Breast BIS sensor based on partition detection, detection device and detection method

Abstract

The invention 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 that the lower surface of a detection component body is a conical surface, and an inner ring electrode group and an outer ring electrode group are mounted on the conical surface; the inner-ring electrode group and the outer-ring electrode group are arranged in a circular array, and the circle centers of the two circular arrays are located on the center line of the conical surface; the area between the inner ring electrode group and the outer ring electrode group is divided into N sub-detection areas which are not overlapped with one another, the whole circle inside the inner ring electrode group is one sub-detection area, and each sub-detection area adopts four electrodes to form one sub-detection area detection electrode group; the detection electrode group of each sub-detection area is used for detecting bioelectrical impedance spectroscopy information of the corresponding sub-detection area. According to the breast BIS sensor based on partition detection, the detection device and the detection method, the partition where a tumor is located can be rapidly positioned, and the lesion type can be rapidly judged.

Description

Technical Field

[0001] The present invention belongs to the technical field of medical sensors, and particularly relates to a breast BIS sensor based on zonal detection, a detection device, and a detection method. Background Art

[0002] Currently, conventional localization methods for breast tumors include clinical palpation, ultrasound examination, mammography (molybdenum target), and magnetic resonance imaging (MRI), etc. However, these traditional detection methods have defects such as radiation exposure, long film waiting time, and high cost. Therefore, there is an urgent need for a means of rapidly localizing breast cancer lesions with low cost, non-invasiveness, and no radiation.

[0003] BIS (bioelectrical impedance spectroscopy) technology, as a non-radiative and non-invasive medical detection means, has been applied to the research of 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 bioelectrical impedance spectroscopy. Medical physics (Lancaster), 2019, 46(5): 2522-2525" compared the BIS detection results with the pathological morphology results and found that BIS, as a detection method for rapidly differentiating the benign and malignant nature of breast lumps, has the characteristics of high efficiency, convenience, and relatively high accuracy.

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

[0006] Reference 3: "Mahdavi R, Hosseinpour P, Abbasvandi F, et al. Bioelectrical pathology 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 A A, 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" used BIS to model and characterize cell abnormalities for the preliminary analysis and prediction of breast cancer.

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

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

[0010] Therefore, directly judging tumor information based on BIS becomes a technical route worthy of research. Summary of the Invention

[0011] The purpose of the present invention is to solve the above-mentioned problems existing in the prior art and provide a breast BIS sensor based on zonal detection, which uses BIS technology to perform zonal detection on the breast to determine whether there is a tumor, so as to achieve rapid localization detection of the tumor.

[0012] Another object of the present application is to provide a detection device.

[0013] Another object of the present application is to provide a detection method.

[0014] The technical solution of this application lies in:

[0015] A breast detection sensor based on zonal detection, comprising: a detection component; the detection component includes: a detection component body and inner and outer ring electrode groups;

[0016] a. 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;

[0017] b. The inner and outer ring 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;

[0018] c. The area between the inner ring electrode group and the outer ring electrode group (the planar projection is an annular area) is divided into N non-overlapping sub-detection areas. The circular part inside the inner ring electrode group is 1 sub-detection area. Each sub-detection area uses 4 electrodes to form 1 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 area is used to detect the bioelectrical impedance spectroscopy information of its corresponding sub-detection area.

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

[0021] Or

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

[0023] Furthermore, the number of the inner ring electrode groups is greater than or equal to 4.

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

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

[0026] a. A signal generation and acquisition module, which is used to generate a multi-sine excitation signal formed by superimposing multi-sine signals and collect the feedback signal of the tissue to be measured;

[0027] b. A multi-frequency module, which converts the multi-sine excitation signal generated by the signal generation and acquisition module into two current signals with the same amplitude and opposite phases, and simultaneously differentially amplifies the collected feedback signal;

[0028] c. A gating module, which is used to control the signal transmission between the signal generation and acquisition module, the multi-frequency module and the aforementioned sensor, and sequentially switch the sub-detection areas according to a preset order to complete the excitation and acquisition operations;

[0029] Among them, the method for the gating module to stimulate and collect a single sub-detection area is as follows: A high-speed analog radio frequency signal is sent out by the signal generation and collection module, and this signal is guided by the gating module to two adjacent electrodes of the sub-detection area, so as to apply an excitation current to this sub-detection area; Subsequently, voltage signals at different frequencies are collected from the other two adjacent electrodes and output to the signal generation and collection module;

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

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

[0032] f, a reference area determination module, which is used to determine the sub-detection area selected for the reference area;

[0033] g, an imaginary part relaxation impedance correction module, which corrects the imaginary part relaxation impedance of all sub-detection areas.

[0034] Furthermore, the multi-channel bio-impedance spectrum detection device further includes:

[0035] h, an MC-BIS data processing module, which is used to locate the tumor position information according to the impedance distribution;

[0036] i, a BIS data processing module, which is used to classify the 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 other modules; The mirror voltage-controlled constant current source module converts the input voltage signal into two current excitation signals with the same amplitude and opposite phases; The two differential voltage acquisition modules respectively differentially acquire the response voltage signal of the target to be measured and the internal resistance of the constant current source.

[0038] Furthermore, the method for the reference area determination module to determine the reference area is as follows: sequentially take L sub-detection areas as the reference areas respectively, calculate the comprehensive correction deviation of each sub-detection area being selected as the reference area, and take the sub-detection area with the smallest comprehensive correction deviation as the reference area;

[0039] The solution method for the comprehensive correction deviation of any j-th sub-detection area as the reference area includes the following steps:

[0040] stepA, calculate the real part impedance correction coefficients a 实-eg1-修 ~a 实-egL-修 、the imaginary part impedance correction coefficients a 虚-eg1-修 ~a 虚-egL-修; where, the real part impedance correction coefficient a of any i-th sub-detection region 实-egi-修 and the imaginary part impedance correction coefficient a 虚-egi-修正 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] stepB, according to the real part and imaginary part impedance correction coefficients in step S401, correct the real part impedance matrix Z 实 and the imaginary part impedance matrix Z 虚 summarized for the detection region to obtain the real part corrected impedance matrix Z 实修正 and the imaginary part corrected impedance matrix Z 虚修正 ;

[0044]

[0045] where, Z 实-ij and Z 虚-ij represent the real part impedance and the imaginary part impedance corresponding to the j-th sub-detection region corresponding to the frequency f i ; n represents the number of frequencies for current excitation measurement;

[0046]

[0047] S403, calculate the imaginary part correction deviation ΔD 虚 and the real part correction deviation ΔD 实 , and calculate the comprehensive correction deviation ΔD:

[0048]

[0049] Furthermore, the method for the imaginary part relaxation impedance correction module to correct the imaginary part relaxation impedance is:

[0050] The reference region is denoted as the k-th sub-detection region, and calculate the imaginary part relaxation impedance correction values Z 虚-eg1-形状校正 ~ Z 虚-egL-形状校正 for the L sub-detection regions with irregular shapes eliminated;

[0051] where, the imaginary part relaxation impedance Z 虚-egi-形状校正 after considering the correction for any i-th sub-detection region is:

[0052]

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

[0054] S100, obtaining the frequency-impedance amplitude-phase matrix Z of L sub-detection regions of the tissue to be detected 1 ~Z L ;

[0055] S200, obtaining the real part impedance matrix Z 1 ~Z L and the imaginary part impedance matrix Z 实 虚 of the detection region summary; ;

[0056]

[0057] wherein, Z 实-ij and Z 虚-ij represent the real part impedance and the imaginary part impedance corresponding to the j-th sub-detection region corresponding to the frequency f i ;

[0058] S300, obtaining the real part relaxation impedance Z 实-eg1 ~Z 实-egL and the imaginary part relaxation impedance Z 虚-eg1 ~Z 虚-egL , wherein, Z 实-egi and Z 虚-egi respectively represent the real part relaxation impedance and the imaginary part relaxation impedance of the i-th sub-detection region;

[0059] S400, determining the reference region: sequentially taking the L sub-detection regions as the reference regions, calculating the comprehensive correction deviation of each sub-detection region being selected as the reference region, and taking the sub-detection region with the smallest comprehensive correction deviation as the reference region;

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

[0061] S401, calculating the real part impedance correction coefficients a 实-eg1-修 ~a 实-egL-修 and the imaginary part impedance correction coefficients a 虚-eg1-修 ~a 虚-egL-修 ; wherein, the real part impedance correction coefficient a 实-egi-修 and the imaginary part impedance correction coefficient a 虚-egi-修正 of any i-th sub-detection region 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. Based on the real part and imaginary part impedance correction coefficients in step S401, correct Z 实 and Z 虚 to obtain the real part corrected impedance matrix Z 实修正 and the imaginary part corrected impedance matrix Z 虚修正 ;

[0065]

[0066] S403. Calculate the imaginary part correction deviation ΔD 虚 and the real part correction deviation ΔD 实 , and calculate the comprehensive correction deviation ΔD:

[0067]

[0068] S500. The reference region determined by S400 is denoted as the k-th sub-detection region. Calculate the imaginary part relaxation impedance correction values Z 虚-eg1-形状校正 to Z 虚-egL-形状校正 for the L sub-detection regions with irregular shapes eliminated;

[0069] Among them, for any i-th sub-detection region, considering the corrected imaginary part relaxation impedance Z 虚-egi-形状修正 is:

[0070]

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

[0072] First, the breast detection sensor based on partition detection proposed in this application is a breast detection sensor based on the combination of partition detection and BIS. Its core lies in: the sensor is divided into L (L = N + 1) sub-detection regions, each sub-detection region is surrounded by 4 adjacent electrodes and corresponds to an independent electrode group; all the electrodes form two circular arrays of an inner circle and an outer circle.

[0073] Second, it is not suitable to directly use the imaginary part relaxation impedance for partition detection. The reason is that: as Figure 3 shown, the impedance information will be affected by the measurement error caused by the shape of the structural partition. Therefore, it is necessary to perform an empty field correction to eliminate the measurement impedance deviation caused by non-structural partitions.

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

[0075] 2.1, Select the reference area.

[0076] Take the L sub-detection areas as the reference area in turn, calculate the comprehensive correction deviation of each sub-detection area being selected as the reference area, and take the sub-detection area with the smallest comprehensive correction deviation as the reference area.

[0077] 2.2, Denote the reference area determined by S400 as the kth sub-detection area, and calculate the imaginary part relaxation impedance correction values Z 虚-eg1-形状校正 ~Z 虚-egL-形状校正 :

[0078] The proportionality coefficient of the ith sub-detection area is:

[0079] The imaginary part relaxation impedance correction value Z 虚-egi-形状校正 of the ith sub-detection area is:

[0080] Third, Z 虚-eg1-形状校正 ~Z 虚-egL-形状校正 is the key information for subsequent judgment of tumor type and location. For a single tumor, the Z 虚-eg1-形状校正 of this area will increase significantly, while in the sub-areas not affected by the tumor, the impedance value is relatively low and stable. Table 1 (obtained by numerical simulation) summarizes the upper quartile (Zimag-uq), lower quartile (Zimag-lq), median (Zimag-med), maximum value (Zimag-max) and minimum value (Zimag-min) of the impedance in each sub-area when there is a tumor. Therefore, when performing MC-BIS detection, if the Z 虚-eg1-形状校正 detected in a certain sub-area exceeds 2.004 Ω, it can be preliminarily determined that there is a tumor in this sub-area, thus realizing the rapid positioning of the UFBC (i.e., unifocal breast cancer) lesion.

[0081] Table 1 Statistical Data Of Impedance Detection For Electrode Groups In Different Regions

[0082]

[0083] For multiple tumors, the rapid positioning of MMBC (multifocal breast cancer) lesions can be realized by cooperating with machine learning algorithms. Brief Description of the Drawings

[0084] The following further elaborates on the present application with reference to the embodiments in the drawings, but does not constitute any limitation to the present application.

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

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

[0087] Figure 3 It is a schematic diagram of the sub-detection area of the present application (the numbers of the inner and outer ring electrode groups are shown on the left; the numbers of the sub-detection areas are shown on the right).

[0088] Figure 4 It is a schematic diagram of the multi-channel bioimpedance spectroscopy detection device of the present application.

[0089] Figure 5 It is a schematic diagram of the overall scheme of the multi-channel bioimpedance spectroscopy detection of the present application.

[0090] Figure 6 It is a schematic diagram of the flow of a multi-channel bioimpedance spectroscopy detection method of the present application.

[0091] The description of the reference numerals is as follows:

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

[0093] Detection component body 1021, inner ring electrode group 1022, outer ring electrode group 1023. Detailed implementation manners

[0094] The objectives, advantages and features of the present invention will be explained by the following non-limiting description of the preferred embodiments. These embodiments are only typical examples of applying the technical solutions of the present invention, and all technical solutions formed by equivalent substitution or equivalent transformation fall within the scope of protection required by the present invention.

[0095] <Example 1: A breast detection sensor>

[0096] Figure 1 It shows a three-dimensional structure diagram of a breast detection sensor. A breast detection sensor 100 includes: a handheld component 101, a detection component 102; the handheld component 101 is installed on the top of the detection component 102.

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

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

[0099] b, on the conical surface of the detection component body 1021, an inner ring electrode group 1022 and an outer ring electrode group 1023 are installed in a circular array arrangement. The centers of the circular arrays where the inner ring electrode group 1022 and the outer ring electrode group 1023 are located are both on the center line of the conical surface;

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

[0101] Or;

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

[0103] The annular region between the inner ring electrode group and the outer ring electrode group is divided into N sub-detection regions (as Figure 3 shown, the sensor is divided into 9 sub-detection regions: the annular region is divided into 8 sub-detection regions, and the circular whole inside the inner ring electrode group is 1 sub-detection region). Between each sub-detection region, 4 electrodes must be used to form 1 detection electrode group; this requirement implicitly requires the number of the inner ring electrode group and the outer ring electrode group.

[0104] If the number of the inner ring electrode group and the outer ring electrode group is the same, in this case, taking 2 adjacent electrodes from the inner and outer rings respectively to form 4 electrodes can form 1 detection electrode group.

[0105] And when the number of the outer ring electrode group is greater than that of the inner ring electrode group, for example: in Figure 2 the "No. 11 - No. 16 - No. 2 - No. 9" such detection electrode group, inserting the outer ring electrodes 1 and 10 to form "No. 11 - No. 16 - No. 9 - No. 10, No. 10 - No. 1 - No. 2 - No. 11" can still meet the requirement that 4 electrodes form 1 detection electrode group. That is, the insertion of the outer ring must be in the form of an increase that is a multiple of 2.

[0106] The electrodes of the inner ring electrode group should be greater than or equal to 4 to ensure that the sub-detection region inside the inner ring electrode group can be measured (that is, there are at least 4 electrodes in the sub-detection region inside the inner ring electrode group; for example, for Area9 in Figure 3 , using electrodes 12 and 16 for excitation and electrodes 13 and 15 for signal acquisition is sufficient).

[0107] When the number of the outer electrode groups is less than that of the inner electrode groups, it can be expressed as: the number of the outer electrode groups 1022 is z, and the number of the inner electrode groups 1023 is z + 2y; 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 essence of multi-channel corresponds to multiple sub-detection regions) includes:

[0110] a, a signal generation and acquisition module, which is used to generate a multi-sine excitation signal formed by superimposing multi-sine signals and collect the feedback signal of the tissue to be measured. Specifically, the signal generation and acquisition module uses a Red Pitaya development board, outputs a custom voltage signal from a high-speed radio frequency analog signal output channel on the development board to the multi-frequency module, and uses two high-speed radio frequency analog signals on the development board to collect the response signals returned by the multi-frequency module.

[0111] b, a multi-frequency module, which converts the multi-sine excitation signal into two current signals with the same amplitude and opposite phases, and at the same time differentially amplifies the collected 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 other modules. The mirror voltage-controlled constant current source module converts the input voltage signal into two current excitation signals with the same amplitude and opposite phases. The two differential voltage acquisition modules differentially acquire the response voltage signal of the target to be measured and the internal resistance of the constant current source respectively.

[0112] c, a gating module, which is used to control the signal transmission between the signal generation and acquisition module and the sensor, and can sequentially switch each sub-detection region to achieve sequential detection of different regions. Specifically, the gating module is used to control the four signals (I + 、I - 、V + 、V - ) emitted by the multi-frequency module, and sequentially switch the sub-detection regions according to a preset order to complete the excitation and acquisition operations. Taking the first sub-detection region (Area1) as an example, this region is surrounded by the 1st, 2nd, 10th, and 11th electrodes. During the detection process, the 1st and 2nd electrodes are used as the input terminals of the excitation current (I + 、I - ), and the 10th and 11th electrodes are used as the output terminals for voltage acquisition (V + 、V -); A high-speed analog radio frequency signal is sent out in the signal generation and acquisition module. Through the gating module, this signal is guided to the 1st and 2nd electrodes, so as to apply an excitation current in Area1. Subsequently, voltage signals at different frequencies (the excitation frequency is 1 kHz - 5 MHz) are collected from the 10th and 11th electrodes and output to the signal generation and acquisition module (that is, current with a frequency range of f 1 ~f n is injected into the human body from a pair of electrodes 1 and 2, and impedance data is collected from another pair of electrodes 10 and 11 at the same time). After the detection of the first sub-detection area is completed, the gating module then switches to the next sub-detection area (Area2) according to the preset order and repeats the above excitation and collection steps. This process is carried out in sequence until the detection tasks of all sub-detection areas are completed.

[0113] d, a 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:

[0114]

[0115] where Z i is the impedance amplitude corresponding to the frequency f i , is the phase angle corresponding to the frequency f i .

[0116] e, an impedance spectrum calculation module, which is used to calculate the imaginary part relaxation impedance, the real part relaxation impedance and the relaxation frequency.

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

[0118] Step1, calculate the frequency-impedance real part-impedance imaginary part matrix corresponding to each sub-detection area:

[0119]

[0120] where Z′ i is the real part impedance corresponding to the frequency f i , Z″ i is the imaginary part impedance corresponding to the frequency f i .

[0121] Step2, determine the imaginary part relaxation impedance, the real part relaxation impedance and the relaxation frequency:

[0122] The relaxation frequency is the frequency corresponding to when the imaginary part of the impedance reaches the maximum value;

[0123] The imaginary part 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 part relaxation impedance is the real part corresponding to the maximum value of the imaginary part of the impedance.

[0125] f, a reference region determination module, is used to determine the sub-detection region for reference region selection.

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

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

[0128] i, a BIS data processing module, is used to classify the lesion type. The BIS data processing module further classifies the tumors in the locked region as benign or malignant on the basis that the MC-BIS data processing module has located the tumor region. The electrical feature division threshold Z for benign and malignant tumors imag-relax2 :

[0129] When Z imag-relax ≤Z imag-relax2 It is a malignant tumor;

[0130] When Z imag-relax >Z imag-relax2 It is a benign tumor.

[0131] <Example 3: A multi-channel bioimpedance spectroscopy detection method>

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

[0133] S100, obtain the frequency-impedance amplitude-phase matrix Z of L sub-detection regions of the tissue to be detected 1 ~Z L ;

[0134] S200, obtain the real part impedance matrix Z 1 ~Z L of the detection region, the imaginary part impedance matrix Z 实 and 虚 ;

[0135]

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

[0137] S300, obtain the real - part relaxation impedance Z 实-eg1 ~Z 实-egL and the imaginary - part relaxation impedance Z 虚-eg1 ~Z 虚-egL , where Z 实-egi , Z 虚-egi respectively represent the real - part relaxation impedance and the imaginary - part relaxation impedance of the i - th sub - detection region;

[0138] S400, determine the reference region: successively take the L sub - detection regions as the reference regions, calculate the comprehensive correction deviation of each sub - detection region when it is selected as the reference region, and take the sub - detection region with the minimum comprehensive correction deviation as the reference region;

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

[0140] S401, calculate the real - part impedance correction coefficients a 实-eg1-修 ~a 实-egL-修 and the imaginary - part impedance correction coefficients a 虚-eg1-修 ~a 虚-egL-修 ;

[0141] Among them, the real - part impedance correction coefficient a 实-egi-修 and the imaginary - part impedance correction coefficient a 虚-egi-修正 of any i - th sub - detection region 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, correct Z 实 , Z 虚 according to the real - part and imaginary - part impedance correction coefficients in step S401 to obtain the real - part corrected impedance matrix Z 实修正 and the imaginary - part corrected impedance matrix Z 虚修正 ;

[0145]

[0146] S403, calculate the imaginary - part correction deviation ΔD 虚 and the real - part correction deviation ΔD 实 , and calculate the comprehensive correction deviation ΔD:

[0147]

[0148] The reference area determined by S500 and S400 is denoted as the k-th sub-detection area, and the imaginary part relaxation impedance correction values Z of L sub-detection areas with irregular shapes eliminated are calculated 虚-eg1-形状校正 ~Z 虚-egL-形状校正 ;

[0149] Among them, for any i-th sub-detection area, the considered corrected imaginary part relaxation impedance Z 虚-egi-形状修正 is:

[0150]

[0151] Table 2 Symbol-Physical Meaning Table of the Present Application

[0152]

[0153] The above-mentioned embodiments are the preferred embodiments of the present invention, which are only used to conveniently illustrate the present invention and do not impose any formal restrictions on the present invention. Any person with ordinary knowledge in the technical field, without departing from the technical features of the present invention, makes local changes or modified equivalent embodiments by using the technical content disclosed in the present invention, and without departing from the technical feature content of the present invention, still belongs to the scope of the technical features of the present invention.

Claims

1. A breast BIS sensor based on partition detection, characterized in that: include: Detection components; The detection component comprises: a detection component body and inner and outer electrode groups; a. The lower surface of the detection component body is a conical surface, and the inner and outer electrode groups are installed on the conical surface; 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; c. The area between the inner circle electrode group and the outer circle electrode group is divided into N non-overlapping sub-detection areas, the circular area inside the inner circle electrode group is a sub-detection area, and each sub-detection area uses 4 electrodes to form a sub-detection area detection electrode group; N is a natural number greater than or equal to 8; d. The detection electrode group of each sub-detection area is used to detect the bioelectrical impedance spectrum information of its corresponding sub-detection area.

2. The breast BIS sensor based on partition detection according to claim 1 is characterized in that: The number of the inner circle electrode groups is x, and the number of the outer circle electrode groups is x+2y; y is any natural number from 0 to x; or The number of the outer circle electrode groups is z, and the number of the inner circle electrode groups is z+2y; y is any natural number from 0 to z.

3. The breast BIS sensor based on partition detection according to claim 1, characterized in that: The number of inner circle electrode groups is greater than or equal to 4.

4. The breast BIS sensor based on partition detection according to claim 1, characterized in that: The bottom diameter of the cone is 130 mm and the height is 20 mm.

5. A detection device, which is a multi-channel bioimpedance spectrum detection device, characterized in that: include: a, a signal generation and acquisition module, which is used to generate a multi-sinusoidal excitation signal formed by superposition of multiple sinusoidal signals, and to collect feedback signals of the tissue to be tested; b, a multi-frequency module, which converts the multi-sinusoidal excitation signals generated by the signal generation and acquisition modules into two current signals with the same amplitude and opposite phases, and differentially amplifies the collected feedback signals; c, a gating module, which is used to control the signal transmission between the signal generation and acquisition module, the multi-frequency module and the sensor as claimed in claim 1, and switch the sub-detection areas in sequence according to a preset order to complete the excitation and acquisition operations; The method for the gating module to excite and collect data for a single sub-detection area is as follows: a high-speed analog radio frequency signal is sent out from the signal generation and collection module, and the signal is guided to two adjacent electrodes of any sub-detection area through the gating module, thereby applying an excitation current to the sub-detection area; subsequently, voltage signals at different frequencies are collected from the other two electrodes of the sub-detection area, and output to the signal generation and collection module; d, a storage module, which is used to store multi-channel impedance spectrum data, where the multi-channel impedance spectrum data is a frequency-impedance amplitude-phase matrix; e, an impedance spectrum calculation module, which is used to calculate the imaginary relaxation impedance, the real relaxation impedance and the relaxation frequency; f, a reference region determination module, used to determine a sub-detection region selected by the reference region; g, the imaginary relaxation impedance correction module is used to correct the imaginary relaxation impedance of all sub-detection areas.

6. A detection device according to claim 5, characterized in that: Also includes: h, MC-BIS data processing module, which determines whether there is a tumor and locates the tumor position information according to the corrected imaginary relaxation impedance obtained by the imaginary relaxation impedance correction module; i, BIS data processing module, which is used to classify lesion types.

7. A detection device according to claim 5, characterized in that: The multi-frequency module includes: a power supply module, a mirror voltage-controlled constant current source module and a two-way differential voltage acquisition module; the power supply module supplies power to other modules; the mirror voltage-controlled constant current source module converts the input voltage signal into two current excitation signals with the same amplitude and opposite phases; the two-way differential voltage acquisition modules respectively differentially acquire the response voltage signal and the constant current source internal resistance of the target to be measured.

8. The detection device according to claim 5, characterized in that: The reference region determination module determines the reference region by: taking L sub-detection regions as reference regions in turn, calculating the comprehensive correction deviation of each sub-detection region selected as the reference region, and taking the sub-detection region with the smallest comprehensive correction deviation as the reference region; The method for solving the comprehensive correction deviation of any j-th sub-detection area as a reference area includes the following steps: stepA, calculate the real impedance correction coefficient a of all sub-detection areas 实-eg1-修 ~a 实-egL-修 , Imaginary impedance correction coefficient a 虚-eg1-修 ~a 虚-egL-修 ; Among them, the real impedance correction coefficient a of any i-th sub-detection area 实-egi-修 , Imaginary impedance correction coefficient a 虚-egi-修正 They are: and 实-egi-修正 =Z 实-egi / Z 实-egj ; and 虚-egi-修正 =Z 虚-egi / Z 虚-egj ; stepB, the real impedance matrix Z of the detection area is summarized according to the real and imaginary impedance correction coefficients of step S401 实 , imaginary impedance matrix Z 虚 The real part of the modified impedance matrix Z is obtained by correction 实修正 , the imaginary part corrected impedance matrix Z 虚修正 ; Among them, Z 实-ij , Z 虚-ij Represents the frequency f i The real impedance and imaginary impedance corresponding to the j-th sub-detection area; n represents the number of frequencies of current excitation measurement; S403, calculating the imaginary correction deviation ΔD 虚 and real part correction deviation ΔD 实 , and calculate the comprehensive correction deviation ΔD:

9. The detection device according to claim 5, characterized in that: The method for correcting the imaginary relaxation impedance by the imaginary relaxation impedance correction module is: The reference area is recorded as the kth sub-detection area, and the imaginary relaxation impedance correction value Z of the L sub-detection areas with irregular shapes eliminated is calculated. 虚-eg1-形状校正 ~Z 虚-egL-形状校正 ; Among them, any i-th sub-detection area considers the corrected imaginary relaxation impedance Z 虚-egi-形状校正 for:

10. 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, obtaining frequency-impedance amplitude-phase matrices Z1 to Z1 of L sub-detection areas of the tissue to be detected L ; S200, according to Z1~Z L Get the real impedance matrix Z of the detection area summary 实 , imaginary impedance matrix Z 虚 ; Among them, Z 实-ij , Z 虚-ij Represents the frequency f i The real impedance and imaginary impedance corresponding to the j-th sub-detection area; S300, obtaining the real relaxation impedance Z of L sub-detection areas 实-eg1 ~Z 实-egL And the imaginary relaxation impedance Z 虚-eg1 ~Z 虚-egL , where Z 实-egi , Z 虚-egi They represent the real relaxation impedance and imaginary relaxation impedance of the i-th sub-detection area respectively; S400, determining a reference area: sequentially taking L sub-detection areas as reference areas respectively, calculating a comprehensive correction deviation of each sub-detection area selected as a reference area, and taking the sub-detection area with the smallest comprehensive correction deviation as the reference area; The method for solving the comprehensive correction deviation of any j-th sub-detection area as a reference area includes the following steps: S401, calculating the real impedance correction coefficient a of all sub-detection areas 实-eg1-修 ~a 实-egL-修 , Imaginary impedance correction coefficient a 虚-eg1-修 ~a 虚-egL-修 ; Among them, the real impedance correction coefficient a of any i-th sub-detection area 实-egi-修 , Imaginary impedance correction coefficient a 虚-egi-修正 They are: and 实-egi-修正 =Z 实-egi / Z 实-egj ; and 虚-egi-修正 =Z 虚-egi / Z 虚-egj ; S402: According to the real and imaginary impedance correction coefficients of step S401, Z 实 , Z 虚 The real part of the modified impedance matrix Z is obtained by correction 实修正 , the imaginary part corrected impedance matrix Z 虚修正 ; S403, calculating the imaginary correction deviation ΔD 虚 and real part correction deviation ΔD 实 , and calculate the comprehensive correction deviation ΔD: S500, the reference area determined in S400 is recorded as the kth sub-detection area, and the imaginary relaxation impedance correction value Z of the L sub-detection areas with irregular shapes eliminated is calculated. 虚-eg1-形状校正 ~Z 虚-egL-形状校正 ; Among them, any i-th sub-detection area considers the corrected imaginary relaxation impedance Z 虚-egi-形状修正 for:

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