Drawer-type anti-interference human expiration pH and acetone concentration detection device

Abstract

The invention discloses a drawer type anti-interference human exhaled gas pH and acetone concentration detection device which comprises a shell, a driving rotor, a follow-up rotor, a flexible friction film piece, a first stator disc and a second stator disc. The first stator disc and the second stator disc can be inserted into a first slot and a second slot on the shell; a plurality of mutually independent flexible friction thin film sheets are fixedly arranged on the follow-up rotor to form a fan-shaped structure; after the first stator disc or the second stator disc is inserted into the first slot, the rotor is driven to rotate under the expiration action of a human body, so that the fan-shaped structure periodically drives the acetone sensitive film and the first electrode to be in contact and separated, inductive charges are generated, and electric signals are output through the first electrode and the second electrode; or the fan-shaped structure periodically drives the PH sensitive film and the third electrode to be contacted and separated so as to output an electric signal. According to the invention, the initial detection of the pH value and the acetone concentration of the expired gas of the human body can be simply and conveniently realized, and the method can be used for the initial monitoring of ketoacidosis.

Description

Technical Field

[0001] The present invention relates to the technical field of health monitoring, and in particular to a drawer-type anti-interference human breath pH and acetone concentration detection device. Background Art

[0002] Ketoacidosis is a dangerous condition caused by the accumulation of acidic substances in the body, and its main symptoms are shortness of breath, nausea and vomiting, and even coma. This disease is common in diabetic patients when their blood sugar is out of control, and it may also occur in people who have been on an excessive diet for a long time. Under normal circumstances, the human body mainly relies on breaking down sugar for energy. However, when the body cannot effectively use sugar or when sugar intake is too low, it will break down fat for energy. This process produces byproducts called "ketone bodies". Small amounts of ketone bodies can be naturally metabolized by the body, but if the production rate exceeds the processing capacity, it will make the blood acidic like garbage accumulation, causing poisoning.

[0003] Existing medical diagnosis is mainly based on three key indicators: elevated blood sugar, accumulation of acidic substances in the blood, and excessive ketone bodies in the body. However, these methods are suitable for laboratory or hospital examinations and rely on analytical instruments such as gas chromatography-mass spectrometry and selective ion flow tube mass spectrometry. They cannot be widely used in daily personal metabolic health monitoring, which is not conducive to patients' prevention, management and preliminary diagnosis of diseases.

[0004] Therefore, it is necessary to design a simple and convenient detection device for preliminary monitoring of ketoacidosis. Summary of the Invention

[0005] The present invention provides a drawer-type anti-interference human breath pH and acetone concentration detection device to solve the above technical problems.

[0006] In order to achieve the above object, the technical solution of the present invention is:

[0007] A drawer-type, anti-interference human breath pH and acetone concentration detection device comprises: a housing, a driving rotor rotatably mounted on the housing, a follower rotor driven and rotated synchronously by the driving rotor, a flexible friction film, a first stator disc, and a second stator disc; the housing is provided with a first slot and a second slot, each of which is insertable into the first slot and the second slot; a plurality of independent flexible friction films are fixed to the follower rotor to form a fan-shaped structure;

[0008] The first stator disk includes: a first mounting plate, a first electrode, a second electrode and an acetone-sensitive film, wherein the first electrode and the second electrode are independent of each other and are arranged on the first mounting plate, the shape and size of the second electrode match the shape and size of the fan-shaped structure, and the acetone-sensitive film is attached to the second electrode;

[0009] The second stator disk includes: a second mounting plate, a third electrode, a fourth electrode and a pH sensitive film. The third electrode and the fourth electrode are independent of each other and are arranged on the second mounting plate. The shape and size of the fourth electrode match the shape and size of the fan-shaped structure. The pH sensitive film is attached to the fourth electrode.

[0010] When the first stator disk or the second stator disk is inserted into the first slot, the driving rotor rotates under the action of human exhalation, so that the fan-shaped structure periodically drives the acetone-sensitive film to contact and separate with the first electrode, thereby generating induced charges and outputting electrical signals through the first electrode and the second electrode; or, the fan-shaped structure periodically drives the pH-sensitive film to contact and separate with the third electrode, thereby generating induced charges and outputting electrical signals through the third electrode and the fourth electrode.

[0011] Preferably, the first stator disk further comprises a first stator disc fixedly mounted on the first mounting plate, the first stator disc being divided into an inner and outer section by a first flower-shaped groove, the first electrode and the second electrode being disposed in the inner and outer sections respectively, and the first and second electrodes being alternately disposed; all the first electrodes being connected to form a first output end, and all the second electrodes being connected to form a second output end;

[0012] The second stator disk also includes a second stator disc fixed on the second mounting plate, and the second stator disc is divided into two inner and outer sections by a second flower-shaped groove. A third electrode and a fourth electrode are respectively arranged in the inner and outer sections, and the third electrodes and the fourth electrodes are arranged alternately; all the third electrodes are connected to serve as a third output end, and all the fourth electrodes are connected to serve as a fourth output end.

[0013] Preferably, the shell is also provided with an air inlet, a support frame is fixed at the air inlet, and a rotating shaft is rotatably provided on the support frame; a follower rotor is provided at one end of the rotating shaft extending into the shell, and a driving rotor is provided at the other end extending out of the shell.

[0014] Preferably, the driving rotor includes a central axis and a plurality of fan blades arranged around the central axis, the fan blades including a fan-facing surface, the fan-facing surface facing the exhaled air of the human body to generate torque;

[0015] The fan blade includes a fan blade body, which is enclosed in a tubular or arc shape. The center line of the fan blade body is a spiral line around the central axis, and the inner wall of the fan blade body is the fan-facing surface.

[0016] Preferably, the acetone-sensitive film is a SWCNTs-CTS-ZnO film, and the preparation method of the SWCNTs-CTS-ZnO film comprises the following steps:

[0017] S1: mixing a zinc source and a dopant, adding a chitosan solution and a carbon nanotube dispersion, stirring to form a mixed solution, and performing a hydrothermal reaction. After the hydrothermal reaction is completed, cooling and washing to obtain a nanomaterial doped with carbon nanotubes, which is then dispersed in deionized water to form a suspension;

[0018] S2: The suspension is coated on a PET substrate, and after drying and annealing, a SWCNTs-CTS-ZnO thin film is obtained.

[0019] Preferably, the zinc source is zinc acetate solution, and the concentration of the zinc acetate solution is 0.03 g / mL;

[0020] The concentration of the carbon nanotube dispersion was 100 mg / mL;

[0021] The concentration of chitosan solution was 4 mg / mL;

[0022] The doping agent is sodium nitrate solution, and the concentration of the sodium nitrate solution is 0.5 mol / L;

[0023] In S1, the volume ratio of zinc acetate solution to chitosan solution, dopant, and carbon nanotube dispersion is 50:1:10:20.

[0024] Preferably, the chitosan solution is prepared by dissolving 2 g of chitosan in 80 ml of a 1% acetic acid aqueous solution, heating to 60° C. and stirring continuously for 2 hours until the solution becomes clear and transparent, thereby completing the preparation of the chitosan solution;

[0025] The specific method for preparing the carbon nanotube dispersion is as follows: adding single-walled carbon nanotubes into deionized water, and ultrasonically treating the water for 2-3 hours to disperse the carbon nanotubes to form a carbon nanotube dispersion with a concentration of 100 mg / mL.

[0026] Preferably, the pH sensitive film is a SWCNTs-PDMS-ZnO film, and the preparation method of the SWCNTs-PDMS-ZnO film comprises the following steps:

[0027] S1: Dissolve ZnAc2·2H2O in deionized water, stir, add NaOH solution, transfer the mixed solution to a beaker, and perform a hydrothermal reaction; after the solution is cooled to room temperature, centrifuge, wash, and dry the product to obtain rod-shaped ZnO, and add ultrapure water to prepare a ZnO aqueous solution for later use;

[0028] S2: Mixing single-walled carbon nanotubes (SWCNTs) with a ZnO aqueous solution and ultrasonically treating the mixture to form a uniform suspension, which serves as a precursor solution.

[0029] The precursor solution is added to a mold containing PDMS, heated and cured to form a thin film, the film is peeled off from the mold, and then the film is pre-cured, sintered, and dried to obtain a SWCNTs-PDMS-ZnO film.

[0030] Preferably, the concentration of the ZnO aqueous solution is 2 mg / mL; the mass ratio of SWCNTs to rod-shaped ZnO is 25:1; and the molar ratio of ZnAc2·2H2O to NaOH is 1:8-9.

[0031] Preferably, in S2, the specific steps of pre-curing, sintering and drying the film are: the film is first pre-cured at 200°C for 10 minutes, and then sintered at 270°C for 60 minutes; after sintering, the film is placed in a vacuum drying oven at 70°C for 60 minutes.

[0032] Beneficial effects:

[0033] The present application discloses a drawer-type, anti-interference human exhaled breath pH and acetone concentration detection device. A follower rotor is provided to drive a flexible friction film to interact with a first stator disk or a second stator disk inserted into a first slot, thereby achieving triboelectric charging between the flexible friction film and the acetone-sensitive film, or between the flexible friction film and the pH-sensitive film. The sensitivity of the acetone-sensitive film and the pH-sensitive film to acetone concentration and pH affects the output of electrical signals, thereby enabling simple and convenient preliminary detection of both human exhaled breath pH and acetone concentration, and can be used for preliminary monitoring of ketoacidosis. BRIEF DESCRIPTION OF THE DRAWINGS

[0034] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following is a brief introduction to the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative labor.

[0035] Figure 1 This is a structural schematic diagram of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 1 of the present invention;

[0036] Figure 2 This is a top view of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 1 of the present invention;

[0037] Figure 3 This is a front view of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 1 of the present invention;

[0038] Figure 4 for Figure 3Cross-sectional view of AA;

[0039] Figure 5 This is a schematic structural diagram of a drive rotor of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 1 of the present invention;

[0040] Figure 6 A top view of the driving rotor of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 1 of the present invention;

[0041] Figure 7 This is a structural schematic diagram of a follower rotor of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 1 of the present invention;

[0042] Figure 8 This is a schematic diagram showing the principle of the follower rotor driving the flexible friction diaphragm in a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 1 of the present invention;

[0043] Figure 9 This is a diagram showing the mechanism of action of the acetone-sensitive film disclosed in the present invention;

[0044] Figure 10 Graph showing the output voltage test results of the SWCNTs-CTS-ZnO thin films prepared in Example 2 of the present invention and the comparative group;

[0045] Figure 11 Graph showing the output voltage test results of the SWCNTs-PDMS-ZnO films prepared in Example 3 of the present invention and the comparative group;

[0046] Figure 12 This is a test graph of the output voltage of a drawer-type anti-interference human breath pH and acetone concentration detection device under different acetone concentrations disclosed in Example 4 of the present invention;

[0047] Figure 13 This is a test graph showing the relationship between the output voltage and respiratory rate of a drawer-type anti-interference human exhaled breath pH and acetone concentration detection device disclosed in Example 4 when detecting acetone;

[0048] Figure 14 This is a test chart showing the response of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 4 to 10 ppm acetone and other interfering biomarkers;

[0049] Figure 15 This is a graph comparing the output voltages of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 4 for normal breath and simulated gas after stabilization when detecting acetone;

[0050] Figure 16This is a graph comparing the output currents of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 4 at different pH values;

[0051] Figure 17 This is a graph comparing the output voltages of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 4 at different pH values;

[0052] Figure 18 This is a test diagram of the relationship between the response time and recovery time of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 4;

[0053] Figure 19 This is a durability test diagram of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 4;

[0054] Figure 20 Schematic diagram of the preparation of a thermoelectric power generation sheet of a thermoelectric power generation unit of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 1;

[0055] Figure 21 This is a schematic structural diagram of the thermoelectric power generation chip of the thermoelectric power generation unit of a drawer-type anti-interference human breath pH and acetone concentration detection device disclosed in Example 1.

[0056] 1. Housing; 11. First slot; 12. Second slot; 13. Air inlet; 14. Support frame; 15. Rotating shaft;

[0057] 2. Driving rotor; 21. Central axis; 22. Fan blades; 221. Fan blade body; 222. Fan facing surface;

[0058] 3. Follower rotor; 31. Central connecting shaft; 32. Paddle shaft;

[0059] 4. Flexible friction film;

[0060] 5. First stator disc; 51. First mounting plate; 52. First electrode; 53. Second electrode; 54. Acetone sensitive film; 55. First stator disc;

[0061] 6. Second stator disc; 61. Second mounting plate; 62. Third electrode; 63. Fourth electrode; 64. pH sensitive film; 65. Second stator disc;

[0062] 7. Thermoelectric power generation unit; 71. Cold end substrate; 72. Hot end substrate; 73. N-type semiconductor; 74. P-type semiconductor; 75. PI / Cu substrate. DETAILED DESCRIPTION

[0063] To make the objectives, technical solutions, and advantages of the embodiments of the present invention more clear, the technical solutions in the embodiments of the present invention will be clearly and completely described below in conjunction with the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. All other embodiments obtained by ordinary technicians in this field based on the embodiments of the present invention without making any creative efforts shall fall within the scope of protection of the present invention.

[0064] Example 1

[0065] A drawer-type anti-interference human breath pH and acetone concentration detection device, combined with Figures 1-8 As shown, it includes: a housing 1, a driving rotor 2 rotatably mounted on the housing 1, a follower rotor 3 driven by the driving rotor 2 to rotate synchronously, a flexible friction film 4, a first stator disc 5, and a second stator disc 6; the housing 1 is provided with a first slot 11 and a second slot 12, and the first stator disc 5 and the second stator disc 6 can both be inserted into the first slot 11 and the second slot 12; a plurality of independent flexible friction films 4 are fixed on the follower rotor 3 to form a fan-shaped structure;

[0066] The first stator disc 5 includes a first mounting plate 51, a first electrode 52, a second electrode 53, and an acetone-sensitive film 54. The first electrode 52 and the second electrode 53 are independent of each other and are arranged on the first mounting plate 51. The shape and size of the second electrode 53 match those of the fan-shaped structure. The acetone-sensitive film 54 is attached to the second electrode 53.

[0067] The second stator disc 6 includes a second mounting plate 61, a third electrode 62, a fourth electrode 63, and a pH-sensitive film 64. The third electrode 62 and the fourth electrode 63, which are independent of each other, are arranged on the second mounting plate 61. The shape and size of the fourth electrode 63 match those of the fan-shaped structure. The pH-sensitive film 64 is attached to the fourth electrode 63.

[0068] When the first stator disk 5 or the second stator disk 6 is inserted into the first slot 11, the driving rotor 2 rotates under the action of human exhalation, so that the fan-shaped structure periodically drives the acetone-sensitive film 54 and the first electrode 52 to contact and separate, thereby generating induced charges and outputting electrical signals through the first electrode 52 and the second electrode 53; or, the fan-shaped structure periodically drives the pH-sensitive film 64 and the third electrode 62 to contact and separate, thereby generating induced charges and outputting electrical signals through the third electrode 62 and the fourth electrode 63.

[0069] Patients with ketoacidosis experience decreased carbon dioxide binding capacity and pH in their blood, a decrease in excess base levels, and a significant increase in the anion gap. Ketones, similar to a rotten apple, can also be present in their breath. In more severe cases, Kussmaul respirations may occur, characterized by labored, deep, and rapid breathing. Deep, full breaths expel carbon dioxide and alleviate acidosis, which in turn leads to changes in exhaled pH. Therefore, monitoring exhaled pH and acetone concentrations allows for personalized, simple, and convenient initial monitoring.

[0070] The present application drives the rotor 2 to rotate under the action of human exhalation, thereby driving the follower rotor 3 to rotate synchronously. The follower rotor 3 drives the flexible friction film 4 to interact with the first stator disk 5 or the second stator disk 6 inserted into the first slot 11, thereby realizing friction electrification between the flexible friction film 4 and the acetone sensitive film 54, or friction electrification between the flexible friction film 4 and the pH sensitive film 64; after the first stator disk 5 is inserted into the first slot 11, the acetone sensitive film 54 is sensitive to the acetone concentration, thereby affecting the output value of the electrical signal, thereby simply and conveniently realizing preliminary detection of the acetone concentration in human exhalation; after the second stator disk 6 is inserted into the first slot 11, the pH sensitive film 64 is sensitive to pH, thereby affecting the output value of the electrical signal, thereby simply and conveniently realizing preliminary monitoring of the pH of human exhalation; finally, preliminary detection of both the pH and acetone concentration of human exhalation is realized, which can be used for preliminary monitoring of ketoacidosis and long-term health management.

[0071] Specifically, the system also includes a signal processing module that transmits the detected electrical signals to the signal processing module, which stores and processes the data to provide indicative indicators related to pathological characteristics. During the test, breathing is required to be stable and a certain exhalation time is limited. Multiple measurements are then performed to avoid measurement errors caused by exhalation differences and single measurements.

[0072] Preferably, the first stator disc 5 further includes a first stator disc 55 fixed on the first mounting plate 51. The first stator disc 55 is divided into two inner and outer sections by a first flower-shaped groove. First electrodes 52 and second electrodes 53 are respectively provided in the inner and outer sections, and the first electrodes 52 and second electrodes 53 are alternately provided. All the first electrodes 52 are connected to form a first output end, and all the second electrodes 53 are connected to form a second output end.

[0073] The second stator disk 6 also includes a second stator disc 65 fixed on the second mounting plate 61. The second stator disc 65 is divided into two inner and outer sections by a second flower-shaped groove. A third electrode 62 and a fourth electrode 63 are respectively provided in the inner and outer sections, and the third electrodes 62 and the fourth electrodes 63 are alternately provided. All the third electrodes 62 are connected to form a third output end, and all the fourth electrodes 63 are connected to form a fourth output end.

[0074] The first electrodes 52 and the second electrodes 53 are alternately arranged, and the third electrodes 62 and the fourth electrodes 63 are alternately arranged. Electric energy is generated by the approach-separation cycle friction during the rotation process, and then an electric signal is output.

[0075] Specifically, the driving rotor 2 and the follower rotor 3 are both made of lightweight insulating materials, such as plastic, to ensure that the driving rotor 2 rotates smoothly under the action of human exhalation. The first electrode 52 and the second electrode 53, the third electrode 62 and the fourth electrode 63 are all made of the same conductive material, such as copper, to utilize their conductive properties to achieve electrical signal output; the acetone-sensitive film 54 is affected by acetone and its ability to gain and lose electrons changes, and the pH-sensitive film 64 is affected by pH and its ability to gain and lose electrons changes, so as to obtain different electrical signals according to the acetone concentration and pH value, and achieve preliminary detection. The mechanism by which the acetone-sensitive film 54 is affected by acetone is as follows: Figure 9 shown.

[0076] Specifically, the first electrode 52 and the second electrode 53, the third electrode 62 and the fourth electrode 63 all include multiple fan-shaped petals, so as to form a ring-shaped alternating structure, which can maximize the area involved in friction while ensuring mutual independence and is conducive to coating.

[0077] Preferably, the housing 1 is further provided with an air inlet 13, a support frame 14 is fixedly provided at the air inlet 13, and a rotating shaft 15 is rotatably provided on the support frame 14; the end of the rotating shaft 15 extending into the housing 1 is provided with a follower rotor 3, and the end extending out of the housing 1 is provided with a driving rotor 2.

[0078] Specifically, the housing 1 is a square box-shaped structure, with an upper opening serving as an air inlet 13 for exhalation. Two sets of rectangular openings are located near the bottom on either side. The upper set of opposing rectangular openings serves as a first slot 11, while the lower set serves as a second slot 12, facilitating replacement and maintenance. To test a specific item, the corresponding drawer-shaped first or second stator disc 5 6 is inserted into the first slot 11. For example, to detect acetone concentration in exhaled breath, the first stator disc 5 is inserted into the first slot 11, and the flexible friction film 4 rubs against the acetone-sensitive film 54 and the second electrode 53 during rotation.

[0079] Specifically, support frame 14 is shaped like a cross, meter, or X, ensuring proper gas flow and the proper installation of shaft 15. Shaft 15 is mounted at the center of support frame 14 via bearings and flanges. Rotation of the driving rotor 2 drives shaft 15, which in turn drives the follower rotor 3. Furthermore, shaft 15 maintains the axial position of the follower rotor 3, ensuring contact between the flexible friction diaphragm 4 and the first or second stator disc 5, 6.

[0080] Preferably, the driving rotor 2 includes a central axis 21 and a plurality of blades 22 arranged around the central axis 21, the blades 22 including a wind-facing air surface 222, and the wind-facing air surface 222 faces the exhalation of the human body to generate torque. The blades 22 include a blade body 221, the blade body 221 is enclosed in a tubular or arc shape, the center line of the blade body 221 is a spiral line around the axis of the central axis 21, and the inner wall of the blade body 221 is the wind-facing air surface 222. The dimension of the center line of the blade body 221 along the axial direction of the central axis 21 is less than one-fourth of the pitch of the spiral line. The structure of the driving rotor 2 of the present application can increase the windward area, achieve lightweight while ensuring the torque, and facilitate the airflow to fill the inner cavity of the shell 1 and avoid safety hazards such as scratches.

[0081] Preferably, the blade body 221 is arc-shaped, with one end of the blade body 221 fixed to the periphery of the central axis 21 and the other end fixed to the outer wall of another blade 22, which is beneficial for reducing size and weight while ensuring an aerodynamic shape.

[0082] Preferably, the follower rotor 3 includes a central connecting shaft 31 and a plurality of paddles 32 arranged around the central connecting shaft 31. The plurality of flexible friction films 4 correspond one-to-one with the plurality of paddles 32. The flexible friction film 4 is strip-shaped, with one end adhered to the lower surface of the paddle 32 and the other end drooping downward to form a free end for friction with the first stator disc 5 or the second stator disc 6. While ensuring normal power generation, this effectively reduces friction and wear on friction components, thereby increasing the service life of the device. The flexible friction film 4 is made of FEP film, which is at the most negative end of the triboelectric series and easily steals electrons from other materials. Upon contact, the surface becomes strongly negatively charged, and the film exhibits strong charge storage capacity and wear resistance.

[0083] Preferably, a thermoelectric power generation unit 7 is further provided on the outer wall of the housing 1, which uses the electrical energy generated by the temperature difference between the body surface temperature and the internal temperature of the device to power the signal processing module, thereby realizing a detection method without the need for an external power supply.

[0084] Specifically, combined Figure 1 、 Figure 20 and Figure 21 As shown, the thermoelectric power generation unit 7 includes: a thermoelectric power generation sheet and a contact button. The structure of the thermoelectric power generation sheet is as follows: Figure 21 As shown, it includes a cold end substrate 71 and a hot end substrate 72. A number of N-type semiconductors 73 and P-type semiconductors 74 are arranged between the cold end substrate 71 and the hot end substrate 72. The N-type semiconductors 73 and the P-type semiconductors 74 are electrically connected through a PI / Cu substrate 75. The cold end substrate 71 is connected to a contact button. When the human body touches the contact button to transfer heat, a heat difference is generated between the cold end substrate 71 and the hot end substrate 72, thereby generating electricity, which is then transmitted through wires for power supply.

[0085] Specifically, to prepare the thermoelectric power generation material, 1g of bisphenol F epoxy resin, 0.85g of methylhexahydrophthalic anhydride, 0.2g of 1-(2-cyanoethyl)-2-ethyl-4-methylimidazole (including the 5-methyl isomer), 0.1g of butyl glycidyl ether, and 0.1g of toluene were weighed separately and then thoroughly stirred to mix the liquid solutions. 8-12g of P-type or N-type BiTe3 were then added to the solutions, respectively, and finally stirred thoroughly to form P-type and N-type BiTe slurries.

[0086] Then, using adhesive dispensing equipment, N-type and P-type BinTe slurries were sequentially deposited onto a PI / Cu substrate until several pairs of P-type and N-type BizTe thermoelectric legs were obtained. The spacing between the P-type BizTe and N-type BiTe was 2.5 mm. The flexible thermoelectric film was pre-cured by heating at 493 K and then sintered in a muffle furnace at 498 K for 40 minutes. Finally, copper wires were soldered to both ends of the device, and a thermally conductive metal was poured over the device. After waiting for 60 minutes of natural curing, the MTEG was prepared.

[0087] Example 2

[0088] The difference between this embodiment and embodiment 1 is that the acetone sensitive film 54 is a SWCNTs-CTS-ZnO film. The preparation method of the SWCNTs-CTS-ZnO film includes the following steps:

[0089] S1: Using zinc acetate (Zn(CH3COO)2·2H2O) as a Zn source, weighing 1.5g of zinc acetate and dissolving it in 50ml of deionized water, stirring it with a magnetic stirrer for 30 minutes to ensure complete dissolution, forming a zinc acetate solution with a concentration of 0.03g / mL; weighing 2g of chitosan (deacetylation degree greater than 90%), dissolving it in 50ml of 1% acetic acid aqueous solution, heating it to 60°C and stirring it continuously for 2 hours until the solution is clear and transparent, to prepare a chitosan solution with a concentration of 4mg / mL; selecting a sodium nitrate (NaNO3) solution with a concentration of 0.5mol / L as a dopant, measuring 10ml for standby use; weighing 10g of single-walled carbon nanotubes (SWCNTs), adding it to 100ml of deionized water, and ultrasonically treating it for 2-3 hours to uniformly disperse it to form a carbon nanotube dispersion with a concentration of 100mg / mL, which is standby use;

[0090] A PET substrate with a size of 5 cm × 5 cm was cut and ultrasonically cleaned with deionized water and ethanol, respectively. It was then dried on a hot plate at 80°C for 20 minutes. To enhance the adhesion between the film and the substrate, it was treated with ultraviolet ozone (UVO) for 10 minutes and then used.

[0091] The prepared zinc source zinc acetate solution and the dopant sodium nitrate solution were mixed, and then 1 ml of the CTS solution was added, and then 20 ml of the carbon nanotube dispersion was added. The mixture was fully stirred to obtain a mixed solution, and the mixed solution was transferred to a polytetrafluoroethylene (PTFE)-lined autoclave and subjected to a hydrothermal reaction at 200° C. for 12 hours. After the hydrothermal reaction was completed and cooled to room temperature, the mixture was centrifuged and washed three times with deionized water and ethanol to obtain a CTS-ZnO nanomaterial doped with carbon nanotubes, which was then uniformly dispersed in 10 ml of deionized water to prepare a suspension.

[0092] S2: On the pretreated PET substrate, a dispensing machine is used to dispense glue layer by layer: First, 5 ml of the suspension is evenly applied on the pretreated PET substrate to form a first sensitive layer with a thickness of about 5 μm. After natural drying for 10 minutes, the second sensitive layer is applied. The above operation is repeated until a multi-layer sensitive layer (film) with a total thickness of about 20 μm is formed; the film is placed in a vacuum drying oven and dried at 60°C and a vacuum degree of 0.08 MPa for 6 hours to remove residual solvent and prevent the film from cracking; then, The film was placed in a tube furnace for annealing treatment, heated to 300°C and maintained for 2 hours. The heating rate was controlled at 5°C / min to enhance the crystallinity of the ZnO nanostructure and the overall stability of the film, while optimizing the interaction between chitosan, carbon nanotubes and ZnO. After the annealing was completed, it was removed from the tube furnace and cooled at room temperature. Finally, the film was peeled off from the PET substrate on an ultra-clean workbench, and the single-walled carbon nanotube-doped CTS-ZnO sensitive film was completed, that is, the SWCNTs-CTS-ZnO film was obtained.

[0093] Single-walled carbon nanotubes (SWCNTs) have a high specific surface area and excellent conductivity, providing abundant adsorption sites for acetone molecules and amplifying the weak signal caused by acetone adsorption. Chitosan (CTS) is a natural polymer material that can enhance the selective adsorption of acetone through intermolecular interactions and reduce interference from other gases in exhaled breath. The gas-sensitive properties of ZnO semiconductors further enhance the film's sensitivity and response speed to acetone. Through the redox reaction between surface oxygen species and acetone molecules, the material's carrier concentration is rapidly changed, achieving a rapid response to changes in acetone concentration.

[0094] In order to explore the optimal dosage of CTS solution, the following control experiment was set up:

[0095] Control group 1:

[0096] The difference between this control group and the example group (Example 2) is that in this control group, the amount of CTS solution added is 5 ml.

[0097] Control group 2:

[0098] The difference between this control group and the example group (Example 2) is that in this control group, the amount of CTS solution added is 0.2 ml.

[0099] The output voltage of the SWCNTs-CTS-ZnO thin film materials prepared in the embodiment group (Example 2) and the control groups 1 and 2 was tested under different humidity conditions. The results are as follows: Figure 10 As shown, in order to facilitate the comparison between Example 2 and the control group, the output voltage test results of the SWCNTs-CTS-ZnO thin film materials prepared in Example 2, Control Group 1, and Control Group 2 under different humidity conditions are integrated into one figure, corresponding to the conditions of 0% RH, 20% RH, 40% RH, 60% RH, and 80% RH, respectively. Figure 10 It can be seen that the CTS material selection ratio in Example 2 shows the highest output performance in the experiment. Therefore, this amount can achieve the best balance between film structure stability and gas-sensitive response efficiency, that is, this ratio is selected as the final preparation ratio; the excessive amount of CTS in Control Group 1 will destroy the SWCNTs conductive path and hinder the diffusion of acetone gas, resulting in a decrease in the response amplitude, so its voltage test result is significantly lower than that of Example 2; and the insufficient amount of CTS in Control Group 2 cannot effectively cover the SWCNTs-ZnO interface, and the sensitive interface is prone to failure, resulting in poor structural stability, and ultimately causing the output voltage test to be significantly lower than that of Example 2.

[0100] Example 3

[0101] The difference between this embodiment and embodiment 1 is that the pH sensitive film 64 adopts a SWCNTs-PDMS-ZnO film. The preparation method of the SWCNTs-PDMS-ZnO film includes the following steps:

[0102] S1: First, 1 g of ZnAc2·2H2O was dissolved in 50 mL of deionized water and stirred with a magnetic stirrer for 20 minutes. Subsequently, 20 mL of a 2 M NaOH aqueous solution (the molar ratio of ZnAc2·2H2O to NaOH was 1:8.8) was added to the solution and stirred for 20 minutes. The mixed solution was then transferred to a beaker with a PTFE liner and placed in an autoclave for a hydrothermal reaction at 220°C for 15 hours. After the solution was cooled to room temperature, the product was centrifuged and washed several times with ethanol and deionized water. Finally, the product was dried in a vacuum drying oven at 80°C to obtain rod-shaped ZnO. The rod-shaped ZnO was added to ultrapure water and mixed to prepare a ZnO aqueous solution with a concentration of 2 mg / mL for later use.

[0103] S2: 5 g of single-walled carbon nanotubes (SWCNTs) were mixed with 100 mL of a 2 mg / mL ZnO aqueous solution (the mass ratio of SWCNTs to rod-shaped ZnO was 25:1) and ultrasonicated for 1 hour to prepare a homogeneous suspension as the precursor solution;

[0104] The precursor solution was added to a mold filled with uncured PDMS, and after thorough stirring, the mold was placed on a constant temperature heating table and heated at 70°C for 2 hours. After the solution solidified, a thin film was formed. The film was peeled off on a clean workbench and then placed in a muffle furnace. It was pre-cured at 200°C for 10 minutes and then sintered at 270°C for 60 minutes. After sintering, the film was placed in a vacuum drying oven and dried at 70°C for 60 minutes to prepare a SWCNTs-PDMS-ZnO film.

[0105] As a semiconductor metal oxide, ZnO has a large number of hydroxyl groups on its surface, which can react reversibly with acidic / alkaline gases in exhaled breath, resulting in changes in surface charge density. When the pH value of exhaled breath changes, the adsorption / desorption of ions on the ZnO surface will change its carrier concentration (such as electrons or holes), thereby affecting its conductivity, thereby achieving a sensitive response to pH value. Single-walled carbon nanotubes SWCNTs have excellent conductivity and high specific surface area. When compounded with ZnO, they can accelerate electron transport, amplify the electrical signals caused by pH changes, and improve the sensitivity of thin film materials to pH.

[0106] In order to explore the optimal dosage ratio of single-walled carbon nanotubes (SWCNTs) and ZnO, the following control experiment was set up:

[0107] Control group 1:

[0108] The only difference between this control group and the above preparation steps is that in this control group, 1 g of single-walled carbon nanotubes (SWCNTs) was mixed with 100 mL of a 2 mg / mL ZnO aqueous solution (the mass ratio of SWCNTs to rod-shaped ZnO was 5:1) to prepare a precursor solution, and the SWCNTs-PDMS-ZnO thin film material was prepared.

[0109] Control group 2:

[0110] The only difference between this control group and the above preparation steps is that in this control group, 10 g of single-walled carbon nanotubes (SWCNTs) were mixed with 100 mL of a 2 mg / mL ZnO aqueous solution (the mass ratio of SWCNTs to rod-shaped ZnO was 50:1) to prepare a precursor solution, and the SWCNTs-PDMS-ZnO thin film material was prepared.

[0111] The output voltage of the SWCNTs-PDMS-ZnO thin film materials prepared in the embodiment group (Example 3) and the control groups 1 and 2 was tested. The results are as follows: Figure 11 As shown, in order to facilitate the comparison between Example 3 and the control group, the output voltage test results of the SWCNTs-PDMS-ZnO thin film materials prepared in Example 3, Control Group 1, and Control Group 2 are integrated into one figure, and the test acquisition time of the three is equal. Figure 11 It can be seen that compared with controls 1-2, the material in Example 3 showed the highest output performance in the experiment. This is attributed to the maximization of the synergistic effect achieved by the appropriate ratio of single-walled carbon nanotubes (SWCNTs) and ZnO. In control group 1, the amount of SWCNTs was too small, resulting in blocked electron transport and insufficient modification of the ZnO surface, which weakened the charge transfer efficiency. In control group 2, the amount of SWCNTs was too high, and the excess carbon nanotubes agglomerated, which not only destroyed the uniformity of the film but also occupied the reaction sites between ZnO and gas molecules, increased gas diffusion resistance, and caused a decrease in response sensitivity. The appropriate amount of SWCNTs in Example 3 not only ensured the continuity of the conductive path inside the film, but also enhanced the adsorption activity of ZnO for pH-sensitive gases through surface modification, while avoiding structural defects caused by material accumulation, thereby achieving a significant increase in output voltage.

[0112] Example 4

[0113] In this embodiment, the acetone sensitive film 54 adopts the SWCNTs-CTS-ZnO film in Example 2, and the pH sensitive film 64 adopts the SWCNTs-PDMS-ZnO film in Example 3.

[0114] In order to better illustrate the technical effect of this embodiment, a performance test was conducted on the detection device for thin film preparation in Example 4.

[0115] When detecting acetone:

[0116] (1) Comparison of voltage of the detection device at different acetone concentrations

[0117] Test method:

[0118] Connect the flow meter outlet and the air inlet of the detection device through a sealed pipe to ensure that there is no leakage in the air line. You can use soapy water to smear the interface to check the air tightness.

[0119] Blank experiment: First, introduce high-purity nitrogen and record the baseline current value of the detection device. Continue to ventilate for 10 minutes to ensure that the residual impurities in the device are completely purged. After the baseline current stabilizes, record the data.

[0120] Concentration test: Adjust the flow meter in sequence and pass acetone-nitrogen mixed gas of different concentrations into the detection device at a constant flow rate of 0.5L / min. Each concentration gas is ventilated continuously for 5 minutes. After the current value stabilizes, record the current data every 30 seconds. Repeat the measurement for each concentration 3 times.

[0121] Concentration switching: When switching between gases of different concentrations, first introduce high-purity nitrogen to purge the detection device for 3 minutes. After the current returns to the baseline level, introduce the next concentration of mixed gas.

[0122] Results: As Figure 12 To facilitate comparison of the overall output voltage trends at different acetone concentrations, the test results for air and a 2-10 ppm acetone gas mixture are combined into a single graph, with equal acquisition time for each test. Within the 2-10 ppm acetone concentration range, the sensor's output voltage increases monotonically with increasing concentration, demonstrating excellent linear response within this concentration range.

[0123] (2) Relationship between the output voltage of the detection device and the respiratory rate

[0124] Test method:

[0125] Basic data collection: At a respiratory rate of 15 breaths / minute (normal resting frequency), introduce 200 ppm acetone gas. After the voltage signal stabilizes, collect data continuously for 5 minutes as a baseline reference.

[0126] Respiratory rate gradient test: Set the respiratory rate gradient to 0.3Hz, 0.63Hz, and 0.8Hz. Keep all other experimental conditions unchanged at each frequency point. Acetone gas was introduced for 5 minutes. After the voltage signal stabilized, data was collected continuously for 3 minutes. Repeat the test 5 times for each respiratory rate.

[0127] Transition phase processing: Between adjacent respiratory rate tests, high-purity nitrogen is introduced into the system for 5 minutes. At the same time, the frequency of the simulated breathing device is adjusted to 15 times / minute and operated stably for 2 minutes to ensure that the system returns to the baseline state.

[0128] Reverse verification test: After completing the forward frequency gradient test, perform reverse test in the order of 0.8Hz, 0.63Hz, and 0.3Hz to verify the reversibility and repeatability of the experimental results.

[0129] (3) Data processing and analysis

[0130] Results: As Figure 13As shown in the figure, in order to facilitate the comparison of the overall trend of the output voltage under different breathing frequencies and explore the relationship between output voltage and breathing frequency, the test results of each breathing frequency are integrated into one figure, and the acquisition time of each test is equal. The test results show that the breathing frequency only significantly changes the frequency of the output voltage, while the overall effect on the voltage amplitude is not significant (the change is less than 7.3%). This is because when the device structure and the environment are fixed, the output voltage mainly depends on the maximum separation distance between the sensitive film and the friction film, and the breathing frequency itself only changes the vibration frequency of the device and has little effect on the expansion and contraction of the vortex elastic TENG module.

[0131] (3) Response of the detection device to 10 ppm acetone and other interfering biomarkers

[0132] Test method:

[0133] 1. Experimental Preparation

[0134] (1) Gas preparation

[0135] Prepare high-purity acetone, ethanol, CH4, H2S, NH3 and CO2 gases, as well as high-purity nitrogen as diluent gas.

[0136] A dynamic gas distribution device was used to precisely control the gas flow rate via a mass flow controller (MFC) to prepare standard gases of 10ppm for acetone, ethanol, CH4, H2S, and NH3. For CO2, a standard gas with a concentration of 1% (10,000ppm) was prepared, with a volume of no less than 2L for each gas to ensure multiple testing requirements.

[0137] The prepared gas needs to be left in a sealed container for at least 1 hour to ensure that the gas is evenly mixed and to avoid uneven concentration affecting the test results.

[0138] (2) Instrument calibration

[0139] Start up and preheat the detection device for no less than 30 minutes. After the device is running stably, introduce high-purity nitrogen and record the baseline signal of the detection device to ensure that the baseline is stable and the value is within the normal range of the device.

[0140] Calibrate the detector using a standard gas of known concentration (similar to the concentration to be measured). Adjust the device parameters so that the error between the measured value and the standard gas concentration is within ±5%. If the error exceeds the range, recalibrate the device or check whether there is a malfunction.

[0141] (3) Experimental environment setup

[0142] The experiment was carried out in a clean, sealed environmental chamber with the temperature controlled at 25±1°C and the relative humidity maintained at 50±5% to reduce the impact of environmental factors on the response of the detection device.

[0143] Ensure that there are no strong electromagnetic interference sources in the experimental environment to avoid electromagnetic interference from interfering with the signal acquisition and processing of the detection device.

[0144] 2. Experimental testing process

[0145] (1) Blank test

[0146] Turn on the detection device and introduce high-purity nitrogen at a flow rate of 0.5 L / min for 10 minutes to clean the internal pipes and sensor elements of the detection device and remove residual impurities and possible interfering gases.

[0147] After the output signal of the detection device stabilizes, record the baseline signal at this time as blank control data.

[0148] (2) Single gas test

[0149] 10ppm acetone, ethanol, CH4, H2S, NH3 standard gas and 1% CO2 standard gas were introduced in sequence, with the flow rate of each gas being 0.5L / min and the ventilation time being 5 minutes.

[0150] During the gas introduction process, the response signal of the detection device to each gas is recorded in real time, and the data is recorded every 10 seconds until the response signal reaches a stable state (the signal fluctuation amplitude is within ±5%).

[0151] After each gas test is completed, high-purity nitrogen is immediately introduced to purge the detection device at the same flow rate for 5 minutes to restore the detection device to the baseline state before the next gas test is carried out.

[0152] Results: As Figure 14 As shown, the sensor's response to 10 ppm acetone and other interfering biomarkers, including ethanol (10 ppm), CH4 (10 ppm), H2S (10 ppm), NH3 (10 ppm), and CO2 (1%), was compared. The device's response to acetone was at least 2.8 times greater than its response to the other biomarkers, indicating that the sensor has a certain ability to discriminate acetone responses.

[0153] (4) Comparison of the stable output voltage of the detection device after normal exhalation and simulated gas

[0154] Test method:

[0155] Select healthy subjects with no special dietary intake (such as drinking alcohol or eating foods containing a large amount of ketones) and sit and rest for 15 minutes before the experiment to stabilize their breathing state. The subjects wear a breathing mask and exhale into the exhaled breath collection bag through the breathing mask. The exhalation process lasts for more than 30 seconds to ensure that the collection bag is filled with sufficient exhaled breath samples. Immediately connect the exhaled breath collection bag to the detection device, pass the exhaled breath into the detection device at a flow rate of 0.3L / min, and turn on the data recording function at the same time to record the output voltage changes of the detection device in real time.

[0156] Connect the prepared simulated gas to the detection device through a pipeline, and set the gas flow rate to 0.3L / min, which is consistent with the breath test flow rate.

[0157] Start the simulated gas flow and record the output voltage change of the detection device at the same time. Continue to flow the simulated gas until the output voltage reaches a stable state (the judgment standard is the same as that of a normal breath test), and record the stable output voltage value at this time.

[0158] Results: The comparison of the stable output voltage of the device after exposure to the simulated gas is shown in Figure 2. Figure 15 To facilitate comparison of the output voltages after stabilization with normal exhaled breath and simulated gas, the two gas test results are integrated into a single graph, with equal acquisition time for each test. The device's output voltage rises after exposure to the simulated gas. The calculated response to 10 ppm acetone in the simulated exhaled breath environment is 11.92%, demonstrating that the sensor has a reasonable ability to detect acetone in exhaled breath.

[0159] When testing pH:

[0160] (1) Comparison of current of detection device at different pH values

[0161] Test method:

[0162] The test structure was placed in a sealed test chamber in a constant temperature (25°C) and humidity (80% relative humidity) environment. Saturated vapor with a specific pH value (pH = 1-13) was introduced using an atomizer to simulate human exhalation. The gas flow rate was fixed at 1.5 L / min (simulating natural exhalation flow). The current signal was recorded in real time using an electrostatic high resistance meter (sampling rate 100 Hz). Each pH value was tested three times and the average value was obtained.

[0163] result:

[0164] like Figure 16 、 17 As shown, Figure 16 To facilitate comparison of the overall trend of output current at different pH values, the test results at different pH values ​​are integrated into one graph, with equal acquisition time for each test; Figure 17To facilitate comparison of the overall trend of the output voltage at different pH values, the test results at different pH values ​​are integrated into a single figure, with equal acquisition time for each test. When the pH values ​​were set to 1, 3, 5, 7, 9, and 13, the measured current and voltage of the electrical signal fluctuated over time. When the experiment was conducted in an acidic breath environment with a pH of 1, the measured voltage was 29.1 V and the current was 0.398 mA. As the pH value increased, the voltage decreased but remained stable. When the pH reached 9, the voltage began to rise again, reaching a peak at pH 13, where V = 57.9 V and I = 0.615 mA. This indicates that the output signal of the pH-TENG formed by pH-sensitive film 4 and polytetrafluoroethylene film is significantly affected by the pH of the solution. This phenomenon can be attributed to the fact that acidic or alkaline solutions simulate human exhaled air, leading to an increase in the concentration of hydrogen ions (H+) or hydroxyl ions (OH-) on the material surface, thereby increasing the triboelectric charge density on the pH-sensitive film surface. This effect can be attributed to the fact that strong acid or base conditions lead to more mechanical free radicals and stronger electron transfer. Strong acid and base environments may change the electrochemical properties of the electrode surface, such as surface potential and charge density, which in turn affects the generation and transmission of electrical signals, resulting in differences in current fluctuations. In contrast, in a neutral environment, these effects are relatively weakened, resulting in lower levels of both voltage and current.

[0165] (2) Response time and recovery time test of detection device

[0166] Test method:

[0167] In a constant temperature (25°C) and constant humidity (relative humidity 80%) environment, the detection structure is placed in a closed test chamber. Use an atomization device to introduce saturated steam with a specific pH value (such as pH = 13) to simulate human exhalation, and the gas flow rate is fixed at 1.5L / min (simulating natural exhalation flow). The current signal is recorded in real time by a high-precision oscilloscope (sampling rate 1kHz). The response time is defined as the time required for the current value to rise from the initial baseline to 90% of the steady-state value. Each group of pH values ​​is tested three times and the average value is taken.

[0168] result:

[0169] like Figure 18 As shown in the figure, under the environmental condition of pH 13, the measured response time is about 149 milliseconds and the recovery time is about 186 milliseconds. The response speed is fast, which is conducive to continuous monitoring of the exhaled pH value. The recovery time is short, which is conducive to continuous monitoring of the exhaled pH value.

[0170] (3) Durability test of detection device

[0171] Test method:

[0172] In a constant temperature (25°C) and humidity (relative humidity 80%) environment, atomized steam with pH = 7, pH = 10, or pH = 4 was circulated through a blower at a flow rate of 1.5 L / min (exhalation for 2 seconds and inhalation for 2 seconds, one exhalation and one exhalation as one cycle) for 3600 breathing cycles. The peak voltage of each cycle was recorded in real time using an electrostatic high resistance meter (sampling rate 100 Hz).

[0173] result:

[0174] like Figure 19 As shown in the figure, after about 3600 consecutive cycles of testing in a simulated exhalation environment, the output voltage remained basically stable, which shows that the structure has excellent mechanical stability and is suitable for subsequent gas-sensing performance testing.

[0175] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or replace some or all of the technical features therein with equivalents. However, these modifications or replacements do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present invention.

Claims

1. A drawer-type anti-interference human breath pH and acetone concentration detection device, characterized in that: include: A housing (1), a driving rotor (2) rotatably arranged on the housing (1), a follower rotor (3) driven by the driving rotor (2) to rotate synchronously, a flexible friction film (4), a first stator disc (5) and a second stator disc (6); the housing (1) is provided with a first slot (11) and a second slot (12), and the first stator disc (5) and the second stator disc (6) can both be inserted into the first slot (11) and the second slot (12); a plurality of mutually independent flexible friction films (4) are fixed on the follower rotor (3) to form a fan-shaped structure; The first stator disk (5) comprises: a first mounting plate (51), a first electrode (52), a second electrode (53) and an acetone sensitive film (54); the first electrode (52) and the second electrode (53) are independent of each other and are arranged on the first mounting plate (51); the shape and size of the second electrode (53) match the shape and size of the fan-shaped structure; and the acetone sensitive film (54) is attached to the second electrode (53); The second stator disc (6) comprises: a second mounting plate (61), a third electrode (62), a fourth electrode (63) and a pH sensitive film (64); the third electrode (62) and the fourth electrode (63) are independent of each other and are arranged on the second mounting plate (61); the shape and size of the fourth electrode (63) match the shape and size of the fan-shaped structure; and the pH sensitive film (64) is attached to the fourth electrode (63); When the first stator disc (5) or the second stator disc (6) is inserted into the first slot (11), the driving rotor (2) rotates under the action of human exhalation, so that the fan-shaped structure periodically drives the acetone sensitive film (54) and the first electrode (52) to come into contact and separate, thereby generating induced charges, and outputting an electrical signal through the first electrode (52) and the second electrode (53); or, the fan-shaped structure periodically drives the pH sensitive film (64) and the third electrode (62) to come into contact and separate, thereby generating induced charges, and outputting an electrical signal through the third electrode (62) and the fourth electrode (63).

2. A drawer-type anti-interference human breath pH and acetone concentration detection device according to claim 1, characterized in that: The first stator disk (5) further comprises a first stator disc (55) fixed on the first mounting plate (51); the first stator disc (55) is divided into two inner and outer sections by a first flower-shaped groove; a first electrode (52) and a second electrode (53) are respectively provided in the inner and outer sections, and the first electrodes (52) and the second electrodes (53) are alternately provided; all the first electrodes (52) are connected to form a first output end, and all the second electrodes (53) are connected to form a second output end; The second stator disc (6) further comprises a second stator disc (65) fixed on the second mounting plate (61); the second stator disc (65) is divided into two inner and outer sections by a second flower-shaped groove; a third electrode (62) and a fourth electrode (63) are respectively arranged in the inner and outer sections, and the third electrodes (62) and the fourth electrodes (63) are arranged alternately; all the third electrodes (62) are connected to form a third output end, and all the fourth electrodes (63) are connected to form a fourth output end.

3. A drawer-type anti-interference human breath pH and acetone concentration detection device according to claim 1, characterized in that: The housing (1) is further provided with an air inlet (13), a support frame (14) is fixedly provided at the air inlet (13), and a rotating shaft (15) is rotatably provided on the support frame (14); a follower rotor (3) is provided at one end of the rotating shaft (15) extending into the housing (1), and a driving rotor (2) is provided at the other end extending out of the housing (1).

4. A drawer-type anti-interference human breath pH and acetone concentration detection device according to claim 3, characterized in that: The driving rotor (2) includes a central axis (21) and a plurality of blades (22) arranged around the central axis (21), the blades (22) including a fan-facing surface (222), and the fan-facing surface (222) faces the exhalation of the human body to generate torque; The fan blade (22) includes a fan blade body (221), the fan blade body (221) is enclosed in a tubular or arc shape, the center line of the fan blade body (221) is a spiral line around the axis of the central axis (21), and the inner wall of the fan blade body (221) is a fan-facing surface (222).

5. The drawer-type anti-interference human breath pH and acetone concentration detection device according to claim 1, characterized in that: The acetone sensitive film (54) is a SWCNTs-CTS-ZnO film, and the preparation method of the SWCNTs-CTS-ZnO film comprises the following steps: S1: mixing a zinc source and a dopant, adding a chitosan solution and a carbon nanotube dispersion, stirring to form a mixed solution, and performing a hydrothermal reaction. After the hydrothermal reaction is completed, cooling and washing to obtain a nanomaterial doped with carbon nanotubes, which is then dispersed in deionized water to form a suspension; S2: The suspension is coated on a PET substrate, and after drying and annealing, a SWCNTs-CTS-ZnO thin film is obtained.

6. A drawer-type anti-interference human breath pH and acetone concentration detection device according to claim 5, characterized in that: The zinc source is a zinc acetate solution, and the concentration of the zinc acetate solution is 0.03 g / mL; The concentration of the carbon nanotube dispersion is 100 mg / mL; The concentration of the chitosan solution is 4 mg / mL; The dopant is sodium nitrate solution, and the concentration of the sodium nitrate solution is 0.5 mol / L; In S1, the volume ratio of the zinc acetate solution to the chitosan solution, the dopant, and the carbon nanotube dispersion is 50:1:10:

20.

7. The drawer-type anti-interference human breath pH and acetone concentration detection device according to claim 5, characterized in that: The chitosan solution was prepared by dissolving 2 g of chitosan in 80 ml of a 1% acetic acid aqueous solution, heating to 60° C. and stirring for 2 hours until the solution became clear and transparent, thereby completing the preparation of the chitosan solution. The specific method for preparing the carbon nanotube dispersion is as follows: adding single-walled carbon nanotubes into deionized water, and ultrasonically treating the water for 2-3 hours to disperse the carbon nanotubes to form a carbon nanotube dispersion with a concentration of 100 mg / mL.

8. The drawer-type anti-interference human breath pH and acetone concentration detection device according to claim 1, characterized in that: The pH sensitive film (64) is a SWCNTs-PDMS-ZnO film, and the preparation method of the SWCNTs-PDMS-ZnO film comprises the following steps: S1: Dissolve ZnAc2·2H2O in deionized water, stir, add NaOH solution, transfer the mixed solution to a beaker, and perform a hydrothermal reaction; after the solution is cooled to room temperature, centrifuge, wash, and dry the product to obtain rod-shaped ZnO, and add ultrapure water to prepare a ZnO aqueous solution for later use; S2: Mixing single-walled carbon nanotubes (SWCNTs) with a ZnO aqueous solution and ultrasonically treating the mixture to form a uniform suspension, which serves as a precursor solution. The precursor solution is added to a mold containing PDMS, heated and cured to form a thin film, the film is peeled off from the mold, and then the film is pre-cured, sintered, and dried to obtain a SWCNTs-PDMS-ZnO film.

9. The drawer-type anti-interference human breath pH and acetone concentration detection device according to claim 8, characterized in that: The concentration of the ZnO aqueous solution is 2 mg / mL; the mass ratio of the SWCNTs to the rod-shaped ZnO is 25:1; and the molar ratio of the ZnAc2·2H2O to NaOH is 1:8-9.

10. The drawer-type anti-interference human breath pH and acetone concentration detection device according to claim 8, characterized in that: In S2, the film is pre-cured, sintered, and dried in the following steps: the film is pre-cured at 200°C for 10 minutes and then sintered at 270°C for 60 minutes; After sintering, the film was placed in a vacuum drying oven at 70°C for 60 minutes.

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