Breast bisensor based on partition detection, detection device, detection method

Abstract

The application provides a breast BIS sensor based on partition detection, a detection device and a detection method, and belongs to the field of medical sensors.The technical key points are as follows: the lower surface of the detection component body is a conical surface, and the inner and outer ring electrode groups are installed on the conical surface;the inner and outer ring electrode groups are arranged in a circular array, and the centers of the two circular arrays are on the center line of the conical surface;the area between the inner and outer ring electrode groups is divided into N non-overlapping sub-detection areas, the circular whole inside the inner ring electrode group is one sub-detection area, and each sub-detection area divided between the inner and outer ring electrode groups adopts four electrodes to form one sub-detection area detection electrode group;and the detection electrode group of each sub-detection area is used for detecting the bioelectrical impedance spectrum information of the corresponding sub-detection area.The breast BIS sensor based on partition detection, the detection device and the detection method can quickly locate the partition where the tumor is located and judge the lesion type.

Description

Technical Field

[0001] This invention belongs to the technical field of medical sensors, specifically relating to a breast BIS sensor, detection device, and detection method based on zone detection. Background Technology

[0002] Currently, routine methods for locating breast tumors include clinical palpation, ultrasound examination, mammography, and magnetic resonance imaging (MRI). However, these traditional methods have drawbacks such as radiation exposure, long waiting times for images, and high costs. Therefore, there is an urgent need for a low-cost, non-invasive, and radiation-free method for rapid localization of breast cancer lesions.

[0003] BIS (Bioimpedance Spectroscopy), as a radiation-free and non-invasive medical detection method, has been applied to research on breast tumor detection. For example:

[0004] Reference 1: "Wu J, Wang P, Tang Y, et al. Technical Note: A new method to rapidly identify benign and malignant breast lumps through bioelectricalimpedance spectroscopy. Medical Physics (Lancaster), 2019, 46(5): 2522-2525" Comparing the BIS test results with the pathological morphology results, it was found that BIS, as a rapid method for differentiating benign and malignant breast masses, has the characteristics of high efficiency, convenience and high accuracy.

[0005] Reference 2: "Stupin DD, Kuzina EA, Abelit AA, et al. Bioimpedance Spectroscopy: Basics and Applications. ACS Biomater Sci Eng, 2021, 7(6): 1962-1986" BIS technology was used to classify samples from 976 breast cancer patients. A simplified equation was fitted based on the Cole-Cole curve as a classification index. It was found that the diagnostic ability of BIS technology is basically equivalent to that of frozen section.

[0006] Reference 3: "Mahdavi R, Hosseinpour P, Abbasvandi F, et al. Bioelectricalpathology of the breast; real-time diagnosis of malignancy by clinically calibrated impedance spectroscopy of freshly dissected tissue. Biosensors & bioelectronics, 2020, 165(112421-112421)" developed an integrated handheld bioimpedance sensor.

[0007] Reference 4: "Amin N, Rayhan S, Anik AA, Jameel R. Modelling and characterization of cell abnormality using electrical impedance spectroscopy (EIS) system for the preliminary analysis to predict breast cancer, F 2016; 2017; IEEE". Using BIS to model and characterize cell abnormalities can provide preliminary analysis and prediction of breast cancer.

[0008] Reference 5: CN115399734B, which first uses EIT detection and localization, and then uses BIS technology to collect the electrical characteristics of the tumor to determine the cause.

[0009] In summary, the current application of BIS technology in the field of breast tumor detection mainly focuses on how to extract the electrical characteristic parameters of tumors and determine the characteristics of tumors.

[0010] Therefore, directly determining tumor information based on BIS has become a technical approach worthy of research. Summary of the Invention

[0011] The purpose of this invention is to solve the problems existing in the prior art and provide a breast BIS sensor based on partition detection. It uses BIS technology to perform partition detection of the breast to detect the presence of tumors, so as to achieve rapid localization and detection of tumors.

[0012] Another objective of this application is to provide a detection device.

[0013] Another objective of this application is to provide a detection method.

[0014] The technical solution of this application is as follows:

[0015] A breast cancer detection sensor based on zone detection includes: a detection component; the detection component includes: a detection component body and inner and outer electrode groups;

[0016] a. The lower surface of the detection component body is a conical surface, and the inner and outer electrode groups are mounted on the conical surface;

[0017] b. The inner and outer electrode groups are arranged in a circular array and the centers of the two circular arrays are on the center line of the cone surface.

[0018] c. The area between the inner and outer electrode groups (projected as a ring area on the plane) is divided into N non-overlapping sub-detection areas. The entire circle inside the inner electrode group is one sub-detection area. Each sub-detection area between the inner and outer electrode groups uses 4 electrodes to form one sub-detection area detection electrode group; N is a natural number greater than or equal to 8.

[0019] d, The detection electrode group of each sub-detection region is used to detect the bioelectrical impedance spectrum information of its corresponding sub-detection region.

[0020] Furthermore, the number of inner electrode groups is x, and the number of outer electrode groups is x+2y; where y is any natural number from 0 to x.

[0021] or

[0022] The number of outer electrode groups is z, and the number of inner electrode groups is z+2y; y is any natural number from 0 to z.

[0023] Furthermore, the number of inner electrode groups is greater than or equal to four.

[0024] Furthermore, the bottom diameter of the cone is 130mm and the height is 20mm.

[0025] A multi-channel bioimpedance spectroscopy detection device, comprising:

[0026] a. Signal generation and acquisition module, which is used to generate a multi-sinusoidal excitation signal formed by superimposing multiple sinusoidal signals and to acquire the feedback signal of the tissue under test;

[0027] b. Multi-frequency module, which converts the multiple sinusoidal excitation signals generated by the signal generation and acquisition module into two current signals with the same amplitude but opposite phase, and differentially amplifies the acquired feedback signal.

[0028] c. The gating module is used to control the signal transmission between the signal generation and acquisition module, the multi-frequency module and the aforementioned sensors, and to switch the sub-detection areas in a preset order to complete the excitation and acquisition operations.

[0029] The method by which the gating module excites and acquires a single sub-detection region is as follows: a high-speed analog radio frequency signal is emitted from the signal generation and acquisition module, and the signal is guided to two adjacent electrodes of the sub-detection region through the gating module, thereby applying an excitation current to the sub-detection region; subsequently, voltage signals at different frequencies are acquired from the other two adjacent electrodes and output to the signal generation and acquisition module.

[0030] d, storage module, which is used to store multi-channel impedance spectrum data. The multi-channel impedance spectrum data is a frequency-impedance amplitude-phase matrix.

[0031] e, Impedance spectrum calculation module, which is used to calculate the imaginary relaxation impedance, real relaxation impedance and relaxation frequency;

[0032] f, Reference area determination module, is used to determine the sub-detection area selected by the reference area;

[0033] g, the imaginary relaxation impedance correction module, corrects the imaginary relaxation impedance of all sub-detection regions.

[0034] Furthermore, the multi-channel bioimpedance spectroscopy detection device also includes:

[0035] h, MC-BIS data processing module, used to locate tumor location information based on impedance distribution;

[0036] i, BIS data processing module, which is used to classify lesion types.

[0037] Furthermore, the multi-frequency module includes: a power supply module, a mirror voltage-controlled constant current source module, and two differential voltage acquisition modules; the power supply module supplies power to the other modules; the mirror voltage-controlled constant current source module converts the input voltage signal into two current excitation signals with the same amplitude but opposite phase; the two differential voltage acquisition modules differentially acquire the response voltage signal of the target under test and the internal resistance of the constant current source.

[0038] Furthermore, the reference region determination module determines the reference region by: sequentially using L sub-detection regions as reference regions, calculating the comprehensive correction deviation of each sub-detection region selected as a reference region, and using the sub-detection region with the smallest comprehensive correction deviation as the reference region;

[0039] The method for solving the comprehensive correction bias of any j-th sub-detection region as the reference region includes the following steps:

[0040] Step A: Calculate the real impedance correction factor a for all sub-detection regions. 实-eg1-修 ~a 实-egL-修 The imaginary impedance correction factor avirtual - eg1 - correction ~ avirtual -egL-Repair; where the real impedance correction coefficient a for any i-th sub-detection region is real. -egi- Correction factor a for the imaginary part impedance 虚-egi-修正 They are respectively:

[0041] a 实-egi-修正 =Z 实-egi / Z 实-egj ;

[0042] a 虚-egi-修正 =Z 虚-egi / Z 虚-egj ;

[0043] Step B involves calculating the real impedance matrix Z of the detection region based on the real and imaginary impedance correction coefficients obtained in Step A. 实 The imaginary impedance matrix Z 虚 The real part of the corrected impedance matrix Z is obtained by making corrections. 实修正 Imaginary part correction impedance matrix Z 虚修正 ;

[0044]

[0045] Among them, Z 实-ij Z 虚-ij Represents frequency f i The real and imaginary impedances of the j-th sub-detection region; n represents the number of frequencies measured by current excitation.

[0046]

[0047] Step C: Calculate the imaginary part correction deviation ΔD 虚 Real part correction deviation ΔD 实 And calculate the overall correction deviation ΔD:

[0048]

[0049] Furthermore, the method by which the imaginary relaxation impedance correction module corrects the imaginary relaxation impedance is as follows:

[0050] The reference region is denoted as the k-th sub-detection region. The imaginary relaxation impedance correction value Z, which eliminates the irregular shapes of the L sub-detection regions, is calculated. 虚-eg1-形状校正 ~Z 虚-egL-形状校正 ;

[0051] In this context, the corrected imaginary relaxation impedance Z is considered for any i-th sub-detection region. 虚-egi-形状校正 for:

[0052]

[0053] A multi-channel bioimpedance spectroscopy detection method, which is a non-disease detection method, includes the following steps:

[0054] S100, Obtain the frequency-impedance amplitude-phase matrix Z1~Z1 of the L sub-detection regions of the tissue to be detected. L ;

[0055] S200, according to Z1~Z L Obtain the real impedance matrix Z of the detection region. 实 The imaginary impedance matrix Z 虚 ;

[0056]

[0057] Among them, Z 实-ij Z 虚-ij Represents frequency f i The real impedance and imaginary impedance corresponding to the j-th sub-detection region;

[0058] S300, obtain the real relaxation impedance Z of L sub-detection regions. 实-eg1 ~Z 实-egL and the imaginary relaxation impedance Z 虚-eg1 ~Z 虚-egL Among them, Z 实-egi Z 虚-egi Let represent the real relaxation impedance and the imaginary relaxation impedance of the i-th sub-detection region, respectively;

[0059] S400, Determine the reference area: Sequentially select L sub-detection areas as reference areas, calculate the comprehensive correction deviation of each sub-detection area selected as the reference area, and select the sub-detection area with the smallest comprehensive correction deviation as the reference area.

[0060] The method for solving the comprehensive correction bias of any j-th sub-detection region as the reference region includes the following steps:

[0061] S401, Calculate the real impedance correction factor a for all sub-detection regions. 实-eg1-修 ~a 实-egL-修 The imaginary impedance correction factor avirtual - eg1 - correction ~ avirtual -egL- Repair; where the real impedance correction coefficient a for any i-th sub-detection region is real. -egi- Correction factor a for the imaginary part impedance 虚-egi-修正 They are respectively:

[0062] a 实-egi-修正 =Z 实-egi / Z 实-egj ;

[0063] a 虚-egi-修正 =Z 虚-egi / Z虚-egj ;

[0064] S402, adjust Z according to the real and imaginary impedance correction coefficients from step S401. 实 Z 虚 The real part of the corrected impedance matrix Z is obtained by making corrections. 实修正 Imaginary part correction impedance matrix Z 虚修正 ;

[0065]

[0066] S403, Calculate the imaginary part correction deviation ΔD 虚 Real part correction deviation ΔD 实 And calculate the overall correction deviation ΔD:

[0067]

[0068] The reference area defined by S500 and S400 is denoted as the k-th sub-detection area. The imaginary relaxation impedance correction value Z, which eliminates the irregular shape of the L sub-detection areas, is calculated. 虚-eg1-形状校正 ~Z 虚-egL-形状校正 ;

[0069] In this context, the corrected imaginary relaxation impedance Z is considered for any i-th sub-detection region. 虚-egi-形状修正 for:

[0070]

[0071] The advantages of the technical solution of this invention are mainly reflected in:

[0072] First, the breast cancer detection sensor based on zone detection proposed in this application is a breast cancer detection sensor based on zone detection combined with BIS. Its core is that: the sensor is divided into L (L=N+1) sub-detection regions, and each sub-detection region between the inner and outer electrode groups uses 4 electrodes to form a sub-detection region detection electrode group, which corresponds to an independent electrode group; all electrodes form two circular arrays, the inner circle and the outer circle.

[0073] Second, directly using the imaginary relaxation impedance for zone detection is unsuitable. The reason is: ... Figure 3 As shown, impedance information is subject to measurement errors caused by the shape of structural partitions. Therefore, it is necessary to perform void correction to eliminate measurement impedance deviations caused by non-structural partitions.

[0074] Accordingly, this application proposes a field correction method (which is also suitable for BIS information correction of tissues such as the brain and abdomen), which eliminates the influence of the irregular shape of the sub-detection region on the measured impedance by multiplying the impedance spectrum data obtained by each sub-detection region by a corresponding scaling factor.

[0075] 2.1 Select the reference area.

[0076] Each of the L sub-detection regions is used as a reference region. The comprehensive correction deviation of each sub-detection region selected as a reference region is calculated, and the sub-detection region with the smallest comprehensive correction deviation is selected as the reference region.

[0077] 2.2, The reference area determined by S400 is denoted as the k-th sub-detection area. The imaginary relaxation impedance correction value Z, which eliminates the irregular shape of the L sub-detection areas, is calculated. 虚-eg1-形状校正 ~Z 虚-egL-形状校正 :

[0078] The scaling factor for the i-th sub-detection region is:

[0079] The imaginary relaxation impedance correction value Z of the i-th sub-detection region 虚-egi-形状校正 for:

[0080] Third, Z 虚-eg1-形状校正 ~Z 虚-egL-形状校正 This is crucial information for subsequent determination of tumor type and location. For a single tumor, the Z-region... 虚-eg1-形状校正 The impedance value will increase significantly, while in sub-regions unaffected by tumors, the impedance value is relatively low and stable. Table 1 (obtained from numerical simulation) summarizes the upper quartile (Zimag-uq), lower quartile (Zimag-lq), median (Zimag-med), maximum (Zimag-max), and minimum (Zimag-min) impedance values ​​for each sub-region when a tumor is present. Therefore, when performing MC-BIS detection, if the Z value of a certain sub-region is significantly increased, the impedance value will increase significantly, while in sub-regions unaffected by tumors, the impedance value will be relatively low and stable. 虚-eg1-形状校正 If the Ω value exceeds 2.004Ω, it can be preliminarily determined that there is a tumor in the sub-region, thereby enabling rapid localization of UFBC (i.e., unifocal breast cancer) lesions.

[0081] Table 1Statistical Data OfImpedance Detection For Electrode Groups InDifferent Regions

[0082]

[0083] For multiple tumors, machine learning algorithms can be used to quickly locate MMBC (multifocal breast cancer) lesions. Attached Figure Description

[0084] The present application will be further described in detail below with reference to the embodiments in the accompanying drawings, but this does not constitute any limitation on the present application.

[0085] Figure 1 This is a three-dimensional structural schematic diagram of the breast detection sensor of this application.

[0086] Figure 2 This is a three-dimensional structural schematic diagram of the detection component body of this application.

[0087] Figure 3 This is a schematic diagram of the sub-detection area of ​​this application (the left side shows the numbering of the inner and outer electrode groups; the right side shows the numbering of the sub-detection area).

[0088] Figure 4 This is a schematic diagram of the multichannel bioimpedance spectroscopy detection device of this application.

[0089] Figure 5 This is a schematic diagram of an overall scheme for multi-channel bioimpedance spectroscopy detection according to this application.

[0090] Figure 6 This is a flowchart illustrating a multichannel bioimpedance spectroscopy detection method according to this application.

[0091] The annotations in the attached figures are explained as follows:

[0092] Breast detection sensor 100, handheld component 101, detection component 102;

[0093] The detection component body 1021, inner electrode group 1022, and outer electrode group 1023 are tested. Detailed Implementation

[0094] The objectives, advantages, and features of this invention will be explained through the following non-limiting description of preferred embodiments. These embodiments are merely typical examples of applying the technical solutions of this invention, and all technical solutions formed by equivalent substitutions or equivalent transformations fall within the scope of protection claimed by this invention.

[0095] <Example 1: A Breast Detection Sensor>

[0096] Figure 1 A three-dimensional structural diagram of a breast cancer detection sensor is shown. The breast cancer detection sensor 100 includes: a handheld component 101 and a detection component 102; the handheld component 101 is mounted on the top of the detection component 102.

[0097] The detection component 102 includes: a detection component body 1021, an inner electrode group 1022, and an outer electrode group 1023;

[0098] a. The lower surface of the detection component body 1021 is a conical surface (e.g., Figure 2As shown: a conical surface, used to maintain close contact with the surface to be tested (such as human breast tissue). The bottom diameter of the conical surface is 130 mm and the height is 20 mm.

[0099] b. The detection component body 1021 has an inner ring electrode group 1022 and an outer ring electrode group 1023 arranged in a circular array on its conical surface. The center of the circular array where the inner ring electrode group 1022 and the outer ring electrode group 1023 are located is on the center line of the conical surface.

[0100] c, the number of inner circle electrode groups 1022 is x, and the number of outer circle electrode groups 1023 is [2, x+2y]; y is any natural number from 0 to x;

[0101] or;

[0102] The number of outer electrode groups 1022 is z, and the number of inner electrode groups 1023 is z+2y; y is any natural number from 1 to z.

[0103] The annular region between the inner and outer electrode groups is divided into N sub-detection regions (e.g., Figure 3 As shown, the sensor is divided into 9 sub-detection areas: the annular area is divided into 8 sub-detection areas, and the entire circular area inside the inner ring electrode group is 1 sub-detection area. Each sub-detection area of ​​the annular area must use 4 electrodes to form a detection electrode group; this requirement creates an implicit requirement for the number of inner and outer ring electrode groups.

[0104] If the number of inner and outer electrode groups is the same, then taking two adjacent electrodes from each of the inner and outer circles to form four electrodes can constitute one detection electrode group.

[0105] When the number of outer electrode groups is greater than the number of inner electrode groups, for example: Figure 2 In a detection electrode group like “11-16-2-9”, electrodes 1 and 10 are inserted into the outer ring to form “11-16-9-10” or “10-1-2-11” to still meet the requirement that 4 electrodes constitute 1 detection electrode group. That is, the number of electrodes inserted into the outer ring must be increased in multiples of 2.

[0106] The inner electrode group must have at least four electrodes to ensure that the sub-detection areas within the inner electrode group can be measured (i.e., each sub-detection area within the inner electrode group must have at least four electrodes). Figure 3 For Area 9, electrodes 12 and 16 are used for excitation, and electrodes 13 and 15 are used for signal acquisition.

[0107] When the number of outer electrode groups is less than that of inner electrode groups, it can be expressed as: the number of outer electrode groups 1022 is z, and the number of inner electrode groups 1023 is z+2y; where y is any natural number from 0 to z.

[0108] <Example 2: A Multi-channel Bioimpedance Spectroscopy (MC-BIS) Detection Device>

[0109] Figure 4 A structural design diagram of a multi-channel bioimpedance spectroscopy detection device is shown. A multi-channel bioimpedance spectroscopy detection device (the multi-channel essentially corresponds to a majority carrier detection region) includes:

[0110] a) Signal generation and acquisition module: This module generates a multi-sinusoidal excitation signal by superimposing multiple sinusoidal signals and acquires the feedback signal from the tissue under test. Specifically, the signal generation and acquisition module uses a Red Pitaya development board. A custom voltage signal is output from one high-speed RF analog signal output channel on the development board to the multi-frequency module. The response signal returned by the multi-frequency module is acquired using two high-speed RF analog signal output channels on the development board.

[0111] b. Multi-frequency module, which converts multiple sinusoidal excitation signals into two current signals with the same amplitude but opposite phase, and differentially amplifies the acquired feedback signal. Specifically, the multi-frequency module includes: a power supply module, a mirror voltage-controlled constant current source module, and two differential voltage acquisition modules. The power supply module supplies power to the other modules. The mirror voltage-controlled constant current source module converts the input voltage signal into two current excitation signals with the same amplitude but opposite phase. The two differential voltage acquisition modules differentially acquire the response voltage signal of the target under test and the internal resistance of the constant current source, respectively.

[0112] c. The gating module controls the signal transmission between the signal generation and acquisition module and the sensor, and can sequentially switch between different sub-detection areas to achieve individual detection of different areas. Specifically, the gating module controls the four signals (I1, I2, I3) emitted by the multi-frequency module. + I - V + V - The system sequentially switches between sub-detection areas according to a preset order to complete the excitation and acquisition operations. Taking the first sub-detection area (Area1) as an example, this area is surrounded by electrodes 1, 2, 10, and 11. During the detection process, electrodes 1 and 2 serve as the input terminals of the excitation current (I0). + I - Electrodes 10 and 11 serve as the output terminals for voltage acquisition (V). + V -The signal generation and acquisition module emits a high-speed analog radio frequency signal, which is then guided to electrodes 1 and 2 via a gating module, thereby applying an excitation current to the Area 1 region. Subsequently, voltage signals at different frequencies (excitation frequencies of 1kHz-5MHz) are acquired from electrodes 10 and 11 and output to the signal generation and acquisition module (i.e., the frequency range of f1 to f2 is selected). n Current is injected into the human body from a pair of electrodes 1 and 2, while impedance data is collected from another pair of electrodes 10 and 11. After the first sub-detection area is detected, the gating module switches to the next sub-detection area (Area 2) according to a preset sequence and repeats the above excitation and acquisition steps. This process is carried out sequentially until the detection tasks of all sub-detection areas are completed.

[0113] d, Storage module, which stores multi-channel impedance spectrum data. The multi-channel impedance spectrum data is a frequency-impedance amplitude-phase matrix.

[0114]

[0115] Among them, Z i For frequency f i The corresponding impedance amplitude, For frequency f i The corresponding phase angle.

[0116] e, Impedance Spectrum Calculation Module, is used to calculate the imaginary relaxation impedance, real relaxation impedance, and relaxation frequency.

[0117] The impedance spectrum calculation module calculates the imaginary relaxation impedance, real relaxation impedance, and relaxation frequency, including the following steps:

[0118] Step 1: Calculate the frequency-impedance real part-impedance imaginary part matrix for each sub-detection region:

[0119]

[0120] Among them, Z i 'For frequency f i The corresponding real impedance, Z i "For frequency f" i The corresponding imaginary impedance,

[0121] Step 2, determine the imaginary relaxation impedance, real relaxation impedance, and relaxation frequency:

[0122] The relaxation frequency is the frequency at which the imaginary part of the impedance reaches its maximum value.

[0123] The imaginary relaxation impedance is the maximum value of the imaginary part of the impedance, that is, the imaginary part of the impedance corresponding to the relaxation frequency;

[0124] The real relaxation impedance is the real part corresponding to the maximum value of the imaginary part of the impedance.

[0125] f, Reference Area Determination Module, is used to determine the sub-detection areas selected by the reference area.

[0126] g, Imaginary relaxation impedance correction module, corrects the imaginary relaxation impedance.

[0127] h, the MC-BIS data processing module, is used to locate tumor position information based on impedance distribution. Specifically, it uses the imaginary relaxation impedance Z calculated in the imaginary relaxation impedance correction module. imag-relax Locate the tumor's location.

[0128] i. The BIS data processing module is used to classify lesion types. Based on the tumor region already located by the MC-BIS data processing module, the BIS data processing module further classifies tumors within the locked area into benign or malignant forms. The threshold Z for classifying benign and malignant tumors using electrical characteristics is used. imag-relax2 :

[0129] When Z imag-relax ≤Z imag-relax2 At that time, it was a malignant tumor;

[0130] When Z imag-relax >Z imag-relax2 At that time, it was a benign tumor.

[0131] <Example 3: A Multichannel Bioimpedance Spectroscopy Detection Method>

[0132] like Figure 5 and Figure 6 As shown, a multichannel bioimpedance spectroscopy (MC-BIS) detection method is a non-disease detection method, which includes the following steps:

[0133] S100, Obtain the frequency-impedance amplitude-phase matrix Z1~Z1 of the L sub-detection regions of the tissue to be detected. L ;

[0134] S200, according to Z1~Z L Obtain the real impedance matrix Z of the detection region 实 The imaginary impedance matrix Z 虚 ;

[0135]

[0136] Among them, Z 实-ij Z 虚-ij Represents frequency f i The real impedance and imaginary impedance corresponding to the j-th sub-detection region;

[0137] S300, obtain the real relaxation impedance Z of L sub-detection regions. 实-eg1 ~Z 实-egL and the imaginary relaxation impedance Z 虚-eg1 ~Z 虚-egL Among them, Z 实-egi Z 虚-egi Let represent the real relaxation impedance and the imaginary relaxation impedance of the i-th sub-detection region, respectively;

[0138] S400, Determine the reference area: Sequentially select L sub-detection areas as reference areas, calculate the comprehensive correction deviation of each sub-detection area selected as the reference area, and select the sub-detection area with the smallest comprehensive correction deviation as the reference area.

[0139] The method for solving the comprehensive correction bias of any j-th sub-detection region as the reference region includes the following steps:

[0140] S401, Calculate the real impedance correction factor a for all sub-detection regions. 实-eg1-修 ~a 实-egL-修 Imaginary part impedance correction factor a 虚-eg1-修 ~a 虚-egL-修 ;

[0141] Wherein, the real impedance correction coefficient a for any i-th sub-detection region 实-egi-修 Imaginary part impedance correction factor a 虚-egi-修正 They are respectively:

[0142] a 实-egi-修正 =Z 实-egi / Z 实-egj ;

[0143] a 虚-egi-修正 =Z 虚-egi / Z 虚-egj ;

[0144] S402, adjust Z according to the real and imaginary impedance correction coefficients from step S401. 实 Z 虚 The real part of the corrected impedance matrix Z is obtained by making corrections. 实修正 Imaginary part correction impedance matrix Z 虚修正 ;

[0145]

[0146] S403, Calculate the imaginary part correction deviation ΔD 虚 Real part correction deviation ΔD 实 And calculate the overall correction deviation ΔD:

[0147]

[0148] The reference area defined by S500 and S400 is denoted as the k-th sub-detection area. The imaginary relaxation impedance correction value Z, which eliminates the irregular shape of the L sub-detection areas, is calculated. 虚-eg1-形状校正 ~Z 虚-egL-形状校正 ;

[0149] In this context, the corrected imaginary relaxation impedance Z is considered for any i-th sub-detection region. 虚-egi-形状修正 for:

[0150]

[0151] Table 2. Symbol-Physical Meaning Table of this Application

[0152]

[0153] The above-described embodiments are preferred embodiments of the present invention and are only used to facilitate the illustration of the present invention. They are not intended to limit the present invention in any way. Any person skilled in the art who makes local modifications or alterations to the technical content disclosed in the present invention without departing from the scope of the technical features of the present invention shall still fall within the scope of the technical features of the present invention.

Claims

1. A detection device, which is a multi-channel bioimpedance spectroscopy detection device, characterized in that, include: a. Signal generation and acquisition module, which is used to generate a multi-sinusoidal excitation signal formed by superimposing multiple sinusoidal signals and to acquire the feedback signal of the tissue under test; b. Multi-frequency module, which converts the multiple sinusoidal excitation signals generated by the signal generation and acquisition module into two current signals with the same amplitude but opposite phase, and differentially amplifies the acquired feedback signal. c. The gating module is used to control the signal transmission between the signal generation and acquisition module, the multi-frequency module and the breast BIS sensor based on partition detection. It switches the sub-detection areas in a preset order to complete the excitation and acquisition operations. The method by which the gating module excites and acquires a single sub-detection region is as follows: a high-speed analog radio frequency signal is emitted from the signal generation and acquisition module, and the signal is guided to two adjacent electrodes of any sub-detection region through the gating module, thereby applying an excitation current to the sub-detection region; subsequently, voltage signals at different frequencies are acquired from the other two electrodes of the sub-detection region and output to the signal generation and acquisition module. d, storage module, which is used to store multi-channel impedance spectrum data. The multi-channel impedance spectrum data is a frequency-impedance amplitude-phase matrix. e, Impedance spectrum calculation module, which is used to calculate the imaginary relaxation impedance, real relaxation impedance and relaxation frequency; f, Reference area determination module, is used to determine the sub-detection area selected by the reference area; g, the imaginary relaxation impedance correction module, corrects the imaginary relaxation impedance of all sub-detection regions; The reference region determination module determines the reference region by: sequentially using L sub-detection regions as reference regions, calculating the comprehensive correction deviation of each sub-detection region selected as the reference region, and selecting the sub-detection region with the smallest comprehensive correction deviation as the reference region; where L=N+1; The method for solving the comprehensive correction bias of any j-th sub-detection region as the reference region includes the following steps: Step A: Calculate the real impedance correction factor a for all sub-detection regions. 实-eg1-修 ~a 实-egL-修 Imaginary part impedance correction factor a 虚-eg1-修 ~a 虚-egL-修 Wherein, the real impedance correction coefficient a for any i-th sub-detection region 实-egi-修 Imaginary part impedance correction factor a 虚-egi-修正 They are respectively: and 实-egi-修正 = Z 实-egi / From 实-egj ; and 虚-egi-修正 = Z 虚-egi / From 虚-egj ; Among them, Z 实-egi Z 虚-egi Z represents the real relaxation impedance and the imaginary relaxation impedance of the i-th sub-detection region, respectively; 实-egj Z 虚-egj Let represent the real relaxation impedance and the imaginary relaxation impedance of the j-th sub-detection region, respectively; Step B involves calculating the real impedance matrix Z of the detection region based on the real and imaginary impedance correction coefficients obtained in Step A. 实 The imaginary impedance matrix Z 虚 The real part of the corrected impedance matrix Z is obtained by making corrections. 实修正 Imaginary part correction impedance matrix Z 虚修正 ; ， ， in, , Represents frequency f i The real and imaginary impedances of the j-th sub-detection region; n represents the number of frequencies measured by current excitation. ， ， Step C: Calculate the imaginary part correction deviation. Real part correction deviation And calculate the overall correction deviation. : 。 2. The detection device according to claim 1, characterized in that, Also includes: The breast BIS sensor based on partition detection includes: a detection component; the detection component includes: a detection component body and inner and outer electrode groups; the lower surface of the detection component body is a conical surface, and the inner and outer electrode groups are mounted on the conical surface; the inner and outer electrode groups are arranged in a circular array and the centers of the two circular arrays are both on the center line of the conical surface; The area between the inner and outer electrode groups is divided into N non-overlapping sub-detection regions. The entire circular area inside the inner electrode group is one sub-detection region. Each sub-detection region between the inner and outer electrode groups uses four electrodes to form a detection electrode group for that sub-detection region. N is a natural number greater than or equal to 8. The detection electrode group for each sub-detection region is used to detect the bioelectrical impedance spectrum information of its corresponding sub-detection region.

3. The detection device according to claim 1, characterized in that, Also includes: h, the multi-channel bioimpedance spectroscopy data processing module, uses the corrected imaginary relaxation impedance obtained from the imaginary relaxation impedance correction module to determine whether a tumor exists and to locate the tumor location. i, BIS data processing module, which is used to classify lesion types.

4. The detection device according to claim 1, characterized in that, The multi-frequency module includes: a power supply module, a mirror voltage-controlled constant current source module, and two differential voltage acquisition modules; the power supply module supplies power to the other modules; the mirror voltage-controlled constant current source module converts the input voltage signal into two current excitation signals with the same amplitude but opposite phase; the two differential voltage acquisition modules differentially acquire the response voltage signal of the target under test and the internal resistance of the constant current source.

5. The detection device according to claim 2, characterized in that, The number of inner electrode groups is x, and the number of outer electrode groups is x+2y; y is any natural number from 0 to x. or The number of outer electrode groups is z, and the number of inner electrode groups is z+2y; y is any natural number from 0 to z.

6. The detection device according to claim 2, characterized in that, The number of inner electrode groups is greater than or equal to 4.

7. The detection device according to claim 2, characterized in that, The bottom diameter of the cone is 130mm and the height is 20mm.

8. The detection device according to claim 1, characterized in that, The method by which the imaginary relaxation impedance correction module corrects the imaginary relaxation impedance is as follows: The reference region is denoted as the k-th sub-detection region. The imaginary relaxation impedance correction value Z, which eliminates the irregular shapes of the L sub-detection regions, is calculated. 虚-eg1-形状校正 ~Z 虚-egL-形状校正 ; In this context, the corrected imaginary relaxation impedance Z is considered for any i-th sub-detection region. 虚-egi-形状校正 for: ； Among them, Z 虚-egk Let represent the imaginary relaxation impedance of the k-th sub-detection region, respectively.

9. A detection method, which is a multi-channel bioimpedance spectroscopy detection method for non-disease detection purposes, characterized in that, It includes the following steps: S100, Obtain the frequency-impedance amplitude-phase matrix Z1~Z1 of the L sub-detection regions of the tissue to be detected. L ; S200, based on Z1~Z L Obtain the real impedance matrix Z of the detection region. 实 The imaginary impedance matrix Z 虚 ; ， ， in, , Representation and frequency The real and imaginary impedances of the j-th sub-detection region; n represents the number of frequencies measured by current excitation. S300, obtain the real relaxation impedance Z of L sub-detection regions. 实-eg1 ~Z 实-egL and the imaginary relaxation impedance Z 虚-eg1 ~Z 虚-egL Among them, Z 实-egi Z 虚-egi Let represent the real relaxation impedance and the imaginary relaxation impedance of the i-th sub-detection region, respectively; S400, Determine the reference area: Sequentially select L sub-detection areas as reference areas, calculate the comprehensive correction deviation of each sub-detection area selected as the reference area, and select the sub-detection area with the smallest comprehensive correction deviation as the reference area. The method for solving the comprehensive correction bias of any j-th sub-detection region as the reference region includes the following steps: S401, Calculate the real impedance correction factor a for all sub-detection regions. 实-eg1-修 ~a 实-egL-修 Imaginary part impedance correction factor a 虚-eg1-修 ~a 虚-egL-修 Wherein, the real impedance correction coefficient a for any i-th sub-detection region 实-egi-修 Imaginary part impedance correction factor a 虚-egi-修正 They are respectively: and 实-egi-修正 =Z 实-egi / Z 实-egj ; and 虚-egi-修正 =Z 虚-egi / Z 虚-egj ; S402, adjust Z according to the real and imaginary impedance correction coefficients from step S401. 实 Z 虚 The real part of the corrected impedance matrix Z is obtained by making corrections. 实修正 Imaginary part correction impedance matrix Z 虚修正 ; ， ， S403, Calculate the imaginary part correction deviation Real part correction deviation And calculate the overall correction deviation. : ， The reference area defined by S500 and S400 is denoted as the k-th sub-detection area. The imaginary relaxation impedance correction value Z, which eliminates the irregular shape of the L sub-detection areas, is calculated. 虚-eg1-形状校正 ~Z 虚-egL-形状校正 ; In this context, the corrected imaginary relaxation impedance Z is considered for any i-th sub-detection region. 虚-egi-形状修正 for: 。

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