A portable urine testing platform

Abstract

The application discloses a portable urine detection platform, which comprises a support module, an air path module, a sensing module of a micro-cavity integrated electronic nose, a multi-path resistance test module, a micro-pump module and a control module, realizes real-time online monitoring of volatile organic compounds in urine, and further realizes identification and differentiation of urine diseases by combining data obtained by using the platform with a machine learning algorithm.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of sensing devices, in particular to a preparation of a portable urine detection platform. BACKGROUND

[0002] Urine contains the final metabolites filtered by the kidney after metabolism. Urine metabolites can directly reflect the pathological and physiological conditions of the body, and are an ideal source of disease markers. Disease recognition using the differences in metabolites contained in urine (i.e., urine markers) has become an ideal non-invasive early detection and clinical screening method. Current research on urine metabolites mainly focuses on the detection of soluble metabolites (such as proteins) and volatile organic compounds (VOCs) in urine. Most of the traditional techniques used are offline and rely on large and expensive instruments, such as gas chromatography-mass spectrometry (GC-MS), and require specific sample pretreatment steps. Although these techniques have achieved remarkable results, they are slightly insufficient in terms of direct, rapid, and real-time online detection, and rarely meet the requirements of point-of-care testing (POCT). Compared with GC-MS, electronic noses are lower in cost, faster in speed, and more suitable for portability in identifying different VOCs. The high cost, difficulty in carrying, and complex detection procedures of traditional electronic nose-based urine detection platforms limit their widespread use. Therefore, the development of a portable urine detection platform that can be used for non-invasive disease recognition, is economical and efficient, and has high performance will help to directly, rapidly, and sensitively detect changes in urine VOCs, seamlessly integrate laboratory techniques and clinical diagnosis, achieve early non-invasive disease recognition, and ultimately develop individualized health care and treatment strategies to bring blessings to patients and the public. SUMMARY

[0003] The purpose of the present application is to overcome the shortcomings of traditional electronic nose-based urine detection platforms, such as high cost, difficulty in carrying, and complex detection procedures, and to provide a portable urine detection platform for rapid detection and analysis of urine.

[0004] The specific technical solution to achieve the purpose of the present application is:

[0005] A portable urine detection platform, characterized in that it comprises a support module, an air path module, a micro-pump module, a control module, a multi-channel resistance test module, and a micro-cavity integrated electronic nose sensing module.

[0006] The support module is prepared by 3D printing, and is used for fixing and assembling each module, and specifically comprises a gas path box, a base and a plurality of reagent bottle racks. The gas path box is a square cavity structure, and is provided with a plurality of sliding grooves on the front surface, a plurality of sliding blocks on the side surface and a microcavity integrated electronic nose slot on the top.

[0007] The sensing module of the microcavity integrated electronic nose comprises a screw with a gasket and a nut, a polytetrafluoroethylene joint, a stainless steel clamp, a polytetrafluoroethylene tube, a top chamber, a bottom chamber, an LIGIE sensing array and a rubber ring. The LIGIE sensing array comprises a flexible polyimide film, interdigital electrodes (flexible LIGIE) composed of interdigital electrodes engraved on the film and lead wires, and an LIGIE silver conductive area formed by coating conductive silver paste at the lead wire position of the flexible LIGIE.

[0008] The bottom chamber is a piece of organic glass plate, one side of which is pasted with kraft paper. The organic glass plate on the side of the kraft paper is cut to have the same number of through welding holes as the lead wires of the LIGIE sensing array, the same number of non-through I-shaped patterns as the lead wires, and 4-6 through screw holes, and is engraved with a streamlined groove. A bent needle is inserted into the through welding hole to form a connection circuit.

[0009] The top chamber is a piece of organic glass plate, and a through screw hole is optionally cut on one side of the organic glass plate, the number and size of which correspond to the through screw holes of the bottom chamber, and a plurality of through air holes and a plurality of through concave ports are cut.

[0010] The LIGIE sensing array is covered on the upper surface of the bottom chamber, wherein the silver conductive area in the LIGIE sensing array is attached to the connection circuit of the bottom chamber to form a contact circuit connection; and the rubber ring is covered on the upper surface of the LIGIE sensing array.

[0011] The top chamber is covered on the rubber ring, wherein the through screw holes of the top chamber correspond to the through screw holes of the bottom chamber in the vertical direction one by one.

[0012] The screw with the gasket and the nut is inserted into the aligned through screw holes and tightened to form a tightly fitted microcavity; the tightly fitted microcavity is placed in the stainless steel clamp, the polytetrafluoroethylene joint containing the polytetrafluoroethylene tube is placed in the stainless steel clamp and tightened, wherein the joint of the polytetrafluoroethylene joint corresponds to the through air hole of the top chamber, and is used for directional guiding of gas in and out.

[0013] The gas path module includes a bubbler, a buffer, a T-shaped joint, several commercial two-position three-way electromagnetic valves, and a polytetrafluoroethylene tube; wherein the bubbler and the buffer are both composed of a reagent bottle with a polytetrafluoroethylene gasket and two stainless steel needles with luer connectors inserted into the reagent bottle; the gas outlet of the first two-position three-way electromagnetic valve, the bubbler, the buffer, the gas inlet and outlet of the second two-position three-way electromagnetic valve, and any one interface of the T-shaped joint are sequentially connected by a polytetrafluoroethylene tube; at the same time, the gas outlet of the first two-position three-way electromagnetic valve is connected to the remaining one interface of the T-shaped joint by a polytetrafluoroethylene tube.

[0014] The micro-pump module includes a micro-pump and a battery, which are connected by a DuPont wire.

[0015] The multi-channel resistance test module includes a multi-channel resistance tester and a smartphone, which transmit signals through Bluetooth.

[0016] The control module includes a switch power supply with a plug.

[0017] The micro-pump is fixed in the micro-pump card slot position of the base of the support module, the battery is fixed in the battery card slot position of the base, the switch power supply is fixed in the switch power supply card slot position of the base, and the multi-channel resistance tester is fixed in the multi-channel resistance tester card slot position of the base. The microcavity integrated electronic nose is fixed in the microcavity integrated electronic nose card slot position on the top of the gas path box, and is fixed with the aid of screws; the remaining components in the gas path module, except the bubbler and the buffer, are fixed in the internal cavity of the gas path box containing the reagent bottle rack, and the bubbler and the buffer are respectively placed in the reagent bottle rack outside the gas path box; the gas inlet of the first two-position three-way electromagnetic valve of the gas path module is connected to the gas outlet of the micro-pump in the micro-pump module by a polytetrafluoroethylene tube; the remaining one joint of the T-shaped joint in the gas path module is connected to one end of the microcavity integrated electronic nose for directing the gas inlet and outlet by a polytetrafluoroethylene tube; the bent needle of the microcavity integrated electronic nose and the interface for circuit connection in the multi-channel resistance tester are connected by a DuPont wire to form a conductive loop.

[0018] The construction process of the portable urine detection platform includes:

[0019] Step 1: Place the switch power supply with a plug, the micro-pump, the battery, and the multi-channel resistance tester in the switch power supply card slot position, the micro-pump card slot position, the battery card slot position, and the multi-channel resistance tester card slot position of the base, respectively; and fix the microcavity integrated electronic nose to the microcavity integrated electronic nose card slot of the gas path box.

[0020] Step 2: Assemble several reagent bottle racks to the slide groove on the front of the gas path box through their slide blocks; place the bubbler and the buffer in different reagent bottle racks, respectively.

[0021] Step 3: Several commercially available two-position three-way electromagnetic valves are combined with screws to be fixed in the gas circuit box; the gas outlet of the first two-position three-way electromagnetic valve, the bubbler, the buffer, the gas inlet and the gas outlet of the second two-position three-way electromagnetic valve and the T-shaped joint are connected in sequence through a polytetrafluoroethylene pipe, and the exhaust port of the first two-position three-way electromagnetic valve is connected to the other interface of the T-shaped joint through a polytetrafluoroethylene pipe;

[0022] Step 4: The gas inlet of the first two-position three-way electromagnetic valve is connected to the gas outlet of the micropump through a polytetrafluoroethylene pipe; the remaining interface of the T-shaped joint is connected to the microcavity integrated electronic nose through a polytetrafluoroethylene pipe;

[0023] Step 5: The slider on the gas circuit box is assembled into the sliding groove of the base;

[0024] Step 6: The microcavity integrated electronic nose and the multi-channel resistance tester are connected through a Dupont wire; the micropump and the battery are connected through a Dupont wire.

[0025] The urine sample testing process of the portable urine detection platform comprises:

[0026] Step 1: Collect 2 mL ~10 mL fresh urine and add it to the bubbler;

[0027] Step 2: Turn on the multi-channel resistance tester switch, and connect it to the corresponding APP in the mobile phone through the mobile phone Bluetooth;

[0028] Step 3: Turn on the switch of the battery, and the micropump works, and air enters the microcavity integrated electronic nose chamber through the gas circuit module;

[0029] Step 4: Click the start button on the APP interface to start collecting resistance signals;

[0030] Step 5: After several minutes, turn off the power supply, and the volatile gases in the urine enter the microcavity integrated electronic nose chamber through the gas circuit module; after several minutes, turn off the switch power supply, and air enters the microcavity integrated electronic nose chamber through the gas circuit module again to remove the volatile gases in the urine;

[0031] Step 6: After several minutes, click the stop button on the APP interface; turn off the switch of the battery;

[0032] Step 7: Export the data obtained by the APP software testing, and end one test;

[0033] Step 8: Replace the bubbler and the buffer, test different urine samples, and repeat steps 1-7.

[0034] Compared with the prior art, the present application has the following advantages:

[0035] 1) The design of the sliding groove and the sliding block in the support module of the application facilitates the quick assembly and disassembly of the modules.

[0036] 2) The portable urine detection platform in the application is easy to operate, fast in detection, requires a small amount of sample, and does not require any pretreatment.

[0037] 3) The urine samples of healthy people and patients are tested on the portable urine detection platform, and after obtaining the data, the machine learning algorithm analysis can be combined to realize the high accuracy, sensitivity and specificity of various diseases. BRIEF DESCRIPTION OF DRAWINGS

[0038] Figure 1 Preparation flow chart of the LIGIE sensor array of the microcavity integrated electronic nose in the application;

[0039] Figure 2 Preparation flow chart of the bottom chamber of the microcavity integrated electronic nose in the application;

[0040] Figure 3 Top chamber schematic diagram of the microcavity integrated electronic nose in the application;

[0041] Figure 4 Structure explosion diagram of the microcavity integrated electronic nose in the application;

[0042] Figure 5 Structure explosion diagram of the support module in the application;

[0043] Figure 6 Structure schematic diagram of the gas path module in the application;

[0044] Figure 7 Front view of the application;

[0045] Figure 8 Side view of the application;

[0046] Figure 9 Urine sample online test schematic diagram in the application;

[0047] Figure 10 Analysis schematic diagram of the clinical urine sample by machine learning algorithm using the data obtained by the application. DETAILED DESCRIPTION

[0048] To make the purpose, technical scheme and advantages of the embodiments of the application clearer, the technical scheme of the embodiments of the application will be described clearly and completely below. Obviously, the described embodiments are part of the embodiments of the application, not all the embodiments. Based on the described embodiments of the application, all other embodiments obtained by those skilled in the art without creative labor are within the protection scope of the application.

[0049] The endpoints of the ranges and any values disclosed herein are not limited to the precise values recited as the exact dimensions are not to be understood as being crucial to the invention. Any numeric range recited is intended to include all values from the lower value to the upper value. For numeric ranges, the endpoints of each range, the endpoints of each range and individual point values, and individual point values can be combined to form one or more new numeric ranges, which are to be construed as being explicitly disclosed herein.

[0050] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this disclosure belongs.

[0051] Referring to Figures 7-8 The portable urine detection platform comprises a support module, a gas path module, a sensing module of a microcavity integrated electronic nose, a multi-channel resistance testing module, a micropump module, and a control module. The overall size is about 205 mm in length, 180 mm in width, and 120 mm in height.

[0052] Referring to Figure 5 The support module is prepared by 3D printing and is used for fixing and assembling the modules. Specifically, the support module comprises a gas path box, a base, and a plurality of reagent bottle racks. The gas path box is a square cavity structure. A plurality of sliding grooves 40 are arranged on the front surface, a plurality of sliding blocks 41 are arranged on the side surface, and a card slot 35 for placing the corresponding microcavity integrated electronic nose is arranged on the top. The base is a plate. A plurality of sliding grooves 42, a micropump card slot 32, a battery card slot 43, a switching power supply card slot 33, and a multi-channel resistance tester card slot 34 are arranged on the base. The reagent bottle rack is a cylindrical structure with an unsealed upper surface. A sliding block 44 is arranged on the side surface. The sliding blocks 44 on the reagent bottle racks are assembled into the sliding grooves 40 outside the gas path box, and the side of the reagent bottle rack fixed to the gas path box is regarded as the front surface of the gas path box. The sliding blocks 41 on the gas path box are assembled into the sliding grooves 42 on the base.

[0053] Referring to Figure 6 The gas path module comprises a bubbler 36, a buffer 37, a T-shaped joint 38, a plurality of commercial two-position three-way electromagnetic valves 39, and a polytetrafluoroethylene pipe 1. The bubbler 36 and the buffer 37 are composed of reagent bottles with polytetrafluoroethylene gaskets and two stainless steel needles connected with luer joints inserted into the reagent bottles.

[0054] Referring to Figures 7-8 The micropump module comprises a micropump and a battery. The micropump and the battery are connected by a DuPont wire.

[0055] The multi-channel resistance testing module comprises a multi-channel resistance tester and a smartphone. The multi-channel resistance tester and the smartphone transmit signals through Bluetooth.

[0056] The control module comprises a switching power supply with a plug.

[0057] Example 1: Preparation of the sensing module of the microcavity integrated electronic nose, see Figures 1-4

[0058] 1.1: Using a CO2 laser 21 to manufacture 8 graphene electrodes on a polyimide film 12 with dimensions of 25 mm * 18 mm * 1 mm, each electrode having two leads 14 and 4 pairs of interdigital electrodes, with an interdigital electrode width of 200 μm and a spacing of 200 μm; that is, a flexible LIGIE;

[0059] 1.2: Using a PET tape (thickness 80 μm) as a mask plate attached to the flexible LIGIE, using a doctor blade 16 to squeegee conductive silver paste 17, after heating at 80°C for 2 h, removing the PET tape 15, and the conductive silver paste is fixed at the lead position of the LIGIE, that is, the LIGIE silver conductive area 18;

[0060] 1.3: Laser cutting of the PI tape, the size of the cut PI tape 19 matches the flexible LIGIE, and the PI tape 19 corresponding to the interdigital electrode 13 area of the flexible LIGIE is removed; the tape is attached vertically to the flexible LIGIE, and finally 8 different performance gas sensitive materials 20 are dropped on the 8 interdigital electrode areas to prepare a LIGIE sensing array 7 containing 8 sensing units;

[0061] Select a piece of organic glass plate 22 with a length of 10 cm, a width of 10 cm, and a thickness of 2 mm, and optionally the largest area of the side as the front side to paste the kraft paper 23;

[0062] 1.4: Using a CO2 laser 21 to carve a streamlined groove 27 in the organic glass plate 22 containing the kraft paper 23 side; At the same time, 16 through-welding holes 25 with a diameter of 0.8 mm are cut, with 8 holes in each group, and the two groups are located on the two sides of the streamlined groove 27; 16 non-through I-shaped patterns 24, with 8 as a group, and the two groups are located on the two sides of the streamlined groove 27; 4 through-screw holes 26 with a diameter of 4 mm;

[0063] 1.5: Remove the kraft paper corresponding to the I-shaped pattern 24 area, and use a doctor blade 16 to squeegee conductive silver paste 17 in the I-shaped pattern 24 area to obtain the I-shaped pattern circuit structure 28; At the same time, insert the pin array 10 formed by 8 bent pins into the two groups of through-welding holes 25, respectively; After heating the organic glass plate at 80°C for 2 h, remove all the kraft paper 23 to form the bottom chamber 9;

[0064] 1.6 Select another piece of organic glass plate with a length of 10 cm, a width of 10 cm and a thickness of 2 mm, optionally the largest area of one face as the front, and use a CO2 laser 21 to cut 4 through screw holes 29 with a diameter of 4 mm and two through air holes 30 with a diameter of 3 mm on the face; two symmetrical through concave mouths 31;

[0065] 1.7: The silver glue conductive area 18 of the LIGIE sensor array 7 is aligned with the circuit structure 28 of the I-shaped pattern 24 in the bottom chamber 9, and the LIGIE sensor array 7 is covered on the upper surface of the bottom chamber 9; the rubber ring 6 is covered on the LIGIE sensor array 7, and is aligned with the streamlined groove 27 in the bottom chamber 9 in the vertical direction; the top chamber 5 is covered on the rubber ring 6, wherein the four through screw holes 29 in the top chamber 5 are aligned with the four through screw holes 26 of the bottom chamber 9 in the vertical direction; four screws 3 with gaskets and nuts are respectively put into the four aligned through screw holes, and the screws are tightened to form a tightly fitted microcavity;

[0066] 1.8: The tightly fitted microcavity is put into two stainless steel clamps 8, and the threaded holes of the two stainless steel clamps 8 are respectively aligned with the two through air holes 30; the polytetrafluoroethylene joint 2 with a polytetrafluoroethylene tube 1 is put into the threaded hole of the stainless steel clamp 8, and is connected with the through air hole 30, wherein one end is used as an air inlet and the other end is used as an air outlet.

[0067] Example 2: A portable urine detection platform is built, please refer to Figures 5-8 ;

[0068] 2.1: Put the switching power supply, micro module, battery, multi-channel resistance tester into the corresponding positions of the switching power supply card slot 33, micro pump card slot 32, battery card slot 43 and multi-channel resistance tester card slot 34 on the base of the support module; the microcavity integrated electronic nose is fixed to the position of the microcavity integrated electronic nose card slot 35 in the gas path box;

[0069] 2.2: Two reagent bottle racks are assembled with their sliding blocks 44 on the sliding grooves 40 outside the gas path box; a 20 mL bubbler 36 and a 20 mL buffer 37 are respectively put into the reagent bottle racks; select the side with the reagent bottle racks as the front;

[0070] 2.3: Two commercial two-position three-way solenoid valves 39 are fixed on the side of the gas path box by screws; the gas outlet of the first two-position three-way solenoid valve 39, the bubbler 36, the buffer 37, the gas inlet and outlet of the second two-position three-way solenoid valve 39, and any one interface of the T-shaped joint 38 are connected in turn by polytetrafluoroethylene pipes 1, and the exhaust port of the first two-position three-way solenoid valve 39 is connected to the remaining one of the interfaces of the T-shaped joint 38 by a polytetrafluoroethylene pipe 1;

[0071] 2.4: The gas inlet of the first two-position three-way solenoid valve 39 is connected to the gas outlet of the micropump by a polytetrafluoroethylene pipe 1; the remaining interface of the T-shaped joint 38 is connected to the end of the microcavity integrated electronic nose for directing gas in any direction by a polytetrafluoroethylene pipe 1;

[0072] 2.5: The slider 41 on the gas path box is assembled into the sliding groove 42 on the base;

[0073] 2.6: The microcavity integrated electronic nose composed of eight sensors and the multi-channel resistance tester are connected by DuPont wires; the micropump and the battery are connected by DuPont wires.

[0074] Example 3: A portable urine detection platform for clinical urine sample detection, see Figure 9 ;

[0075] 3.1: Collect urine (15 mL per person) from patients with diabetes co-depression (DCD), patients with diabetes (D), patients with liver injury (LI), and healthy (H) people, and store the urine samples at -80°C for later use. Before detection, thaw the urine sample, and transfer 5 mL of the urine sample (without pretreatment) to a bubbler with a capacity of 20 mL. The stainless steel needle in the gas path closest to the gas outlet of the first two-position three-way solenoid valve 39 is below the liquid level of the urine, and the other stainless steel needle in the bubbler 36 is above the liquid level of the urine;

[0076] 3.2: Turn on the multi-channel resistance tester switch, connect it to the corresponding APP in the mobile phone through the mobile phone Bluetooth, turn on the switch of the battery, and the micropump works. Air enters the microcavity integrated electronic nose chamber through the gas path module, with a flow rate of about 450 mL / min;

[0077] 3.3: Click the start button on the APP interface to start collecting resistance signals; turn off the power supply after 1 min, and the volatile gases in the urine pass through the gas path module into the microcavity integrated electronic nose chamber; turn off the switch power supply after 1 min, and the air again passes through the gas path module into the microcavity integrated electronic nose chamber to remove the volatile gases in the urine; click the stop button on the APP interface after 2 min to end the collection of resistance signals; turn off the switch of the battery; export the data obtained by the APP software test, and end one test; export the data obtained by the APP software test, a total of 8 dynamic resistance change curves;

[0078] 3.4: Replace the bubbler and buffer, take different urine samples, and repeat steps 3.1-3.3 to test different urine samples.

[0079] Example 4: The data obtained using the portable urine detection platform is further used for clinical urine sample analysis through a machine learning algorithm, see Figure 10 ;

[0080] Extract 8 resistance change rates obtained from each urine sample test to form a data set; the measured data set is divided into a test set and a training set according to a ratio of 3:7; after standardizing the test set and the training set data, the training set data is used to build a model through a machine learning algorithm, and the test set verifies the model's ability to predict disease categories; the portable urine detection platform can achieve high recognition of three diseases, diabetes (D), diabetes co-depression (DCD), and liver injury (LI), and healthy people (H) (accuracy of 94.4%, specificity of 77.8%, and sensitivity of 100%).

Claims

1. A portable urine testing platform, characterized in that, The portable urine testing platform includes: a support module, an air circuit module, a micropump module, a control module, a multi-channel resistance testing module, and a sensing module for a microcavity integrated electronic nose; The support module is fabricated by 3D printing and is used for fixing and assembling various modules. Specifically, it consists of a gas path box, a base, and several reagent bottles. The gas path box is a square cavity structure with several sliding grooves (40) on the front, several sliders (41) on the side, and a slot (35) on the top for placing a microcavity integrated electronic nose. The base is a plate with several sliding grooves (42), a micropump slot (32), a battery slot (43), a switching power supply slot (33), and a multi-channel resistance tester slot (34). The reagent bottle holder is a cylindrical structure with an unsealed upper surface and sliders (44) on its side. The sliders (44) on the reagent bottle holder are assembled into the sliding grooves (40) on the outside of the front of the gas path box. The sliders (41) on the gas path box are assembled into the sliding grooves (42) on the base. The sensing module of the microcavity integrated electronic nose includes a screw (3) with a gasket (4) and a nut (11), a polytetrafluoroethylene connector (2), a stainless steel clamp (8), a polytetrafluoroethylene tube (1), a top chamber (5), a bottom chamber (9), a LIGIE sensing array (7), and a rubber ring (6). The LIGIE sensing array (7) is formed by engraving interdigitated fingers (13) and leads (14) on a flexible polyimide film (12) to form interdigitated electrodes, i.e., flexible LIGIE, and then coating conductive silver paste at the position of the leads (14) to form a silver conductive area (18). The bottom chamber (9) is an organic glass plate (22) with kraft paper (23) attached to one side. The organic glass plate on the kraft paper side has through-welding holes (25) with the same number of leads (14) as the LIGIE sensor array (7), non-through I-shaped patterns (24) with the same number of leads (14), and 4 to 6 through screw holes (26). At the same time, a streamlined groove (27) is engraved. A bent pin (10) is inserted into the through-welding hole (25) to form a connection circuit (28). The top chamber (5) is a piece of plexiglass, on which through screw holes (29) are cut, the number and size of which correspond to the through screw holes (26) of the bottom chamber (9), as well as several through air holes (30) and several through concave openings (31). The LIGIE sensor array (7) covers the upper surface of the bottom chamber (9), wherein the silver conductive area (18) in the LIGIE sensor array (7) is attached to the connection circuit (28) of the bottom chamber (9) for contact circuit connection; the rubber ring (6) covers the upper surface of the LIGIE sensor array (7). The top chamber (5) covers the rubber ring (6), wherein the through screw hole (29) of the top chamber (5) corresponds one-to-one with the through screw hole (26) of the bottom chamber (9) in the vertical direction; Screws (3) with washers and nuts are inserted into the aligned through screw holes and tightened to form a tightly fitting microcavity; the tightly fitting microcavity is placed in a stainless steel clamp (8), and a polytetrafluoroethylene connector (2) containing a polytetrafluoroethylene tube (1) is placed in the stainless steel clamp (8) and tightened, wherein the connector of the polytetrafluoroethylene connector (2) corresponds to the through vent (30) of the top chamber (5) to guide the gas in and out in a directional manner; The gas path module includes a bubbler (36), a buffer (37), a T-connector (38), several commercial two-position three-way solenoid valves (39), and a polytetrafluoroethylene (PTFE) tube (1); wherein the bubbler (36) and the buffer (37) are both composed of a reagent bottle with a PTFE gasket and two stainless steel needles with Luer connectors inserted in the reagent bottle; the outlet of the first two-position three-way solenoid valve (39), the bubbler (36), the buffer (37), the inlet and outlet of the second two-position three-way solenoid valve (39), and any one of the interfaces of the T-connector (38) are connected in sequence through the PTFE tube (1); at the same time, the exhaust port of the first two-position three-way solenoid valve (39) is connected to one of the remaining interfaces of the T-connector (38) using the PTFE tube (1). The micropump module includes a micropump and a battery, which are connected by DuPont wires. The multi-channel resistance test module includes a multi-channel resistance tester and a smartphone, which transmit signals via Bluetooth. The control module includes a switching power supply with a plug; The micropump is fixed in the micropump slot (32) of the base of the support module, the battery is fixed in the battery slot (43) of the base, the switching power supply is fixed in the switching power supply slot (33) of the base, and the multi-channel resistance tester is fixed in the multi-channel resistance tester slot (34) of the base. The microcavity integrated electronic nose is fixed in the microcavity integrated electronic nose slot (35) on the top of the gas path box, and is also fixed with screws. The remaining components of the gas path module, except for the bubbler (36) and the buffer (37), are fixed in the internal cavity of the gas path box containing the reagent bottle rack. The bubbler (36) and the buffer (37) are placed in the reagent bottle rack outside the gas circuit box respectively; the inlet of the first two-position three-way solenoid valve (39) of the gas circuit module is connected to the outlet of the micropump in the micropump module through a polytetrafluoroethylene tube (1); the remaining connector of the T-type connector (38) in the gas circuit module is connected to one end of the microcavity integrated electronic nose that guides the gas in and out through a polytetrafluoroethylene tube (1); the bent needle (10) of the microcavity integrated electronic nose and the interface used for circuit connection in the multi-channel resistance tester are connected through DuPont wires to form a conductive circuit.

2. The portable urine testing platform according to claim 1, characterized in that, The process of testing urine samples using the portable urine testing platform specifically includes: Step 1: Collect 2 mL to 10 mL of fresh urine and add it to the bubbler; Step 2: Turn on the multi-channel resistance tester and connect it to the corresponding APP on your mobile phone via Bluetooth; Step 3: Turn on the battery switch, the micro-pump starts working, and air enters the micro-cavity integrated electronic nasal chamber through the air circuit module; Step 4: Click the start button on the APP interface to begin collecting resistance signals; Step 5: After several minutes, turn on the power switch. The volatile gases in the urine enter the microcavity integrated electronic nasal chamber through the air path module. After several minutes, turn off the power switch. Air enters the microcavity integrated electronic nasal chamber again through the air path module to remove the volatile gases in the urine. Step 6: After a few minutes, click the stop button on the app interface; turn off the battery. Step 7: Export the data obtained from the APP software test to end one test; Step 8: Replace the bubbler and buffer, test different urine samples, and repeat steps 1-7.

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