A traditional Chinese medicine abdominal impedance detection method and device based on data analysis

Abstract

The application discloses a traditional Chinese medicine abdominal impedance detection method and device based on data analysis, relates to the technical field of data analysis, and solves the point deviation and repeated error problems caused by the fact that the existing device positioning relies on manual operation and has no standardized calibration by performing benchmark calibration through a cross wide-angle laser, and guaranteeing safety by matching an inclination sensor, generating cosine and sine reference signals which are the same in frequency and phase as the first waveform excitation signal according to a micro control unit, processing discrete time voltage sequences in combination with parameters such as an analog-to-digital converter sampling frequency, extracting useful signals and suppressing noise, obtaining reliable alternating current signal amplitude, and improving the instability problem of impedance measurement benchmarks, and the application can also adjust the excitation signal frequency to generate second waveform excitation signals of different frequency bands, calculate a difference value and an impedance contribution value after a second impedance value is obtained, obtain a comprehensive impedance value through normalization processing and dynamic weight coefficient setting, solve the single-frequency detection limitation and low data utilization efficiency problem, and make up for the missing short board of quantitative diagnosis.

Description

Technical Field

[0001] This invention relates to the field of data analysis technology, specifically a method and device for detecting abdominal impedance in traditional Chinese medicine based on data analysis. Background Technology

[0002] The TCM impedance detection device integrates sensing and signal processing modules adapted to TCM meridians to non-invasively and quantitatively collect impedance signals from the detection site. This not only makes up for the shortcomings of traditional diagnostic data quantification but also provides objective hardware support for organ function identification and early health screening.

[0003] Existing impedance detection devices suffer from significant technical deficiencies due to a combination of factors, including the lack of a positioning mechanism, insufficient signal stability, and limitations in processing methods. Positioning relies on manual operation and lacks standardized calibration methods, leading to significant deviations in detection point location and prominent repeatability errors. The excitation signal is susceptible to interference from load variations, and its insufficient constant current characteristics directly cause instability in the impedance measurement benchmark. Furthermore, the detection mode is limited to a single frequency band, failing to cover the impedance characteristics of different tissue layers at the detection site. Therefore, there is an urgent need for a data-analyzed method and device for abdominal impedance detection in Traditional Chinese Medicine. Summary of the Invention

[0004] The purpose of this invention is to provide a method and device for detecting abdominal impedance in traditional Chinese medicine based on data analysis, so as to solve the problems raised in the prior art.

[0005] To achieve the above objectives, the present invention provides the following technical solution: a traditional Chinese medicine abdominal impedance detection method based on data analysis, the traditional Chinese medicine abdominal impedance detection method comprising the following steps:

[0006] Step S1: Initialize the impedance detection equipment and set its operating parameters;

[0007] Step S1-1: Power on the impedance detection device and set the excitation signal parameters through the built-in microcontroller unit of the impedance detection device. The excitation signal parameter setting includes setting the frequency and amplitude value of the excitation signal; and synchronously setting the analog switch switching timing parameters. The analog switch switching timing parameters are used to control the analog switch according to the set timing sequence.

[0008] Step S1-2: The excitation signal waveform is set to a sine wave using the microcontroller unit and a reference is calibrated using the cross-shaped wide-angle laser of the impedance detection device. The specific process of the reference calibration is as follows: the center reference line of the cross-shaped wide-angle laser is aligned with the center axis of the preset detection part.

[0009] The frequency of the excitation signal is limited to the range of 500Hz-100kHz, which is consistent with the frequency range of the excitation source emitted by the main control MCU; the detection area is mostly centered on the navel, and the longitudinal line of the cross laser needs to be aligned with the lower edge of the xiphoid process of the sternum and the midpoint of the pubic symphysis to form a longitudinal baseline; the transverse line of the cross laser needs to form a 90° angle with the above longitudinal baseline to ensure that the receiving electrodes can be radially distributed with the navel as the center, covering the maximum designed detection diameter; the laser emission angle is 90-150°;

[0010] Step S2: The microcontroller unit in the impedance detection device generates a first waveform excitation signal according to the operating parameters set in step S1 and injects it into the detection part.

[0011] Step S2-1: Based on the excitation signal parameters set by the microcontroller unit according to step S1, generate a first waveform excitation signal in the form of a sine wave, and transmit the first waveform excitation signal to the current conversion circuit, which converts it into an AC constant current source with stable amplitude that is independent of the load.

[0012] Step S2-2: Inject an AC constant current source into the detection area using a disposable impedance patch sensor;

[0013] The first waveform excitation signal is generated and injected by the operating parameters set by the microcontroller unit, achieving precise matching between the excitation output and the preset parameters. The first waveform excitation signal in the form of a sine wave is converted into an AC constant current source with stable amplitude and independent of the load by the current conversion circuit. This not only meets the safety requirement of maximum output current ≤5mA, but also ensures the stability of the excitation signal, laying the foundation for the accuracy of subsequent impedance detection data. The AC constant current source is injected through a disposable impedance patch sensor. The sensor has a built-in encryption chip to ensure single use, effectively avoiding cross-contamination and improving detection security.

[0014] Step S3: Set the excitation signal acquisition frequency, and acquire voltage data at the preset detection points of the detection part based on the excitation signal acquisition frequency to construct a discrete-time voltage sequence;

[0015] Step S3-1: According to the analog switch switching timing parameters set in step S1, switch sequentially to the receiving electrodes corresponding to each preset detection point of the detection part.

[0016] Step S3-2: Set the sampling frequency of the analog-to-digital converter through the microcontroller unit, denoted as the excitation signal acquisition frequency. The excitation signal acquisition frequency satisfies the Nyquist sampling theorem. Based on the excitation signal acquisition frequency, synchronously sample the voltage signal across the reference resistor in the sampling circuit at each detection point, and convert the acquired voltage signal into an electrical digital signal.

[0017] Step S3-3: Arrange the acquired point digital signals in chronological order to obtain the discrete-time voltage sequence V_ref[n]={V_ref[0],V_ref[1],V_ref[2],...,V_ref[N-1]} corresponding to the preset detection points of each detection location.

[0018] By setting the excitation signal acquisition frequency and collecting voltage data at the detection points, a discrete-time voltage sequence is constructed, providing basic data support for subsequent impedance value calculation. The analog switch is switched sequentially to the receiving electrodes at each detection point, enabling comprehensive acquisition of all preset detection points radially distributed around the navel (3-8 rings, outer ring maximum diameter ≤200mm, 24 points on the outer ring, and 5-10 points on the inner ring), ensuring the integrity of the detection range. The analog-to-digital converter sampling frequency set by the microcontroller unit satisfies the Nyquist sampling theorem, meaning the sampling frequency is much greater than twice the excitation signal frequency. Furthermore, the voltage signal across the reference resistor in each detection point circuit is synchronously sampled and converted into a digital signal, avoiding signal aliasing and ensuring the accuracy and validity of the voltage sampling data. The acquired digital signals are sorted by time to obtain the discrete-time voltage sequence V_ref[n] corresponding to each detection point, directly providing structured data for subsequent calculations of in-phase components, quadrature components, and the final impedance value, ensuring the complexity of impedance calculation.

[0019] Step S4: Based on the operating parameters set in step S1, generate a digital reference signal with the same frequency and phase as in step S2 in the microcontroller unit, process the discrete-time voltage sequence using the digital reference signal, analyze and obtain the AC signal amplitude when the detection part is detected, and use the AC signal amplitude to perform analysis and calculation to obtain the first impedance value corresponding to each preset detection point of the detection part.

[0020] Step S4-1: The microcontroller generates two digital reference signals with the same frequency and phase as the first waveform excitation signal according to the excitation signal parameters set in step S1. The digital reference signals specifically include a cosine reference signal and a sine reference signal.

[0021] The formula for calculating the cosine reference signal is as follows:

[0022] Ref_cos[n]=cos(2×π×f×n÷Fs);

[0023] In the formula, Ref_cos[n] represents the cosine reference signal; f represents the frequency of the first waveform excitation signal; n represents the index of the discrete-time voltage sequence, specifically the subscript of the corresponding preset detection point; Fs represents the sampling frequency of the analog-to-digital converter;

[0024] The formula for calculating the sinusoidal reference signal is as follows:

[0025] Ref_sin[n]=sin(2×π×f×n÷Fs);

[0026] In the formula, Ref_sin[n] represents the sinusoidal reference signal;

[0027] Step S4-2: Multiply the voltage signal corresponding to the discrete-time voltage sequence with the cosine reference signal and the sine reference signal respectively. Sum the results of each multiplication according to the sampling point index from 0 to the total number of samples n to obtain the in-phase component and quadrature component when the detection part is detected.

[0028] The formula for calculating the in-phase component is as follows:

[0029] I_component=(2÷N)×Σ(V_ref[n]×Ref_cos[n]);

[0030] In the formula, I_component represents the in-phase component of the voltage signal when the detection part is detected;

[0031] The formula for calculating the orthogonal components is as follows:

[0032] Q_component=(2÷N)×Σ(V_ref[n]×Ref_sin[n]);

[0033] In the formula, Q_component represents the orthogonal component of the voltage signal when the detection part is detected;

[0034] Step S4-3: Calculate the square and square root of the two components I_component and Q_component of the voltage signal of the detection part to obtain the AC signal amplitude A_ref when the detection part is detected.

[0035] The formula for calculating the amplitude of the AC signal is as follows:

[0036] A_ref=sqrt(I_component²+Q_component²);

[0037] In the formula, A_ref represents the amplitude of the AC signal;

[0038] Step S4-4: Based on the excitation signal amplitude in the excitation signal parameters set in step S1 and the preset precision reference resistor in the detection circuit, substitute the AC signal amplitude A_ref into the impedance calculation formula to obtain the first impedance value corresponding to the detection part when it is detected.

[0039] The impedance calculation formula is as follows:

[0040] Z_measured_1=((V_drive×R_ref)÷A_ref)-R_ref;

[0041] In the formula, Z_measured_1 represents the first impedance value corresponding to the detection part when it is detected; V_drive represents the amplitude of the excitation signal set in the excitation signal parameters; and R_ref represents the preset precision reference resistor in the detection circuit.

[0042] The microcontroller generates cosine and sine reference signals with the same frequency and phase as the first waveform excitation signal, ensuring the correlation and accuracy of subsequent signal processing. The reference signal calculation formula strictly combines the sampling frequency of the analog-to-digital converter, the frequency of the first waveform excitation signal, and the index of the discrete-time voltage sequence, highly adapting to the set parameters and acquired data. The discrete-time voltage sequence is multiplied by the two reference signals and summed to obtain in-phase and quadrature components, effectively extracting useful information related to the excitation from the voltage signal and suppressing noise interference. The summation operation covers sampling point index 0 to the total number of samples, ensuring the integrity of component calculations. Based on the two components, the AC signal amplitude is calculated using the square and square root, ensuring reliable amplitude data. Finally, the set excitation signal amplitude is combined with a preset precision reference resistor in the detection circuit. This allows for the accurate acquisition of the first impedance value corresponding to each preset detection point in the detection area, providing reliable core data support for subsequent impedance distribution analysis and quantitative diagnosis, effectively improving the problems of missing quantitative diagnosis and limitations in impedance technology in existing technologies.

[0043] Step S5: Generate second waveform excitation signals of different frequency bands through step S2, and simultaneously perform steps S3 to S4 to obtain the second impedance value corresponding to the secondary detection; analyze the first impedance value and the second impedance value to obtain the impedance contribution value of the first impedance value and the second impedance value respectively; dynamically set the weight coefficient of the first impedance value and the second impedance value based on the impedance contribution value analysis; and calculate the comprehensive impedance value of the detection part based on the weight coefficient.

[0044] Step S5-1: The microcontroller unit adjusts the frequency of the excitation signal to a frequency band different from the first waveform excitation signal according to the excitation signal parameters set in step S1, and generates a second waveform excitation signal; simultaneously, steps S3 to S4 are processed to obtain the second impedance value corresponding to the secondary detection.

[0045] Step S5-2: For the same preset detection point at the detection location, extract the first impedance value Z_measured_1 and the second impedance value Z_measured_2 of the detection point, and calculate the absolute difference between the first impedance value Z_measured_1 and the second impedance value Z_measured_2, denoted as the impedance difference ΔZ. r ;

[0046] Step S5-3: When the impedance difference ΔZ r = 0, the weight coefficients of the first impedance value Z_measured_1 and the second impedance value Z_measured_2 are default set to 0.5; when the impedance difference ΔZ r ≠ 0, analyze and calculate according to the first impedance value Z_measured_1 and the second impedance value Z_measured_2 to obtain the impedance contribution values of the first impedance value Z_measured_1 and the second impedance value Z_measured_2 respectively;

[0047] The calculation formula for the impedance contribution value of the first impedance value Z_measured_1 is as follows:

[0048] C 1r = |Z_measured_1| ÷ ΔZ r ;

[0049] In the formula, C 1r represents the impedance contribution value of the first impedance value Z_measured_1;

[0050] The calculation formula for the impedance contribution value of the second impedance value Z_measured_2 is as follows:

[0051] C 2r = |Z_measured_2| ÷ ΔZ r ;

[0052] In the formula, C 2r represents the impedance contribution value of the second impedance value Z_measured_2;

[0053] Step S5-4: Read the maximum impedance measurement value Z_max preset by the impedance detection device; the maximum impedance measurement value Z_max represents the upper limit value of impedance measurement calibrated at the time of factory of the impedance detection device, calculate the ratio of the sum of contribution values C_total_r to Z_max to obtain the normalized sum of contribution values;

[0054] The calculation formula for the normalized sum of contribution values is as follows:

[0055] C_total_r = (C 1r + C 2r ) ÷ Z_max;

[0056] In the formula, C_total_r represents that the sum of contribution values is mapped to the interval from 0 to 1 after normalization;

[0057] Step S5-5: Dynamically set the weighting coefficients of the first and second impedance values ​​based on the sum of the normalized contribution values, as follows:

[0058] The formula for calculating the weighting coefficient W1 of the first impedance value is as follows:

[0059] W1 = Z_measured_1 ÷ C_total_r;

[0060] The formula for calculating the weighting coefficient W2 of the second impedance value is as follows:

[0061] W2 = Z_measured_2 ÷ C_total_r;

[0062] The comprehensive impedance value of the detection part is obtained by weighted fusion calculation based on the weighting coefficient W1 of the first impedance value and the weighting coefficient W2 of the second impedance value.

[0063] The specific process of weighted fusion calculation is as follows: the product of the first impedance value and the weighting coefficient W1 is added to the product of the second impedance value and the weighting coefficient W2 to obtain the comprehensive impedance value of the detection part.

[0064] The microcontroller unit adjusts the excitation signal frequency to a different frequency band than the first waveform excitation signal to generate a second waveform excitation signal. Synchronous processing yields the second impedance value, enabling multi-band impedance detection. This covers the impedance response characteristics of different abdominal tissues to excitation signals of different frequencies, avoiding the limitations of single-band detection. For the same preset detection point on the abdomen, the absolute difference between the two impedance values ​​is calculated. When the difference is 0, the weighting coefficients of the two impedance values ​​are assumed to be equal. When the difference is not 0, the impedance contribution values ​​of the two impedance values ​​are calculated separately, achieving dynamic contribution assessment based on actual impedance differences, rather than fixed weight settings. The sum of the two impedance contribution values ​​is normalized using the impedance measurement upper limit calibrated at the factory, mapping it to the 0-1 range to eliminate the influence of differences in the device's measurement range on the contribution value calculation and ensure data comparability. The weighting coefficients of the two impedance values ​​are calculated separately, and finally, a weighted fusion is obtained to obtain a comprehensive impedance value. The weighting coefficients are dynamically generated based on actual detection data, avoiding subjective setting deviations. By making full use of multi-band impedance detection data and obtaining a more comprehensive and accurate abdominal impedance value through dynamic weighted fusion, the limitations of impedance technology and inefficient data utilization in existing technologies can be effectively improved. This provides more reliable core data support for the subsequent formation of abdominal impedance distribution and the realization of quantitative diagnosis in traditional Chinese medicine, and further makes up for the lack of quantitative diagnosis in existing technologies.

[0065] Furthermore, a data analysis-based TCM abdominal impedance detection device includes a microcontroller unit, a receiving electrode assembly, an excitation electrode assembly, a current conversion circuit, an analog-to-digital converter, a cross-shaped wide-angle laser head, a tilt sensor, a precision reference resistor, and a Bluetooth module.

[0066] The microcontroller unit is used to generate excitation signals;

[0067] The receiving electrode assembly is arranged radially with the navel as the center, and includes a pluggable needle body, a base and an internal spring. The base is connected to the analog switch module, and the spring is set inside the base to realize the connection between the needle body and the base.

[0068] The encryption chip built into the excitation electrode assembly is a magnetic snap-on chip with a diameter of 10mm. It interacts with the microcontroller unit through electrode lines to record the usage status of the excitation electrode assembly.

[0069] The input terminal of the current conversion circuit is connected to the microcontroller unit, and the output terminal is connected to the excitation electrode assembly. It is used to convert the waveform excitation signal generated by the microcontroller unit into an AC constant current source with stable amplitude and independent of the load.

[0070] The analog-to-digital converter is integrated inside the microcontroller unit and is used to synchronously sample the voltage signal across the precision reference resistor to generate a discrete-time voltage sequence.

[0071] The cross-shaped wide-angle laser head is positioned at the center of the device and is used to emit cross-shaped lasers for detection, positioning, and calibration.

[0072] The tilt sensor is electrically connected to the microcontroller unit and is used to detect the tilt angle of the device;

[0073] One end of the precision reference resistor is connected to the analog switch module, and the other end is grounded;

[0074] The Bluetooth module is electrically connected to the microcontroller unit and is used to transmit the impedance data processed by the microcontroller unit to the control terminal.

[0075] The specific structural parameters of the receiving electrode assembly are as follows:

[0076] The receiving electrode assembly is arranged in multiple radial rings centered on the detection site. The needle diameter of the receiving electrode assembly is 0.8mm-4mm, and the stroke is 5mm-20mm.

[0077] The positioning and calibration logic of the cross-shaped wide-angle laser head is as follows: the center of the cross laser coincides with the center of the detection area, the upper part of the cross laser is aligned with the lower edge of the xiphoid process of the sternum, the lower part is aligned with the midpoint of the pubic symphysis, and the laser lines in the left and right directions form a 90° angle with the laser lines in the up and down directions, thus forming a positioning reference.

[0078] Compared with the prior art, the beneficial effects of the present invention are:

[0079] 1. This invention uses a cross-shaped wide-angle laser for benchmark calibration, and is equipped with an angle sensor to ensure safety. During calibration, the laser center is aligned with the navel, and the longitudinal line is aligned with the lower edge of the xiphoid process of the sternum and the midpoint of the pubic symphysis. This ensures that the receiving electrodes are distributed in a radial pattern with the navel as the center. This solves the problem of position deviation and repetition error caused by the reliance on manual positioning and lack of standardized calibration in existing devices, and lays the foundation for accurate abdominal impedance acquisition.

[0080] 2. This invention generates cosine and sine reference signals with the same frequency and phase as the first waveform excitation signal through a microcontroller unit. Combined with the sampling frequency of the analog-to-digital converter, the frequency of the excitation signal, and the discrete-time voltage sequence index, it is highly compatible with parameter settings and data acquisition. By multiplying and summing the discrete-time voltage sequence with the reference signal, the useful signal related to the excitation can be accurately extracted and noise interference can be suppressed. Then, the amplitude of the AC signal is calculated through in-phase and quadrature components to ensure the reliability of the amplitude data. This provides an accurate basis for calculating the first impedance value using the impedance formula, effectively improves the problem of unstable impedance measurement benchmarks in existing technologies, and provides key support for quantitative diagnosis of abdominal pain in traditional Chinese medicine.

[0081] 3. This invention generates second waveform excitation signals of different frequency bands by adjusting the excitation signal frequency, obtains the second impedance value through a synchronous process, calculates the difference between the two impedance values, dynamically calculates the impedance contribution value, normalizes it by combining the maximum impedance measurement value calibrated by the equipment at the factory, and then dynamically sets weighting coefficients to obtain a comprehensive impedance value. This solves the limitations of single-frequency band detection and the problem of inefficient data utilization, making the impedance value more comprehensive and accurate, providing reliable data support for quantitative diagnosis of abdominal pain in traditional Chinese medicine, and making up for the shortcomings of existing quantitative diagnosis technologies. Attached Figure Description

[0082] Figure 1 This is a schematic flowchart of a traditional Chinese medicine abdominal impedance detection method based on data analysis according to the present invention.

[0083] Figure 2 This is a schematic diagram of the electrode distribution of the receiving electrode assembly of a traditional Chinese medicine abdominal impedance detection device based on data analysis according to the present invention.

[0084] Figure 3 This is a schematic diagram of the electrode structure of the receiving electrode assembly of a traditional Chinese medicine abdominal impedance detection device based on data analysis according to the present invention.

[0085] Figure 4 This is a schematic diagram of the encrypted chip structure built into the excitation electrode assembly in a data analysis-based traditional Chinese medicine abdominal impedance detection device of the present invention.

[0086] In the diagram, a is the needle body; b is the base; c is the spring; d is the center of the detection area; e is the encryption chip; and f is the magnetic clasp. Detailed Implementation

[0087] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0088] Example 1: As Figure 1 As shown, this invention provides a technical solution: a traditional Chinese medicine abdominal impedance detection method based on data analysis. The traditional Chinese medicine abdominal impedance detection method includes the following steps:

[0089] Step S1: Initialize the impedance detection equipment and set its operating parameters;

[0090] Step S1-1: Power on the impedance detection device and set the excitation signal parameters through the built-in microcontroller unit of the impedance detection device. The excitation signal parameter setting includes setting the frequency and amplitude value of the excitation signal; and synchronously setting the analog switch switching timing parameters. The analog switch switching timing parameters are used to control the analog switch according to the set timing sequence.

[0091] Step S1-2: The excitation signal waveform is set to a sine wave using the microcontroller unit and a reference is calibrated using the cross-shaped wide-angle laser of the impedance detection device. The specific process of the reference calibration is as follows: the center reference line of the cross-shaped wide-angle laser is aligned with the center axis of the preset detection part.

[0092] In practical implementation, the core principle of initializing the impedance detection equipment and setting its operating parameters is to uniformly configure the key parameters of the excitation signal and the switching sequence of the analog switch through the built-in microcontroller unit, thereby establishing a consistent operating benchmark for all subsequent detection stages. The cross-shaped wide-angle laser benchmark calibration relies on the abdominal anatomical features to construct a spatial positioning framework, ensuring that the receiving electrodes can accurately cover the target detection area according to the preset radial distribution. During implementation, it is important to ensure that the laser calibration accurately corresponds to the specific anatomical reference point on the abdomen. At the same time, the tilt angle of the equipment must be monitored in real time during operation to prevent the laser irradiation from deviating from the safe range due to equipment tilt, which could affect the positioning accuracy or pose a safety hazard to surrounding personnel.

[0093] Step S2: The microcontroller unit in the impedance detection device generates a first waveform excitation signal according to the operating parameters set in step S1 and injects it into the detection part.

[0094] Step S2-1: Based on the excitation signal parameters set by the microcontroller unit according to step S1, generate a first waveform excitation signal in the form of a sine wave, and transmit the first waveform excitation signal to the current conversion circuit, which converts it into an AC constant current source with stable amplitude that is independent of the load.

[0095] Step S2-2: Inject an AC constant current source into the detection area using a disposable impedance patch sensor;

[0096] In practical implementation, the principle of generating the first waveform excitation signal through the microcontroller and injecting it into the detection site is that the microcontroller generates a sinusoidal excitation signal based on the pre-set parameters. This signal is then converted into an AC constant current source by the current conversion circuit. This design can effectively avoid the interference of load changes on the stability of the excitation signal. The constant current source is then injected into the abdomen through a disposable impedance patch sensor. This not only ensures the consistency of the excitation signal to improve the accuracy of subsequent impedance detection, but also prevents cross-contamination from the source of use. During implementation, it is important to ensure that the current conversion circuit is in a stable working state to ensure that the characteristics of the output constant current source are not affected by external environmental factors. At the same time, before using the disposable impedance patch sensor, it must be confirmed that it has not been activated in advance to avoid the risk of contamination due to repeated use of the sensor, which would affect the safety of the detection and the reliability of the data.

[0097] Step S3: Set the excitation signal acquisition frequency, and acquire voltage data at the preset detection points of the detection part based on the excitation signal acquisition frequency to construct a discrete-time voltage sequence;

[0098] Step S3-1: According to the analog switch switching timing parameters set in step S1, switch sequentially to the receiving electrodes corresponding to each preset detection point of the detection part.

[0099] Step S3-2: Set the sampling frequency of the analog-to-digital converter through the microcontroller unit, denoted as the excitation signal acquisition frequency. The excitation signal acquisition frequency satisfies the Nyquist sampling theorem. Based on the excitation signal acquisition frequency, synchronously sample the voltage signal across the reference resistor in the sampling circuit at each detection point, and convert the acquired voltage signal into an electrical digital signal.

[0100] Step S3-3: Arrange the acquired point digital signals in chronological order to obtain the discrete-time voltage sequence V_ref[n]={V_ref[0],V_ref[1],V_ref[2],...,V_ref[N-1]} corresponding to the preset detection points of each detection location.

[0101] In practical implementation, the principle of setting the excitation signal acquisition frequency and constructing the discrete-time voltage sequence is as follows: according to the pre-set analog switch switching sequence, the receiving electrodes corresponding to each preset detection point on the abdomen are sequentially connected to the detection circuit. The microcontroller unit controls the analog-to-digital converter to synchronously sample the voltage signal across the reference resistor in the circuit at a frequency that conforms to the sampling theorem. After the acquired analog voltage signal is converted into a digital signal, it is arranged in chronological order to form the discrete-time voltage sequence corresponding to each detection point, providing structured data support for subsequent digital reference signal processing. During implementation, it is important to ensure that the switching action of the analog switch is strictly synchronized with the sampling frequency of the analog-to-digital converter to prevent misalignment of the sampled data with the corresponding detection point due to channel switching delay. At the same time, it is necessary to ensure that the connection between the reference resistor and the detection circuit is stable during sampling to avoid poor contact or loosening that introduces additional resistance and causes deviation in the voltage sampling data.

[0102] Step S4: Based on the operating parameters set in step S1, generate a digital reference signal with the same frequency and phase as in step S2 in the microcontroller unit, process the discrete-time voltage sequence using the digital reference signal, analyze and obtain the AC signal amplitude when the detection part is detected, and use the AC signal amplitude to perform analysis and calculation to obtain the first impedance value corresponding to each preset detection point of the detection part.

[0103] Step S4-1: The microcontroller generates two digital reference signals with the same frequency and phase as the first waveform excitation signal according to the excitation signal parameters set in step S1. The digital reference signals specifically include a cosine reference signal and a sine reference signal.

[0104] The formula for calculating the cosine reference signal is as follows:

[0105] Ref_cos[n]=cos(2×π×f×n÷Fs);

[0106] In the formula, Ref_cos[n] represents the cosine reference signal; f represents the frequency of the first waveform excitation signal; n represents the index of the discrete-time voltage sequence, specifically the subscript of the corresponding preset detection point; Fs represents the sampling frequency of the analog-to-digital converter;

[0107] The formula for calculating the sinusoidal reference signal is as follows:

[0108] Ref_sin[n]=sin(2×π×f×n÷Fs);

[0109] In the formula, Ref_sin[n] represents the sinusoidal reference signal;

[0110] Step S4-2: Multiply the voltage signal corresponding to the discrete-time voltage sequence with the cosine reference signal and the sine reference signal respectively. Sum the results of each multiplication according to the sampling point index from 0 to the total number of samples n to obtain the in-phase component and quadrature component when the detection part is detected.

[0111] The formula for calculating the in-phase component is as follows:

[0112] I_component=(2÷N)×Σ(V_ref[n]×Ref_cos[n]);

[0113] In the formula, I_component represents the in-phase component of the voltage signal when the detection part is detected;

[0114] The formula for calculating the orthogonal components is as follows:

[0115] Q_component=(2÷N)×Σ(V_ref[n]×Ref_sin[n]);

[0116] In the formula, Q_component represents the orthogonal component of the voltage signal when the detection part is detected;

[0117] Step S4-3: Calculate the square and square root of the two components I_component and Q_component of the voltage signal of the detection part to obtain the AC signal amplitude A_ref when the detection part is detected.

[0118] The formula for calculating the amplitude of the AC signal is as follows:

[0119] A_ref=sqrt(I_component²+Q_component²);

[0120] In the formula, A_ref represents the amplitude of the AC signal;

[0121] Step S4-4: Based on the excitation signal amplitude in the excitation signal parameters set in step S1 and the preset precision reference resistor in the detection circuit, substitute the AC signal amplitude A_ref into the impedance calculation formula to obtain the first impedance value corresponding to the detection part when it is detected.

[0122] The impedance calculation formula is as follows:

[0123] Z_measured_1=((V_drive×R_ref)÷A_ref)-R_ref;

[0124] In the formula, Z_measured_1 represents the first impedance value corresponding to the detection part when it is detected; V_drive represents the amplitude of the excitation signal set in the excitation signal parameters; and R_ref represents the preset precision reference resistor in the detection circuit.

[0125] In practical implementation, the principle of using digital reference signals to process data and calculate the first impedance value is that the microcontroller generates a cosine reference signal and a sine reference signal with the same frequency and phase as the first waveform excitation signal based on the previously set excitation signal parameters. By multiplying the discrete-time voltage sequence with the two reference signals respectively and summing the results according to the sampling point index, the in-phase and quadrature components related to the excitation signal in the voltage signal are extracted. Then, the AC signal amplitude is calculated based on these two components. Finally, the amplitude is substituted into the preset impedance calculation formula to obtain the first impedance value corresponding to each detection point. This process can effectively filter environmental noise and irrelevant interference signals, ensuring the accuracy of the impedance calculation results. During implementation, it is important to ensure that the frequency and phase of the digital reference signal strictly match the parameters of the first waveform excitation signal to avoid errors in the calculation of the in-phase and quadrature components due to frequency shift or phase deviation. At the same time, when summing the sampling points, all acquired digital signal points must be covered to prevent the accuracy of the AC signal amplitude calculation from decreasing due to missing some sampling points, which would affect the accuracy of the first impedance value.

[0126] Step S5: Generate second waveform excitation signals of different frequency bands through step S2, and simultaneously perform steps S3 to S4 to obtain the second impedance value corresponding to the secondary detection; analyze the first impedance value and the second impedance value to obtain the impedance contribution value of the first impedance value and the second impedance value respectively; dynamically set the weight coefficient of the first impedance value and the second impedance value based on the impedance contribution value analysis; and calculate the comprehensive impedance value of the detection part based on the weight coefficient.

[0127] Step S5-1: The microcontroller unit adjusts the frequency of the excitation signal to a frequency band different from the first waveform excitation signal according to the excitation signal parameters set in step S1, and generates a second waveform excitation signal; simultaneously, steps S3 to S4 are processed to obtain the second impedance value corresponding to the secondary detection.

[0128] Step S5-2: For the same preset detection point at the detection location, extract the first impedance value Z_measured_1 and the second impedance value Z_measured_2 of the detection point, and calculate the absolute difference between the first impedance value Z_measured_1 and the second impedance value Z_measured_2, denoted as the impedance difference ΔZ. r ;

[0129] Step S5-3, when the impedance difference ΔZ rWhen =0, the weight coefficients of the first impedance value Z_measured_1 and the second impedance value Z_measured_2 are default set to 0.5; when the impedance difference ΔZ r ≠0, perform analysis and calculation based on the first impedance value Z_measured_1 and the second impedance value Z_measured_2, and obtain the impedance contribution values of the first impedance value Z_measured_1 and the second impedance value Z_measured_2 respectively;

[0130] The calculation formula for the impedance contribution value of the first impedance value Z_measured_1 is as follows:

[0131] C 1r =|Z_measured_1|÷ΔZ r ;

[0132] In the formula, C 1r represents the impedance contribution value of the first impedance value Z_measured_1;

[0133] The calculation formula for the impedance contribution value of the second impedance value Z_measured_2 is as follows:

[0134] C 2r =|Z_measured_2|÷ΔZ r ;

[0135] In the formula, C 2r represents the impedance contribution value of the second impedance value Z_measured_2;

[0136] Step S5-4, read the maximum impedance measurement value Z_max preset by the impedance detection device; the maximum impedance measurement value Z_max represents the upper limit value of the impedance measurement calibrated when the impedance detection device leaves the factory, calculate the ratio of the total contribution value C_total_r to Z_max, and obtain the normalized total contribution value;

[0137] The calculation formula for the normalized total contribution value is as follows:

[0138] C_total_r=(C 1r +C 2r )÷Z_max;

[0139] In the formula, C_total_r represents that the total contribution value is mapped to the interval from 0 to 1 after normalization;

[0140] Step S5-5, dynamically set the weight coefficients of the first impedance value and the second impedance value according to the normalized total contribution value, specifically as follows:

[0141] The calculation formula for the weight coefficient W1 of the first impedance value is as follows:

[0142] W1 = Z_measured_1 ÷ C_total_r;

[0143] The formula for calculating the weighting coefficient W2 of the second impedance value is as follows:

[0144] W2 = Z_measured_2 ÷ C_total_r;

[0145] The comprehensive impedance value of the detection part is obtained by weighted fusion calculation based on the weighting coefficient W1 of the first impedance value and the weighting coefficient W2 of the second impedance value.

[0146] In practical implementation, the principle of generating the second waveform excitation signal and calculating the comprehensive impedance value is as follows: the microcontroller adjusts the frequency of the excitation signal to a frequency band different from that of the first waveform excitation signal, repeats the previous signal injection, voltage data acquisition, and impedance calculation process to obtain the second impedance value corresponding to each detection point. For the same detection point, the impedance contribution value of each is analyzed by calculating the absolute difference between the two impedance values. The sum of the contribution values ​​is normalized using the maximum impedance measurement value preset by the device to eliminate the influence of the difference in the device's measurement range on the calculation results. Then, the weighting coefficient of the two impedance values ​​is dynamically set based on the sum of the normalized contribution values, and the comprehensive impedance value of each detection point is obtained through weighted fusion. This design can make full use of multi-band impedance data to reflect the impedance characteristics of different tissues in the abdomen, improving the comprehensiveness and reliability of impedance detection. During implementation, it is important to ensure that the frequency band of the second waveform excitation signal is reasonably spaced from the first frequency band to ensure that it can cover the impedance response differences of different tissue layers in the abdomen to the excitation signal. At the same time, when reading the maximum impedance measurement value preset by the device, it is necessary to confirm that the value is the accurate value calibrated by the factory to avoid errors in the normalization result due to numerical deviation, which would affect the setting of the weighting coefficient and the calculation accuracy of the comprehensive impedance value.

[0147] Example 2, as Figure 2-4 As shown, the present invention provides a TCM abdominal impedance detection device based on data analysis. The TCM abdominal impedance detection device includes a microcontroller unit, a receiving electrode assembly, an excitation electrode assembly, a current conversion circuit, an analog-to-digital converter, a cross-shaped wide-angle laser head, a tilt sensor, a precision reference resistor, and a Bluetooth module.

[0148] The microcontroller unit is used to generate excitation signals;

[0149] The receiving electrode assembly is arranged radially with the navel as the center, and includes a pluggable needle body, a base and an internal spring. The base is connected to the analog switch module, and the spring is set inside the base to realize the connection between the needle body and the base.

[0150] The encryption chip built into the excitation electrode assembly is a magnetic snap-on chip with a diameter of 10mm. It interacts with the microcontroller unit through electrode lines to record the usage status of the excitation electrode assembly.

[0151] The input terminal of the current conversion circuit is connected to the microcontroller unit, and the output terminal is connected to the excitation electrode assembly. It is used to convert the waveform excitation signal generated by the microcontroller unit into an AC constant current source with stable amplitude and independent of the load.

[0152] The analog-to-digital converter is integrated inside the microcontroller unit and is used to synchronously sample the voltage signal across the precision reference resistor to generate a discrete-time voltage sequence.

[0153] The cross-shaped wide-angle laser head is positioned at the center of the device and is used to emit cross-shaped lasers for detection, positioning, and calibration.

[0154] The tilt sensor is electrically connected to the microcontroller unit and is used to detect the tilt angle of the device;

[0155] One end of the precision reference resistor is connected to the analog switch module, and the other end is grounded;

[0156] The Bluetooth module is electrically connected to the microcontroller unit and is used to transmit the impedance data processed by the microcontroller unit to the control terminal.

[0157] The specific structural parameters of the receiving electrode assembly are as follows:

[0158] The receiving electrode assembly is arranged in multiple radial rings centered on the detection site. The needle diameter of the receiving electrode assembly is 0.8mm-4mm, and the stroke is 5mm-20mm.

[0159] The positioning and calibration logic of the cross-shaped wide-angle laser head is as follows: the center of the cross laser coincides with the center of the detection area, the upper part of the cross laser is aligned with the lower edge of the xiphoid process of the sternum, the lower part is aligned with the midpoint of the pubic symphysis, and the laser lines in the left and right directions form a 90° angle with the laser lines in the up and down directions, thus forming a positioning reference.

[0160] It will be apparent to those skilled in the art that the present invention is not limited to the details of the exemplary embodiments described above, and that the invention can be implemented in other specific forms without departing from its spirit or essential characteristics. Therefore, the embodiments should be considered in all respects as exemplary and non-limiting, and the scope of the invention is defined by the appended claims rather than the foregoing description. Thus, all variations falling within the meaning and scope of equivalents of the claims are intended to be included within the present invention. No reference numerals in the claims should be construed as limiting the scope of the claims.

Claims

1. A traditional Chinese medicine abdominal impedance detection method based on data analysis, characterized in that: The traditional Chinese medicine abdominal impedance detection method comprises the following steps: Step S1, initialize the impedance detection device and set the operating parameters; Step S1-1, power on the impedance detection device, and set the excitation signal parameters through the micro control unit built in the impedance detection device, the excitation signal parameter setting including setting the frequency and amplitude value of the excitation signal; The analog switch switching time sequence parameter is set synchronously; The analog switch switching time sequence parameter is used to control the analog switch according to the set time sequence; Step S1-2, set the excitation signal waveform of the excitation signal parameter to sine wave by the micro control unit, and calibrate the reference by the cross wide-angle laser of the impedance detection device, the specific process of the reference calibration is that the center reference line of the cross wide-angle laser coincides with the center axis of the preset detection part; Step S2, generate the first waveform excitation signal and inject it into the detection part through the micro control unit in the impedance detection device according to the operating parameters set in step S1; Step S2-1, according to the excitation signal parameters set by the micro control unit according to step S1, generate the first waveform excitation signal in the form of sine wave, transmit the first waveform excitation signal to the current conversion circuit, and convert it to an AC constant current source with stable amplitude and independent of load through the current conversion circuit; Step S2-2, inject the AC constant current source into the detection part through the disposable impedance patch type sensor; Step S3, set the excitation signal acquisition frequency, and collect voltage data of the preset detection point of the detection part based on the excitation signal acquisition frequency, and construct a discrete time voltage sequence; Step S4, generate a digital reference signal with the same frequency and phase as step S2 in the micro control unit according to the operating parameters set in step S1, process the discrete time voltage sequence with the digital reference signal, analyze the AC signal amplitude when the detection part is detected, and analyze and calculate the AC signal amplitude to obtain the first impedance value corresponding to each preset detection point of the detection part; Step S5, generate the second waveform excitation signal of different frequency bands through step S2, and process steps S3 to S4 synchronously to obtain the second impedance value corresponding to the second detection; According to the analysis of the first impedance value and the second impedance value, the impedance contribution value of the first impedance value and the second impedance value is obtained respectively, the weight coefficient of the first impedance value and the second impedance value is set dynamically based on the impedance contribution value, and the comprehensive impedance value of the detection part is calculated based on the weight coefficient.

2. The traditional Chinese medicine abdominal impedance detection method based on data analysis according to claim 1, characterized in that: The specific steps of step S3 are as follows: Step S3-1, according to the analog switch switching time sequence parameter set in step S1, switch to the receiving electrode corresponding to each detection point of the detection part in turn; Step S3-2, set the sampling frequency of the analog-to-digital converter through the micro control unit, which is recorded as the excitation signal acquisition frequency, the excitation signal acquisition frequency meets the Nyquist sampling theorem; Based on the excitation signal acquisition frequency, the voltage signal between the reference resistors in the sampling loop is sampled synchronously, and the collected voltage signal is converted into digital signal; Step S3-3, the point digital signal collected is arranged in time sequence to obtain a discrete time voltage sequence V_ref[n]={V_ref[0], V_ref[1], V_ref[2],..., V_ref[N-1]} corresponding to each detection point of the detection part.

3. The traditional Chinese medicine abdominal impedance detection method based on data analysis according to claim 2, characterized in that: The specific steps of the step S4 are as follows: Step S4-1, the micro control unit generates two digital reference signals with the same frequency and phase as the first waveform excitation signal according to the excitation signal parameters set in step S1, and the digital reference signal specifically includes a cosine reference signal and a sine reference signal; The calculation formula of the cosine reference signal is as follows: Ref_cos[n]=cos(2×π×f×n÷Fs); In the formula, Ref_cos[n] represents the cosine reference signal; f represents the frequency of the first waveform excitation signal; n represents the index of the discrete time voltage sequence, specifically the subscript corresponding to the preset detection point; and Fs represents the sampling frequency of the analog-to-digital converter; The calculation formula of the sine reference signal is as follows: Ref_sin[n]=sin(2×π×f×n÷Fs); In the formula, Ref_sin[n] represents the sine reference signal; Step S4-2, the corresponding voltage signal in the discrete time voltage sequence is multiplied by the cosine reference signal and the sine reference signal respectively, and the sum of each multiplication result is summed from 0 to the total sampling number n according to the sampling point index, to obtain the in-phase component and the quadrature component when the detection part is detected; The calculation formula of the in-phase component is as follows: I_component=(2÷N)×Σ(V_ref[n]×Ref_cos[n]); In the formula, I_component represents the in-phase component of the voltage signal when the detection part is detected; The calculation formula of the quadrature component is as follows: Q_component=(2÷N)×Σ(V_ref[n]×Ref_sin[n]); In the formula, Q_component represents the quadrature component of the voltage signal when the detection part is detected; Step S4-3, the square root of the sum of squares of the in-phase component I_component and the quadrature component Q_component of the detection part voltage signal is calculated to obtain the alternating current signal amplitude A_ref when the detection part is detected; The calculation formula of the alternating current signal amplitude is as follows: A_ref=sqrt(I_component²+Q_component²); In the formula, A_ref represents the alternating current signal amplitude; Step S4-4, according to the excitation signal amplitude in the excitation signal parameters set in step S1 and the preset precision reference resistance in the detection loop, the alternating current signal amplitude A_ref is substituted into the impedance calculation formula to obtain the corresponding first impedance value when the detection part is detected; The impedance calculation formula is as follows: Z_measured_1=((V_drive×R_ref)÷A_ref)-R_ref; In the formula, Z_measured_1 represents the first impedance value corresponding to the detection of the detection site; V_drive represents the excitation signal amplitude set in the excitation signal parameter; and R_ref represents the precision reference resistance preset in the detection circuit.

4. The traditional Chinese medicine abdominal impedance detection method based on data analysis according to claim 3, characterized in that: In step S5, In step S5-1, the micro control unit adjusts the excitation signal frequency to a frequency band different from the first waveform excitation signal according to the excitation signal parameter set in step S1, and generates a second waveform excitation signal; steps S3 to S4 are processed synchronously to obtain a second impedance value corresponding to secondary detection; Step S5-2, for the same preset detection point of the detection site, the first impedance value Z_measured_1 and the second impedance value Z_measured_2 of the detection point are extracted, and the absolute value difference of the first impedance value Z_measured_1 and the second impedance value Z_measured_2 is calculated, which is recorded as the impedance difference ΔZ r .

5. A data analysis-based traditional Chinese medicine abdominal impedance detection device applied to the data analysis-based traditional Chinese medicine abdominal impedance detection method of any one of claims 1-4, characterized in that: The traditional Chinese medicine abdominal impedance detection device comprises a micro control unit, a receiving electrode assembly, an excitation electrode assembly, a current conversion circuit, an analog-to-digital converter, a cross wide-angle laser head, an inclination sensor, a precision reference resistance and a Bluetooth module. The micro control unit is used for generating an excitation signal. The receiving electrode assembly is radially arranged around the navel and comprises a pluggable needle body, a base and an embedded reed. The encryption chip embedded in the excitation electrode assembly is a magnetic buckle type chip with a diameter of 10 mm, which realizes data interaction with the micro control unit through an electrode wire and is used for recording the use state of the excitation electrode assembly. The input end of the current conversion circuit is connected with the micro control unit, and the output end is connected with the excitation electrode assembly, which is used for converting the waveform excitation signal generated by the micro control unit into an AC constant current source with stable amplitude and independent of load. The analog-to-digital converter is integrated in the micro control unit and is used for synchronously sampling the voltage signal between the precision reference resistance to generate a discrete time voltage sequence. The cross wide-angle laser head is arranged at the center of the device and is used for emitting cross laser for detection, positioning and calibration. The inclination sensor is electrically connected with the micro control unit and is used for detecting the inclination angle of the device. One end of the precision reference resistance is connected with the analog switch module, and the other end is grounded. The Bluetooth module is electrically connected with the micro control unit and is used for transmitting the impedance data processed by the micro control unit to a control terminal.

6. The traditional Chinese medicine abdominal impedance detection device based on data analysis according to claim 5, characterized in that: The structural parameters of the receiving electrode assembly are as follows: The receiving electrode assembly is radially distributed around the center of the detection site.

7. The traditional Chinese medicine abdominal impedance detection device based on data analysis according to claim 5, characterized in that: The positioning and calibration logic of the cross wide-angle laser head is that the center of the cross laser coincides with the center of the detection site, the upper part of the cross laser is aligned with the lower edge point of the xiphoid process, the lower part is aligned with the mid-point of the pubic symphysis, and the laser lines in the left and right directions form a 90° angle with the laser lines in the upper and lower directions, thereby forming a positioning reference.

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