Electrochemical detection method and system for early screening of oral-throat diseases

Abstract

The invention provides an electrochemical detection method and system for early screening of oral-throat diseases, and the method comprises the steps: obtaining an original electric signal generated by each working electrode, and obtaining a current detection environment and sample difference parameters; constructing a space-time coupling correction model according to the detection environment and the sample difference parameters in combination with the dynamic process of saliva flow and marker diffusion in the oral cavity, and dynamically correcting the original electric signal according to the space-time coupling correction model; analyzing the corrected electric signals to obtain the concentration value of each marker; according to the method, the concentration value of each marker is compared with the corresponding threshold value, the comparison result is output, and suggestions are pushed according to the comparison result, specifically, the dynamic change in the detection process is considered, so that the correction precision is effectively improved, the concentration value of each marker, which is finally obtained by analyzing the corrected electric signal, is more accurate, and the detection accuracy is improved. And the suggestions can be pushed accurately.

Description

Electrochemical detection methods and systems for early screening of oral and pharyngeal diseases Technical Field

[0001] This invention belongs to the field of electrochemical detection technology, and specifically relates to an electrochemical detection method and system for early screening of oral and pharyngeal diseases. Background Technology

[0002] Oral cancer and oropharyngeal cancer are common malignant tumors of the head and neck. Early symptoms are often hidden, and most patients are diagnosed at an advanced stage, resulting in poor treatment outcomes and a low 5-year survival rate. Chronic inflammations such as periodontitis, oral mucositis, and pharyngitis, if they recur frequently over a long period, can significantly increase the risk of cancer, and their symptoms (such as mucosal ulcers and sore throat) can be easily confused with early-stage cancer. If early tooth decay is not detected in time, it will gradually develop into cavities and even lead to complications such as pulpitis, seriously affecting oral health.

[0003] In existing detection technologies, the diagnosis of oral cancer and oropharyngeal cancer relies on pathological biopsy, which is invasive, time-consuming, and dependent on specialized equipment and medical personnel, making it difficult to use for large-scale screening and home self-examination. The diagnosis of chronic inflammation relies mainly on symptom observation and blood routine tests, lacking convenient on-site simultaneous detection methods. Early caries is mainly detected through visual observation and probing, which is highly subjective and makes it difficult to detect early lesions in the enamel demineralization stage.

[0004] Although some saliva-based electrochemical detection devices have emerged in the existing technology, they have drawbacks such as detecting only one disease (either only cancer or only inflammation), relying on enzymatic reactions (poor stability, requiring low-temperature storage and transportation), complex operation, lack of multi-channel wireless transmission and intelligent identification functions, and the detection accuracy is easily affected by impurities in the sample, making it difficult to meet the needs of primary healthcare, dental clinics and home screening for high-risk groups. Summary of the Invention

[0005] Based on this, the present invention provides an electrochemical detection method and system for early screening of oral and pharyngeal diseases. It aims to achieve non-invasive, rapid, and accurate simultaneous detection of oral cancer, oropharyngeal cancer, precancerous inflammation, and early dental caries based on an enzyme-free system and multi-channel electrode design. The system is easy to operate and adaptable to multiple scenarios.

[0006] The first aspect of this invention provides an electrochemical detection method for early screening of oral and pharyngeal diseases, applied in a scenario with an intelligent detection tongue depressor. The intelligent detection tongue depressor is equipped with multiple independent working electrodes, each coated with a specific adaptant for specific binding reactions with corresponding biomarkers in the sample, causing changes in the electrochemical properties of each electrode surface and generating independent electrical signals. The method includes: acquiring the original electrical signals generated by each working electrode, and acquiring the current detection environment and sample difference parameters, wherein the detection environment includes at least temperature, and the sample difference parameters include at least saliva viscosity and pH value; constructing a spatiotemporal coupling correction model based on the temperature, saliva viscosity, and pH value, combined with the dynamic processes of saliva flow and biomarker diffusion in the oral cavity, and dynamically correcting the original electrical signals according to the spatiotemporal coupling correction model; analyzing the corrected electrical signals to obtain the concentration values ​​of each biomarker; comparing the concentration values ​​of each biomarker with corresponding thresholds, outputting the comparison results, and providing suggestions based on the comparison results.

[0007] Furthermore, the step of constructing a spatiotemporal coupling correction model based on the temperature, saliva viscosity, and pH value, combined with the dynamic processes of saliva flow and marker diffusion in the oral cavity, and dynamically correcting the original electrical signal based on the spatiotemporal coupling correction model includes: constructing a partial differential equation describing the change of marker concentration with time and space based on Fick's diffusion law and Michaelis-Menten kinetic equations to obtain the spatiotemporal coupling correction model, wherein the influence of the detection environment and the sample difference parameters is embedded in the partial differential equation; discretizing the spatial change direction of marker concentration into several nodes, calculating only the concentration change on the electrode surface, and iterating once at preset time intervals to obtain the theoretical concentration on the electrode surface; calculating the correction coefficient based on the original electrical signal and the theoretical concentration on the electrode surface; dynamically correcting the original electrical signal based on the correction coefficient, and outputting the corrected electrical signal.

[0008] Furthermore, in the step of constructing a partial differential equation describing the temporal and spatial variation of biomarker concentration based on Fick's diffusion law and the Mie kinetic equation, to obtain the spatiotemporal coupling correction model, the expression of the spatiotemporal coupling correction model is as follows: ; ; ; ;in, Let be the concentration of the marker at a distance x from the electrode surface at time t. The diffusion coefficient reflects the effects of temperature and saliva viscosity on the diffusion of the marker. Let T be the initial diffusion coefficient, T be the temperature, and T0 be the initial temperature. The viscosity of saliva. The initial saliva viscosity, Here, R is the diffusion activation energy, and R is the gas constant. This is the reaction rate constant, reflecting the effect of pH on the binding reaction of specific aptamers and markers. The reaction rate constant is the pH value at the optimal pH. pH tolerance coefficient For the effective reaction area, This is the initial effective area. This is the attenuation coefficient.

[0009] Furthermore, in the step of discretizing the marker concentration along the spatial direction into several nodes, calculating only the concentration change at the electrode surface, and performing an iteration at preset time intervals to obtain the theoretical concentration at the electrode surface, the number of nodes is 5, and the formula for calculating the concentration change at the electrode surface is: The expression for iteration is: Where L represents the sampling area range, t is the preset interval time.

[0010] Furthermore, the step of calculating the correction coefficient based on the original electrical signal and the theoretical concentration on the electrode surface includes: calculating the response coefficient in real time based on the temperature and the pH value; determining the interference concentration based on the response coefficient and the original electrical signal; adding an error compensation term to the theoretical concentration on the electrode surface to obtain the predicted true concentration; and determining the correction coefficient based on the interference concentration and the predicted true concentration.

[0011] Furthermore, the step of dynamically correcting the original electrical signal according to the correction coefficient and outputting the corrected electrical signal includes: determining whether the predicted true concentration is greater than or equal to the preset electrode saturation concentration; if so, using nonlinear mapping to determine the corrected electrical signal; if not, calculating the corrected electrical signal according to the correction coefficient and the original electrical signal.

[0012] Furthermore, in the step of calculating the response coefficient in real time based on the temperature and the pH value, the formula for calculating the response coefficient is as follows: ;in, Here is the response coefficient under the reference condition, and T is the temperature. Temperature is the reference temperature, and pH is the pH value. α is the pH value under reference conditions, α is the electron transfer coefficient, n is the number of transferred electrons, F is the Faraday constant, and R is the gas constant.

[0013] A second aspect of this invention provides an electrochemical detection system for early screening of oral and pharyngeal diseases, used to implement the electrochemical detection method for early screening of oral and pharyngeal diseases described in the first aspect. The system includes: an acquisition module for acquiring raw electrical signals generated by each working electrode, and acquiring the current detection environment and sample difference parameters, wherein the detection environment includes at least temperature, and the sample difference parameters include at least saliva viscosity and pH value; a correction module for constructing a spatiotemporal coupling correction model based on the temperature, saliva viscosity, and pH value, combined with the dynamic process of saliva flow and marker diffusion in the oral cavity, and dynamically correcting the raw electrical signals according to the spatiotemporal coupling correction model; an analysis module for analyzing the corrected electrical signals to obtain the concentration values ​​of each marker; and a comparison module for comparing the concentration values ​​of each marker with corresponding thresholds, outputting the comparison results, and pushing suggestions based on the comparison results.

[0014] A third aspect of the present invention provides a computer-readable storage medium having a computer program stored thereon, which, when executed by a processor, implements the electrochemical detection method for early screening of oral and pharyngeal diseases provided in the first aspect.

[0015] A fourth aspect of the present invention provides an electronic device including a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor executes the program to implement the electrochemical detection method for early screening of oral and pharyngeal diseases provided in the first aspect.

[0016] This invention provides an electrochemical detection method and system for early screening of oral and pharyngeal diseases. It acquires the raw electrical signals generated by each working electrode, along with the current detection environment and sample difference parameters. The detection environment includes at least temperature, and the sample difference parameters include at least saliva viscosity and pH. Based on temperature, saliva viscosity, and pH, and considering the dynamic processes of saliva flow and biomarker diffusion within the oral cavity, a spatiotemporal coupling correction model is constructed. The raw electrical signals are then dynamically corrected according to this model. The corrected electrical signals are analyzed to obtain the concentration values ​​of each biomarker. The concentration values ​​of each biomarker are compared with their corresponding thresholds, and the comparison results are output. Based on these results, recommendations are pushed. Specifically, by considering the dynamic changes during the detection process, the correction accuracy is effectively improved, resulting in more accurate concentration values ​​of each biomarker obtained through the analysis of the corrected electrical signals, which facilitates precise recommendation delivery. Attached Figure Description

[0017] Figure 1 is a flowchart of an electrochemical detection method for early screening of oral and pharyngeal diseases provided in Embodiment 1 of the present invention; Figure 2 is a structural block diagram of an electrochemical detection system for early screening of oral and pharyngeal diseases provided in Embodiment 2 of the present invention; Figure 3 is a structural block diagram of an electronic device provided in Embodiment 3 of the present invention. Detailed Implementation

[0018] To facilitate understanding of the present invention, a more complete description will be given below with reference to the accompanying drawings. Several embodiments of the invention are illustrated in the drawings. However, the invention can be implemented in many different forms and is not limited to the embodiments described herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete.

[0019] It should be noted that when a component is said to be "fixed to" another component, it can be directly on the other component or there may be an intervening component. When a component is said to be "connected to" another component, it can be directly connected to the other component or there may be an intervening component. The terms "vertical," "horizontal," "left," "right," and similar expressions used in this document are for illustrative purposes only.

[0020] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains. The terminology used herein in the description of the invention is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. The term "and / or" as used herein includes any and all combinations of one or more of the associated listed items.

[0021] Example 1: According to an embodiment of the present invention, an electrochemical detection method for early screening of oral and pharyngeal diseases is provided. It should be noted that the steps shown in the flowchart in the accompanying drawings can be executed in a computer system such as a set of computer-executable instructions. Furthermore, although a logical order is shown in the flowchart, in some cases, the steps shown or described may be executed in a different order than that shown here.

[0022] This embodiment provides an electrochemical detection method for early screening of oral and pharyngeal diseases, applied in a scenario with an intelligent detection tongue depressor. One end of the intelligent detection tongue depressor is provided with a detection functional area and an electrode area corresponding to the detection functional area. The detection functional area includes a tooth surface scraping end and a porous adsorption sampling area. The tooth surface scraping end is used for adsorbing samples from the tooth area, and the porous adsorption sampling area is used for adsorbing samples from the oral and pharyngeal areas. The electrode area is provided with multiple independent working electrodes, and the surface of each working electrode is coated with a specific adaptant for specific binding reactions with corresponding markers in the sample, causing changes in the electrochemical properties of each electrode surface and generating independent electrical signals.

[0023] In this embodiment of the invention, the intelligent detection tongue depressor is made of medical-grade sterile material, the tooth surface scraping end is made of biocompatible flexible material, and the porous adsorption sampling area is made of medical porous material with adsorption properties. A multi-channel micro three-electrode electrochemical chip is embedded on the back of the intelligent detection tongue depressor. The electrochemical chip includes multiple independent working electrodes, a common reference electrode, and a common counter electrode. Each working electrode surface is sequentially modified with an enzyme-free composite coating and an anti-interference layer. The enzyme-free composite coating contains specific adaptants for specific markers of oral cancer, oropharyngeal cancer, early dental caries, and precancerous inflammatory markers. Different working electrodes correspond to different detection targets (malignant diseases / inflammation / dental caries), realizing independent detection of multiple targets.

[0024] Specifically, the specific biomarkers include malignant disease biomarkers, inflammatory biomarkers, and dental caries biomarkers, totaling at least four types; the malignant disease biomarkers are selected from biomarkers related to oral cancer and oropharyngeal cancer, including but not limited to any one or more of miRNA-21, squamous cell carcinoma antigen (SCC), carcinoembryonic antigen (CEA), microRNA-155 (miRNA-155), and cytokeratin 19 fragment (CYFRA21-1); the inflammatory biomarkers are selected from precancerous / high-risk inflammatory biomarkers related to periodontitis, oral mucositis, pharyngitis, and tonsillitis, including but not limited to any one or more of interleukin-8 (IL-8), matrix metalloproteinase-9 (MMP-9), C-reactive protein (CRP), and tumor necrosis factor-α (TNF-α); the dental caries biomarkers are selected from biomarkers related to early dental caries, including but not limited to any one or more of lactate dehydrogenase (LDH), sialic acid, and Streptococcus mutans-specific antigen.

[0025] Please refer to Figure 1, which shows a flowchart of an electrochemical detection method for early screening of oral and pharyngeal diseases provided in Embodiment 1 of the present invention, specifically including steps S01 to S04.

[0026] Step S01: Obtain the raw electrical signals generated by each working electrode, and obtain the current detection environment and sample difference parameters. The detection environment includes at least temperature, and the sample difference parameters include at least saliva viscosity and pH value.

[0027] The original electrical signal is the raw current signal output by the working electrode, without considering the detection environment and sample variability parameters.

[0028] Step S02: Based on the temperature, saliva viscosity, and pH value, and combined with the dynamic processes of saliva flow and marker diffusion in the oral cavity, a spatiotemporal coupling correction model is constructed, and the original electrical signal is dynamically corrected based on the spatiotemporal coupling correction model.

[0029] Specifically, based on Fick's diffusion law and the Michaelis-Menten kinetic equation, a partial differential equation describing the temporal and spatial variation of biomarker concentration is constructed, resulting in the spatiotemporal coupling correction model. The influence of the detection environment and the sample variability parameters is embedded in the partial differential equation. The expression for the spatiotemporal coupling correction model is as follows: ; ; ; ;in, Let be the concentration of the marker at a distance x from the electrode surface at time t. The diffusion coefficient reflects the effects of temperature and saliva viscosity on the diffusion of the marker. Let T be the initial diffusion coefficient, T be the temperature, and T0 be the initial temperature. The viscosity of saliva. The initial saliva viscosity, Here, R is the diffusion activation energy, and R is the gas constant. This is the reaction rate constant, reflecting the effect of pH on the binding reaction of specific aptamers and markers. The reaction rate constant is the pH value at the optimal pH. pH tolerance coefficient For the effective reaction area, This is the initial effective area. The attenuation coefficient is used. The concentration of the marker is discretized into several nodes along the spatial direction. Only the concentration change at the electrode surface is calculated, and an iteration is performed at preset time intervals to obtain the theoretical concentration at the electrode surface. It is understood that, in order to reduce the computational power requirement, the spatiotemporal coupling correction model can be simplified into a low-dimensional computational model to ensure that an iteration can be completed in a short time. In this embodiment of the invention, the x-direction (0~L) is discretized into 5 nodes (x=0, L / 4, L / 2, 3L / 4, L). Only the concentration change at the electrode surface (x=0) is calculated (because the electrical signal is only related to the reaction at x=0). The formula for calculating the concentration change at the electrode surface is: The expression for iteration is: Where L represents the sampling area range, t represents the preset interval time. It should be noted that x = -L / 2 represents a virtual node, determined by symmetry conditions. To simplify and avoid boundary errors, a correction coefficient is calculated based on the original electrical signal and the theoretical concentration on the electrode surface. Specifically, the response coefficient under the current state is calculated in real time based on the temperature and pH value. The formula for calculating the response coefficient is as follows: ;in, Here is the response coefficient under the reference condition, and T is the temperature. Temperature is the reference temperature, and pH is the pH value. The pH value is the reference value, α is the electron transfer coefficient, n is the number of transferred electrons, F is the Faraday constant, and R is the gas constant. Based on the response coefficient and the original electrical signal, the interference concentration is determined, and the interference concentration is expressed as: ;in, For the concentration affected by interference, The original electrical signal, For the response coefficient, The background current is obtained through blank saliva detection and is automatically calibrated before each detection to avoid baseline drift. An error compensation term is added to the theoretical concentration at the electrode surface to obtain the predicted true concentration, expressed as: ;in, For the predicted true concentration, This represents the theoretical concentration at the electrode surface. The error compensation term is obtained through verification using an auxiliary electrode; the correction coefficient is determined based on the affected concentration and the predicted true concentration, expressed as: ;in, The correction coefficient is used to dynamically correct the original electrical signal and output the corrected electrical signal. Specifically, it is determined whether the predicted true concentration is greater than or equal to the preset electrode saturation concentration; if so, a nonlinear mapping is used to determine the corrected electrical signal, expressed as: ;in, The corrected electrical signal For saturation current, If the value is the Mie constant, then the corrected electrical signal is calculated based on the correction coefficient and the original electrical signal, and the expression is: ;in, This is the corrected electrical signal.

[0030] Step S03: Analyze the corrected electrical signal to obtain the concentration values ​​of each marker.

[0031] Specifically, a quantitative relationship between electrical signal and concentration can be established in advance using standards of known concentration. Once the corrected electrical signal is obtained, it can be substituted into the quantitative relationship to obtain the concentration value. Alternatively, machine learning methods can be used to extract features of the electrical signal (such as peak current, peak potential, characteristic frequencies of impedance spectrum, etc.), train an SVM regression model, and directly output the concentration value.

[0032] Step S04: Compare the concentration values ​​of each marker with the corresponding threshold, output the comparison results, and push suggestions based on the comparison results.

[0033] In this embodiment of the invention, the warning signal includes four levels: "Normal," "Suspected Inflammation," "Attention Notice," and "Red Alert." When the concentrations of all markers are below a preset threshold, "Normal" is displayed, and oral health maintenance suggestions are pushed. When only inflammatory markers (such as IL-8 and CRP) are abnormal, and malignant / carious markers are normal, "Suspected Inflammation" is displayed, and targeted anti-inflammatory care and follow-up examination suggestions are pushed. When the concentration of malignant / carious markers is 80%-100% of the threshold (inflammatory markers may be normal), "Attention Notice" is displayed, and suggestions for enhanced health intervention and regular testing are pushed. When the concentration of malignant markers exceeds the threshold, a "Red Alert" is triggered, and guidance to the nearest medical institution's stomatology or ENT department is pushed. This approach is more practical. For example, if the concentrations of all biomarkers are below the threshold, a "normal" signal is output, and health maintenance suggestions such as oral hygiene and reducing sugar intake are pushed. If only the concentrations of IL-8 and CRP exceed the threshold, a "suspected inflammation" signal is output, and suggestions such as "use mouthwash, avoid spicy and irritating foods, and have a follow-up examination in one month" are pushed. If the LDH concentration is 90% of the threshold, a "pay attention" signal is output, and suggestions such as "strengthen dental hygiene and have regular dental checkups" are pushed. If the miRNA-21 concentration exceeds the threshold, a "red alarm" is triggered, and guidance to the nearest hospital is pushed. At the same time, the test data is encrypted and stored through the data storage module and synchronized to the cloud data platform through the cloud synchronization module.

[0034] In summary, the electrochemical detection method for early screening of oral and pharyngeal diseases in the above embodiments of the present invention acquires the original electrical signals generated by each working electrode, and obtains the current detection environment and sample difference parameters. The detection environment includes at least temperature, and the sample difference parameters include at least saliva viscosity and pH value. Based on temperature, saliva viscosity, and pH value, combined with the dynamic process of saliva flow and marker diffusion in the oral cavity, a spatiotemporal coupling correction model is constructed, and the original electrical signals are dynamically corrected according to the spatiotemporal coupling correction model. The corrected electrical signals are analyzed to obtain the concentration values ​​of each marker. The concentration values ​​of each marker are compared with the corresponding thresholds, the comparison results are output, and suggestions are pushed based on the comparison results. Specifically, because the dynamic changes in the detection process are considered, the correction accuracy is effectively improved, making the concentration values ​​of each marker obtained by the analysis of the corrected electrical signals more accurate, which is conducive to accurate suggestion pushing.

[0035] Please refer to Figure 2 for Embodiment 2. Figure 2 is a structural block diagram of an electrochemical detection system for early screening of oral and pharyngeal diseases provided in Embodiment 2 of the present invention. This electrochemical detection system 200 for early screening of oral and pharyngeal diseases is used to implement the above embodiments and preferred embodiments, and will not be repeated for details already described. As used below, the term "module" can refer to a combination of software and / or hardware that performs a predetermined function. Although the apparatus described in the following embodiments is preferably implemented in software, hardware implementation, or a combination of software and hardware, is also possible and contemplated.

[0036] Specifically, the electrochemical detection system 200 for early screening of oral and pharyngeal diseases includes: an acquisition module 21, a correction module 22, an analysis module 23, and a comparison module 24. The acquisition module 21 acquires the original electrical signals generated by each working electrode and obtains the current detection environment and sample difference parameters. The detection environment includes at least temperature, and the sample difference parameters include at least saliva viscosity and pH value. The correction module 22 constructs a spatiotemporal coupling correction model based on the temperature, saliva viscosity, and pH value, combined with the dynamic processes of saliva flow and marker diffusion in the oral cavity, and dynamically corrects the original electrical signals according to the spatiotemporal coupling correction model. The analysis module 23 analyzes the corrected electrical signals to obtain the concentration values ​​of each marker. The comparison module 24 compares the concentration values ​​of each marker with the corresponding threshold, outputs the comparison results, and pushes suggestions based on the comparison results.

[0037] Furthermore, in some optional embodiments of the present invention, the correction module 22 includes: a construction unit, used to construct a partial differential equation describing the temporal and spatial variation of biomarker concentration based on Fick's diffusion law and the Michaelis-Menten kinetic equation, to obtain the spatiotemporal coupling correction model, wherein the influence of the detection environment and the sample difference parameter is embedded in the partial differential equation, and the expression of the spatiotemporal coupling correction model is: ; ; ; ;in, Let be the concentration of the marker at a distance x from the electrode surface at time t. The diffusion coefficient reflects the effects of temperature and saliva viscosity on the diffusion of the marker. Let T be the initial diffusion coefficient, T be the temperature, and T0 be the initial temperature. The viscosity of saliva. The initial saliva viscosity, Here, R is the diffusion activation energy, and R is the gas constant. This is the reaction rate constant, reflecting the effect of pH on the binding reaction of specific aptamers and markers. The reaction rate constant is the pH value at the optimal pH. pH tolerance coefficient For the effective reaction area, This is the initial effective area. The attenuation coefficient is used; the first calculation unit is used to discretize the concentration of the marker as a function of space into several nodes, calculate only the concentration change at the electrode surface, and iterate once at preset time intervals to obtain the theoretical concentration at the electrode surface. The number of nodes is 5, and the formula for calculating the concentration change at the electrode surface is: The expression for iteration is: Where L represents the sampling area range, t is a preset interval time; the second calculation unit is used to calculate the correction coefficient based on the original electrical signal and the theoretical concentration on the electrode surface; the correction unit is used to dynamically correct the original electrical signal based on the correction coefficient and output the corrected electrical signal.

[0038] Furthermore, in some optional embodiments of the present invention, the second calculation unit includes: a first calculation subunit, configured to calculate the response coefficient in real time under the current state based on the temperature and the pH value, wherein the calculation formula for the response coefficient is: ;in, Here is the response coefficient under the reference condition, and T is the temperature. Temperature is the reference temperature, and pH is the pH value. Here, pH is the reference value, α is the electron transfer coefficient, n is the number of transferred electrons, F is the Faraday constant, and R is the gas constant; the first determining subunit is used to determine the disturbed concentration based on the response coefficient and the original electrical signal; the adding subunit is used to add an error compensation term to the theoretical concentration on the electrode surface to obtain the predicted true concentration; the second determining subunit is used to determine the correction coefficient based on the disturbed concentration and the predicted true concentration.

[0039] Furthermore, in some optional embodiments of the present invention, the correction unit includes: a judgment subunit, used to judge whether the predicted true concentration is greater than or equal to a preset electrode saturation concentration; a third determination subunit, used to determine the corrected electrical signal by using nonlinear mapping when the predicted true concentration is greater than or equal to the preset electrode saturation concentration; and a second calculation subunit, used to calculate the corrected electrical signal based on the correction coefficient and the original electrical signal when the predicted true concentration is less than the preset electrode saturation concentration.

[0040] Example 3: Another aspect of the present invention provides an electronic device. Please refer to Figure 3, which shows the electronic device in Example 3 of the present invention. It includes a memory 20, a processor 10, and a computer program 30 stored in the memory and executable on the processor. When the processor 10 executes the computer program 30, it implements the electrochemical detection method for early screening of oral and pharyngeal diseases as described above.

[0041] In some embodiments, the processor 10 may be a central processing unit (CPU), controller, microcontroller, microprocessor or other data processing chip, used to run program code stored in memory 20 or process data, such as executing access restriction programs.

[0042] The memory 20 includes at least one type of readable storage medium, such as flash memory, hard disk, multimedia card, card-type memory (e.g., SD or DX memory), magnetic memory, magnetic disk, optical disk, etc. In some embodiments, the memory 20 can be an internal storage unit of an electronic device, such as the hard disk of the electronic device. In other embodiments, the memory 20 can also be an external storage device of the electronic device, such as a plug-in hard disk, SmartMediaCard (SMC), SecureDigital (SD) card, FlashCard, etc., equipped on the electronic device. Furthermore, the memory 20 can include both internal and external storage units of the electronic device. The memory 20 can be used not only to store application software and various types of data of the electronic device, but also to temporarily store data that has been output or will be output.

[0043] It should be noted that the structure shown in Figure 3 does not constitute a limitation on the electronic device. In other embodiments, the electronic device may include fewer or more components than shown, or combine certain components, or have different component arrangements.

[0044] This invention also proposes a computer-readable storage medium storing a computer program that, when executed by a processor, implements the electrochemical detection method for early screening of oral and pharyngeal diseases as described above.

[0045] Those skilled in the art will understand that the logic and / or steps represented in the flowcharts or otherwise described herein, for example, can be considered as a ordered list of executable instructions for implementing logical functions, and can be embodied in any computer-readable medium for use by, or in conjunction with, an instruction execution system, apparatus, or device (such as a computer-based system, a processor-included system, or other system that can fetch and execute instructions from, an instruction execution system, apparatus, or device). For the purposes of this specification, "computer-readable medium" can mean any means that can contain, store, communicate, propagate, or transmit programs for use by, or in conjunction with, an instruction execution system, apparatus, or device.

[0046] More specific examples of computer-readable media (a non-exhaustive list) include: electrical connections (electronic devices) having one or more wires, portable computer disk drives (magnetic devices), random access memory (RAM), read-only memory (ROM), erasable and editable read-only memory (EPROM or flash memory), fiber optic devices, and portable optical disc read-only memory (CDROM). Furthermore, computer-readable media can even be paper or other suitable media on which the program can be printed, because the program can be obtained electronically, for example, by optically scanning the paper or other medium, followed by editing, interpreting, or otherwise processing as necessary, and then stored in computer memory.

[0047] It should be understood that various parts of the present invention can be implemented in hardware, software, firmware, or a combination thereof. In the above embodiments, multiple steps or methods can be implemented in software or firmware stored in memory and executed by a suitable instruction execution system. For example, if implemented in hardware, as in another embodiment, it can be implemented using any one or a combination of the following techniques known in the art: discrete logic circuits having logic gates for implementing logical functions on data signals, application-specific integrated circuits (ASICs) having suitable combinational logic gates, programmable gate arrays (PGAs), field-programmable gate arrays (FPGAs), etc.

[0048] In the description of this specification, references to terms such as "one embodiment," "some embodiments," "example," "specific example," or "some examples," etc., indicate that a specific feature, structure, material, or characteristic described in connection with that embodiment or example is included in at least one embodiment or example of the invention. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples.

[0049] The above embodiments merely illustrate several implementation methods of the present invention, and their descriptions are relatively specific and detailed, but they should not be construed as limiting the scope of the present invention. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of the present invention, and these all fall within the protection scope of the present invention. Therefore, the protection scope of this patent should be determined by the appended claims.

Claims

1. An electrochemical detection method for early screening of oral and pharyngeal diseases, characterized in that, In scenarios involving intelligent tongue depressors, the intelligent tongue depressor is equipped with multiple independent working electrodes, each coated with a specific adaptant for specific binding reactions with corresponding biomarkers in the sample. This causes changes in the electrochemical properties of each electrode surface, generating independent electrical signals. The method includes: acquiring the original electrical signals generated by each working electrode, and acquiring the current detection environment and sample difference parameters, wherein the detection environment includes at least temperature, and the sample difference parameters include at least saliva viscosity and pH value; constructing a spatiotemporal coupling correction model based on the temperature, saliva viscosity, and pH value, combined with the dynamic processes of saliva flow and biomarker diffusion in the oral cavity, and dynamically correcting the original electrical signals according to the spatiotemporal coupling correction model; analyzing the corrected electrical signals to obtain the concentration values ​​of each biomarker; comparing the concentration values ​​of each biomarker with corresponding thresholds, outputting the comparison results, and providing suggestions based on the comparison results.

2. The electrochemical detection method for early screening of oral and pharyngeal diseases according to claim 1, characterized in that, The steps of constructing a spatiotemporal coupling correction model based on the temperature, saliva viscosity, and pH value, combined with the dynamic processes of saliva flow and biomarker diffusion in the oral cavity, and dynamically correcting the original electrical signal based on the spatiotemporal coupling correction model, include: constructing a partial differential equation describing the change of biomarker concentration with time and space based on Fick's diffusion law and Michaelis-Menten kinetic equations, thereby obtaining the spatiotemporal coupling correction model, wherein the influence of the detection environment and the sample difference parameters is embedded in the partial differential equation; discretizing the direction of biomarker concentration change with space into several nodes, calculating only the concentration change at the electrode surface, and iterating once at preset time intervals to obtain the theoretical concentration at the electrode surface; calculating correction coefficients based on the original electrical signal and the theoretical concentration at the electrode surface; dynamically correcting the original electrical signal based on the correction coefficients, and outputting the corrected electrical signal.

3. The electrochemical detection method for early screening of oral and pharyngeal diseases according to claim 2, characterized in that, In the step of constructing a partial differential equation describing the temporal and spatial variation of biomarker concentration based on Fick's diffusion law and the Mie kinetic equation, to obtain the spatiotemporal coupling correction model, the expression of the spatiotemporal coupling correction model is as follows: ； ； ； ;in, Let be the concentration of the marker at a distance x from the electrode surface at time t. The diffusion coefficient reflects the effects of temperature and saliva viscosity on the diffusion of the marker. Let T be the initial diffusion coefficient, T be the temperature, and T0 be the initial temperature. The viscosity of saliva. This refers to the initial saliva viscosity. Here, R is the diffusion activation energy, and R is the gas constant. This is the reaction rate constant, reflecting the effect of pH on the binding reaction of specific aptamers and markers. The reaction rate constant is the pH value at the optimal pH. pH tolerance coefficient For the effective reaction area, This is the initial effective area. This is the attenuation coefficient.

4. The electrochemical detection method for early screening of oral and pharyngeal diseases according to claim 3, characterized in that, In the step of discretizing the marker concentration along the spatial direction into several nodes, calculating only the concentration change at the electrode surface, and performing an iteration at preset time intervals to obtain the theoretical concentration at the electrode surface, the number of nodes is 5, and the formula for calculating the concentration change at the electrode surface is: The expression for iteration is: Where L represents the sampling area range, t is the preset interval time.

5. The electrochemical detection method for early screening of oral and pharyngeal diseases according to claim 4, characterized in that, The step of calculating the correction coefficient based on the original electrical signal and the theoretical concentration on the electrode surface includes: calculating the response coefficient in real time based on the temperature and the pH value; determining the interference concentration based on the response coefficient and the original electrical signal; adding an error compensation term to the theoretical concentration on the electrode surface to obtain the predicted true concentration; and determining the correction coefficient based on the interference concentration and the predicted true concentration.

6. The electrochemical detection method for early screening of oral and pharyngeal diseases according to claim 5, characterized in that, The step of dynamically correcting the original electrical signal according to the correction coefficient and outputting the corrected electrical signal includes: determining whether the predicted true concentration is greater than or equal to the preset electrode saturation concentration; if so, using nonlinear mapping to determine the corrected electrical signal; if not, calculating the corrected electrical signal according to the correction coefficient and the original electrical signal.

7. The electrochemical detection method for early screening of oral and pharyngeal diseases according to claim 6, characterized in that, In the step of calculating the response coefficient in real time based on the temperature and pH value, the formula for calculating the response coefficient is as follows: ;in, Here is the response coefficient under the reference condition, and T is the temperature. Temperature is the reference temperature, and pH is the pH value. α is the pH value under reference conditions, α is the electron transfer coefficient, n is the number of transferred electrons, F is the Faraday constant, and R is the gas constant.

8. An electrochemical detection system for early screening of oral and pharyngeal diseases, characterized in that, The system, used to implement the electrochemical detection method for early screening of oral and pharyngeal diseases as described in any one of claims 1-7, comprises: an acquisition module for acquiring raw electrical signals generated by each working electrode, and acquiring the current detection environment and sample difference parameters, wherein the detection environment includes at least temperature, and the sample difference parameters include at least saliva viscosity and pH value; a correction module for constructing a spatiotemporal coupling correction model based on the temperature, saliva viscosity, and pH value, combined with the dynamic processes of saliva flow and biomarker diffusion in the oral cavity, and dynamically correcting the raw electrical signals according to the spatiotemporal coupling correction model; an analysis module for analyzing the corrected electrical signals to obtain the concentration values ​​of each biomarker; and a comparison module for comparing the concentration values ​​of each biomarker with corresponding thresholds, outputting the comparison results, and providing suggestions based on the comparison results.

9. A computer-readable storage medium having a computer program stored thereon, characterized in that, When executed by a processor, the program implements the electrochemical detection method for early screening of oral and pharyngeal diseases as described in any one of claims 1-7.

10. An electronic device, characterized in that, It includes a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor, when executing the program, implements the electrochemical detection method for early screening of oral and pharyngeal diseases as described in any one of claims 1-7.

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