Real-time urine detection method

Abstract

The present invention provides a real-time urine detection method, which belongs to the field of urine detection technology and solves the problem in the prior art that conventional urine detection can only detect a single data and is difficult to detect a variety of urine indicators. The real-time urine detection method includes: selecting a urine detection mode, wherein the urine detection mode includes at least one of a basic detection mode, a precise detection mode, and a composite detection mode; performing urine sampling; testing the sampled urine according to the selected urine detection mode; and outputting the urine test results. The real-time urine detection method provided by the present invention can detect both a single indicator and a variety of indicators, and has a wide range of application scenarios and strong applicability.

Description

Technical Field

[0001] The present invention belongs to the technical field of urine detection, and in particular relates to a real-time urine detection method. Background Art

[0002] Urinalysis includes routine urine analysis, urine formed element detection (such as urine red blood cells, white blood cells, etc.), quantitative determination of protein components, urine enzyme determination, etc. Urinalysis is of great value in clinical diagnosis, judgment of therapeutic effect and prognosis.

[0003] To facilitate urine testing for users, smart toilets have appeared on the market. However, existing smart toilets can usually only detect relatively single data. Single data can only detect a certain type or category of urine indicators of the human body, and it is difficult to detect diverse urine indicators. Summary of the Invention

[0004] In view of this, the present invention provides a real-time urine detection method to solve the problem in the prior art that conventional urine detection can only detect single data and is difficult to detect diverse urine indicators.

[0005] The technical solution adopted in the present invention is:

[0006] In a first aspect, the present invention provides a method for real-time urine detection, comprising:

[0007] Selecting a urine testing mode, wherein the urine testing mode includes at least one of a basic testing mode, a precise testing mode, and a composite testing mode;

[0008] Perform urine sampling;

[0009] Testing the sampled urine according to the selected urine testing mode;

[0010] Output urine test results.

[0011] As a preferred embodiment of the above-mentioned real-time urine detection method, the precise detection mode includes at least one of an optical detection method and an electrochemical detection method. The optical detection method is used to collect optical information of urine and perform urine detection based on the optical information of urine. The electrochemical detection method is used to collect electrochemical information of urine and perform urine detection based on the electrochemical information of urine.

[0012] As a preferred embodiment of the above-mentioned real-time urine detection method, the urine detection based on the collected electrochemical information includes:

[0013] The collected electrochemical information is compared with the preset electrochemical information, and the detection result is output.

[0014] As a preferred embodiment of the above-mentioned real-time urine detection method, the optical detection method includes at least one of a microscopic image detection method, a fluorescence detection method, and a spectral detection method. The microscopic image detection method is used to collect microscopic information of urine and perform urine detection based on the microscopic information of the urine. The fluorescence detection method is used to collect fluorescence information of urine and perform urine detection based on the fluorescence information of urine. The spectral detection method is used to collect spectral information of urine and perform urine detection based on the spectral information of urine.

[0015] As a preferred embodiment of the above-mentioned real-time urine detection method, the basic detection mode includes a dry chemical detection method, which is used to collect dry chemical information of urine and perform urine detection based on the dry chemical information of urine.

[0016] As a preferred embodiment of the above-mentioned real-time urine detection method, the urine sampling comprises:

[0017] Set the urine volume for urine testing according to the selected urine testing mode;

[0018] Urine sampling was performed according to the urine volume.

[0019] As a preferred embodiment of the above-mentioned real-time urine detection method, after the step of sampling urine according to the urine volume, the method further comprises:

[0020] The urine sample is precipitated and filtered, and the precipitated and filtered urine sample is temporarily stored.

[0021] As a preferred embodiment of the above-mentioned real-time urine detection method, before the step of detecting the sampled urine according to the selected urine detection mode, the method further includes: setting injection paths corresponding to the basic detection mode and the precise detection mode, respectively, for the urine that has undergone temporary storage transition, and selecting the corresponding injection path for injection according to the selected detection mode.

[0022] As a preferred embodiment of the above-mentioned real-time urine detection method, after the step of detecting the sampled urine according to the selected urine detection mode, the method further comprises:

[0023] After the test is completed, perform cleaning operations.

[0024] As a preferred embodiment of the above-mentioned urine real-time detection method, urine detection is performed using the aforementioned urine real-time detection method.

[0025] In a second aspect, the present invention provides a rapid detection system for human biochemical indicators, which uses the aforementioned real-time urine detection method to perform urine detection.

[0026] In summary, the beneficial effects of the present invention are as follows:

[0027] The real-time urine detection method provided by the present invention includes selecting a urine detection mode, taking urine samples, testing the sampled urine according to the selected urine detection mode, and outputting the urine detection results. Accordingly, the selected urine detection mode determines the urine detection results finally output. In the present invention, the urine detection mode includes at least one of a basic detection mode, a precise detection mode and a composite detection mode. The composite detection mode is a basic detection mode combined with a precise detection mode. When the user only needs to test a certain item or a certain category of indicators, the corresponding basic detection mode or precise detection mode can be selected, which can perform targeted testing and reduce testing costs. When the user needs to perform diversified indicator testing, the composite detection mode can be enabled.

[0028] The rapid detection system for human biochemical indicators provided by the present invention adopts the aforementioned real-time urine detection method to perform urine detection. It can detect both single indicators and diversified indicators, has a wide range of application scenarios, and is highly applicable. BRIEF DESCRIPTION OF THE DRAWINGS

[0029] In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the following briefly introduces the drawings required for use in the embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without any creative work, and these are all within the scope of protection of the present invention.

[0030] Figure 1 A three-dimensional diagram of the smart toilet of the present invention;

[0031] Figure 2 A side view of the smart toilet of the present invention;

[0032] Figure 3 This is a diagram showing the internal structure of the smart toilet of the present invention;

[0033] Figure 4 This is an exploded view of the smart toilet of the present invention;

[0034] Figure 5 A perspective view of the urine sampling head of the present invention;

[0035] Figure 6 It is a structural schematic diagram of the elastic member of the present invention;

[0036] Figure 7 This is a schematic structural diagram of the upper portion of the circular sampling head body of the present invention;

[0037] Figure 8 This is a schematic structural diagram of the upper portion of the concave sampling head body of the present invention;

[0038] Figure 9This is a schematic structural diagram of the upper portion of the planar sampling head body of the present invention;

[0039] Figure 10 Schematic diagram of the structure of the urine sampler of the present invention;

[0040] Figure 11 A three-dimensional diagram of the switching mechanism of the present invention;

[0041] Figure 12 The structure of the replaceable reagent consumables box of the present invention is schematically shown. Figure 1 ;

[0042] Figure 13 The structure of the replaceable reagent consumables box of the present invention is schematically shown. Figure 2 ;

[0043] Figure 14 This is a diagram of the internal structure of the replaceable reagent consumables box of the present invention;

[0044] Figure 15 This is a schematic diagram of the structure of the consumables storage box of the present invention. Figure 1 ;

[0045] Figure 16 This is a schematic diagram of the structure of the consumables storage box of the present invention. Figure 2 ;

[0046] Figure 17 This is a diagram of the internal structure of the consumables storage box of the present invention;

[0047] Figure 18 is a three-dimensional diagram of the microfluidic detection chip of the present invention;

[0048] Figure 19 This is a diagram showing the internal structure of the microfluidic detection chip of the present invention;

[0049] Figure 20 This is an exploded view of the microfluidic detection chip of the present invention;

[0050] Figure 21 is a stereoscopic diagram of the microscopic image information acquisition module of the present invention;

[0051] Figure 22 This is a structural diagram of the interior of the microscope body of the present invention;

[0052] Figure 23 A stereoscopic diagram of the microscopic image acquisition module of the present invention;

[0053] Figure 24 A three-dimensional diagram of the optical information acquisition module of the present invention;

[0054] Figure 25 A diagram showing the positional relationship between the optical information acquisition component and the microfluidic detection chip of the present invention;

[0055] Figure 26 This is a diagram showing the internal structure of the fluorescence / spectroscopy microfluidic detection chip of the present invention;

[0056] Figure 27 Exploded view of the fluorescence / spectroscopy microfluidic detection chip of the present invention;

[0057] Figure 28 Schematic diagram of the electrochemical detection chip structure in which the reaction part and the conductive part are located on different sides of the present invention;

[0058] Figure 29 Schematic diagram of the structure of the reaction part of the present invention;

[0059] Figure 30 Schematic diagram of the structure of the conductive part of the present invention;

[0060] Figure 31 Schematic diagram of the electrochemical detection chip structure in which the reaction part and the conductive part are located on the same side of the present invention;

[0061] Figure 32 Schematic diagram of the structure of the body fluid electrochemical detection module of the present invention Figure 1 ;

[0062] Figure 33 Schematic diagram of the structure of the body fluid electrochemical detection module of the present invention Figure 2 ;

[0063] Figure 34 This is an exploded view of the body fluid electrochemical detection module of the present invention;

[0064] Figure 35 The internal structure of the body fluid electrochemical detection module of the present invention Figure 1 ;

[0065] Figure 36 The internal structure of the body fluid electrochemical detection module of the present invention Figure 2 ;

[0066] Figure 37 Schematic diagram of the structure of the reaction chamber of the present invention;

[0067] Figure 38 is a perspective view of the electrochemical body fluid detection device of the present invention;

[0068] Figure 39 An exploded view of the electrochemical body fluid detection device of the present invention;

[0069] Figure 40 This is a schematic diagram of a rapid detection system for human biochemical indicators according to Example 20 of the present invention;

[0070] Figure 41 1 is a schematic flow chart of the steps of the urine detection method based on microscopic images according to Example 15 of the present invention;

[0071] Figure 42 1 is a schematic flow chart of the steps of the urine detection method based on microscopic images after step S120 in Example 15 of the present invention;

[0072] Figure 43 15 is a flow chart of the steps included in step S150 of embodiment 15 of the present invention;

[0073] Figure 44 16 is a schematic flow chart of the steps of a method for detecting urine components based on a fluorescent reagent according to Example 16 of the present invention;

[0074] Figure 45 1 is a flow chart of the steps of the method for detecting urine components based on a fluorescent reagent after step S220 in Example 16 of the present invention;

[0075] Figure 46 17 is a schematic flow chart of the steps of the spectral detection method for urine components according to Example 17 of the present invention;

[0076] Figure 47 17 is a schematic flow chart of the steps of the urine electrochemical detection method according to Example 17 of the present invention;

[0077] Figure 48 18 is a flow chart of the steps included in step S450 of embodiment 18 of the present invention;

[0078] Figure 49 This is a schematic diagram of the Euler distance between two time series in Example 18 of the present invention;

[0079] Figure 50 19 is a flow chart of the steps of the real-time urine detection method according to Example 19 of the present invention;

[0080] Parts and numbers in the picture:

[0081] 100. Toilet body;

[0082] 110, base; 120, trough;

[0083] 200, toilet seat;

[0084] 210, third bearing;

[0085] 300, toilet seat cover;

[0086] 310, toilet front cover; 311, first bearing; 320, toilet rear cover; 321, first rotating shaft;

[0087] 400, urine sampler;

[0088] 410, urine sampling head;

[0089] 411, sampling head body; 411a, through hole; 411b, sampling head upper part; 411c, sampling head lower part;

[0090] 412, connecting mechanism; 412a, elastic member; 412b, groove; 412c, protrusion; 412d, limiting mechanism;

[0091] 420, transfer mechanism; 421, transfer mechanism body; 421a, transfer groove; 421b, installation cavity;

[0092] 500, sampling micro flow pump;

[0093] 600, consumables storage box;

[0094] 610, consumables storage box body; 611, electronic tag reader; 612, transparent window; 613, ejector pin; 614, consumables storage box liquid outlet;

[0095] 620, replaceable reagent and consumables box;

[0096] 621, consumable box body; 621a, electronic label; 621b, transparent part; 621c, mounting hole;

[0097] 622, consumable box reagent inlet; 623, consumable box reagent outlet;

[0098] 624, consumable box sealing member; 624a, reset member; 624b, spring pin; 624c, cover plate;

[0099] 625, first gap; 626, second gap;

[0100] 630, upper cover of consumables storage box;

[0101] 700, urine testing module;

[0102] 710. Microfluidic detection chip;

[0103] 711, detection chip body; 711a, first device chamber; 711b, light-emitting device; 711c, second device chamber; 711d, temperature control device; 711e, device seal; 711f, first chamber cover; 711g, second chamber cover; 711h, excitation light filter layer;

[0104] 712, detection chip sample inlet; 713, sample detection chamber; 714, first microfluidic channel; 715, detection chip sample outlet; 716, second microfluidic channel;

[0105] 720. Microscopic image acquisition module;

[0106] 730. Microscopic image information acquisition module;

[0107] 731, microscope body;

[0108] 732, lens set;

[0109] 733, zoom assembly; 733a, first magnifying lens; 733b, second magnifying lens; 733c, protective lens;

[0110] 734, filter assembly; 734a, first filter; 734b, first filter;

[0111] 735, stage;

[0112] 736. Microscopic optical information acquisition component;

[0113] 740. Optical information acquisition module;

[0114] 741. Optical information acquisition component;

[0115] 750. Electrochemical body fluid detection device;

[0116] 760, electrochemical detection chip;

[0117] 761, insulating substrate; 761a, first isolation member; 761b, second isolation member;

[0118] 762, chip electrode; 762a, reaction part; 762b, conductive part; 762c, reaction part liquid outlet;

[0119] 770. Body fluid electrochemical detection module;

[0120] 771, detection module body; 771a, reaction area; 771b, connection area; 771c, reaction chamber; 771d, chamber; 771e, sealing structure; 771f, liquid collecting tank; 771g, sample injection pipe installation hole;

[0121] 772, electrochemical injection port;

[0122] 773. Connect electrodes;

[0123] 774, electrochemical sample outlet;

[0124] 775, sampling pipe; 775a, sampling pipe body; 775b, sampling pipe liquid outlet; 775c, bending portion;

[0125] 776, sample outlet pipe;

[0126] 780. Urine transfer duct. DETAILED DESCRIPTION

[0127] In order to make the purpose, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions in the embodiments of the present invention will be clearly and completely described below in conjunction with the drawings in the embodiments of the present invention. It should be noted that, in this article, relational terms such as first and second are only used to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply any such actual relationship or order between these entities or operations. In the description of the present invention, it should be understood that the orientation or position relationship indicated by the terms "center", "upper", "lower", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inside", "outside" and the like is based on the orientation or position relationship shown in the drawings, and is only for the convenience of describing the present application and simplifying the description, rather than indicating or implying that the device or element referred to must have a specific orientation, be constructed and operate in a specific orientation, and therefore cannot be understood as limiting the present invention. Moreover, the terms "include", "comprise" or any other variants thereof are intended to cover non-exclusive inclusion, so that a process, method, article or device including a series of elements includes not only those elements, but also includes other elements not explicitly listed, or also includes elements inherent to such process, method, article or device. In the absence of further limitations, elements defined by the phrase "comprising..." do not preclude the presence of additional identical elements in the process, method, article, or apparatus comprising the elements. The embodiments of the present invention and the features thereof may be combined with each other if there is no conflict, and all are within the scope of protection of the present invention.

[0128] Example 1

[0129] See Figure 1 and Figure 2 The embodiment of the present invention discloses a smart toilet that can be used as an ordinary toilet or in the field of urine testing to test the user's urine. Specifically, it can be used in places such as homes, businesses, or hospitals. For example, in homes: patients require long-term recuperation and need to frequently test urine information. By analyzing urine data, the patient's own health status can be determined. Although hospitals have complete urine testing equipment and doctors are relatively professional, the expenses incurred in hospitals are also relatively high. Currently, many families are relatively tight on money, and these hospital expenses will bring a huge burden to the entire family. If the smart toilet of this application is used, patients can undergo urine testing at home, which not only saves various hospital expenses, but also makes it more convenient for family members to take care of the patient. At home, family members can take care of personal and family affairs and have more time to care for the patient. In addition, patients with a certain degree of self-care ability can also recuperate alone at home and know their physical health status in real time as needed.

[0130] For example, in a hospital, users need to queue up for testing first. During the testing process, users can only take samples by themselves while using the toilet. After sampling is completed, the samples are handed over to medical staff for testing and analysis. The sampling process of the whole process is inconvenient, and queuing is time-consuming. If the smart toilet provided by this application is used, customers do not need to go to the hospital or queue up, and the sampling process is relatively simple, which is more convenient to use and saves time and effort.

[0131] The smart toilet includes a toilet body 100, a toilet seat 200, a toilet lid 300, a urine sampler 400, and a urine detection module. The toilet body 100, as the base of the smart toilet, has the function of carrying various components and can also realize the defecation function of an ordinary toilet. The toilet seat 200 is set on the toilet body 100. The toilet seat 200 has a high degree of fit with the human body and can increase the user's comfort when using the toilet. For example, in cold weather, putting the toilet seat 200 on the toilet can prevent the cold toilet from coming into direct contact with the human body. In addition, a toilet with a toilet seat 200 is more hygienic and healthy. When the toilet is flushed, there is a certain water pressure, which will cause bacteria to splash around, while the toilet seat 200 has a certain isolation and protection effect. The toilet lid 300 ensures the hygiene of the toilet. When the toilet is not in use, the lid 300 is closed, sealing the toilet body 100 and preventing impurities such as bacteria, dust, or liquids from entering the toilet. The urine sampler 400 can be located inside the toilet body 100 or above the toilet body 100, located on the path where urine flows into the toilet body 100, for sampling urine. The urine detection module is located in the toilet lid 300 or the toilet body 100 and is used to sample the urine sampled by the urine sampler 400.

[0132] To facilitate understanding of the structure of the smart toilet, the following is a further description of the various components of the smart toilet:

[0133] The toilet body 100 includes a base 110 and a toilet bowl 120. The lower surface of the base 110 contacts the ground, while the upper surface of the base 110 contacts the toilet seat 200. The length and width of the upper surface of the base 110 are both greater than those of the lower surface, providing a larger toilet space while occupying a small space. The toilet bowl 120 has a conical structure, which is inverted and positioned with the apex located below the bottom surface. The toilet body 100 also includes a sewer pipe, one end of which is connected to the apex of the cone of the toilet bowl 120 and the other end is connected to the toilet bowl. The conical structure effectively collects urine and feces in the toilet bowl 120, as well as the cleaning fluid during flushing.

[0134] The toilet cover 300 includes a toilet front cover 310 and a toilet rear cover 320. The toilet rear cover 320 is fixedly mounted on the toilet body 100 and is located at the rear of the toilet body 100. The toilet front cover 310 is rotatably connected to the toilet body 100 or the toilet rear cover 320, is located at the front of the toilet, covers the toilet seat 200, and covers the toilet bowl 120. Preferably, in this embodiment, the toilet front cover 310 and the toilet rear cover 320 are rotatably connected. Specifically, a first rotation axis 321 is provided on both sides of the toilet rear cover 320. A first bearing 311 is provided on the toilet front cover 310, and the first rotation axis 321 is mounted on the first bearing 311. The toilet front cover 310 can rotate back and forth relative to the toilet rear cover 320 to cover the toilet bowl 120 and protect the toilet. When the toilet front cover 310 is lifted, the user can use the toilet or perform a urine test. When the toilet front cover 310 is rotationally connected to the toilet body 100, a second rotating shaft (not shown) is fixedly provided on the toilet body 100, and a second bearing (not shown) is provided on the toilet front cover 310. The second bearing is sleeved on the second rotating shaft, and the toilet front cover 310 can rotate back and forth relative to the toilet body 100.

[0135] When the toilet front cover 310 covers the toilet bowl 120, the toilet seat 200 is arranged between the toilet front cover 310 and the toilet body 100. The toilet cover 300 can also protect the toilet seat 200. The toilet seat 200 is rotatably connected to the toilet body 100 or the toilet cover 300. A third bearing 210 is provided on the toilet seat 200. In this way, when the toilet seat 200 is connected to the toilet cover 300, the third bearing 210 is connected to the first rotating shaft 321. When the toilet seat 200 is connected to the toilet body 100, the third bearing 210 is connected to the second rotating shaft.

[0136] The smart toilet also includes a consumables storage box 600, which is used to provide detection conditions for the urine detection module. The consumables storage box 600 includes a number of replaceable reagent consumable boxes 620, which contain reagents for mixing with urine.

[0137] The urine detection module includes an optical urine detection module, which is mounted on the toilet body 100 or the toilet lid 300. The optical urine detection module includes a microscopic image acquisition module 720, a fluorescent image acquisition module, and a spectral information acquisition module. The microscopic image acquisition module 720 uses the microscopic image-based urine detection method described later for urine detection. The fluorescent image acquisition module uses the fluorescent reagent-based urine component detection method described later for urine detection. The spectral information acquisition module uses the spectral detection method for urine components described later for urine detection. The urine detection module also includes a chemical urine detection module, which is mounted on the toilet body 100 or the toilet lid 300. The chemical urine detection module includes a dry chemical urine detection module and an electrochemical body fluid detection device 750. The electrochemical body fluid detection device 750 of this embodiment uses the urine electrochemical detection method described later for urine detection.

[0138] The smart toilet also includes a control system, a urine transmission pipe 780 and a sampling micro-flow pump 500. The urine transmission pipe 780 is used to transmit urine. The sampling micro-flow pump 500 can remove bubbles in urine and can also quantitatively obtain and transport urine. The control system is used to control the urine sampler 400 for urine sampling and control the urine detection module 700 for urine detection.

[0139] Example 2

[0140] The smart toilet includes a urine sampler 400 , which can be disposed inside the toilet body 100 or above the toilet body 100 for sampling urine flowing into the toilet.

[0141] See Figure 10 and Figure 11 The present invention provides a urine sampler. The urine sampler 400 includes a switching mechanism 420 and a urine sampling head 410. The urine sampling head 410 is detachably connected to the switching mechanism 420. The urine sampling head 410 directly contacts the urine to sample the urine.

[0142] Specifically, the urine sampling head 410 includes an elastic member 412a, and the adapter mechanism 420 includes an adapter mechanism body 421. The adapter mechanism body 421 is provided with a mounting cavity 421b. The elastic member 412a is inserted into the mounting cavity 421b. The elastic member 412a is elastically connected to the mounting cavity 421b. Under the action of an external force, the urine sampling head 410 can be inserted or removed. When the urine sampler 400 is clogged or needs to be cleaned, the urine sampling head 410 can be easily disassembled, thereby cleaning, repairing or replacing the urine sampling head 410 and the urine sampler 400. The operation is simple and convenient.

[0143] Example 3

[0144] See Figure 5 and Figure 6 The embodiment of the present invention discloses a urine sampling head 410, which includes a sampling head body 411 and a connecting mechanism 412. The sampling head body 411 is provided with a through hole 411a for preventing foreign matter from entering. When external urine enters the sampling head body 411 through the through hole 411a, the through hole 411a can filter the urine and block foreign matter in the urine from entering the sampling head body 411. The connecting mechanism 412 is provided at one end of the sampling head body 411. 12 is provided with a detachable structure, which enables the urine sampling head 410 to be detachably connected to the sampling device as a whole. The sampling device as a whole is a device that can be used for urine sampling. Under the action of external force, the urine sampling head 410 is connected to the sampling device as a whole, and the sampling device as a whole and the urine sampling head 410 are driven to perform urine sampling. The urine sampling head 410 and the sampling device as a whole are disassembled to clean, repair or replace the urine sampling head 410 and the sampling device as a whole. The structure is simple and the operation is convenient.

[0145] To facilitate understanding of the structure of the urine sampling head 410, the components of the urine sampling head 410 are described separately as follows:

[0146] The specific structure of the detachable structure is not limited here, as long as the urine sampling head 410 can be detachably connected to the sampling device as a whole. In this embodiment, the detachable structure includes at least one of detachable structures such as elastic parts, threaded structures and snaps. Preferably, the detachable structure uses elastic parts, which have good connection performance and are easy to install and disassemble.

[0147] For further information, see Figures 5 to 7 The connecting mechanism 412 is provided with an elastic member 412a. When the urine sampling head 410 is connected to the urine sampler 400, the elastic member 412a will cooperate with the urine sampler 400, and the elastic force of the elastic member 412a will act on the urine sampler 400. The urine sampler 400 will also apply an opposite force to the elastic member 412a. At the same time, there is friction between the elastic member 412a and the urine sampler 400. Under the action of the friction, the urine sampling head 410 and the urine sampler 400 are stably connected. When the urine sampling head 410 needs to be disassembled, an external force is applied to the urine sampling head 410 and the urine sampler 400. The applied external force is greater than the friction between the elastic member 412a and the urine sampler 400, and the urine sampling head 410 can be pulled out.

[0148] The elastic member 412a is an independent component. A groove 412b or a protrusion 412c is provided on the connecting mechanism 412. The elastic member 412a matches the groove 412b or the protrusion 412c. The elastic member 412a is sleeved on the groove 412b or the protrusion 412c and fixed by the groove 412b or the protrusion 412c. When the elastic member 412a needs to be installed, the elastic member 412a is opened under the action of external force, so that the elastic member 412a can pass through the connecting mechanism 412 and enter the periphery of the groove 412b or the protrusion 412c. At this time, the external force is removed, so that the elastic member 412a is sleeved on the groove 412b or the protrusion 412c. There can be one or more elastic parts 412a. When there is only one elastic part 412a, the elastic part 412a is matched with the connecting mechanism 412. The elastic part 412a may slide out of the groove 412b or the protrusion 412c under the action of external force, and the installation cannot be completed. Preferably, the number of elastic parts 412a can be set to multiple. Multiple elastic parts 412a are not easy to slide out of the groove 412b or the protrusion 412c, which can improve the stability of the connection. Of course, the number of grooves 412b or protrusions 412c should be consistent with the number of elastic parts 412a. Furthermore, the elastic member 412a includes one or more of an O-ring, a V-ring, a rectangular ring, a wedge-shaped ring, an X-ring, an L-ring, a U-ring, a grooved O-ring, or a star-shaped ring. When multiple elastic members 412a of different shapes are selected, it is necessary to ensure that each elastic member 412a can fully connect with the groove 412b or the protrusion 412c. Preferably, multiple elastic members 412a of the same shape, such as O-rings, are selected to ensure more complete contact with the urine sampler 400 and easier processing. It is understood that the shape of the groove 412b or the protrusion 412c is adapted to the shape of the elastic member 412a. When the elastic member 412a has a protrusion 412c structure, the groove 412b is selected to match the protrusion 412c. When the elastic member 412a has a groove 412b structure, the protrusion 412c structure that matches the groove 412b is selected.

[0149] In one embodiment, the elastic member 412a is integrated into the connecting mechanism 412, and the elastic member 412a and the connecting mechanism 412 are integrally arranged. In this case, the connecting mechanism 412 does not include the groove 412b or the protrusion 412c. The elastic member 412a can be an annular structure, covering the circumference of the connecting mechanism 412. The contact area between the elastic member 412a and the urine sampler 400 is larger, and the connection is more stable.

[0150] In addition to fixing the urine sampling head 410, the elastic member 412a also has a sealing function. The inner ring of the elastic member 412a fits tightly with the groove 412b or the protrusion 412c, and the outer ring of the elastic member 412a fits tightly with the urine sampler 400. The elastic member 412a itself has a waterproof effect. In this way, the elastic member 412a can prevent the filtered urine from flowing out of the connecting mechanism 412, thereby gathering the urine in the sampling head body 411, providing sufficient urine samples for the urine detection module.

[0151] In this embodiment, the sampling head body 411 is made of metal, ceramic, plastic or other materials, which are not limited here. Preferably, the sampling head body 411 should be made of a material with strong corrosion resistance, such as ceramic.

[0152] See Figure 5 The sampling head body 411 includes a sampling head upper portion 411b and a sampling head lower portion 411c. A through hole 411a is provided in the sampling head upper portion 411b. The sampling head upper portion 411b is in direct contact with urine. Urine flows into the sampling head body 411 through the through hole 411a. The shape of the through hole 411a is not limited herein. Preferably, it can be a geometric shape such as a circle, a square, an ellipse, or a triangle. The purpose of providing the through hole 411a is to prevent foreign matter from entering the sampling head body 411. Foreign matter can be coarse granular matter. Any matter whose minimum width is greater than the maximum width of the through hole 411a can be filtered by the through hole 411a. Furthermore, the through holes 411a are arranged at intervals in the sampling head upper portion 411b in a certain arrangement manner. They can be arranged in an array or in a staggered arrangement. The arrangement is as uniform as possible to fully utilize the area of ​​the sampling head upper portion 411b, so that more through holes 411a can be provided in the sampling head upper portion 411b, thereby increasing the amount of liquid entering and improving the filtering effect.

[0153] See Figure 7 The sampling head body 411 further includes a urine transfer pipe 780, which is used to transfer urine passing through the upper portion 411b of the sampling head. After the urine enters the urine transfer pipe 780, the urine transfer pipe 780 transfers the urine to the urine detection module for urine detection.

[0154] For further information, see Figures 5 to 9, the upper part 411b of the sampling head is flat, concave or convex. The urine is in direct contact with the upper part 411b of the sampling head. When the upper part 411b of the sampling head is a flat structure, the sampling head is easy to process and can save costs; when the upper part 411b of the sampling head is a concave structure, the urine remaining on the upper part 411b of the sampling head will flow into the sampling head body 411 along the concave structure as much as possible, resulting in less urine loss, fast urine collection speed, and higher detection efficiency; when the upper part 411b of the sampling head is a convex structure, the internal volume of the sampling head body 411 is larger, and the urine sampling head 410 has a larger liquid storage capacity, which can provide sufficient urine samples. The above three structures are selected according to actual conditions. Since the urine sampling head 410 is independently set, the sampling heads of the above three stages can be processed, and a more suitable sampling head can be selected in different situations.

[0155] Furthermore, the lower portion 411 c of the sampling head completely or partially accommodates the urine filtered through the through hole 411 a.

[0156] In the case where the lower portion 411c of the sampling head partially accommodates filtered urine, the lower portion 411c of the sampling head is sealed or not sealed, and the urine passes through the filter structure directly downward after being filtered through the through hole 411a, and will not gather in the filter structure. In this case, the setting position of the urine transmission pipe 780 is not fixed, and the opening of the pipe is set on the path of urine inflow, and part of the urine flows directly into the urine transmission pipe 780. At this time, the urine samples obtained by the urine sampler 400 are all fresh urine, and the urine detection module performs detection based on the fresh urine, and the reference value of the detection result is higher.

[0157] When the liquid collection chamber completely contains the filtered urine, the lower portion 411c of the sampling head is completely sealed, and the urine is collected in the sampling head body 411. The end of the urine transfer pipe 780 is close to or close to the bottom of the lower portion 411c of the sampling head. The urine transfer pipe 780 can more stably absorb urine, with fewer bubbles in the urine, and can absorb a larger amount of urine, thereby improving detection efficiency.

[0158] Furthermore, the connecting mechanism 412 includes a limiting mechanism 412d, which is used to limit the assembly angle of the urine sampling head 410. Specifically, the limiting mechanism 412d is a limiting boss or a limiting groove. The adapter mechanism 420 of the urine sampler 400 is connected to the connecting mechanism 412. The adapter mechanism 420 is provided with a transfer groove 421a or a transfer boss that matches the limiting boss or the limiting groove. The boss cooperates with the groove to limit the assembly angle of the urine sampling head 410 and prevent the installed urine sampling head 410 from rotating, making the connection more stable.

[0159] The sampling head body 411 and the connecting mechanism 412 are integrated or detachably connected. The integrated configuration has fewer production steps, and the detachably connected sampling head body 411 and the connecting mechanism 412 are less difficult to process. In this embodiment, the sampling head body 411 and the connecting mechanism 412 are integrated.

[0160] Example 4

[0161] The smart toilet also includes a sampling micro-flow pump 500, which is arranged on the urine transmission pipeline between the urine sampler 400 and the urine detection module, and can be used to remove gas in the urine. Through the setting of the sampling micro-flow pump 500, urine detection can be realized in real time and controllable settings, which facilitates accurate urine detection and control.

[0162] Example 5

[0163] See Figures 12 to 14 The embodiment of the present invention discloses a replaceable reagent consumable box 620, which includes a consumable box body 621, a consumable box reagent inlet 622, a consumable box reagent outlet 623 and a consumable box seal 624. The consumable box reagent inlet 622 and the consumable box reagent outlet 623 are both arranged on the consumable box body 621, and the consumable box seal 624 is arranged at the consumable box reagent outlet 623. When the consumable box body 621 is installed, the consumable box seal 624 is opened under the action of external force, and the consumable box reagent outlet 623 is connected to the outside world. The reagent in the replaceable reagent consumable box 620 can flow out from the consumable box reagent outlet 623 and mix with urine in the next process; when the consumable box body 621 is disassembled, the consumable box seal 624 is reset, the consumable box reagent outlet 623 is closed, and the reagent cannot flow out of the consumable box reagent outlet 623 and is stored in the replaceable reagent consumable box 620. The provision of the consumable box seal 624 allows the replaceable reagent consumable box 620 to be disassembled at will and conveniently. After disassembly, the replaceable reagent consumable box 620 has good sealing performance, making it easy to add or replace reagents.

[0164] To facilitate understanding of the structure of the replaceable reagent consumable box 620, the consumable box body 621, the consumable box reagent inlet 622, the consumable box reagent outlet 623 and the consumable box seal 624 are described separately as follows:

[0165] The shape of the consumable box body 621 can be a tetrahedron, a cone, a cylinder or other polyhedron structure, and its structure is not limited. In this embodiment, the consumable box body 621 is preferably a rectangular structure. When there are multiple replaceable reagent consumable boxes 620, the consumable box body 621 with a rectangular structure will be installed more compactly. Because the internal structure of the smart toilet is complicated and the space is limited, the compact installation of the consumable box body 621 can be reasonably used in the internal space of the smart toilet. Moreover, the volume of the rectangular consumable box body 621 is larger. When occupying the same space, the rectangular consumable box body 621 has a larger capacity and can accommodate more reagents.

[0166] The reagent inlet 622 of the consumable box is set on the consumable box body 621, and can be set on the top surface of the consumable box body 621, or on the side of the consumable box body 621. When the reagent inlet 622 of the consumable box is set on the side of the consumable box body 621, it should be set as high as possible. In this embodiment, preferably, the reagent inlet 622 of the consumable box is set on the top surface of the consumable box body 621. The higher the position of the reagent inlet 622 of the consumable box is set, the less likely it is to affect the storage of the reagent. For example: the reagent inlet 622 of the consumable box is set on the side of the consumable box body 621, the liquid level of the reagent should be lower than the lowest point of the reagent inlet 622 of the consumable box. When the reagent inlet 622 of the consumable box is set on the top surface of the consumable box body 621, the reagent can fill the entire container, and there is no situation where the liquid level height is limited.

[0167] See Figure 13An electronic tag 621a for reading reagent information is provided on the outside of the consumable box body 621. When the replaceable reagent consumable box 620 is filled with reagents, the electronic tag 621a can detect the reagents and read the relevant information of the reagents, including the reagent model, reagent capacity, reagent quality, and reagent storage time. Furthermore, the electronic tag 621a is an RFID or NFC tag. RFID technology - radio frequency identification, also known as radio frequency identification technology (RFID), is a type of automatic identification technology that performs non-contact two-way data communication through wireless radio frequency, and uses wireless radio frequency to read and write recording media (electronic tags or radio frequency cards), thereby achieving the purpose of identifying targets and exchanging data. NFC (Near Field Communication) is an emerging technology that enables devices (such as mobile phones) to exchange data when in close proximity. It is an evolution of contactless radio frequency identification (RFID) and interconnection technologies. By integrating an inductive card reader, inductive card, and point-to-point communication functions on a single chip, it enables mobile payment, electronic ticketing, access control, mobile identity recognition, anti-counterfeiting, and other applications using mobile terminals. RFID tags are preferably used in this embodiment for their low cost and high stability.

[0168] See Figure 12 A transparent member 621b is provided on the outside of the consumable box body 621 for checking the reagent capacity. The transparent member 621b can be made of glass or transparent tape to achieve both sealing and observation functions. Furthermore, a scale is provided on the transparent member 621b, and the scale range covers the height range of the reagent to accurately detect the reagent capacity.

[0169] See Figure 14 The consumable box body 621 is also provided with a mounting hole 621c. The consumable box sealing member 624 includes a reset member 624a, a spring pin 624b, and a cover plate 624c. The reset member 624a is disposed in the mounting hole 621c and reciprocates within the mounting hole 621c. The spring pin 624b is disposed at the lower end of the reset member 624a. The reset member 624a drives the spring pin 624b to reciprocate, and during the reciprocating motion of the spring pin 624b, the reagent outlet 623 of the consumable box can be closed and opened. The cover plate 624c is disposed at the upper end of the reset member 624a. The cover plate 624c is used to support the reset member 624a and limit the reset position of the reset member 624a. The reset member 624a is fixedly disposed on the cover plate 624c. The cover plate 624c is fixedly disposed in the replaceable reagent consumable box 620. The direction of the reciprocating motion of the reset member 624a is away from the cover plate 624c.

[0170] When the consumables box body 621 is installed, the spring pin 624b compresses the reset member 624a under the action of an external force, so that the spring pin 624b does not contact the consumables box reagent outlet 623. The cover plate 624c is connected to the reset member 624a, and the reagent flows out of the consumables box reagent outlet 623 from the consumables box body 621 through the cover plate 624c, the reset member 624a, and the spring pin 624b. Furthermore, the cover plate 624c is provided with a plurality of small holes for the flow of reagent. These small holes are arranged in a frame shape on the cover plate 624c, which not only supports the reset member 624a but also allows the circulation of reagent. A first gap 625 is formed between the reset member 624a and the wall of the mounting hole 621c, through which the reagent can flow out of the consumables box reagent outlet 623. In this embodiment, the reset member 624a is preferably a spring, the width of which is smaller than the diameter of the mounting hole 621c. The spring is hollow in the middle, allowing the reagent to flow into the spring through the cover, out of the spring into the first gap 625, and then out through the first gap 625. A second gap 626 is formed between the spring pin 624b and the wall of the mounting hole 621c. The first gap 625 is connected to the second gap 626, and the second gap 626 is connected to the reagent outlet 623 of the consumables box. The reagent flows through the first gap 625 into the second gap 626 and then out of the reagent outlet 623 of the consumables box. In this embodiment, the width of the spring pin 624b is smaller than the diameter of the mounting hole 621c. The spring pin 624b is fixedly connected to the reset member 624a, and the seal between the spring pin 624b and the reset member 624a allows the reagent to flow smoothly out of the reagent outlet 623 of the consumables box.

[0171] The position of the spring needle 624b corresponds to the position of the reagent outlet 623 of the consumable box. When the consumable box body 621 is disassembled, the external force is removed, the reset member 624a is reset, and the reset member 624a drives the spring needle 624b to move downward until the spring needle 624b contacts the reagent outlet 623 of the consumable box. The lower end surface of the spring needle 624b covers the reagent outlet 623 of the consumable box, thereby closing the reagent outlet 623 of the consumable box.

[0172] Example 6

[0173] See Figures 15 to 17 The embodiment of the present invention discloses a consumables storage box 600, which includes a consumables storage box body 610 and an electronic tag reader 611. The consumables storage box body 610 contains a number of replaceable reagent consumable boxes 620, and the replaceable reagent consumable boxes 620 contain a number of reagents. The multiple reagents can be simultaneously combined with sample urine to form a number of different mixed liquids to perform different types of tests and improve the detection accuracy and range. The electronic tag reader 611 is set on the consumables storage box body 610 and is used to read the electronic tag 621a data on the replaceable reagent consumable box 620. The electronic tag 621a data includes the data of each reagent so that the operator can know the relevant information of the reagent in a timely manner.

[0174] To facilitate understanding of the structure of the consumables storage box 600, the consumables storage box body 610, the electronic tag reader 611 and the replaceable reagent consumables box 620 are described separately as follows:

[0175] The types of reagents contained in the consumables storage box body 610 are limited by the operator. Multiple reagents are placed in the replaceable reagent consumable box 620, which is convenient for operation and allows for unified management, and can also fully utilize the narrow internal space of the smart toilet. In this embodiment, preferably, the reagents include four types. After the four reagents are mixed with urine, the respective mixtures are respectively sent to the urine detection module for microscopic examination, fluorescence detection, spectral detection, and electrochemical detection. Multiple detection methods can improve the range and accuracy of urine detection.

[0176] For preference, see Figure 15 The consumables storage box 600 also includes a consumables storage box cover 630, which is used to seal the consumables storage box body 610. When the consumables box needs to be replaced, the consumables storage box cover 630 is opened and the consumables box is placed in the consumables storage box body 610. After placement, the consumables storage box cover 630 is installed to seal the consumables storage box body 610. Furthermore, the consumables box is fastened between the consumables storage box body 610 and the consumables storage box cover 630 to secure the consumables box.

[0177] See Figure 15 The consumables storage box body 610 is provided with a transparent window 612, which is used to observe the reagent capacity. The replaceable reagent consumable box 620 is provided with a transparent part 621b. The position of the transparent window 612 corresponds to the position of the transparent part 621b on the replaceable reagent consumable box 620. The transparent part 621b corresponds to the reagent in the replaceable reagent consumable box 620. The reagent capacity in the replaceable reagent consumable box 620 can be observed through the transparent part 621b. In order to facilitate more intuitive observation of the reagent capacity in several replaceable reagent consumable boxes 620, it is necessary to provide a transparent window 612 to observe the information reflected by the transparent part 621b. Furthermore, the transparent window 612 can be partially transparent or fully transparent, and its degree of transparency will determine the accuracy of the operator's observation. In this embodiment, a fully transparent transparent window 612 is selected for better observation. Furthermore, the transparent window 612 can be made of transparent elements such as glass. Of course, in order to ensure that the reagent capacity reflected by the transparent part 621b is more intuitive, the transparent window 612 can be just a window, and no other components are installed in the window. The operator can directly observe the reagent capacity reflected by the transparent part 621b through the window, and the observation effect is better. However, in this embodiment, a transparent window 612 with glass is preferably used to effectively isolate external dust and prevent dust from entering the replaceable reagent consumable box 620 and affecting the detection effect.

[0178] See Figure 17 The consumables storage box body 610 is provided with a plurality of ejector pins 613 at the bottom thereof. The ejector pins 613 are used to open the reagent outlet 623 of the replaceable reagent consumable box 620. The positions of the ejector pins 613 correspond to the positions of the spring pins 624b of the replaceable reagent consumable box 620. The ejector pins 613 can provide external force to the replaceable reagent consumable box 620. When the replaceable reagent consumable box 620 is installed, the ejector pins 613 contact the spring pins 624b, the reset member 624a is compressed, and the reagent outlet 623 of the replaceable reagent consumable box 620 is connected to the outside world. The reagent in the replaceable reagent consumable box 620 can flow out from the reagent outlet 623 of the consumable box. When the replaceable reagent consumable box 620 is disassembled, the spring pin 624b moves away from the ejector pin 613 until the ejector pin 613 is no longer in contact with the spring pin 624b. There is no external force acting on the spring pin 624b, and the reset member 624a is reset. The spring pin 624b closes the reagent outlet 623 of the consumable box.

[0179] For further information, see Figure 16 The consumables storage box body 610 also includes a consumables storage box liquid outlet 614. The position of the consumables storage box liquid outlet 614 corresponds to the position of the consumables box reagent outlet 623. The reagent flows out of the consumables storage box 600 from the consumables box reagent outlet 623 through the consumables storage box liquid outlet 614. The reagent enters the next detection process and mixes with urine to form a mixed liquid. The human body condition is judged by detecting relevant data of the mixed liquid.

[0180] For further information, see Figure 16An electronic tag 621a for reading reagent information is provided on the outside of the consumable box body 621, and an electronic tag reader 611 is provided on the consumable storage box body 610. The position of the electronic tag reader 611 corresponds to the position of the electronic tag 621a on the replaceable reagent consumable box 620. When the replaceable reagent consumable box 620 is loaded with reagents, the electronic tag 621a can detect the reagents and read relevant information about the reagents, including information such as the reagent model, reagent capacity, reagent quality, and reagent storage time. The electronic tag reader 611 can read and write the reagent information obtained by the electronic tag 621a, thereby realizing monitoring and correction of the reagent information. Furthermore, the electronic tag 621a is an RFID electronic tag or an NFC electronic tag 621a, and the electronic tag reader 611 is an RFID or NFC electronic tag reader 611. RFID technology, also known as radio frequency identification (RFID), is a type of automatic identification technology that uses wireless radio frequency to conduct non-contact two-way data communication and reads and writes recording media (electronic tags or radio frequency cards) using wireless radio frequency, thereby achieving the purpose of identifying targets and exchanging data. NFC technology, also known as near-field communication (NFC), is an emerging technology that enables devices (such as mobile phones) using NFC technology to exchange data when they are close to each other. It is an integration of contactless radio frequency identification (RFID) and interconnection technologies. By integrating the functions of an inductive card reader, an inductive card, and point-to-point communication on a single chip, it uses mobile terminals to implement applications such as mobile payment, electronic ticketing, access control, mobile identity recognition, and anti-counterfeiting. Preferably, in this embodiment, RFID electronic tags and RFID electronic tag readers are selected for higher stability.

[0181] Example 7

[0182] See Figures 18 to 20 The embodiment of the present invention discloses a microfluidic detection chip 710, which is arranged in an optical urine detection module to provide a detection environment for optical urine detection. Specifically, the optical urine detection module includes a microscopic image acquisition module 720, a fluorescence image acquisition module 740 and a spectral image acquisition module, all of which are equipped with the microfluidic detection chip 710.

[0183] See Figure 18 and Figure 19The microfluidic detection chip 710 provided by the present invention includes a detection chip body 711, a detection chip sampling port 712, a sample detection chamber 713 and a first microchannel 714. The sample detection chamber 713 is arranged in the detection chip body 711 for accommodating and assisting in detecting samples. The first microchannel 714 is arranged in the detection chip body 711. The sample flows from the detection chip sampling port 712 through the first microchannel 714 into the sample detection chamber 713. In this embodiment, the detection chip sampling port 712, the sample detection chamber 713 and the first microchannel 714 are connected in sequence. The sample can flow directly into the sample detection chamber 713 through the first microchannel 714 for detection. The microfluidic detection chip 710 has a high degree of integration, does not require manual transfer of detection samples, and the detection process is relatively simple.

[0184] The microfluidic detection chip 710 is detachably connected to the microscopic image acquisition module 720, the fluorescence image acquisition module 740, and the spectral image acquisition module. When the detection chip body 711 in the three is contaminated, the microfluidic detection chip 710 can be disassembled and the contaminated detection device can be replaced to ensure the accuracy of the detection results.

[0185] The microfluidic detection chip 710 is easy to clean. A cleaning solution is injected into the first microchannel 714 and the cleaned sample flows out from the second microchannel 716 . This makes it easier to clean the detection chip body 711 , the first microchannel 714 and the second microchannel 716 .

[0186] To facilitate understanding of the structure of the microfluidic detection chip 710, the detection chip body 711, the detection chip inlet 712, the sample detection chamber 713 and the first microchannel 714 are described separately as follows:

[0187] See Figures 18 to 20 , the sample detection chamber 713 is partially transparent or fully transparent. The sample detection chamber is used to assist in the detection of samples. The sample detection chamber 713 includes an upper cavity wall, a lower cavity wall and a side wall. When the side wall is transparent and the upper cavity wall or the lower cavity wall is also transparent, the sample passes into the interior of the detection chamber, and an external light source can pass through the side wall, the transparent upper cavity wall or the lower cavity wall into the sample detection chamber 713. The light is reflected out of the sample detection chamber 713 through the transparent upper cavity wall or the lower cavity wall, thereby providing a light source environment for sample detection. When the upper cavity wall and the lower cavity wall are both transparent, the light provided by the light source can penetrate the upper cavity wall and the lower cavity wall from one side of the upper cavity wall or the lower cavity wall, providing a light environment for sample detection. The microfluidic detection chip 710 in this embodiment is used to assist in the detection of samples, has a high degree of integration, a simple structure, and reduces the detection cost.

[0188] In this embodiment, the first microfluidic channel 714 is arranged in the detection chip body 711, the sample detection chamber 713 is located in one section of the first microfluidic channel 714, and the detection chip sampling port 712 is arranged at one end of the first microfluidic channel 714 and is connected to the outside world. The sample flows from the detection chip sampling port 712 into the first microfluidic channel 714 and directly enters the sample detection chamber 713. In the sample detection chamber 713, the detection module can directly detect urine without the need for manual transfer of the detection sample, and the detection process is relatively simple.

[0189] The detection chip also includes a detection chip sample outlet 715 and a second microfluidic channel 716. The detection chip sample outlet 715 is located at one end of the second microfluidic channel 716 and is connected to the outside world. The sample flows from the sample detection chamber 713 through the second microfluidic channel 716 and out of the detection chip sample outlet 715. The second microfluidic channel 716 is located within the detection chip body 711. The first microfluidic channel 714 is connected to the second microfluidic channel 716. The sample first enters the sample detection chamber 713 from the first microfluidic channel 714, then flows from the sample detection chamber 713 into the second microfluidic channel 716, and finally flows out of the detection chip through the detection chip sample outlet 715, completing the sample detection. In this embodiment, the detection chip includes both the first microfluidic channel 714 and the second microfluidic channel 716. If the sample is a test sample, the sample is tested in the first microfluidic channel 714 and then flows out of the second microfluidic channel 716 as waste liquid. The detection chip is reusable. If the sample is a cleaning solution, the interior of the detection chip can be cleaned for next use.

[0190] In another embodiment, the detection chip only includes the first microfluidic channel 714 but not the second microfluidic channel 716 , and the sample only enters but does not exit, and the detection chip is a disposable product.

[0191] See Figure 19 and Figure 20 The detection chip body 711 also includes a device chamber, which is used to accommodate a detection device, and the detection device is used to provide a detection environment for sample detection.

[0192] Furthermore, the device chamber includes a first device chamber 711a, which is used to accommodate a light-emitting device 711b. Light-emitting device 711b emits light for detecting a sample. The light is projected onto the sample, and the sample, after being projected by the light, is transmitted out of the microfluidic detection chip 710, allowing the optical urine detection module to detect and analyze the sample. Furthermore, light-emitting device 711b includes at least one of an ultraviolet light source, an infrared light source, or a visible light source.

[0193] Furthermore, the device chamber also includes a second device chamber 711c, which is used to accommodate a temperature control device 711d. The location of the second device chamber 711c is not limited herein, as long as it can provide a suitable temperature environment for the sample detection chamber. Preferably, in this embodiment, the second device chamber 711c is located between the first device chamber 711a and the sample detection chamber 713 and is used to adjust the temperature of the sample detection chamber 713. When testing a sample, it is necessary to ensure that the sample is under constant temperature conditions. The temperature control device 711d provides a constant temperature environment for sample testing, and the detection effect is better under constant temperature conditions. Furthermore, the temperature control device 711d is partially or fully translucent and is located between the light-emitting device 711b and the sample. Only when the temperature control device 711d is fully or partially translucent can the light emitted by the light-emitting device 711b be projected onto the sample. Furthermore, the temperature control device 711d includes a temperature sensor and a temperature control unit.

[0194] Furthermore, the device chamber also includes a device seal 711e. In this embodiment, the device seal 711e seals the bottom of the sample detection chamber 713. In other embodiments, the device seal 711e can be set at other locations, as long as the device seal 711e is located between the sample detection chamber 713 and the second device chamber 711c to ensure that the light emitted by the light-emitting device 711b can pass through the device seal 711e to assist in detecting the sample. The device seal 711e also seals the device chamber. The sample detection chamber 713 passes through the first microchannel 714. If the sample flows into the device chamber, it will affect the normal operation of each detection device. Accordingly, the device seal 711e isolates the sample detection chamber 713 from the device chamber, which can effectively prevent sample leakage. Furthermore, the device seal 711e is partially or fully transparent. Only when the device seal 711e is fully or partially transparent can the light emitted by the light-emitting device 711b be projected onto the sample.

[0195] See Figures 18 to 20 The detection chip body 711 also includes a first chamber cover 711f, which is used to seal the sample detection chamber 713 to prevent sample leakage and effectively store the sample. Furthermore, the first chamber cover 711f is partially or fully translucent. Only when the first chamber cover 711f is fully or partially translucent can the light emitted by the light-emitting device 711b be projected onto the sample. Under the illumination of the light source, the translucent chamber cover can transmit relevant information about the sample, facilitating sample analysis.

[0196] The detection chip body 711 also includes a second chamber cover 711g, which is provided on one side of the second microchannel 716 and is used to seal the second microchannel 716. The first chamber cover 711f and the second chamber cover 711g seal the entire detection chip body 711. The second chamber cover 711g serves as a supporting body to support and accommodate each detection device, and the first chamber cover 711f serves as a cover plate to cover the second chamber cover 711g. The first chamber cover 711f and the second chamber cover 711g are detachably connected. Specifically, the first chamber cover 711f and the second chamber cover 711g are connected by snapping, bonding, or sliding. By disassembling the first chamber cover 711f, the internal structure of the microfluidic detection chip 710 can be viewed, which facilitates cleaning, repair, or replacement of internal components.

[0197] Furthermore, a sample detection chamber 713 is formed between the first chamber cover 711f and the device chamber. Sample detection chamber 713 is used to store samples to be tested. The location of sample detection chamber 713 corresponds to that of the device chamber. The shape and area of ​​the upper and lower bottom surfaces of sample detection chamber 713 also conform to the cross-sectional shape and area of ​​the device chamber, facilitating sample testing. Specifically, in this embodiment, the shape and area of ​​sample detection chamber 713 are consistent with those of the device chamber. The light source of sample detection chamber 713 can fully illuminate the sample in the sample storage chamber, fully utilizing the light source and achieving higher detection efficiency.

[0198] Example 8

[0199] See Figure 21 and Figure 22 The embodiment of the present invention discloses a microscopic image information acquisition module 730, which includes a microscope body 731, a stage 735 and a microscopic optical information acquisition component 736. The microscope body 731 includes a lens group 732. The sample to be detected is set on the stage 735, which is located on the side where the image of the lens group 732 is incident. The microscopic optical information acquisition component 736 is located on the microscope body 731. The sample to be detected is magnified by the lens group 732 to form a current microscopic image of the sample to be detected. The current microscopic image of the sample to be detected reflects the current state of the sample to be detected. The microscopic optical information acquisition component 736 located on the microscope body 731 can capture the current state of the sample to be detected, extract biological information of the sample to be detected magnified by the microscope, and save the biological information in the form of a picture. The picture can be transferred to the detection site for detection, which has higher detection accuracy. At the same time, in order to avoid detection errors, the picture can also be called for secondary verification. The positions of the stage 735, the microscope body 731 and the microscopic optical information acquisition component 736 are relatively fixed, and the sample to be tested can be directly tested after entering the stage 735, which makes the test more convenient.

[0200] To facilitate understanding of the structure of the microscopic image information acquisition module 730, the microscope body 731, the stage 735, and the microscopic optical information acquisition assembly 736 are described separately as follows:

[0201] See Figure 22 The microscope includes a filter component 734 and a zoom component 733. The filter component 734 is arranged between the microscopic optical information collection component 736 and the zoom component 733. The filter component 734 includes a first filter 734b and a second filter arranged in sequence from one end of the microscopic optical information collection component 736. The first filter 734b and the second filter can select the required radiation band so that the sample presents an image that is easy to observe. The zoom component 733 can change the focal length within a certain range, thereby obtaining different widths of field angles, different sizes of images and different ranges of scenery. The zoom component 733 can change the shooting range by changing the focal length without changing the shooting distance, which is very beneficial for picture composition. In this embodiment, the positions of the filter component 734, the zoom component 733, and the filter component 734 and the zoom component 733 are relatively fixed. The filter component 734 is combined with the zoom component 733 to clearly project the image of the sample.

[0202] Furthermore, the zoom assembly 733 includes a first magnifying lens 733a, a second magnifying lens 733b, and a protective lens 733c, which are sequentially arranged at one end of the filter assembly 734. The first magnifying lens 733a and the second magnifying lens 733b provide a magnifying environment for the sample. The second magnifying lens 733b is positioned in a fixed position. The sample is stored in the microfluidic detection chip 710 and is located between the first and second focal lengths of the second magnifying lens 733b. The image of the sample is outside the second focal length of the first magnifying lens 733a, appearing as an inverted and magnified real image. The second magnifying lens 733b is positioned in a fixed position and magnifies the inverted real image of the first magnifying lens 733a, presenting it as an upright false image. The protective lens 733c is used to protect the internal components of the microscope, preventing external dust or impurities from entering the microscope and contaminating the lenses.

[0203] Furthermore, the first magnifying lens 733a, the second magnifying lens 733b, and the protective lens 733c are centrally aligned and stacked. The first magnifying lens 733a is positioned near the filter assembly 734, the protective lens 733c is positioned at the end of the microscope near the microfluidic detection chip 710, and the second magnifying lens 733b is positioned between the first magnifying lens 733a and the protective lens 733c. This centrally aligned stacking ensures that the relative positions of the first magnifying lens 733a, the second magnifying lens 733b, and the protective lens 733c are fixed, the magnification is a preset magnification, and the position of the stage 735 corresponds to the positions of the first magnifying lens 733a, the second magnifying lens 733b, and the protective lens 733c of the microscope. The relative positions of the sample, the protective lens 733c, the second magnifying lens 733b, and the first magnifying lens 733a are fixed, allowing direct inspection of the sample on the stage 735 without frequent adjustments to the positions of the various components.

[0204] Furthermore, the first magnifying lens 733a is a Fresnel lens, and the second magnifying lens 733b is a meniscus lens or a Fresnel lens. Using a meniscus lens for sample testing can produce the smallest focal point for collimated incident light, resulting in better projection. Fresnel lenses are threaded lenses. Fresnel lenses are typically made of thin sheets of injection-molded polyolefin material, though some are made of glass. One side of the lens surface is smooth, while the other side is engraved with concentric circles from small to large. The texture is designed based on light interference and perturbation, relative sensitivity, and reception angle requirements.

[0205] Furthermore, the protective mirror 733c is a plane mirror, and the microfluidic detection chip 710 includes a light-emitting device 711b. The light source of the light-emitting device 711b is directly projected onto the sample. The position of the sample corresponds to the position of the microscope. The light source emitted by the light-emitting layer will directly project into the microscope, which is inconvenient for observation. The plane mirror has a weak ability to reflect light. The plane mirror is arranged at the end of the microscope near the microfluidic detection chip 710, which can provide a better lighting environment and a better microscope imaging effect.

[0206] See Figure 21 Furthermore, the microscopic optical information acquisition component 736 includes a CCD / CMOS integrated component. The CCD integrated component can convert light into electric charge and store and transfer the charge, and can also take out the stored charge to change the voltage. Therefore, it is an ideal imaging element. The CCD integrated component has the advantages of small size, light weight, no influence of magnetic field, and resistance to vibration and impact. CMOS is a complementary metal oxide semiconductor. There are N semiconductors with negative charge and P semiconductors with positive charge on COMS. The current generated by the two complementary effects is interpreted as a picture and displayed on the chip. The image obtained is low cost and more energy-saving.

[0207] Example 9

[0208] See Figure 21 and Figure 23 The embodiment of the present invention discloses a microscopic image acquisition module 720, which includes a microfluidic detection chip 710 and the aforementioned microscopic image information acquisition module 730. The stage 735 is arranged on the microfluidic detection chip 710. The microfluidic detection chip 710 provides a detection environment for sample detection, such as: a light environment and a constant temperature environment. Accordingly, the image collected by the microscopic image acquisition module 720 will be clearer and can better reflect the relevant information of the sample to be detected.

[0209] Furthermore, the stage 735 is a sample detection chamber 713 provided on the microfluidic detection chip 710 for accommodating a sample.

[0210] Example 10

[0211] See Figure 24 and Figure 25 The embodiment of the present invention discloses an optical information acquisition module 740,

[0212] The optical information acquisition module 740 includes a microfluidic detection chip 710 and an optical information acquisition component 741. The microfluidic detection chip 710 is used to accommodate samples and provide a detection environment for optical detection of the samples to assist in collecting the optical information of the samples. During the image acquisition process, no microscope is required. The microfluidic detection chip 710 can provide a detection environment for optical detection of the samples and assist in collecting the optical information of the samples. The microfluidic detection chip 710 projects the optical image of the sample into the optical information acquisition component 741, and the optical information acquisition component 741 obtains and saves the optical image information of the sample, which can save costs. In addition, the sample can flow into the microfluidic detection chip 710, and the optical information acquisition component 740 directly collects the optical information of the sample. There is no need to manually transfer the detection sample, and the detection process is relatively simple, saving costs.

[0213] To facilitate understanding of the structure of the optical information acquisition module 740 , the microfluidic detection chip 710 and the fluorescence optical information acquisition component 741 are described separately as follows:

[0214] See Figure 26 and Figure 27The microfluidic detection chip 710 provided in an embodiment of the present invention includes a detection chip body 711, a detection chip sampling port 712, a sample detection chamber 713 and a first microchannel 714. The sample detection chamber 713 is arranged in the detection chip body 711 for accommodating and assisting in detecting samples. The first microchannel 714 is arranged in the detection chip body 711. The sample flows from the detection chip sampling port 712 through the first microchannel 714 into the sample detection chamber 713. In this embodiment, the detection chip sampling port 712, the sample detection chamber 713 and the first microchannel 714 are connected in sequence. The sample can flow directly into the sample detection chamber 713 through the first microchannel 714 for detection. The microfluidic detection chip 710 has a high degree of integration, does not require manual transfer of detection samples, and the detection process is relatively simple. The microfluidic detection chip 710 is easy to clean. A cleaning solution is injected into the first microchannel 714 and the cleaned sample flows out from the second microchannel 716 . This makes it easier to clean the detection chip body 711 , the first microchannel 714 and the second microchannel 716 .

[0215] The sample detection chamber 713 is partially transparent or fully transparent. The sample detection chamber is used to assist in the detection of samples. The sample detection chamber 713 includes an upper cavity wall, a lower cavity wall and a side wall. When the side wall is transparent and the upper cavity wall or the lower cavity wall is also transparent, the sample passes into the interior of the detection chamber, and an external light source can pass through the side wall, the transparent upper cavity wall or the lower cavity wall to enter the sample detection chamber 713. The light is reflected out of the sample detection chamber 713 through the transparent upper cavity wall or the lower cavity wall, thereby providing a light source environment for sample detection. When the upper cavity wall and the lower cavity wall are both transparent, the light provided by the light source can penetrate the upper cavity wall and the lower cavity wall from one side of the upper cavity wall or the lower cavity wall, providing a light environment for sample detection. The microfluidic detection chip 710 in this embodiment is used to assist in the detection of samples, has a high degree of integration, a simple structure, and reduces the detection cost.

[0216] In this embodiment, the first microchannel 714 is arranged in the detection chip body 711, the sample detection chamber 713 is located in one section of the first microchannel 714, and the detection chip inlet 712 is arranged at one end of the first microchannel 714 and is connected to the outside world. The sample flows from the detection chip inlet 712 into the first microchannel 714 and directly enters the sample detection chamber 713. In the sample detection chamber 713, the detection module can directly detect the sample without manual transfer of the detection sample, and the detection process is relatively simple.

[0217] The detection chip also includes a detection chip sample outlet 715 and a second microfluidic channel 716. The detection chip sample outlet 715 is located at one end of the second microfluidic channel 716 and is connected to the outside world. The sample flows from the sample detection chamber 713 through the second microfluidic channel 716 and out of the detection chip sample outlet 715. The second microfluidic channel 716 is located within the detection chip body 711. The first microfluidic channel 714 is connected to the second microfluidic channel 716. The sample first enters the sample detection chamber 713 from the first microfluidic channel 714, then flows from the sample detection chamber 713 into the second microfluidic channel 716, and finally flows out of the detection chip through the detection chip sample outlet 715, completing the sample detection. In this embodiment, the detection chip includes both the first microfluidic channel 714 and the second microfluidic channel 716. If the sample is a urine sample, the waste liquid flows out of the second microfluidic channel 716 after the sample is detected by the first microfluidic channel 714. The detection chip is reusable. If the sample is a cleaning solution, the interior of the detection chip can be cleaned for next use.

[0218] In another embodiment, the detection chip only includes the first microfluidic channel 714 but not the second microfluidic channel 716 , and the sample only enters but does not exit, and the detection chip is a disposable product.

[0219] The detection chip body 711 further includes a device chamber, which is used to accommodate a detection device, and the detection device is used to provide a detection environment for sample detection.

[0220] Furthermore, the device chamber includes a first device chamber 711a, which is used to accommodate a light-emitting device 711b. Light-emitting device 711b emits light for detecting a sample. The light is projected onto the sample, and the sample, after being projected by the light, is transmitted out of the microfluidic detection chip 710, allowing the optical sample detection device to detect and analyze the sample. Furthermore, light-emitting device 711b includes at least one of an ultraviolet light source, an infrared light source, or a visible light source.

[0221] When microfluidic detection chip 710 is used to collect fluorescence image information, light-emitting device 711b emits light to excite the fluorescent substance in the sample. The light is projected onto the sample, and the sample, after being projected by the light, transmits light out of microfluidic detection chip 710, allowing optical sample detection equipment to detect and analyze the sample's fluorescence image. Furthermore, light-emitting device 711b includes at least one of an ultraviolet light source and a blue-violet light source.

[0222] When microfluidic detection chip 710 is used to collect spectral information, light-emitting device 711b emits light to excite the sample's spectral information. This light is projected onto the sample, and the sample, after being projected by the light, is transmitted out of microfluidic detection chip 710, allowing optical sample detection equipment to detect and analyze the sample's spectral information. Furthermore, light-emitting device 711b includes at least one of an infrared light source and an X-ray source.

[0223] Furthermore, the device chamber also includes a second device chamber 711c, which is used to accommodate a temperature control device 711d. The location of the second device chamber 711c is not limited herein, as long as it can provide a suitable temperature environment for the sample detection chamber. Preferably, in this embodiment, the second device chamber 711c is located between the first device chamber 711a and the sample detection chamber 713 and is used to adjust the temperature of the sample detection chamber 713. When testing a sample, it is necessary to ensure that the sample is under constant temperature conditions. The temperature control device 711d provides a constant temperature environment for sample testing, and the detection effect is better under constant temperature conditions. Furthermore, the temperature control device 711d is partially or fully translucent and is located between the light-emitting device 711b and the sample. Only when the temperature control device 711d is fully or partially translucent can the light emitted by the light-emitting device 711b be projected onto the sample. Furthermore, the temperature control device 711d includes a temperature sensor and a temperature control unit.

[0224] Furthermore, the device chamber also includes a device seal 711e. In this embodiment, the device seal 711e seals the bottom of the sample detection chamber 713. In other embodiments, the device seal 711e can be set at other locations, as long as the device seal 711e is located between the sample detection chamber 713 and the second device chamber 711c to ensure that the light emitted by the light-emitting device 711b can pass through the device seal 711e to assist in detecting the sample. The device seal 711e also seals the device chamber. The sample detection chamber 713 passes through the first microchannel 714. If the sample flows into the device chamber, it will affect the normal operation of each detection device. Accordingly, the device seal 711e isolates the sample detection chamber 713 from the device chamber, which can effectively prevent sample leakage. Furthermore, the device seal 711e is partially or fully transparent. Only when the device seal 711e is fully or partially transparent can the light emitted by the light-emitting device 711b be projected onto the sample.

[0225] See Figures 18 to 27 The detection chip body 711 also includes a first chamber cover 711f, which is used to seal the sample detection chamber 713 to prevent sample leakage and effectively store the sample. Furthermore, the first chamber cover 711f is partially or fully translucent. Only when the first chamber cover 711f is fully or partially translucent can the light emitted by the light-emitting device 711b be projected onto the sample. Under the illumination of the light source, the translucent chamber cover can transmit relevant information about the sample, facilitating sample analysis.

[0226] Furthermore, the first chamber cover 711f includes an excitation light filter layer 711h, which is located between the light-emitting device 711b and the sample. Excitation light filter layer 711h is used to filter a spectrum of light or light other than fluorescence. When excitation light filter layer 711h is used to filter light other than fluorescence, the excitation light filter layer includes four groups: ultraviolet light, violet light, blue light, and green light.

[0227] The detection chip body 711 also includes a second chamber cover 711g, which is provided on one side of the second microchannel 716 and is used to seal the second microchannel 716. The first chamber cover 711f and the second chamber cover 711g seal the entire detection chip body 711. The second chamber cover 711g serves as a supporting body to support and accommodate each detection device. The first chamber cover 711f serves as a cover plate 624c to cover the second chamber cover 711g. The first chamber cover 711f and the second chamber cover 711g are detachably connected. Specifically, the first chamber cover 711f and the second chamber cover 711g are connected by snapping, bonding, or sliding. By removing the first chamber cover 711f, the internal structure of the microfluidic detection chip 710 can be viewed, facilitating cleaning, repair, or replacement of internal components.

[0228] Furthermore, a sample detection chamber 713 is formed between the first chamber cover 711f and the device chamber. Sample detection chamber 713 is used to store samples to be tested. The location of sample detection chamber 713 corresponds to that of the device chamber. The shape and area of ​​the upper and lower bottom surfaces of sample detection chamber 713 also conform to the cross-sectional shape and area of ​​the device chamber, facilitating sample testing. Specifically, in this embodiment, the shape and area of ​​sample detection chamber 713 are consistent with those of the device chamber. The light source of sample detection chamber 713 can fully illuminate the sample in the sample storage chamber, fully utilizing the light source and achieving higher detection efficiency.

[0229] The optical information acquisition component 741 includes an image information acquisition unit and / or a spectral information acquisition unit. The image information acquisition unit is used to acquire sample image information, and the spectral information acquisition unit is used to acquire sample spectral information. The spectral information acquisition unit can be of any type, as long as it can receive spectral information from the sample. In this embodiment, the spectral information acquisition unit preferably includes light and a micro-spectrometer, wherein the optical fiber receiving path is confocal, i.e., the receiving surface and the object surface are conjugate surfaces, enabling fixed-point spectral reception. One end of the receiving optical fiber is connected to the optical path of the microfluidic detection chip, and the other end is connected to the micro-spectrometer, thereby acquiring spectral information within the microscopic region of the object.

[0230] The image information acquisition unit includes at least one of a fluorescence information acquisition module, a microscopic image information acquisition module 730, and an infrared information acquisition module. As described above, the microscopic image information acquisition module 730 is used to acquire microscopic image information of the sample. The fluorescence information acquisition module and the infrared information acquisition module can acquire fluorescence image information and infrared image information of the sample. The type of fluorescence information acquisition module and the infrared information acquisition module are not limited, as long as they can acquire sample image information. Preferably, in this embodiment, the fluorescence information acquisition module and the infrared information acquisition module can be CCD / CMOS integrated components. CCD integrated components can convert light into electric charge, store and transfer electric charge, and also extract stored charge to change the voltage, making them ideal imaging elements. CCD integrated components have advantages such as small size, light weight, immunity to magnetic fields, and resistance to vibration and impact. CMOS is a complementary metal oxide semiconductor. COMS has negatively charged N and positively charged P semiconductors. The current generated by these two complementary effects is interpreted as an image displayed on the chip. CMOS integrated components are low-cost and more energy-efficient.

[0231] The optical information acquisition component 741 includes a light-emitting device. The light-emitting device includes light sources of different wavelengths, including ultraviolet, infrared, and visible light, providing a light source environment for sample detection. The light-emitting device in this embodiment includes the light-emitting device in the aforementioned microfluidic detection chip. The light-emitting device and the sample detection chamber in the microfluidic detection chip are all located in the microfluidic detection chip, providing an internal light source environment for sample detection. The light-emitting device in this embodiment also provides an external light source environment for sample detection. The sample detection chamber is used to assist in the detection of samples. The sample detection chamber 713 includes an upper cavity wall, a lower cavity wall, and a side wall. When the side wall is transparent and the upper cavity wall or the lower cavity wall is also transparent, the sample enters the detection chamber. The external light source can enter the sample detection chamber 713 through the side wall, the transparent upper cavity wall, or the lower cavity wall without passing through the microfluidic detection chip 710. The light is reflected by the transparent upper cavity wall or the lower cavity wall and exits the sample detection chamber 713. Accordingly, an external light source environment can be provided for sample detection. This embodiment is suitable for use when the microfluidic detection chip 710 is not present or the microfluidic detection chip 710 is not functioning properly.

[0232] The optical information acquisition module includes the aforementioned microscopic image acquisition module 720, as well as a fluorescence image acquisition module and a spectral information acquisition module. It can be applied to urine testing. A urine sample is passed into the sample detection chamber of the microfluidic detection chip, and the optical information acquisition module can collect microscopic images, fluorescence images, and spectral information of the urine sample. The optical information acquisition module is not limited to urine testing and can also be applied to other human biochemical indicator detection fields. Preferably, sample types also include human body fluids such as serum (plasma), urine, and saliva, human tissues such as epithelial tissue, and mixtures of feces and fluids.

[0233] This embodiment provides an optical sample detection device, including the aforementioned microfluidic detection chip and an optical information acquisition module. When the optical sample detection device is used to detect urine samples, the optical sample detection device is an optical urine detection module.

[0234] Example 11

[0235] See Figure 21 、 Figure 23 、 Figure 24 and Figure 3 The embodiment of the present invention discloses a urine detection module, which is arranged on a smart toilet and is used to detect urine. The urine detection module includes a chemical urine detection module and the aforementioned optical urine detection module. The chemical urine detection module detects the chemical components in urine to determine the various inorganic and organic substances in the urine, and through semi-quantitative and quantitative detection of urine, it performs auxiliary diagnosis and efficacy observation on urinary system diseases, liver and gallbladder diseases, diabetes and other diseases, monitors safe medication, and evaluates health status; the optical urine detection module collects urine sample images, sends the collected images to a designated analysis location for analysis or uploads them to the controller of the smart toilet, and the controller controls the analysis component to analyze the images collected by the optical urine detection module, outputs the analysis results of the urine sample, and determines the user's physical condition based on the analysis results.

[0236] The optical urine testing module includes a microscopic image acquisition module 720, a fluorescence image acquisition module, and a spectral information acquisition module. Microscopic image acquisition module 720 uses a microscope to examine the morphology and quantity of cells, casts, and salt crystals in urine. Normal urine generally lacks red blood cells, white blood cells, epithelial cells, or casts. Increased amounts of these components indicate pathological changes in the urinary system, allowing analysis of the user's physical condition. The fluorescence image acquisition module uses fluorescence methods to acquire fluorescence information from urine samples and projects this information directly onto the optical information acquisition component 741, which then captures the fluorescence information. The spectral information acquisition module simultaneously detects the urine sample spectrum and enables real-time image acquisition of the urine sample. The spectrum generates signals related to the observation position, such as the transmitted photon count rate, total or specific peak photoelectron yield, and fluorescence yield. These signals provide various elemental, chemical, and magnetic information, enabling analysis of the user's physical condition.

[0237] Example 12

[0238] See Figures 28 to 31The present embodiment discloses an electrochemical detection chip 760, which is plugged into a body fluid electrochemical detection module 770 and is used to perform electrochemical detection of urine. The electrochemical detection chip 760 includes an insulating substrate 761 and a plurality of chip electrodes 762. The plurality of chip electrodes 762 can be one or more. When there is only one chip electrode 762, urine drops onto the chip electrode 762. When there are multiple chip electrodes 762, the plurality of chip electrodes 762 are arranged at predetermined intervals on the insulating substrate 761. The plurality of chip electrodes 762 form a reaction portion 762a and a conductive portion 762b on the insulating substrate 761. Urine on the reaction portion 762a causes the plurality of chip electrodes 762 to conduct, generating a plurality of electrical signals that are transmitted to the conductive portion 762b for detection. The plurality of electrical signals are used to detect urine electrochemical indicators, eliminating the need for manual visual judgment of urine conditions, and resulting in more accurate urine data. The reaction part is used to react chemically with urine, and the conductive part is used to form an electrical circuit. The conductive part is not necessarily the electrode itself, but can be a connecting conductor as long as it can transmit electrical signals.

[0239] To facilitate understanding of the structure of the electrochemical detection chip 760, the insulating substrate 761 and the plurality of chip electrodes 762 are described separately as follows:

[0240] See Figures 28 to 31 There are at least two chip electrodes 762. Urine is conductive. When urine drops onto at least two chip electrodes 762, the urine connects to the at least two chip electrodes 762. Preferably, taking two chip electrodes 762 as an example, urine connects to the two chip electrodes 762. The two chip electrodes 762 are respectively positive and negative. The conductive portions 762b of the two chip electrodes 762 are connected to the body fluid electrochemical detection module 770. An electrical circuit is formed between the two chip electrodes 762, and the electrical signal on the electrical circuit can be detected. When urine connects to multiple chip electrodes 762, an electrical circuit is formed between each two adjacent chip electrodes 762. By detecting the electrical signals on multiple electrical circuits, multiple sets of data can be compared, and the detection results will be more accurate.

[0241] Furthermore, chip electrode 762 is a patch chip electrode 762. Patch chip electrode 762 is low-cost and easy to install. Simply attach chip electrode 762 to insulating substrate 761. Furthermore, the attached chip electrode 762 is not susceptible to falling off. Furthermore, when there are multiple patch chip electrodes 762, each patch chip electrode 762 has a consistent structure and should be attached at predetermined intervals, preferably at equal intervals, to ensure consistency in the basic parameters of each electrical circuit and reduce detection errors.

[0242] Furthermore, the insulating substrate 761 is an insulating material. In order for the chip electrode 762 to form an electrical circuit, interference from other non-insulating factors needs to be eliminated. Therefore, it is necessary to ensure that the insulating substrate 761 is an insulator. At the same time, the insulating substrate 761 as an insulator will not affect the relevant data information of the electrical circuit, and the detection results will be more accurate.

[0243] Furthermore, the electrochemical indicators include one or more of urine specific gravity, urine pH value, urine protein, uric acid, urine potassium, urine sodium, urine calcium, urine phosphorus, urine sugar, and urine chloride, which can be obtained through electrical signal detection and analysis. Different detection materials are provided on the chip electrodes, and different detection materials can detect the above-mentioned different indicators. The detection principle is the existing technology and will not be elaborated here. The chip electrode on the reaction part itself includes the detection material or the reaction part includes the reaction layer, and the reaction layer is provided with the detection material, and the above-mentioned different electrochemical indicators can be detected by the above-mentioned detection material. Urine specific gravity and urine pH value can be detected directly by the chip electrode itself, without the need to set a reaction layer or detection material.

[0244] See Figures 28 to 31 The reaction portion 762a and the conductive portion 762b are located on the same side of the insulating substrate 761 or are arranged on opposite sides of the insulating substrate. When the reaction portion and the conductive portion are arranged on opposite sides of the insulating substrate, the chip electrode 762 extends from one side of the insulating substrate 761, around the edge of the insulating substrate 761, to the other side, or from one side of the insulating substrate 761, through the interior of the insulating substrate 761, to the other side. This prevents urine from flowing into the conductive portion 762b, causing an electrical short circuit and failing to achieve the purpose of detection. Furthermore, the chip electrode 762 can bypass the long side of the insulating substrate 761 or the short side of the insulating substrate 761. In this embodiment, it is preferred that the chip electrode 762 bypass the short side of the insulating substrate 761. The chip electrode 762 can be laid along the length direction of the insulating substrate 761. The laying distance is longer, and the reaction part 762a and the conductive part 762b are farther apart, which can effectively prevent the urine in the reaction part 762a from flowing into the conductive part 762b. Therefore, the detection results of this embodiment can be made more accurate.

[0245] See Figure 31 In one embodiment, an isolation structure for protecting the reaction portion 762 a and the conductive portion 762 b is provided on the insulating substrate 761 .

[0246] Specifically, the isolation structure includes a first isolator 761a, which isolates the reaction portion 762a and the conductive portion 762b of the substrate from the outside world. The first isolator 761a is compatible with the body fluid electrochemical detection module 770, effectively preventing internal fluid from leaking out. Furthermore, the enclosed space facilitates cleaning of the detection module.

[0247] The isolation structure also includes a second isolation member 761b, which is used to isolate the reaction part 762a from the conductive part 762b. In this case, the height of the reaction part 762a should be lower than the height of the conductive part 762b, so that urine dripping into the reaction part 762a will not penetrate deep into the conductive part 762b, effectively preventing urine from contaminating the conductive part 762b. Furthermore, the second isolation member 761b is a concave structure, and urine flowing into the reaction part 762a is collected in the second isolation member 761b, connecting to the chip electrode 762 in the second isolation member 761b, and urine will not penetrate into the conductive part 762b. Furthermore, each chip electrode 762 includes a chip electrode bend portion, which is adapted to the side wall of the reaction part 762a so that the chip electrode 762 can be continuously and uninterruptedly arranged on the reaction part 762a and the conductive part 762b. Furthermore, a reaction part liquid outlet 762c is provided on the reaction part 762a, and the reaction part liquid outlet 762c extends from the edge of the insulating substrate 761 inside the second isolation member 761b. The liquid in the reaction part 762a can flow out of the reaction part 762a through the reaction part liquid outlet 762c to the bottom of the reaction chamber 771c of the detection module, and the liquid will not overflow into the conductive part 762b, which can effectively protect the conductive part 762b.

[0248] Example 13

[0249] See Figures 32 to 39 The present invention discloses a body fluid electrochemical detection module 770 for detecting human urine. The application is not limited to the field of urine detection, but can also be applied to other human biochemical index detection fields. Preferably, the sample types also include human body fluids such as serum (plasma), urine, saliva, etc., human tissues such as epithelial tissue, and a mixture of feces and liquid, etc. The body fluid electrochemical detection module 770 includes a detection module body 771, an electrochemical injection port 772 and a plurality of connecting electrodes 773. The detection module body 771 includes a reaction area 771a and a connection area 771b. The plurality of connecting electrodes 773 are arranged on the connection area 771b at predetermined intervals. The plurality of connecting electrodes 773 are used to form an electrochemical reaction circuit. The plurality of connecting electrodes 773 can be one or more. When there is one connecting electrode 773, urine drops on the chip electrode 762, and the chip electrode 762 is connected to the connecting electrode 773 to form an electrical circuit. When there are multiple connecting electrodes 773, the plurality of connecting electrodes 773 are arranged on the connection area 771b at predetermined intervals. The liquid enters the reaction area 771a from the electrochemical injection port 772. The liquid includes urine. After the urine enters the reaction area 771a, an electrochemical reaction will occur. The plurality of connecting electrodes 773 can detect a variety of urine data, which can improve the accuracy of urine detection.

[0250] To facilitate understanding of the structure of the body fluid electrochemical detection module 770, the components of the detection module are described separately as follows:

[0251] See Figures 32 to 35 The detection module also includes an electrochemical sampling port 774, which is used for the outflow of liquid. When the liquid is urine, the waste liquid after detection flows from the electrochemical sampling port 774 to the waste liquid pool. When the liquid is a cleaning liquid, the cleaning liquid after cleaning also flows from the electrochemical sampling port 774 to the waste liquid pool. Furthermore, the detection module also includes a sampling pipe 776. The electrochemical sampling port 774 is arranged at one end of the sampling pipe 775. The other end of the sampling pipe 775 is arranged in the reaction area 771a. The liquid from the sampling pipe 775 is discharged from the detection module body 771 through the sampling pipe 776 and the electrochemical sampling port 774.

[0252] Body fluid electrochemical detection module 770 also includes an inlet pipe 775, through which liquid enters reaction zone 771a via electrochemical inlet port 772. The liquid flowing into inlet pipe 775 includes a mixture of urine and reagents. Inlet pipe 775 is equipped with a microfluidic pump to obtain a quantitative liquid sample.

[0253] Furthermore, the sampling conduit 775 includes a sampling conduit outlet 775b, which is directly opposite the reaction zone 771a. This allows the liquid flowing from the sampling conduit 775 to the reaction zone 771a to spread evenly, resulting in more accurate measured data. The sampling conduit 775 also includes a sampling conduit body 775a, which is arranged along the length of the detection module. The sampling conduit 775 also includes a bend 775c, with the sampling conduit outlet 775b located at the end of the bend 775c. The bend 775c is connected to the sampling conduit body 775a at a 90° bend angle, allowing the second liquid outlet of the parallel sampling conduit 775 to be directly opposite the reaction zone 771a.

[0254] Furthermore, the sampling pipe 775 is integrated into the detection module body 771. The sampling pipe 775 can be integrated into the side wall, top wall or interior of the module body, which can support the sampling pipe 775 and prevent the sampling pipe 775 from sliding so that the sampling pipe outlet 775b is misplaced.

[0255] See Figures 34 to 39Furthermore, the reaction area 771a includes a reaction chamber 771c, and a sample outlet pipe 776 is connected to the reaction chamber 771c. The reaction chamber 771c is used to accommodate liquid, specifically to accommodate samples to be tested and waste liquid. The sample outlet pipe 776 is used to discharge the waste liquid out of the detection module body 771. The reaction part 762a of the detection chip is located in the reaction chamber 771c. The reaction part 762a can only accommodate a small amount of liquid flowing in from the sample inlet pipe 775. The excess liquid will flow from the reaction part 762a into the bottom of the reaction chamber 771c and become waste liquid.

[0256] Reaction chamber 771c includes a cavity 771d and a sealing structure 771e. Sealing structure 771e is used to seal cavity 771d, making reaction chamber 771c a closed cavity 771d. After liquid flows into reaction chamber 771c, it flows directly out of sampling pipe 776 without accumulation or overflowing reaction chamber 771c, and liquid does not remain in detection module body 771. Furthermore, sealing structure 771e is provided with a sampling pipe mounting hole 711g. Sampling pipe 775 is connected to reaction chamber 771c through sampling pipe mounting hole 711g. Sampling pipe 775 is sealedly connected to sealing structure 771e through sampling pipe mounting hole 711g.

[0257] For further information, see Figures 35 to 36 A liquid collecting trough 771f is provided at the bottom of the reaction chamber 771c. The liquid collecting trough 771f is connected to the sample outlet pipe 776 and is used to collect the liquid in the reaction zone 771a into the sample outlet pipe 776. The minimum height of the liquid collecting trough 771f is not lower than the minimum height of the sample outlet pipe 776. The sidewalls of the liquid collecting trough 771f are curved or inclined surfaces, and the width of the bottom of the liquid collecting trough 771f is smaller than the height of the top. The liquid in the reaction zone 771a can be collected along the sidewalls of the liquid collecting trough 771f to the bottom of the liquid collecting trough 771f, and then flow into the sample outlet pipe 776 from the bottom.

[0258] The liquid is a urine sample or a cleaning liquid. When the liquid is a urine sample, the urine sample flows from the sampling pipe 775 into the reaction part 762a of the detection chip and forms an electrical circuit. The detection module detects the urine sample parameters through the electrical circuit. Excess urine flows from the reaction part 762a into the reaction chamber 771c. The waste liquid in the reaction chamber 771c will gather in the collection tank 771f and flow into the sampling pipe 776, and finally flow out of the detection module. When the liquid is a cleaning liquid, the liquid cleans the detection module. The cleaning liquid flows from the sampling pipe 775 into the reaction area 771a to clean the reaction part 762a of the detection chip. The excess cleaning liquid and the cleaned waste liquid flow into the reaction chamber 771c, clean the side wall of the cavity 771d and the collection tank 771f, and the cleaned waste liquid flows out of the detection module through the sampling pipe 776.

[0259] Example 14

[0260] See Figure 38 and Figure 39 The present invention discloses an electrochemical body fluid detection device 750, which includes an electrochemical detection chip 760 and the aforementioned body fluid electrochemical detection module 770. The detection module includes a connection area 771b and a reaction area 771a. The detection chip includes a reaction part 762a, a conductive part 762b and an isolation structure. The connection area 771b corresponds to the conductive part b, and the reaction area 771a corresponds to the reaction part 762a. The conductive part 762b is detachably inserted into the connection area 771b. In the reaction area 771a, urine flows into the reaction part 762a, and an electrical circuit is formed on the detection module. The current value on the electrical circuit is measured to calculate the conductivity of the urine. The detection environment of the present invention is relatively wide. When it is necessary to detect the data of multiple urine samples, the detection module can be quickly and conveniently plugged in and out to replace the type of detection module. Different types of detection modules have different electrodes, and different electrodes form different electrical circuits. The current values ​​on different electrical circuits are different, and the final measured conductivity is also different. Based on this, it can be compared and analyzed with the reference value of the substance to be tested that has been pre-entered to obtain different urine sample data. In addition, by analyzing the urine sample data by detecting conductivity, the test results obtained are more accurate. At the same time, the detection module can be reused, which can reduce the detection cost. At the same time, the isolation structure can effectively protect the reaction part 762a and the conductive part 762b.

[0261] Furthermore, the detection module includes a sealing structure 771e, which is used to cooperate with the isolation structure to seal the reaction part 762a and the reaction area 771a. After the sealing structure 771e seals the reaction part 762a and the reaction area 771a, the reaction part 762a and the reaction area 771a can be cleaned.

[0262] Furthermore, the connection electrode 773 of the connection area 771 b is provided corresponding to the chip electrode 762 of the conductive portion 762 b , and the reaction area 771 a is provided corresponding to the reaction portion 762 a .

[0263] Example 15

[0264] See Figures 41 to 43 The present invention discloses a method for detecting urine based on microscopic images, comprising:

[0265] S100, injecting urine into the sample detection chamber;

[0266] The sample detection chamber is located inside the microfluidic detection chip. During the detection process, its position is fixed and its position relative to the microscope body and the microscopic optical information acquisition component is relatively fixed. Urine can be directly injected into the sample detection chamber. After the urine enters the sample detection chamber, it waits to be detected. There is no need to manually adjust the placement of the urine sample, and the detection process is simple.

[0267] S110, controlling the light from the background light source to pass through the wall of the sample detection chamber and enter the sample detection chamber;

[0268] The sample detection chamber includes an upper cavity wall, a lower cavity wall, and a side wall. When the side wall and the upper cavity wall or the lower cavity wall are transparent, the sample is passed into the detection chamber. An external background light source can penetrate the side wall and the transparent upper cavity wall or the lower cavity wall into the sample detection chamber. The light is reflected by the transparent upper cavity wall or the lower cavity wall and then exits the sample detection chamber, thereby providing a lighting environment for sample detection. When both the upper cavity wall and the lower cavity wall are transparent, the light provided by the light source can penetrate the upper cavity wall and the lower cavity wall from one side of the upper cavity wall or the lower cavity wall, providing a lighting environment for sample detection. The background light source set in this step can adapt to the needs of different detection environments.

[0269] S120, collecting microscopic image information of urine through the sample detection chamber;

[0270] The microscopic optical information acquisition assembly of this embodiment is located on one side of the microscope body and can collect microscopic image information from the microscope body. The microscopic optical information acquisition assembly can store the microscopic image information of the collected urine sample and transfer this image information to the testing center for testing, thereby improving detection accuracy. Furthermore, to avoid detection errors, this image information can also be retrieved for secondary verification.

[0271] S130, obtaining a microscopic image of the urine sample;

[0272] The urine microscopic image is captured using a microscopic optical information acquisition component, and the captured microscopic image is saved and sent to the control system for analysis and processing.

[0273] S140, performing preliminary classification of urine sediment using a neural network algorithm;

[0274] In this step, the type of neural network algorithm is not limited, and at least one of a convolutional neural network (CNN), a recurrent neural network (RNN), and a generative adversarial network (GAN) can be selected. Preferably, in this embodiment, the present invention adopts a convolutional neural network (CNN). Urine sediment is a shaped component in urine. It is the sediment formed after urine is centrifuged. It is also a combination of the quality and quantity of urine's formed components. Urine sediment includes various formed components such as cells, casts, crystals, bacteria, and sperm. Urine testing requires determining the content of each component in urine, so it is necessary to perform a preliminary classification of the urine sediment.

[0275] S141. Preliminary classification of urine sediments according to casts, cells, crystals, bacteria, and sperm;

[0276] The CNN network structure consists of convolutional layers, sampling layers, and fully connected layers. Each layer is typically populated with multiple independent neurons, which are interconnected to form a two-dimensional plane. This makes CNNs highly effective at recognizing two-dimensional shapes. This novel network structure remains unchanged when the image to be recognized is scaled, translated, or tilted, making it highly adaptable to image deformation. CNNs employ supervised training because they require a large number of training samples and establish connections between training and test samples.

[0277] CNN is used to preliminarily classify urine sediments into casts, cells, crystals, bacteria, and sperm. The convolution and sampling process mainly includes feature extraction, feature mapping, and subsampling:

[0278] S142. Count bacteria and sperm separately;

[0279] Bacteria and sperm are statistically counted. The number of bacteria reflects the infection of the urinary tract. The more bacteria there are, the more serious the urinary tract infection is; the number of sperm reflects the health of the human reproductive system.

[0280] S150, identifying the preliminarily classified urine sediment through image processing and calculating the morphological parameters and grayscale statistical parameters of each type of urine sediment;

[0281] In this step, the morphological parameters and grayscale statistical parameters reflect the image features of various types of urine sediments. By calculating the morphological parameters and grayscale statistical parameters of various types of urine sediments, the types of various types of urine sediments can be determined.

[0282] See Figure 43 , this step S150 includes:

[0283] S151, performing image denoising processing on the urine sediment image after preliminary classification;

[0284] Noise and other irrelevant information are removed from the urine sediment image, contrast is increased, image quality is improved, and the foreground and background of the urine sediment image are clearly separated. Denoising methods are not limited herein and may include Gaussian low-pass filtering, bilateral filtering denoising, non-local means denoising, and kernel regression for image denoising. Preferably, in this embodiment, a Gaussian filter is used for denoising. The Gaussian filter is a linear filter that can effectively suppress noise and smooth images.

[0285] A two-dimensional Gaussian function is as follows:

[0286]

[0287] Where (x, y) are the coordinates of the point, which can be considered integers in image processing; σ is the standard deviation. To obtain a Gaussian filter template, the Gaussian function can be discretized, and the resulting Gaussian function values ​​can be used as the coefficients of the template, which can then be applied to the image for image processing.

[0288] S152, performing image enhancement processing on the urine sediment image after image denoising processing;

[0289] Image enhancement processing can correct the effect of uneven illumination on urine sediment images.

[0290] The top-hat transform of a grayscale image f is defined as f minus its opening operation:

[0291]

[0292] The bottom-hat transform of a grayscale image f is defined as the closing operation of f minus f:

[0293] B hat (f)=(f·b)-f

[0294] represents the opening operation of the result element on the target image, and (f·b) represents the closing operation on the target element.

[0295] Therefore, the top-hat-bottom-hat transformation is:

[0296] TB hat =f+T hat -B hat

[0297] S153, performing image segmentation processing on the urine sediment image after image enhancement processing;

[0298] This step uses an image edge algorithm for image segmentation, but this processing method is not limited to image edge algorithms. Other possible methods include most image segmentation algorithms, image threshold segmentation algorithms, region-based segmentation algorithms, and morphological watershed algorithms. An edge is a collection of pixels with sudden grayscale changes in an image, and is generally detected using differentials. Edge detection algorithms include the Roberts operator, Prewitt operator, Sobel operator, Marr-Hilderth edge detection algorithm, and Canny edge detection algorithm. In this step, the Canny edge detection algorithm is used.

[0299] a) Calculate the gradient strength and direction for each pixel in the image.

[0300] In an image, gradient is used to represent the degree and direction of change in grayscale value. It can be obtained by multiplying a sobel or other operator to obtain gradient values ​​in different directions: g x (m,n),g y (m,n), the comprehensive gradient is calculated by the following formula:

[0301]

[0302] Where (m,n) is the point coordinate, which can be considered as an integer in image processing.

[0303] b) Apply non-maximum suppression to eliminate spurious responses caused by edge detection. Keep the edge width as small as possible: If a pixel is an edge, then the gradient value of that pixel in the gradient direction is the maximum. Otherwise, it is not an edge and the grayscale value is set to 0.

[0304]

[0305] c) Double-threshold detection is applied to determine true and potential edges. Two thresholds are set: maxVal and minVal. Any pixel above maxVal is detected as an edge, while any pixel below minVal is detected as a non-edge. If a pixel in the middle is adjacent to a pixel identified as an edge, it is considered an edge; otherwise, it is considered a non-edge.

[0306] d) Edge detection is finally completed by suppressing isolated weak edges.

[0307] S154. Identify the shape characteristics of various types of urine sediment;

[0308] S155. Calculate the morphological parameters and grayscale statistical parameters of various types of urine sediment.

[0309] Morphological parameters are calculated based on the binary image captured by the microscope. They are used to obtain morphological information as five sets of eigenvalues. These parameters include area S, perimeter L, circularity C, rectangularity R, and contour fitting error.

[0310] a) Area S

[0311] The area S is the number of pixels within the target area, so it is related to the boundary of the target.

[0312]

[0313]

[0314] Among them, p and q are the maximum values ​​of the region in the horizontal and vertical directions respectively, and R is the target region.

[0315] b) Circumference L

[0316] The perimeter L is the sum of all pixels on the boundary of the target area. Its mathematical expression is:

[0317]

[0318] Where N represents the total number of pixels in the contour, and Ti represents the number of chain codes that track the cell contour from the i-th point to the next point in a counterclockwise direction.

[0319] c) Circularity C

[0320] Image circularity C indicates the degree to which the target image shape is close to a circle. It is a comprehensive measurement parameter of area shape. Its mathematical expression is:

[0321]

[0322] When C is 1, it indicates that the target image shape is a circle. As the C value increases, the target image shape deviates from a circle.

[0323] d) Rectangularity R

[0324] Image rectangularity R is the degree of deviation of the target image contour area from the product of the target height and width. Its mathematical expression is:

[0325]

[0326] Where W represents the width of the circumscribed rectangle of the target image, H represents the height of the circumscribed rectangle of the target image, and when the target area is a rectangle, R=1.

[0327] e) Fitting error:

[0328] The fitting error refers to the distance error between the points on the region outline and the corresponding points on the fitting curve. The fitting error can be expressed as the average distance between the region boundary and the corresponding points on the fitting curve. The calculation formula is shown below.

[0329]

[0330] Among them, N is the number of pixels on the contour, (x k ,y k ) represents a point on the contour, (u k ,y k ) is (x k ,y k ) corresponds to a point on the fitted curve, and the symbol ‖‖ is used to find the distance between two points. Obviously, the smaller the fitting error, the closer the fitting curve fits the target boundary, and the closer the cell is to a circle or ellipse.

[0331] Grayscale statistical features are mainly calculated based on the grayscale histogram of microscopic cell images. The characteristic parameters of grayscale statistical features extraction are: mean value m; variance σ; third-order moment μ_3; consistency U.

[0332] Among them, L represents the grayscale level of the grayscale image, z i represents a random grayscale value, p(z i ) represents the histogram of a region.

[0333] f) Average value m

[0334] The mean value m represents the average gray value of a certain target area in the image, and its mathematical expression is:

[0335]

[0336] g) Variance σ

[0337] Variance σ represents the degree of grayscale dispersion within a certain target area of ​​the image, and its mathematical expression is:

[0338]

[0339] h) Third-order moment μ3

[0340] The third-order moment μ3 reflects the symmetry of the image grayscale histogram, and its mathematical expression is:

[0341]

[0342] i) Consistency

[0343] The consistency U reflects the discrete degree of gray value distribution in a certain area, and its mathematical expression is:

[0344]

[0345] S160, performing secondary classification of various types of urine sediments based on morphological parameters and grayscale statistical parameters of the various types of urine sediments using an interpretable machine learning algorithm;

[0346] The interpretable machine learning algorithm includes one of the LightGBM classification algorithm, logistic regression algorithm, SVM algorithm, random forest algorithm, KNN algorithm and Bayesian algorithm. In this embodiment, the type of classification algorithm used is not limited. Preferably, the LightGBM classification algorithm is used.

[0347] Specifically, step S7 includes:

[0348] S161. Divide the target classification, morphological parameter calculation, and grayscale statistics calculation into a training set and a test set. Use the training set as the input variable to build a LightGBM classification model. Use the grid search method to optimize the parameters of the LightGBM classification model to obtain the optimized LightGBM classification model.

[0349] S162. Use the test set to train the optimized LightGBM classification model to obtain a trained LightGBM classification model.

[0350] S163. Segmentation by model output type.

[0351] The secondary classification of various types of urine sediment is to subdivide the casts, cells and crystals.

[0352] Casts are an important component in urine sediment. The appearance of casts in urine indicates renal parenchymal damage and represents damage to the glomeruli or renal tubules.

[0353] Casts are divided into the following categories:

[0354] 1) hyaline casts; 2) cellular casts; 3) granular casts; 4) waxy casts; 5) fat casts; 6) mixed casts; 7) broad casts.

[0355] Cells are divided into the following categories:

[0356] 1) Red blood cells; 2) White blood cells; 3) Squamous epithelial cells; 4) Non-squamous epithelial cells; 5) Phagocytes; 6) Heterosexual cells.

[0357] Crystallization is divided into the following categories:

[0358] 1) Calcium oxalate crystals; 2) Uric acid crystals; 3) Phosphate crystals; 4) Drug crystals.

[0359] S170, then counting each urine sediment after secondary classification to obtain a counting result;

[0360] S180. Obtain urine test results based on the counting results of each urine sediment.

[0361] Example 16

[0362] This embodiment discloses a method for detecting urine components based on fluorescent reagents, see Figure 44 and Figure 45 , including the following steps:

[0363] S200, injecting urine and fluorescent reagent into the sample detection chamber;

[0364] In this step, urine can be injected first and then the fluorescent reagent, or the fluorescent reagent can be injected first and then the urine, or urine and the fluorescent reagent can be mixed first and then the mixture of urine and the fluorescent reagent can be injected.

[0365] The sample detection chamber is located inside the microfluidic detection chip. During the detection process, its position is fixed. Urine can be directly injected into the sample detection chamber. After the urine enters the sample detection chamber, it waits to be tested. There is no need to manually adjust the placement of the urine sample, and the detection process is simple.

[0366] Before step S200, the method further includes:

[0367] S201, defoaming the urine.

[0368] There are usually certain bubbles in urine, which will affect the amount of urine sampled and the detection effect. Therefore, defoaming treatment is required.

[0369] In this embodiment, the urine defoaming treatment mainly adopts the precipitation defoaming method. Of course, the defoaming method is not limited to this, and can also be a chemical defoaming method, a physical defoaming method and other defoaming methods.

[0370] S210, a fluorescent light source emits fluorescent reagent excitation light to the sample detection chamber, and excites the mixture of the urine and the fluorescent reagent to generate fluorescence;

[0371] The mixture of urine and fluorescent reagent contains fluorescent substances that can be excited to produce fluorescence. When the fluorescent light source shines on the fluorescent substance, the mixture will emit fluorescence.

[0372] Step S210 includes:

[0373] S211 , filtering the light emitted by the fluorescent light source, and then exciting the mixture of the urine and the fluorescent reagent to generate fluorescence.

[0374] In step S211 , the result of the light filtering process is to leave only the fluorescent light source that can excite the fluorescent substance, thereby preventing other light sources from affecting the excitation effect when exciting the fluorescent substance.

[0375] S220 , collecting a fluorescent image of the mixed solution after being excited by a fluorescent light source through the sample detection chamber.

[0376] The sample detection chamber is partially transparent or fully transparent, and the fluorescent image of the mixed liquid can penetrate and emit out of the sample detection chamber.

[0377] The optical information acquisition assembly of this embodiment is located on one side of the sample detection chamber and collects fluorescent image information from the sample detection chamber. The optical information acquisition assembly can store the collected fluorescent image information of the mixed liquid and transmit this image information to the detection site for further testing, thereby achieving higher detection accuracy. Furthermore, to avoid detection errors, this image information can also be retrieved for secondary verification.

[0378] Before step S220, the method further includes:

[0379] S221 , filtering the light passing through the sample detection chamber to retain the fluorescence generated by the mixed solution.

[0380] Step S221 has a denoising effect. Although the fluorescent light source only has light that can excite the fluorescent substance after the first filtering, the light source can generate light of different bands. Light of different bands will pass through the sample detection chamber, but only light within the specified range of bands can excite the fluorescent substance. Light of other bands will be emitted from the sample detection chamber together with the excited fluorescence, which will have a certain interference with the excited fluorescence. In order to improve the detection effect, filtering processing is required in this step.

[0381] Step S220 includes:

[0382] S222. Filter the ambient light on the fluorescence transmission path before acquisition.

[0383] In the aforementioned steps S221 and S222, although the interference of the fluorescent light source itself is eliminated, the interference of external ambient light on urine detection cannot be eliminated. Therefore, before collecting the fluorescent image, the ambient light on the fluorescent transmission path is filtered. Accordingly, the collected fluorescent image is more accurate, and the final urine test result is also more accurate.

[0384] After step S220, the method further includes:

[0385] S223, cleaning the detection device.

[0386] Urine has a certain odor. If left untreated, the odor will worsen and affect the air environment. Furthermore, if left uncleaned, residual urine will affect the next urine test. The detection device involves all devices in the entire detection process, primarily cleaning the urine sampling, urine transport, and urine testing devices. In this embodiment, the cleaning process specifically involves cleaning the urine sampling device, the sampling microfluidic pump, the urine transport pipeline, and the urine testing module.

[0387] After step S220, the present invention further includes the following steps:

[0388] S230, acquiring a urine collection image of the urine sample added with a fluorescent reagent after fluorescence excitation;

[0389] S240, inputting the urine collection image into a preset neural network model;

[0390] To analyze the image data of the urine sample, the urine sample collected after fluorescence excitation needs to be used as the original input image and input into a preset neural network model. Neural network models include Faster R-CNN, SSD, and YOLO. In this embodiment, the type of neural network model used is not limited. Preferably, the Faster R-CNN model is used for recognition in this step.

[0391] Selecting the Faster R-CNN model for recognition includes the following:

[0392] This method uses the relatively simple ResNet50 network instead of the VGG16 network used in the original network. This is because the ResNet50 network uses a residual block structure, which can effectively prevent the vanishing gradient problem caused by the deepening of the network layers. In addition, ResNet50 has a relatively low computation time among the ResNet series networks, so it was ultimately chosen as the network's feature extractor. The input network size is set to 640×640. If the sub-image block size does not meet 640, the sub-image edges are padded with zeros to adjust to the input size. After the image is input to the feature extraction layer, the ResNet50 network uses five stages consisting of a combination of different numbers of convolutional layers, batch normalization layers, ReLU activation layers, and maximum pooling layers for feature extraction. The residual block structure implemented through short links is used to provide residual learning. To intuitively illustrate the effect of the feature extraction layer, the feature maps output by the five feature layers of ResNet50 are visualized. Visualization of the network structure and feature maps of ResNet50. C1 to C5 represent the 1st to 5th feature layers. Each feature layer is obtained by downsampling the upper layer data. Since the input size is fixed at 640×640, the sizes of C1 to C5 are: [320,320], [160,160], [80,80], [40,40], [20,20], respectively.

[0393] S250, weighting the blocked cell images in the urine collection image in each convolutional neural network layer of the neural network model;

[0394] In urine collection images, there may be occlusions between cells, and the occluded cells are difficult to be discovered by the neural network model, so the urine collection images need to be weighted.

[0395] Step S250 includes: S251, embedding an attention mechanism in each layer of the convolutional neural network.

[0396] To solve the problem of occlusion between cells, this step embeds an attention mechanism in each layer of the convolutional neural network and weights the occluded cells in each layer of the convolutional neural network to enhance the receptive field of the feature extraction layer of the convolutional neural network and improve the performance of the neural network model.

[0397] S260: Performing a process on the weighted urine collection image to prevent missing cells from being recognized:

[0398] The attention mechanism includes the following:

[0399] The urine collection image input into the convolutional neural network is first subjected to feature extraction after passing through the feature extraction layer of the convolutional neural network to obtain a feature map with a shape of H×W×C, where the size of the feature map is represented by H×W and C is the number of channels.

[0400] Sequeeze: This compresses features along the spatial dimensions, converting each two-dimensional feature channel into a real number. This real number has a global receptive field, and the output dimension matches the number of input feature channels. It represents the global distribution of responses across feature channels and enables layers close to the input to also obtain a global receptive field. Specifically, this involves applying a global average pooling layer to the original feature map C*W*H, resulting in a 1*1*C feature map with a global receptive field.

[0401] Activation (Excitation): The output 1x1xC feature map is then passed through two fully connected neural networks, and finally a mechanism similar to the gate in the recurrent neural network is used to generate weights for each feature channel through parameters.

[0402] Feature recalibration: Use the result obtained by Excitation as the weight, and then weight it channel by channel by multiplication to the C channels of U to complete the recalibration of the original features in the channel dimension and use it as the input data for the next level.

[0403] Step S260 also includes: S261, performing feature fusion processing on cells of different sizes.

[0404] In urine collection images, there is not only the problem of occlusion between cells, but also the problem of uneven size of fluorescent cells. Cells that are too small and occluded may be missed. Therefore, it is necessary to perform feature fusion processing on cells of different sizes, mainly to identify the bounding boxes of each cell in the urine collection image.

[0405] This embodiment integrates feature pyramid networks (FPN) into Faster R-CNN to increase the detector's understanding of full-image information.

[0406] 1) First, the urine collection image is sent to the fused underlying network, and the feature maps of the five stages are obtained through the network composed of ResNet50 and attention mechanism structure.

[0407] 2) Layers C1 to C5 are the feature layers obtained by the feature extraction network. 1×1 convolution is then used to reduce the dimension of layer C4 so that the number of feature channels in C4 matches that in P5. After upsampling, P5 is made consistent in size with the feature maps in C4. Finally, the two are added together to obtain the fusion layer P4. The same applies to the other layers.

[0408] 3) The resulting layers P2 to P6 (the top-down network, the core of the FPN) are then trained on the RPN to generate region proposals. Similar to the original Faster R-CNN, a 3×3 convolution is then performed, followed by a connection between the classification and regression layers. P2 to P5 are used to predict cell bounding boxes, and P6 is used in the RPN network.

[0409] S270: Improve the identification region suggestion box of the cell.

[0410] The feature map output by the FPN architecture is input into the RPN network layer, where a certain number of prior bounding boxes are generated based on the feature map using a sliding window. The original Faster R-CNN uses three prior bounding boxes with aspect ratios of (1:2, 1:1, and 2:1). These prior bounding boxes can accommodate the various shapes and sizes of objects in the COCO dataset. To adapt the model to the characteristics of cells, the initial aspect ratios of the generated prior bounding boxes are adjusted to (1:2, 4:5, 1:1, and 2:1). The initial dimensions of the prior bounding boxes are set to (16, 32, 64, 128, and 256). Twenty prior bounding boxes are generated for each point in the feature map, for a total of W×H×20 prior bounding boxes on a W×H image. The prior bounding boxes are then classified into two categories using an Intersection-of-Union (IoU) threshold. Prior bounding boxes with an IoU greater than 0.8 with any ground-truth bounding box of a sugarcane seedling are classified as foreground; prior bounding boxes with an IoU less than 0.2 with all ground-truth bounding boxes are classified as background. The formula for calculating IoU is as follows:

[0411]

[0412] Example 17

[0413] See Figure 46 The embodiment of the present invention discloses a spectral detection method for urine components. The spectral detection that can be performed by the present invention includes at least one of Fourier infrared spectral detection, Raman spectral detection, fluorescence spectral detection and ultraviolet spectral detection.

[0414] Spectral detection methods include:

[0415] S300, injecting urine into the sample detection chamber;

[0416] The sample detection chamber is located inside the microfluidic detection chip. During the detection process, its position is fixed and its position relative to the microscope body and the microscopic optical information acquisition component is relatively fixed. Urine can be directly injected into the sample detection chamber. After the urine enters the sample detection chamber, it waits to be detected. There is no need to manually adjust the placement of the urine sample, and the detection process is simple.

[0417] Before step S300, the present invention further includes:

[0418] S301 , injecting a spectrum detection reagent into a sample detection chamber.

[0419] In this step, urine can be injected first and then the spectral detection reagent, or the spectral detection reagent can be injected first and then the urine, or urine and the spectral detection reagent can be mixed first and then the mixture of urine and the spectral detection reagent can be injected.

[0420] After step S300, the present invention further includes:

[0421] S302, adjusting the temperature of urine in the sample detection chamber;

[0422] When testing urine samples, it is necessary to ensure that the urine samples are in a relatively suitable temperature environment. When the external environment of the urine sample is too cold or too hot, the external environment temperature will affect the temperature of the urine sample and ultimately affect the urine detection effect. Therefore, the temperature of the urine in the sample detection chamber needs to be adjusted.

[0423] S310, controlling the light from the background light source to pass through the cavity wall of the sample detection chamber and enter the sample detection chamber;

[0424] The sample detection chamber includes an upper cavity wall, a lower cavity wall, and a side wall. When the side wall and the upper cavity wall or the lower cavity wall are transparent, the sample is passed into the detection chamber. An external background light source can penetrate the side wall and the transparent upper cavity wall or the lower cavity wall into the sample detection chamber. The light is reflected by the transparent upper cavity wall or the lower cavity wall and then exits the sample detection chamber, thereby providing a lighting environment for sample detection. When both the upper cavity wall and the lower cavity wall are transparent, the light provided by the light source can penetrate the upper cavity wall and the lower cavity wall from one side of the upper cavity wall or the lower cavity wall, providing a lighting environment for sample detection. The background light source set in this step can adapt to the needs of different detection environments.

[0425] Before step S310, the present invention further includes:

[0426] S311, filtering the light from the background light source to obtain light within a preset wavelength band;

[0427] Step S311 has a denoising effect. The background light source can generate light of different wavelengths, but only the light within the preset wavelength range can pass through the sample detection chamber to form spectral information. The light of other wavelengths will have a certain interference with the process of forming spectral information of the urine sample. Moreover, the light of other wavelengths will be emitted from the sample detection chamber, which will also affect the optical information acquisition component to collect the spectral information of the urine sample. In order to improve the detection effect, filtering processing is required in this step.

[0428] S320 , collecting spectral information of the urine through the sample detection chamber.

[0429] The optical information acquisition component of this embodiment is located on one side of the sample detection chamber and collects spectral information from the sample detection chamber. This component can store the spectral information of the collected urine sample and transmit it to the testing center for further testing, resulting in higher detection accuracy. Furthermore, to avoid detection errors, this spectral information can also be retrieved for secondary verification.

[0430] Before step S320, the present invention further includes:

[0431] S321 , filtering the light after passing through the sample detection chamber.

[0432] In the aforementioned step S311, although the interference of the background light source itself is eliminated, the interference of external ambient light on urine detection cannot be eliminated. Therefore, before collecting the spectral information, the ambient light on the spectral information transmission path is filtered. Based on this, the collected spectral information is more accurate, and the urine test results finally obtained are also more accurate.

[0433] S330: Perform urine testing based on the collected spectral information of the urine.

[0434] Specifically, the intensity of the collected spectral information varies. Using all of the spectral information for urine testing will result in inaccurate test results. Therefore, it is necessary to select some spectral information with appropriate intensities for testing. The following steps are for selecting spectral information with appropriate intensities. It is understandable that in the aforementioned method for detecting urine components based on fluorescent reagents, the intensity of the fluorescence used to collect the fluorescence image also varies. Fluorescence with varying intensities can also lead to inaccurate detection. Therefore, to further improve the results of fluorescence detection, the spectral detection method for urine components of this embodiment can be applied to fluorescence detection of urine. At the same time, the aforementioned method for detecting urine based on microscopic images includes controlling the light of the background light source to enter the sample detection chamber through the cavity wall of the sample detection chamber and collecting microscopic image information of urine through the sample detection chamber. During the microscopic image acquisition process, the light intensity of the background light source varies. Collecting microscopic images of urine using light sources with varying intensities may result in misjudgment. Therefore, to further improve the accuracy of urine detection based on microscopic images, the spectral detection method for urine components of this embodiment can be applied to microscopic detection of urine. In summary, the urine detection method based on microscopic images, the urine component detection method based on fluorescent reagents, and the spectral detection method of urine components have the same purpose. In order to further improve the accuracy of urine detection, the three detection methods can be recombined, and the recombined urine detection methods are all within the protection scope of the present invention. Moreover, the detection method of the present invention is not limited to urine detection, but can also be used to detect other human tissues and body fluids. Furthermore, it can also be used to apply the detection method to various animals and plants in nature.

[0435] The S330 specifically includes the following steps:

[0436] S331, obtaining wavelength values ​​of spectral information, and arranging spectral information of different wavelengths into a first sequence according to a first preset manner, where the first sequence includes a first noise region and a first characteristic peak region;

[0437] The first preset method includes a wavelength increasing or wavelength decreasing method, the noise area and the characteristic peak area are both areas with higher spectral intensity in the spectral information sequence, and the maximum spectral intensity of the characteristic peak area is greater than the maximum spectral intensity of the noise area.

[0438] S332: Acquire intensity values ​​of the spectral information, and arrange the spectral information of the first sequence into a second sequence according to a second preset manner;

[0439] The second preset mode includes a mode of increasing intensity or decreasing intensity.

[0440] S333, performing smoothing filtering on the spectral information of the second sequence;

[0441] S334, sorting the spectral information of the second sequence after the smoothing filtering process in a third preset manner and defining the sorted sequence as a third sequence, wherein the third sequence includes the second noise region and the second characteristic peak region;

[0442] The third preset mode includes a wavelength increasing or wavelength decreasing mode, and the spectral information suitable for urine detection is located in the second characteristic peak area;

[0443] S335, obtaining a first quantity of target spectrum information corresponding to the second characteristic peak region of the third sequence;

[0444] S336: Perform urine testing based on the first amount of target spectral information.

[0445] The spectral information suitable for urine testing is located in the characteristic peak area. However, the existence of the noise area will interfere with the identification of the characteristic peak area. Therefore, the spectrum needs to be preprocessed and smoothed and filtered to highlight the characteristic peak area in the spectral information sequence. The essence of smoothing and filtering the spectrum is to improve the signal fidelity of the spectral information in the characteristic peak area and improve the signal-to-noise ratio in the noise area.

[0446] Step S333 specifically includes:

[0447] S3331, continuously acquiring a second preset amount of spectral information in a second sequence in a manner of decreasing intensity;

[0448] S3323, calculating the spectral noise level based on the second preset amount of spectral information, mainly including:

[0449] Calculating the average intensity value and the standard deviation intensity value of the second preset amount of spectral information,

[0450] Calculating a spectral noise level based on the mean intensity value and the standard deviation intensity value;

[0451] S3324. Calculate the filter window width according to the spectral noise level;

[0452] S3325. Perform smoothing filtering according to the filtering window width.

[0453] Specifically, in the second sequence, the spectral information with the intensity in the first t% is selected and recorded as the noise sequence N, the number of the spectral information in the first t% is the second preset number of spectral information, and then the spectral intensity of each spectral information in the second preset number is obtained, and then the average spectral intensity of all spectral information in the second preset number is calculated. mean and standard deviation N std The calculation method of the spectral noise level and the calculation method of the filter window width are existing technologies and will not be described in detail here.

[0454] Finally, a Savitzky-Golay filter is selected for smoothing filtering. The filtering method is a prior art and will not be described in detail here. It is understandable that the filtering method is not limited to this, as long as smoothing filtering can be achieved.

[0455] Preferably, step S336 includes:

[0456] Performing ranking detection or fuzzy detection or precise detection based on the first amount of target spectrum information by mainly performing ranking detection and supplemented by fuzzy detection;

[0457] In this embodiment, the first amount of target spectral information selected is a certain amount of spectral information obtained within the characteristic peak region. However, the spectral information within the characteristic peak region may not all meet the requirements. Therefore, abnormal information may still exist in the first amount of target spectral information. This step is to screen out this abnormal information to make the urine test results more accurate.

[0458] Ranking detection is applicable to situations with a certain number of output data points. Its purpose is to screen out a certain number of spectral information whose intensity is within the extreme value range in the first number of target spectral information, and remove these spectral information and not use them for urine detection; fuzzy detection is applicable to situations without a certain number of output data points. Its purpose is to screen out some spectral information worthy of attention and remove it as needed; in ranking detection, the spectral information between the maximum and minimum values ​​is not processed, and the spectral information between the two may still be abnormal. Based on this, fuzzy detection is performed in sequence on the basis of ranking detection, which can screen out the spectral information worthy of attention between the extreme values ​​and remove it as needed, which can further improve the accuracy of urine detection.

[0459] The ranking detection includes:

[0460] Acquire a third preset amount of spectral information in a descending order of intensity, and acquire a fourth preset amount of spectral information in a descending order of intensity.

[0461] Performing urine testing based on the third preset number of spectral information and the fourth preset number of spectral information;

[0462] Preferably, the third preset number is equal to the fourth preset number, and the maximum and minimum values ​​are evenly distributed, which is more conducive to improving detection accuracy.

[0463] The fuzzy detection includes:

[0464] sorting the first number of target spectrum information according to a fourth preset manner and defining the sorting as a third sequence, wherein the fourth preset manner includes an intensity increasing manner or an intensity decreasing manner;

[0465] Determine, according to a fifth preset method, P intensity sudden increase abnormal ranges of different intensities and Q intensity sudden decrease abnormal ranges of different intensities in the third sequence, where P and Q are both positive integers. The fifth preset method may use an n-sigma detection method, which is an existing technology and is not described in detail here.

[0466] Different amounts of spectral information are obtained within the P intensity sudden increase anomaly ranges of different intensities, wherein the intensity of the spectral information is inversely proportional to the amount of spectral information obtained based on the intensity; and different amounts of spectral information are obtained within the Q intensity sudden decrease anomaly ranges of different intensities, wherein the intensity of the spectral information is proportional to the amount of spectral information obtained based on the intensity.

[0467] The urine test is performed after retaining or removing the acquired spectral information according to preset conditions.

[0468] Preferably, in this embodiment, P is set to 3, Q is set to 3, μ is the average spectral intensity of the third sequence, σ is the standard deviation of the spectral intensity of the third sequence, and a 3-sigma detection method is used for anomaly detection. Then, when screening spectral information worthy of attention in the third sequence, the range of sudden increase abnormal points is considered to have three levels, A1, A2, and A3. The sudden increase abnormal points A1>μ+σ, A2>μ+2σ, and A3>μ+3σ, among which the spectral intensity involved in level A1 is the highest. According to the principle that the intensity of spectral information is inversely proportional to the amount of spectral information obtained based on the intensity, the number of spectral information that needs attention is: A1<A2<A3; the range of sudden increase abnormal points is considered to have three levels, B1, B2, and B3. The sudden increase abnormal points B1<μ-σ, B2<μ-2σ, and B3<μ-3σ, among which the spectral intensity involved in level B3 is the lowest. According to the principle that the intensity of spectral information is directly proportional to the amount of spectral information obtained based on the intensity, the number of spectral information that needs attention is: B1>B2>B3.

[0469] After determining the number of spectral information requiring attention, the system determines whether to retain or remove the determined spectral information based on pre-set conditions. Specifically, if spectral information within a certain intensity range is used for urine testing, if the spectral information of interest falls within that range, it is classified as spectral information that can be used for urine testing; if the spectral information of interest falls outside the range, it is removed; and if the spectral information falls on the boundary of the intensity range, it is retained or removed based on the actual situation. This improves urine testing accuracy.

[0470] Example 18

[0471] See Figures 47 to 49The present invention provides a urine electrochemical detection method for electrochemically detecting urine. Conventional detection methods generally use test paper detection. After urine is dropped onto the test paper, the test paper and urine undergo a chemical reaction. The urine detection result is obtained by observing and analyzing the color change of the chemical reaction between the test paper and urine. However, manually comparing the reagent display result with the standard database with the naked eye may lead to inaccurate detection results. Therefore, the present invention uses an electrochemical method to detect urine, including:

[0472] S400, detecting whether the electrochemical detection chip is working properly;

[0473] Only when the electrochemical detection chip works normally will the urine sample be dropped on the reaction part of the electrochemical detection chip for urine detection, so as to avoid the situation where the electrochemical detection chip works abnormally and the sample is still dropped, which will fail to achieve the detection purpose.

[0474] The electrochemical detection chip includes an insulating substrate and a plurality of chip electrodes. The plurality of chip electrodes form a reaction part and a conductive part on the insulating substrate. Urine on the reaction part causes the plurality of chip electrodes to conduct and generate a plurality of electrical signals which are transmitted to the conductive part for detection. The electrochemical indicators of urine are detected by the plurality of electrical signals, and there is no need to manually judge the relevant conditions of urine through visual means. The detected urine data is more accurate.

[0475] Before step S400, the present invention further includes:

[0476] S401, adding detection materials to the chip electrodes of the reaction part;

[0477] When performing electrochemical detection on urine, it is necessary to add the same detection material or multiple detection materials to the chip electrodes of the reaction part.

[0478] When the same detection material is added to the chip electrode, multiple current values ​​of a certain electrochemical indicator can be detected. By calculating the average value of multiple current values, more accurate electrochemical indicator data can be obtained.

[0479] When different detection materials are added to the chip electrodes, multiple current values ​​can be obtained to detect multiple electrochemical indicators of urine.

[0480] Electrochemical indicators include one or more of urine specific gravity, urine pH, urine protein, uric acid, urine potassium, urine sodium, urine calcium, urine phosphorus, urine sugar, and urine chloride, all of which can be obtained through electrical signal detection and analysis. Detection materials are provided on the chip electrodes, and different detection materials can detect the above-mentioned different indicators. The detection principles are existing technologies and are not described here. Urine specific gravity and urine pH can be detected directly by the chip electrodes themselves, without the need for detection materials.

[0481] S410, when the electrochemical detection chip works normally, dropping a urine sample on the reaction part of the electrochemical detection chip;

[0482] Step S410 includes:

[0483] S411. Sampling urine to obtain a urine sample.

[0484] When the electrochemical detection chip does not work properly, an alarm message is issued.

[0485] There are three types of abnormal conditions: the chip itself is damaged, the chip used last time is not removed, or the chip is not installed in the correct position.

[0486] After the alarm is issued, troubleshooting operations are required, including:

[0487] If the fault is caused by chip damage, replace the chip and reinsert it;

[0488] If the fault is that the chip used last time is not removed, replace the chip or reinsert it;

[0489] When the fault is that the chip is not installed in the correct position, adjust the chip installation position.

[0490] After the troubleshooting operation was completed, the chip worked normally and urine testing continued.

[0491] S420, performing conductive identification on the electrochemical detection chip after the urine sample is dropped thereon, wherein the conductive identification is performed by determining whether current is generated on the electrochemical detection chip;

[0492] The urine sample undergoes a chemical reaction in the reaction part, which will produce different current values. By detecting the current values, it can assist in judging urine-related data.

[0493] S430, when the conductive identification indicates that current is generated on the electrochemical detection chip, obtaining at least one current value on the electrochemical detection chip;

[0494] A single current value can detect an electrochemical indicator. When multiple electrochemical indicators need to be detected, multiple current values ​​need to be obtained. At the same time, when a certain electrochemical indicator needs to be detected more accurately, multiple current values ​​related to the electrochemical indicator need to be obtained, and then the average of the multiple current values ​​is taken to obtain a more accurate current value.

[0495] S440: When the conductive method identifies that no current is generated on the electrochemical detection chip, continue to drip the urine sample onto the reaction portion of the electrochemical detection chip.

[0496] When the electrochemical detection chip is working normally, if no current is generated after urine is dripped into it, it is mainly because no urine sample has dripped into the reaction part or the amount of urine sample dripped into the reaction part is insufficient. Continuing to drip urine sample can determine which type of fault it is.

[0497] Continue to drip urine sample, and the conductive recognition will detect that current is generated on the electrochemical detection chip, the fault is resolved, and urine testing can continue;

[0498] Continue to drip the urine sample, and the conductive identification will show that there is still no current generated on the electrochemical detection chip. It is necessary to check whether the urine sample has entered the electrochemical detection chip.

[0499] S450: Compare all current values ​​with a preset reference current value and output a detection result.

[0500] When the test results are output, a prompt is given to remove the electrochemical detection chip and store it for next use.

[0501] After the test results are output, a cleaning operation is initiated. Cleaning fluid is introduced to clean the electrochemical urine detection device. The cleaning operation can be performed before the electrochemical detection chip is prompted to overflow, and the electrochemical detection chip can be cleaned at the same time.

[0502] The present invention does not require manual visual judgment of urine conditions, and the urine data detected in a digital manner is more accurate.

[0503] Step S450 includes:

[0504] S451. Set a reference current sequence A, where sequence A = A1, A2...An, where n represents the sequence length and is a positive integer.

[0505] The reference current sequence A is a time series that changes with time. As an undetected current sequence, in short, the reference current sequence A is the current sequence recorded before the urine is dripped in. It records the current on the electrochemical detection chip. The reference current sequence A is used for denoising to eliminate the situation where the environmental factors change due to changes in time, resulting in unsatisfactory final detection results.

[0506] S452, setting a time current sequence B consisting of current values ​​when current is generated on the electrochemical detection chip, where sequence B = B1, B2...Bm, where m represents the sequence length and is a positive integer;

[0507] S453 , based on the reference current sequence A and the value of m, select a standard current sequence C from a current sequence template library, where sequence C=C1, C2…Cm;

[0508] Time current sequence B is the current sequence recorded after the urine is dripped in, which records the current on the electrochemical detection chip.

[0509] The standard current sequence C is the standard data of urine within a certain period of time. It is the data that should be obtained when the urine indicators are in the most ideal condition. It is obtained from experiments. Its data is not related to the data detected by the current on the electrochemical detection chip. However, in order to detect the data of the current urine indicators, it is necessary to compare it with the data detected by the current on the electrochemical detection chip. In this process, the interference of environmental factors such as weather needs to be eliminated. The time current sequence B needs to be in the same external environment when compared with the standard current sequence C. Accordingly, it is necessary to take the value based on the aforementioned reference current sequence A and the m value.

[0510] S454. Obtain a first dynamic time warping distance DTW1 according to An and Cm.

[0511] S455. Obtain a second dynamic time warping distance DTW2 according to An and Bm.

[0512] By comparing the first dynamic time warping distance DTW1 with the second dynamic time warping distance DTW2, interference of environmental factors such as weather on urine electrochemical detection can be eliminated.

[0513] The second dynamic time warping distance DTW2 between the reference current sequence A and the time current sequence B is calculated as follows:

[0514] Reference current sequence A = A1, A2…An, where n represents the sequence length, which is a positive integer;

[0515] Time current sequence B = B1, B2…Bm, where m represents the sequence length and is a positive integer;

[0516] Construct a (n,m) matrix, the (i,j) unit records two points (a i , b j ), d(a i , b j )=|a i -b j |.

[0517] like Figure 49 As shown, a winding path W is composed of several interconnected matrix units. This path describes a mapping between A and B. Let the kth unit be defined as w k =(i, j) k ,but

[0518] w=w1,w2,w3,...,w K, max(n,m)<=K<=n+m-1

[0519] This winding path satisfies the following conditions:

[0520] 1. Boundary conditions: w1 = (1, 1), and w k =(n,m)

[0521] 2. Continuity: Let w k =(a, b), w k-1 =(a′, b′), then aa′<=1, bb′<=1

[0522] 3. Monotonicity: Let w k =(a, b), w k-1 =(a′, b′), then aa′>=0, bb′>=0

[0523] Among the multiple paths that meet the above conditions, the shortest path with the least cost is:

[0524]

[0525] Then, the distance between two time series is:

[0526] r(i,j)=d(i,j)+minr(i-1,j-1), r(i-1,j), r(i,j-1).

[0527] DTW2=r(i,j).

[0528] The calculation method of the first dynamic time warping distance DTW1 between the reference current sequence A and the standard current sequence C is the same as DTW1.

[0529] S456 : Compare the first dynamic time warping distance DTW1 and the second dynamic time warping distance DTW2 to determine a detection result of the electrochemical detection chip.

[0530] like

[0531]

[0532] If the electrochemical test result is negative, it is considered normal, otherwise it is abnormal.

[0533] Example 19

[0534] At present, the technology for home urine testing has been realized. The urine indicators of home testing can provide a favorable basis for judging one's own physical health status. However, the existing urine testing technology can often only detect single data, such as urine sugar, urine protein, etc. With the improvement of the quality of life, urine testing technology will be widely used, and different users have different needs. For example: some users only need to conduct single data testing at this stage. Extra test items will not only complicate the testing process, but also increase the testing cost; some users need to conduct comprehensive testing, and diversified testing modes can help users obtain diversified urine indicators.

[0535] Accordingly, see Figure 50 The embodiment of the present invention discloses a real-time urine detection method that can meet the different detection needs of different users and has strong adaptability. The method includes:

[0536] S500, selecting a urine testing mode, where the urine testing mode includes at least one of a basic testing mode, a precise testing mode, and a composite testing mode;

[0537] S510, taking urine samples;

[0538] S520, testing the sampled urine according to the selected urine testing mode;

[0539] S530: Output the urine test result.

[0540] In this embodiment, the selected urine detection mode determines the final output urine test results. The urine detection mode includes at least one of a basic detection mode, a precise detection mode, and a composite detection mode. The composite detection mode is a combination of a basic detection mode and a precise detection mode. When the user only needs to test a certain indicator or a certain category of indicators, the corresponding basic detection mode or precise detection mode can be selected, which can perform targeted testing and reduce testing costs. When the user needs to test a variety of indicators, the composite detection mode can be enabled. The real-time urine detection method of this embodiment can be used for urine testing, which can detect both single indicators and diversified indicators, and has a wide range of application scenarios and strong applicability.

[0541] In step S500, the basic testing mode includes a dry chemical testing method, which is used to collect dry chemical information from urine and perform urine testing based on the dry chemical information. Specifically, dry chemical urine testing can be performed as a counting test. Urine dry chemical testing utilizes a urine dry chemical analysis device to detect the corresponding chemical components in urine. Chemical components in urine can cause the modules on the urine multiple test strip to change color, and the color depth is proportional to the concentration of the corresponding substances in the urine. The urine dry chemical analysis device is installed on the smart toilet. This method can be used to assist in the diagnosis and treatment of diseases such as urinary system diseases, hepatobiliary diseases, and diabetes, monitor safe medication use, and assess health status.

[0542] The precise detection mode includes at least one of an optical detection mode and an electrochemical detection mode. The precise detection mode can realize counting-type detection, especially for detecting urine components and other cells that may appear, as well as substances such as RNA.

[0543] Furthermore, an optical detection method is used to collect optical information of urine and perform urine testing based on the optical information of urine. The optical detection method includes at least one of a microscopic image detection method, a fluorescence detection method, and a spectral detection method. The optical information includes microscopic information, fluorescence information, and spectral information of urine.

[0544] Specifically, the microscopic image detection method is used to collect microscopic information of urine and perform urine testing based on the microscopic information. This embodiment injects urine into the sample detection chamber of the microscopic image acquisition module, then controls background light to enter the sample detection chamber of the microscopic image acquisition module to provide a lighting environment for urine testing. Microscopic image information of the urine is then collected. This makes it easier to extract and store information related to the urine sample, and the testing process is simple. In the microscopic image detection method, this embodiment uses the aforementioned microscopic image-based urine testing method to perform urine testing.

[0545] Fluorescence detection is used to collect fluorescence information from urine and perform urine testing based on this fluorescence information. This embodiment injects urine and a fluorescent reagent into the sample detection chamber of the fluorescence image acquisition module. A fluorescent light source then emits excitation light for the fluorescent reagent into the sample detection chamber of the fluorescence image acquisition module, stimulating the mixture of urine and fluorescent reagent to produce fluorescence. Finally, a fluorescent image of the mixture excited by the fluorescent light source is collected through the sample detection chamber. This makes it easier to extract and store information related to the urine sample, and the testing process is simple. Under the fluorescence detection method, this embodiment uses the aforementioned urine component detection method based on fluorescent reagents to perform urine testing.

[0546] The spectral detection method is used to collect spectral information from urine and perform urine testing based on this spectral information. This embodiment injects urine into the sample detection chamber of the spectral information acquisition module, then controls background light to enter the sample detection chamber to provide a lighting environment for urine testing. The spectral information of the urine is then collected. This makes it easier to extract and store relevant information about the urine sample, and the testing process is simple. In the spectral detection method, this embodiment uses the aforementioned spectral detection method for urine components to perform urine testing.

[0547] The electrochemical detection method is used to collect electrochemical information from urine and perform urine testing based on the electrochemical information. Specifically, the collected urine electrochemical information is a number of electrical signals generated when the chip electrodes are turned on. Based on these electrical signals, urine electrochemical indicators can be detected. The electrochemical indicators include at least one of urine specific gravity, urine pH, urine protein, uric acid, urine potassium, urine sodium, urine calcium, urine phosphorus, urine sugar, and urine chloride. Under the electrochemical detection method, this embodiment uses the aforementioned urine electrochemical detection method to perform urine testing.

[0548] Furthermore, urine testing based on the collected electrochemical information includes:

[0549] The collected electrochemical information is compared with the preset electrochemical information and the test result is output. The preset electrochemical information is the preset reference current value. The comparison method is as described in the aforementioned urine electrochemical detection method.

[0550] Furthermore, step S500 includes:

[0551] S501, setting the urine volume for urine testing according to the selected urine testing mode;

[0552] S502: Collect urine samples according to the urine volume.

[0553] Specifically, different urine detection modes require different amounts of urine. The amount of urine required for each urine detection mode is pre-set and a liquid level sensor is provided. Urine sampling is then performed, and the liquid level of the sampled urine is detected by the liquid level sensor. The liquid level of the urine corresponds to the amount of urine. When the urine level reaches the required level, urine sampling is stopped.

[0554] After step S502, the present invention further comprises:

[0555] S503: precipitating and filtering the sampled urine, and temporarily storing the precipitated and filtered urine sample.

[0556] Sedimentation and filtration are mainly used to filter out impurities in urine that will affect the detection effect. Temporary storage and transition are mainly used to remove bubbles in urine. Impurities and bubbles in urine will affect the urine test results.

[0557] Before S503, the present invention further includes:

[0558] S504: For the urine that has undergone temporary storage, set injection paths corresponding to the basic detection mode and the precise detection mode, respectively, and select the corresponding injection path for injection according to the selected detection mode.

[0559] After selecting a urine testing mode, the specific urine testing method is determined based on the selected urine testing mode. Finally, the corresponding sampling path is selected for sampling based on the determined urine testing method. Different urine testing methods have different corresponding sampling paths. Specifically, each urine testing method corresponds to a urine transfer pipeline, and the corresponding urine transfer pipeline is equipped with a microfluidic pump. After the selected urine testing method is determined, the corresponding microfluidic pump on the urine transfer pipeline of the urine testing method is activated to transfer urine.

[0560] After step S520, the present invention further includes:

[0561] S521. After the detection is completed, a cleaning operation is performed.

[0562] During the cleaning operation, urine sampling is stopped and water and cleaning liquid are introduced into the urine transmission pipe. The urine transmission pipe is equipped with devices such as solenoid valves and micro-flow pumps to control the direction and flow rate of the liquid.

[0563] Example 20

[0564] See Figure 40 The embodiment of the present invention discloses a rapid detection system for human biochemical indicators. The system adopts the aforementioned real-time urine detection method to perform urine detection. It can detect both single indicators and diversified indicators. It has a wide range of application scenarios and strong applicability. The rapid detection system for human biochemical indicators includes a sampling device, a sampling device and a detection device. The sampling device collects the samples required for detecting human biochemical indicators. The sampling device is used to transmit the collected samples to a designated location for detection. The detection device is used to detect the samples and obtain human biochemical indicator information. The detection device includes at least: an optical detection module and a chemical detection module. The sampling device transmits the sample to the optical detection module and the chemical detection module respectively. The optical detection module can detect the optical information of the sample, and the chemical detection module can detect the chemical information of the sample. Combining the optical information and chemical information of the sample, the human biochemical indicator information can be detected more comprehensively, and the detected indicator information is also more accurate.

[0565] Preferably, the sample types that can be detected by the rapid detection system for human biochemical indicators mainly include human body fluids such as serum (plasma), urine, saliva, etc., and human tissues such as epithelial tissue.

[0566] Preferably, in this embodiment, the body fluid is urine, and the sampling device includes the aforementioned urine sampler and urine sampling head, which are used to sample urine samples.

[0567] Preferably, the sampling device includes a urine transmission pipeline, which transmits the urine sample collected by the urine sampler to the detection device for urine testing.

[0568] Preferably, the optical detection module includes the aforementioned optical urine detection module, which can detect optical information of a urine sample; and the chemical detection module includes the aforementioned chemical urine detection module, which can detect chemical information of a urine sample.

[0569] Preferably, the optical detection module includes: a microscopic detection module for collecting microscopic images of samples. The microscopic detection module includes the aforementioned microscopic image acquisition module, which is used to perform urine testing using the aforementioned microscopic image-based urine testing method based on the collected microscopic images of urine samples.

[0570] Preferably, the optical detection module includes a fluorescence detection module for collecting images of the sample after fluorescence excitation. The fluorescence detection module includes the aforementioned fluorescence image acquisition module, which is used to perform urine testing using the aforementioned fluorescence reagent-based urine component detection method based on the collected image of the urine sample after fluorescence excitation.

[0571] Preferably, the optical detection module includes: a spectrum detection module for detecting spectrum information of the sample. The spectrum detection module includes the aforementioned spectrum information acquisition module, which is used to perform urine detection using the aforementioned spectrum detection method for urine components based on the detected spectrum information of the urine sample.

[0572] Preferably, the chemical detection module includes an electrochemical detection module for detecting changes in electrical signals of a sample. The electrochemical detection module includes the aforementioned electrochemical body fluid detection device for performing urine detection using the aforementioned urine electrochemical detection method based on changes in electrical signals of the detected urine sample.

[0573] Preferably, the sample injection device comprises: a microfluidic pump for temporarily storing the sample and quantitatively delivering the sample.

[0574] Preferably, the system further comprises a cleaning device for cleaning the human biochemical index rapid detection system. In one embodiment, the system itself can serve as a cleaning system, such as by introducing a cleaning fluid into the urine electrochemical detection module, and after cleaning, the cleaning fluid becomes waste liquid and flows out of the urine electrochemical detection module.

[0575] Preferably, the system further comprises: a driving device for driving the rapid detection system for human biochemical indicators to operate. The driving device can be a stepping motor for driving the various components of the rapid detection system for human biochemical indicators to operate.

[0576] Preferably, the system further comprises a control device for controlling the rapid detection system for human biochemical indicators. The control device may be a central processing unit (CPU), which controls the sampling device to perform sampling, controls the sample introduction device to transfer the collected sample to the detection device for detection, and controls the detection device to perform detection.

[0577] 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 above embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the above 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 real-time urine detection method, characterized in that: include: Selecting a urine testing mode, wherein the urine testing mode includes at least one of a basic testing mode, a precise testing mode, and a composite testing mode; Perform urine sampling; Testing the sampled urine according to the selected urine testing mode; Output urine test results; The precise detection mode includes an electrochemical detection mode, in which urine electrochemical detection method is used to perform urine detection; The urine electrochemical detection method comprises: Conductive identification is performed on the electrochemical detection chip that is normally working after the urine sample is dropped on it, and the conductive identification is performed by determining whether current is generated on the electrochemical detection chip; When the conductive identification indicates that a current is generated on the electrochemical detection chip, obtaining at least one current value on the electrochemical detection chip; Compare all current values ​​with the preset reference current value and output the test results; The method of comparing all current values ​​with a preset reference current value and outputting the detection results includes: Set a reference current sequence; Setting a time-current sequence consisting of current values ​​when current is generated on the electrochemical detection chip; Screening out a standard current sequence from a current sequence template library based on the reference current sequence and the length of the time current sequence; Obtaining a first dynamic time warping distance according to the reference current sequence and the standard current sequence; Obtaining a second dynamic time warping distance according to the reference current sequence and the time current sequence; The first dynamic time warping distance and the second dynamic time warping distance are compared to determine a detection result of the electrochemical detection chip.

2. The urine real-time detection method according to claim 1, characterized in that: The precise detection mode includes at least one of an optical detection method and an electrochemical detection method. The optical detection method is used to collect optical information of urine and perform urine detection based on the optical information of urine. The electrochemical detection method is used to collect electrochemical information of urine and perform urine detection based on the electrochemical information of urine.

3. The urine real-time detection method according to claim 2, characterized in that: The urine test based on the collected electrochemical information includes: The collected electrochemical information is compared with the preset electrochemical information, and the detection result is output.

4. The urine real-time detection method according to claim 2, characterized in that: The optical detection method includes at least one of a microscopic image detection method, a fluorescence detection method, and a spectral detection method. The microscopic image detection method is used to collect microscopic information of urine and perform urine detection based on the microscopic information of the urine. The fluorescence detection method is used to collect fluorescent information of urine and perform urine detection based on the fluorescent information of the urine. The spectral detection method is used to collect spectral information of urine and perform urine detection based on the spectral information of urine.

5. The real-time urine detection method according to claim 1, characterized in that: The basic detection mode includes a dry chemical detection method, which is used to collect dry chemical information of urine and perform urine detection based on the dry chemical information of urine.

6. The real-time urine detection method according to any one of claims 1 to 5, characterized in that: The urine sampling comprises: Set the urine volume for urine testing according to the selected urine testing mode; Urine sampling was performed according to the urine volume.

7. The real-time urine detection method according to claim 6, characterized in that: After the step of sampling urine according to the urine volume, the method further comprises: The urine sample is precipitated and filtered, and the precipitated and filtered urine sample is temporarily stored.

8. The real-time urine detection method according to claim 7, characterized in that: Before the step of testing the sampled urine according to the selected urine detection mode, the method further includes: setting injection paths corresponding to the basic detection mode and the precise detection mode, respectively, for the urine that has undergone temporary storage transition, and selecting the corresponding injection path for injection according to the selected detection mode.

9. The urine real-time detection method according to claim 8, characterized in that: After the step of testing the sampled urine according to the selected urine testing mode, the method further includes: After the test is completed, perform cleaning operations.

10. A rapid detection system for human biochemical indicators, characterized in that: Urine testing is performed using the real-time urine testing method according to any one of claims 1 to 9.

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