can monitor relative humidity through different music song activations, and caregivers can select favorite songs for infants or patients.
Fig. 5 is a relative humidity sensing performance of a flexible wearable humidity sensor of PTFE/ZnO/porous titanium foil structure. As shown in fig. 5 (a), the flexible wearable humidity sensor of the present utility model output voltage is very stable (60 millivolts) with constant sound wave (frequency of 325hz, intensity of 107dB, sound source distance of 5 mm, no angular offset) when the relative humidity is 60%. The flexible wearable humidity sensor of the present utility model output voltages of 71, 70, 61, 51, 39.5 and 10 millivolts when the relative humidity is 40%, 50%, 60%, 70%, 80% and 90%, respectively, the peak output voltage decreases with increasing relative humidity, as shown in fig. 5 (b). Therefore, the flexible wearable humidity sensor can detect the relative humidity of the environment under the drive of sound waves, and external power supply is not needed. FIG. 5 (c) is a graph of relative humidity versus voltage versus relative humidity versus response; response R of the Flexible wearable humidity sensor of the utility model v Defined by formula (2).
In the formula (2), V 0 、V t The relative humidity is 40% of the sensor output voltage and the sensor output voltage under other experimental environments. As shown in fig. 5 (c), the response rates of the flexible wearable humidity sensor of the present utility model are 1.8%, 13.9%, 28%, 44.8% and 85% at relative humidity of 50%, 60%, 70%, 80% and 90%, respectively, and the flexible wearable humidity sensor of the present utility model has high responsiveness.
Through repeated studies of the flexible wearable humidity sensor of the present utility model, it was found (fig. 5 (d)) that when the relative humidity was increased from 40% to 90% and repeated 3 times, the output voltage was mostly decreased from 73 millivolts to 10 millivolts, with good reproducibility. Fig. 5 (e) demonstrates the reversibility of the flexible wearable humidity sensor of the present utility model, which decreases in output voltage from 70 millivolts to 12 millivolts as the relative humidity increases from 50% to 90%. Thereafter, as the relative humidity decreases from 90% to 60%, the flexible wearable humidity sensor output voltage of the present utility model increases from 12 millivolts to 58 millivolts. The result shows that the flexible wearable humidity sensor has higher reversibility. Generally, the relative humidity can reach 80% during exhalation. The utility model thus further investigates the sensing performance of the flexible wearable humidity sensor of the utility model at high relative humidity. As shown in fig. 5 (f), at 70%, 72%, 74%, 76%, 78%, and 80% relative humidity, the flexible wearable humidity sensor of the present utility model output voltages of 56.2, 54.4, 47.7, 42.4, 38.8, and 36.3 millivolts, respectively, and corresponding responses of 3.2%, 15.1%, 24.5%, 31%, and 35.4%, respectively, as shown in fig. 5 (g). The flexible wearable humidity sensor of the present utility model is shown to be useful for detecting relative humidity in exhaled breath. In addition, the detection upper limit and the detection lower limit of the sound-driven flexible wearable humidity sensor are respectively 40% and 90%. Fig. 5 (h) and 5 (i) show the response of the flexible wearable humidity sensor of the present utility model when the indoor natural relative humidity changes (24 hours), and the output of the flexible wearable humidity sensor of the present utility model is highly correlated with the relative humidity changes, confirming the feasibility of the sound-driven flexible wearable humidity sensor of the present utility model for practical application.
The circuit diagram of the system for detecting the urine wetness or the exhalation dehydration of the intelligent paper diaper is shown in fig. 6. The metal substrates of the flexible conductive layer 1 and the functional structural layer 4 are two electrodes of the flexible wearable humidity sensor of the present utility model connected with a circuit. The circuit can amplify the sensing signal, and the singlechip performs analog-to-digital conversion and analysis on the signal through the voltage converter, the shifter and the low-pass filter. Then the circuit can control the wireless transmitter to upload the detected sensing information, and the sensing result is displayed by utilizing the LED lamp of an external platform (analog mobile terminal). The example of the present utility model simply uses the LED lights on and off to reflect the results of humidity changes. However, it should be understood by those skilled in the art that the system may introduce a bluetooth module for efficient wireless transmission, and develop a corresponding mobile APP for practical application.
The sound-driven flexible wearable humidity sensor is placed on the absorption core layer of the paper diaper, and pure water is dropped on the paper diaper to simulate urination of infants or patients. Fig. 7 shows humidity sensing performance of three flexible wearable humidity sensor diapers integrated with PTFE/PANI/copper mesh structure. The output of the diaper 1 was reduced from 0.24 nanoamperes to 0.07 nanoamperes. The output of the diaper 2 is reduced from 0.51 nanoampere to 0.12 nanoampere. The output of the diaper 3 is reduced from 0.2 nanoampere to 0.02 nanoampere. When the microcontroller receives a urination sensing signal, the LED is turned on. These results demonstrate the feasibility of the flexible wearable humidity sensor of the present utility model for monitoring urination in infants, which simply illustrates the practical application of the system in urination monitoring and information uploading.
During exercise, especially after strenuous or long-term exercise, body heat can be discharged through perspiration and respiration, and serious dehydration of the body can cause dehydration of exercise and reduction of the relative humidity of exhaled air. After wearing the dehydration detection system of the flexible wearable humidity sensor based on sound driving, the sensing data of the athlete can be acquired in real time, and the athlete can feel without wireless transmission. When people before the motion, the gas relative humidity who exhales is higher, and the flexible wearable humidity transducer of sound drive passes through data processing circuit and is connected with wireless emission display module, and the LED lamp can not be lighted, and after the motion a period, the gas relative humidity who exhales reduces, and the LED lamp is lighted. The application of this example uses 8 LED lamps in a one-dimensional array, where the first green light indicates that a voltage signal is detected (the threshold can be adjusted for different subjects). The number of red LEDs that emit light depends on the magnitude of the output voltage signal. Two volunteers were taken as subjects and did not illuminate the LED lamp until they moved, even with sound (100 dB). After 1 hour of movement, 5 red LED lamps were lit under sound (100 dB) driving. The system may roughly display the dehydration status of the subject. Figure 8 shows the system's testing (humidity of exhaled air) on two subjects before and after exercise. The test time was 1 hour and the sound intensity was 100dB. Subject 1 (male) the exhaled air relative humidity was reduced from 95% to 81% before and after exercise, and the flexible wearable humidity sensor output voltage of the present utility model was increased from 22 millivolts to 53 millivolts. Subject 2 (female) exhaled air relative humidity decreased from 91% to 85% before and after exercise, and the flexible wearable humidity sensor output voltage of the present utility model increased from 21 millivolts to 53.8 millivolts. These results demonstrate the potential application of the wearable intelligent monitoring system of the sound-driven flexible wearable humidity sensor in analyzing respiration.
The data processing circuit is used for processing the electric signals and comprises a voltage conversion module, a measurement amplifying module, a level shift module and a low-pass filtering module. After the sensing signal passes through the processing circuit, an electric signal meeting preset conditions is generated, and the actual humidity sensing signal is identified. As a possible implementation manner, the signal processing circuit in the embodiment of the present utility model may implement conversion, amplification, noise reduction, and conditioning from a tiny electric signal to a voltage signal. Specifically, in the embodiment of the utility model, the electric signal which is highly related to the change of relative humidity and is generated when the friction surface rubs is processed.
The wireless emission display module comprises a microcontroller and an LED lamp array. The quantization accuracy of the signal is related to the microcontroller, and the sampling frequency of the signal is related to the performance of the microcontroller chip used by the wireless transmission display module. The selection of the chip includes, but is not limited to, any of the following series of single-chip microcomputer: nordic series, STM8 series, STM32 series, arduino series, ESP8266 series, ESP32 series, STC89C51/52 series, NXP K60 series, etc. It should be noted that, a person skilled in the art may select a suitable single chip according to the actual situation, and the LED display mode may fine-tune the circuit according to the need, which is not limited herein.
In summary, the utility model provides a flexible wearable humidity sensor driven by sound, which utilizes an electric signal generated by the triboelectric effect between materials under the driving of sound, and combines the humidity sensing characteristic of the materials to obtain a sensing signal highly related to relative humidity, so that the flexible wearable humidity sensor can work through sound without any external power supply. By constructing the sensing system, the urination of infants and patients can be detected and the dehydration of athletes or patients can be detected under the driving of sound.
Finally, it should be noted that: the foregoing description is only illustrative of the preferred embodiments of the present utility model, and although the present utility model has been described in detail with reference to the foregoing embodiments, it will be apparent to those skilled in the art that modifications may be made to the embodiments described, or equivalents may be substituted for elements thereof, and any modifications, equivalents, improvements or changes may be made without departing from the spirit and principles of the present utility model.
Claims (10)
1. The sound-driven flexible wearable humidity sensor is characterized by comprising a flexible conductive layer, a flexible dielectric layer, a flexible spacing layer and a functional structure layer which are overlapped in sequence; the functional structure layer comprises a metal substrate and a sensitive layer, the sensitive layer is arranged on the outer surface of the metal substrate facing the flexible spacing layer, the functional structure layer is provided with a through hole, and the through hole penetrates through the outer surface of the functional structure layer facing the flexible spacing layer and the outer surface of the functional structure layer opposite to the flexible spacing layer.
2. The sound driven flexible wearable humidity sensor of claim 1 wherein the flexible dielectric layer is a polyvinylidene fluoride film, a perfluoroethylene propylene film, a vinylidene chloride acrylonitrile copolymer film, a polytetrafluoroethylene film, a polyvinyl chloride film, or a polytrifluoroethylene film.
3. The acoustically driven flexible wearable humidity sensor of claim 1 wherein at least that outer surface of the flexible dielectric layer facing the flexible spacer layer is provided with nano-microstructures.
4. The acoustically driven flexible wearable humidity sensor of claim 1 wherein the metal substrate is a flexible metal mesh or a flexible metal foil.
5. The acoustically driven flexible wearable humidity sensor of claim 4 wherein the flexible metal mesh is a gold metal mesh, a silver metal mesh, a platinum metal mesh, a palladium metal mesh, a copper metal mesh, a titanium metal mesh, or a chromium metal mesh, or wherein the flexible metal mesh is an alloy metal mesh of a plurality of metals of gold, silver, platinum, palladium, copper, titanium, chromium.
6. The acoustically driven flexible wearable humidity sensor of claim 4 wherein the flexible metal foil is a gold metal foil, a silver metal foil, a platinum metal foil, a palladium metal foil, a copper metal foil, a titanium metal foil, or a chromium metal foil, or the flexible metal mesh is an alloy metal foil of a plurality of metals of gold, silver, platinum, palladium, copper, titanium, chromium.
7. The acoustically-driven flexible wearable humidity sensor of claim 1 wherein the sensitive layerIs ZnO nanowire, WO 3 Nanowires, snO 2 Nanowires, baTiO 3 Film, znWO 4 Nanowires, znSnO 3 The nano-wire, the element doped ZnO nano-wire, the graphene film layer with the surface modified by functionalization, and the carbon nano-tube or polyaniline film layer with the surface modified by functionalization.
8. The acoustically driven flexible wearable humidity sensor of claim 1 wherein the flexible spacer layer is a flexible insulating layer.
9. The sound driven flexible wearable humidity sensor of claim 1 wherein the flexible conductive layer is a gold metal layer, a silver metal layer, a platinum metal layer, a palladium metal layer, a copper metal layer, a titanium metal layer, or a chromium metal layer or the flexible conductive layer is a conductive film.
10. The utility model provides a system for intelligent panty-shape diapers urine wet detection or exhale dehydration detection which characterized in that includes:
the flexible wearable humidity sensor of any one of claims 1 to 9 for converting the relative humidity of a diaper or an exhalation into an electrical signal under sound drive;
a data processing circuit for amplifying, voltage converting, level shifting and low pass filtering the electrical signal;
and the wireless emission display module is used for converting the electric signals subjected to amplification, voltage conversion, level shift and low-pass filtering into relative humidity signals of paper diapers or human exhalations and displaying the relative humidity signals.
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| CN202222903856.2U CN219206933U (en) | 2022-11-02 | 2022-11-02 | Humidity sensor and system for detecting urine humidity or detecting dehydration of exhale of intelligent paper diaper |
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