Intelligent detection method and system for urinary incontinence

Abstract

The invention provides an intelligent detection method and system for urinary incontinence. A first signal and a second signal are injected into a detection area of a diaper through a driving electrode; collecting a first response signal of the first signal and a second response signal of the second signal through a detection electrode; comparing the phase offset of the first signal with the phase offset of the first response signal, and further identifying a voltage division value caused by capacitance formed between the liquid on the surface layer of the diaper and the driving electrode; signal attenuation of the second signal and the second response signal is compared, and then a current shunt value caused when the diaper surface layer liquid and the diaper shunt layer are connected in parallel is identified; and determining the liquid amount of the surface layer of the diaper by combining the voltage dividing value and the current dividing value, and recording once urinary incontinence if the liquid amount is greater than a preset liquid amount threshold value. By adopting the scheme of the invention, confidence detection can be carried out on urinary incontinence under polarization effect interference.

Description

Technical Field

[0001] This application relates to the field of medical care technology, and more specifically, to an intelligent urinary incontinence detection method and system. Background Art

[0002] Urinary incontinence detection is mainly used to identify whether a patient has urine leakage and analyze parameters such as the frequency and volume of urine leakage for nursing or medical intervention. This technology is widely used in medical care, intelligent health products, and health monitoring devices.

[0003] In the prior art, flexible fabric sensors are usually arranged in wearable diapers to judge urinary incontinence by detecting changes in the electrical properties of urine. The sensors are usually composed of conductive fibers or coated electrodes, and the presence and diffusion of urine are measured through resistance. However, in actual applications, under the action of the electric field applied to the electrodes, ions in the urine will migrate, resulting in the formation of capacitance at the electrode interface, and the urine itself is also a capacitor. The impedance characteristics of these two capacitances are affected by the ion concentration in the urine and the amount of urine, that is, the electrical properties between the two electrodes are dynamically changing, which will lead to misjudgment in urinary incontinence detection. Therefore, how to perform confidence detection of urinary incontinence under the interference of polarization effect has become a difficult problem faced by the industry. Summary of the Invention

[0004] This application provides an intelligent urinary incontinence detection method and system, which can perform confidence detection of urinary incontinence under the interference of polarization effect.

[0005] In a first aspect, this application provides an intelligent urinary incontinence detection method, including: Collecting resistance signals at various positions on the diaper through the flexible fabric sensor; When the resistance value of at least one resistance signal is less than a preset resistance threshold, alternately transmitting a first excitation signal and a second excitation signal into the detection area of the diaper through a driving electrode, where the first excitation signal and the second excitation signal are used to analyze the impedance characteristics of the diaper; Collecting a first response signal of the first excitation signal and a second response signal of the second excitation signal through a detection electrode; Comparing the phase offset between the first excitation signal and the first response signal, and then identifying the voltage division value when a parasitic capacitance is formed between the liquid on the surface of the diaper and the driving electrode; Comparing the signal attenuation between the second excitation signal and the second response signal, and then identifying the current shunt value when a current loop is formed between the liquid on the surface of the diaper and the shunt layer of the diaper; Combining the voltage division value and the current shunt value to determine the polarization effect value of all electrodes in the diaper. When the polarization effect value is greater than a preset polarization threshold, it is recorded as one case of urinary incontinence.

[0006] In some embodiments, the frequency of the first signal is lower than the frequency of the second signal.

[0007] In some embodiments, alternately emitting the first excitation signal and the second excitation signal into the detection area of the diaper through the driving electrode specifically includes: Emitting an electrical signal with a first frequency into the detection area of the diaper through the driving electrode, and using the electrical signal with the first frequency as the first excitation signal; After the first excitation signal ends and a specified time interval elapses, emitting an electrical signal with a second frequency into the detection area of the diaper through the driving electrode, and using the electrical signal with the second frequency as the second excitation signal; After the second excitation signal ends and a specified time interval elapses, emitting an electrical signal with a first frequency into the detection area of the diaper through the driving electrode, and repeating the above steps to complete the alternate emission of the first excitation signal and the second excitation signal.

[0008] In some embodiments, comparing the phase offset between the first excitation signal and the first response signal, and further identifying the voltage division value when a parasitic capacitance is formed between the liquid on the surface of the diaper and the driving electrode specifically includes: Filtering the first response signal to obtain a first smoothed signal; Determining the phase angle of the first smoothed signal; Determining the phase offset according to the phase angle of the first smoothed signal and the phase angle of the first excitation signal; Determining the voltage loss according to the amplitude of the first smoothed signal and the amplitude of the first excitation signal; Determining the voltage division value when a parasitic capacitance is formed between the liquid on the surface of the diaper and the driving electrode according to the phase offset and the voltage loss.

[0009] In some embodiments, comparing the signal attenuation between the second excitation signal and the second response signal, and further identifying the current shunt value when a current loop is formed between the liquid on the surface of the diaper and the diaper shunt layer specifically includes: Filtering the second response signal to obtain a second smoothed signal; Determining the peak factor of the second smoothed signal and the peak factor of the second excitation signal; Determining the signal attenuation according to the peak factor of the second smoothed signal and the peak factor of the second excitation signal; Combining the signal attenuation and the change rate of the alternating current to determine the current shunt value when a current loop is formed between the liquid on the surface of the diaper and the diaper shunt layer.

[0010] In some embodiments, determining the polarization effect values of all the electrodes in the diaper by combining the voltage division value and the current shunt value means taking the ratio of the voltage division value and the current shunt value as the polarization effect values of all the electrodes in the diaper.

[0011] In some embodiments, the diaper includes: a surface layer, a driving electrode layer, a nylon cloth isolation layer, a detection electrode layer, a diversion layer, an absorption core layer, and a bottom layer.

[0012] In a second aspect, the present application provides an intelligent urinary incontinence detection system, including: An acquisition module, configured to acquire resistance signals at various locations on the diaper through the flexible fabric sensor; A signal emission module, configured to alternately emit a first excitation signal and a second excitation signal into the detection area of the diaper through the driving electrode when the resistance value of at least one resistance signal is less than a preset resistance threshold, where the first excitation signal and the second excitation signal are used to analyze the impedance characteristics of the diaper; A signal reception module, configured to acquire a first response signal of the first excitation signal and a second response signal of the second excitation signal through the detection electrode; A processing module, configured to compare the phase offset between the first excitation signal and the first response signal, and further identify the voltage division value when a parasitic capacitance is formed between the liquid on the surface layer of the diaper and the driving electrode; The processing module is further configured to compare the signal attenuation between the second excitation signal and the second response signal, and further identify the current shunt value when a current loop is formed between the liquid on the surface layer of the diaper and the shunt layer of the diaper; An execution module, configured to determine the polarization effect values of all the electrodes in the diaper by combining the voltage division value and the current shunt value, and when the polarization effect value is greater than a preset polarization threshold, record it as one episode of urinary incontinence.

[0013] In a third aspect, the present application provides a computer device, where the computer device includes a memory and a processor, the memory stores code, and the processor is configured to obtain the code and execute the above-mentioned intelligent urinary incontinence detection method.

[0014] In a fourth aspect, the present application provides a computer-readable storage medium, where the computer-readable storage medium stores a computer program, and when the computer program is executed by a processor, the above-mentioned intelligent urinary incontinence detection method is implemented.

[0015] The technical solutions provided by the disclosed embodiments of the present application have the following beneficial effects: In the intelligent urine incontinence detection method and system provided by this application, first, resistance signals at various locations on the urine diaper are collected through the flexible fabric sensor; when the resistance value of at least one resistance signal is less than a preset resistance threshold, a first excitation signal and a second excitation signal are alternately emitted into the detection area of the urine diaper through the drive electrode, where the first excitation signal and the second excitation signal are used to analyze the impedance characteristics of the urine diaper; the first response signal of the first excitation signal and the second response signal of the second excitation signal are collected through the detection electrode; the phase offset between the first excitation signal and the first response signal is compared to identify the voltage division value when a parasitic capacitance is formed between the liquid on the surface of the urine diaper and the drive electrode; the signal attenuation between the second excitation signal and the second response signal is compared to identify the current shunt value when a current loop is formed between the liquid on the surface of the urine diaper and the urine diaper shunt layer; the polarization effect value of all electrodes in the urine diaper is determined by combining the voltage division value and the current shunt value, and when the polarization effect value is greater than a preset polarization threshold, it is recorded as one case of urine incontinence.

[0016] Resistance signals at various locations on the urine diaper are collected through the flexible fabric sensor; when the resistance value of at least one resistance signal is less than a preset resistance threshold, a first excitation signal and a second excitation signal are alternately emitted into the detection area of the urine diaper through the drive electrode, where the first excitation signal and the second excitation signal are used to analyze the impedance characteristics of the urine diaper; the first response signal of the first excitation signal and the second response signal of the second excitation signal are collected through the detection electrode; the phase offset between the first excitation signal and the first response signal is compared to identify the voltage division value when a parasitic capacitance is formed between the liquid on the surface of the urine diaper and the drive electrode; the signal attenuation between the second excitation signal and the second response signal is compared to identify the current shunt value when a current loop is formed between the liquid on the surface of the urine diaper and the urine diaper shunt layer; the polarization effect value of all electrodes in the urine diaper is determined by combining the voltage division value and the current shunt value, and when the polarization effect value is greater than a preset polarization threshold, it is recorded as one case of urine incontinence.

[0017] Thus, when this application detects liquid on the urine diaper (i.e., when the resistance value is less than the resistance threshold), two excitation signals with different frequencies are alternately emitted, and the waveforms between each excitation signal and the corresponding response signal are compared to identify the voltage division of the electrical signal caused by the polarization capacitance of the urine interface in the urine diaper and the shunt of the electrical signal formed by the capacitance due to charge migration (i.e., the voltage division value and the current shunt value). Furthermore, based on the magnitudes of the voltage division and the shunt, the polarization effect value caused by urine between the two electrodes in the urine diaper is determined, and finally, urine incontinence is alarmed through this polarization effect value. In summary, this application can perform confidence detection of urine incontinence under the interference of the polarization effect. Description of the Drawings

[0018] Figure 1It is an exemplary flowchart of an intelligent urinary incontinence detection method according to some embodiments of the present application; Figure 2 It is a schematic structural diagram of a urine diaper according to some embodiments of the present application; Figure 3 It is an equivalent circuit diagram of intelligent urinary incontinence detection according to some embodiments of the present application; Figure 4 It is a schematic structural diagram of an intelligent urinary incontinence detection system according to some embodiments of the present application; Figure 5 It is a schematic structural diagram of a computer device for implementing the intelligent urinary incontinence detection method according to some embodiments of the present application. Detailed implementation manners

[0019] To better understand the technical solution of the present application, the technical solution of the present application will be described in detail below in conjunction with the accompanying drawings of the specification and specific implementation manners.

[0020] Refer to Figure 1 , this figure is an exemplary flowchart of an intelligent urinary incontinence detection method according to some embodiments of the present application. The intelligent urinary incontinence detection method 100 mainly includes the following steps: In step 101, resistance signals at various locations on the urine diaper are collected through the flexible fabric sensor.

[0021] In some embodiments, refer to Figure 2 , this figure is a schematic structural diagram of a urine diaper according to some embodiments of the present application. The urine diaper includes: a surface layer, a driving electrode layer, a nylon cloth isolation layer, a detection electrode layer, a diversion layer, an absorption core layer, and a bottom layer. Among them, the driving electrode layer is provided with driving electrodes, the driving electrodes are negative electrodes, made of silver-plated yarns, the detection electrode layer is provided with detection electrodes, the detection electrodes are positive electrodes, made of graphene yarns.

[0022] Specifically, collecting resistance signals at various locations on the urine diaper through the flexible fabric sensor can be implemented in the following manner, that is: multiple pairs of electrodes are formed by arranging a driving electrode layer and a detection electrode layer on the urine diaper, the resistance value at each electrode is collected at a preset sampling interval, and all the resistance values collected at each electrode are sorted in order. The sequences obtained by sorting at each electrode are respectively used as the resistance signals at each electrode.

[0023] It should be noted that in the present application, the resistance signal is a sequence describing the change of the resistance value between a pair of electrodes in the urine diaper over time.

[0024] In step 102, when the resistance value of at least one resistance signal is less than a preset resistance threshold, a first excitation signal and a second excitation signal are alternately emitted into the detection area of the diaper through the drive electrode, wherein the first excitation signal and the second excitation signal are used to analyze the impedance characteristics of the diaper.

[0025] It should be noted that the resistance threshold in this application is a value preset according to preliminary experiments. For example, in this application, the diaper can be first dried in an oven for 24 hours and then taken out, and the resistance value between any drive electrode layer and detection electrode layer is measured, and 80% of the measured resistance value is used as the resistance threshold.

[0026] In some embodiments, the alternate emission of the first excitation signal and the second excitation signal into the detection area of the diaper through the drive electrode can be achieved by the following steps, namely: An electrical signal with a first frequency is emitted into the detection area of the diaper through the drive electrode, and the electrical signal with the first frequency is used as the first excitation signal; After the first excitation signal ends and after a specified time interval, an electrical signal with a second frequency is emitted into the detection area of the diaper through the drive electrode, and the electrical signal with the second frequency is used as the second excitation signal; After the second excitation signal ends and after a specified time interval, an electrical signal with a first frequency is emitted into the detection area of the diaper through the drive electrode, and the above steps are repeated to complete the alternate emission of the first excitation signal and the second excitation signal.

[0027] It should be noted that the first frequency of the first excitation signal in this application is less than the second frequency of the second excitation signal, and the amplitude of the first excitation signal is the same as the amplitude of the second excitation signal. For example, in this application, the fixed frequency of the first excitation signal is preset to 100 Hz, the fixed frequency of the second excitation signal is preset to 4 kHz, and the amplitudes of the voltages of the first excitation signal and the second excitation signal are both preset to 1 V.

[0028] In addition, it should be noted that the durations of the first excitation signal and the second excitation signal in this application can both be preset according to actual needs. For example, in this application, the duration is preset to 10 s. Further, the specified time interval in this application can be preset according to actual needs. For example, in this application, the specified time interval is preset to 3 s, and this specified time interval is a parameter set to avoid interference between the first excitation signal and the second excitation signal.

[0029] In addition, it should be noted that both the first excitation signal and the second excitation signal in this application are electrical signals used to analyze the impedance characteristics of the diaper, and each time the first excitation signal and the second excitation signal are emitted, the phase angle is zero.

[0030] In step 103, a first response signal of the first excitation signal and a second response signal of the second excitation signal are collected by a detection electrode.

[0031] Specifically, collecting the first response signal of the first excitation signal and the second response signal of the second excitation signal by the detection electrode can be implemented in the following manner: at the moment when each first excitation signal starts to be emitted, the voltage value on the detection electrode is collected by the detection electrode at a preset sampling interval until each second excitation signal starts to be emitted and the collection stops, and all the collected voltage values are arranged in the order of collection, and the obtained sequence is used as the first response signal of the first excitation signal. Subsequently, at the moment when each second excitation signal starts to be emitted, the voltage value on the detection electrode is collected by the detection electrode at a preset sampling interval until each first excitation signal starts to be emitted and the collection stops, and all the collected voltage values are arranged in the order of collection, and the obtained sequence is used as the second response signal of the second excitation signal.

[0032] It should be noted that in this application, the first response signal is an electrical signal in response to the first excitation signal, and the second response signal is an electrical signal in response to the second excitation signal.

[0033] It should be noted that in this application, "first" and "second" do not represent the order of precedence, nor do they limit the response signal and the excitation signal. They are only used to distinguish two different excitation signals and the response signals respectively corresponding to the two excitation signals.

[0034] In step 104, the phase offset between the first excitation signal and the first response signal is compared, and then the voltage division value when a parasitic capacitance is formed between the liquid on the surface of the diaper and the drive electrode is identified.

[0035] In some embodiments, comparing the phase offset between the first excitation signal and the first response signal, and then identifying the voltage division value when a parasitic capacitance is formed between the liquid on the surface of the diaper and the drive electrode can be implemented by the following steps: Filter the first response signal to obtain a first smoothed signal; Determine the phase angle of the first smoothed signal; Determine the phase offset according to the phase angle of the first smoothed signal and the phase angle of the first excitation signal; Determine the voltage loss according to the amplitude of the first smoothed signal and the amplitude of the first excitation signal; Determine the voltage division value when a parasitic capacitance is formed between the liquid on the surface of the diaper and the drive electrode according to the phase offset and the voltage loss.

[0036] In specific implementation, filtering the first response signal to obtain a first smoothed signal can be achieved in the following manner, that is: filtering the first response signal through a low-pass filter in the prior art, and taking the obtained curve as the first smoothed signal, where the cut-off frequency of the low-pass filter can be set to twice the frequency of the first excitation signal.

[0037] It should be noted that in this application, the first smoothed signal is the first response signal after filtering.

[0038] In specific implementation, determining the phase angle of the first smoothed signal can be achieved in the following manner, that is: First, convert the first smoothed signal from the time domain to the frequency domain through a fast Fourier transform in the prior art to obtain a spectrogram of the first smoothed signal. Subsequently, obtain the phase angle of the frequency with the highest amplitude in the spectrogram, and take this phase angle as the phase angle of the first smoothed signal.

[0039] In addition, in specific implementation, determining the phase offset according to the phase angle of the first smoothed signal and the phase angle of the first excitation signal can be achieved in the following manner, that is: obtain the phase angle of the first excitation signal, subtract the phase angle of the first excitation signal from the phase angle of the first smoothed signal, and take the obtained difference as the phase offset.

[0040] It should be noted that in this application, the phase offset is a parameter value used to measure the lag degree of the response signal relative to the excitation signal. The larger the phase offset, the more the response signal lags behind the excitation signal; the smaller the phase offset, the less the response signal lags behind the excitation signal.

[0041] In specific implementation, determining the voltage loss according to the amplitude of the first smoothed signal and the amplitude of the first excitation signal can be achieved in the following manner, that is: obtain the maximum value in the first smoothed signal, take the maximum value in the first smoothed signal as the amplitude of the first smoothed signal, and take the maximum value in the first excitation signal as the amplitude of the first excitation signal. Then, calculate the difference between the amplitude of the first smoothed signal and the amplitude of the first excitation signal. Finally, take the obtained difference as the voltage loss.

[0042] It should be noted that in this application, the voltage loss is a parameter value used to measure the degree of loss of the voltage of the first excitation signal caused by the parasitic capacitance formed between the liquid on the surface of the diaper and the driving electrode. The larger the voltage loss, the more the voltage of the first excitation signal is lost due to the parasitic capacitance formed between the liquid on the surface of the diaper and the driving electrode; the smaller the voltage loss, the less the voltage of the first excitation signal is lost due to the parasitic capacitance formed between the liquid on the surface of the diaper and the driving electrode.

[0043] When specifically implemented, the voltage division value when a parasitic capacitance is formed between the liquid on the surface of the diaper and the driving electrode can be determined according to the phase offset and the voltage loss amount in the following manner, that is: First, calculate the tangent value of the phase offset. Then, multiply the tangent value by the voltage loss amount and divide the result by the maximum value in the first excitation signal. Subsequently, add the obtained quotient to the ratio of the voltage loss amount to the maximum value in the first excitation signal. Finally, use the added value as the voltage division value when a parasitic capacitance is formed between the liquid on the surface of the diaper and the driving electrode.

[0044] It should be noted that in this application, the voltage division value is a parameter value that measures the degree of offset of the parasitic capacitance formed between the liquid on the surface of the diaper and the driving electrode to the excitation signal. The larger the voltage division value, the more the parasitic capacitance formed between the liquid on the surface of the diaper and the driving electrode offsets the excitation signal, that is, more excitation signals are shunted by the parasitic capacitance. The smaller the voltage division value, the less the parasitic capacitance formed between the liquid on the surface of the diaper and the driving electrode offsets the excitation signal, that is, fewer excitation signals are shunted by the parasitic capacitance.

[0045] In addition, it should be noted that in this application, the parasitic capacitance refers to the capacitance formed by the dielectric layer between the driving electrode and the urine. At this time, the low-frequency excitation signal (i.e., the first excitation signal) will be stored and phase-shifted by the parasitic capacitance, that is, the amplitude and phase of the first response signal are different from those of the first excitation signal.

[0046] In step 105, compare the signal attenuation of the second excitation signal and the second response signal, and then identify the current shunt value when a current loop is formed between the liquid on the surface of the diaper and the diaper shunt layer.

[0047] In some embodiments, comparing the signal attenuation of the second excitation signal and the second response signal, and then identifying the current shunt value when a current loop is formed between the liquid on the surface of the diaper and the diaper shunt layer can be implemented in the following manner, that is: Filter the second response signal to obtain a second smoothed signal; Determine the peak coefficient of the second smoothed signal and the peak coefficient of the second excitation signal; Determine the signal attenuation amount according to the peak coefficient of the second smoothed signal and the peak coefficient of the second excitation signal; Combine the signal attenuation amount and the change rate of the alternating current to determine the current shunt value when a current loop is formed between the liquid on the surface of the diaper and the diaper shunt layer.

[0048] In specific implementation, filtering the second response signal to obtain the second smoothed signal can be achieved by the following method: filtering the second response signal through a high-pass filter in the prior art, and taking the filtered curve as the second smoothed signal. The cut-off frequency of the high-pass filter can be set to half of the frequency of the second excitation signal.

[0049] It should be noted that in this application, the second smoothed signal is the second response signal after filtering.

[0050] In specific implementation, determining the peak coefficient of the second smoothed signal and the peak coefficient of the second excitation signal can be achieved by the following method: First, calculate the root mean square of the second smoothed signal, and take the ratio of the maximum value of the second smoothed signal to the root mean square of the second smoothed signal as the peak coefficient of the second smoothed signal. Then, calculate the root mean square of the second excitation signal, and take the ratio of the maximum value of the second excitation signal to the root mean square of the second excitation signal as the peak coefficient of the second excitation signal.

[0051] In specific implementation, determining the signal attenuation amount according to the peak coefficient of the second smoothed signal and the peak coefficient of the second excitation signal can be achieved by the following method: subtracting the peak coefficient of the second smoothed signal from the peak coefficient of the second excitation signal, dividing the obtained difference by the peak coefficient of the second excitation signal, and finally taking the obtained quotient as the signal attenuation amount.

[0052] It should be noted that in this application, the signal attenuation amount is a parameter value that measures the degree of energy attenuation between the response signal and the excitation signal. The larger the signal attenuation amount, the more energy attenuation between the response signal and the excitation signal; the smaller the signal attenuation amount, the less energy attenuation between the response signal and the excitation signal.

[0053] In specific implementation, determining the current shunt value when the liquid on the surface layer of the diaper and the diaper shunt layer form a current loop in combination with the signal attenuation amount and the change rate of the alternating current can be achieved by the following method: First, obtain the maximum value of the second excitation signal. Then, multiply the maximum value of the second excitation signal by the frequency of the second excitation signal. Subsequently, multiply the obtained value by the signal attenuation amount, and take the obtained value as the current shunt value when the liquid on the surface layer of the diaper and the diaper shunt layer form a current loop.

[0054] It should be noted that in this application, the current loop refers to the loop formed by the mutual migration of charges in urine and the migration of charges in urine to the electrodes. When the urine volume is small, the parasitic capacitance formed by the dielectric layer between the urine and the driving electrode can be ignored. Under a high-frequency excitation signal (i.e., the second excitation signal), the impedance of this current loop is very small, and there is a serious shunt phenomenon.

[0055] In addition, it should be noted that in this application, the current shunt value is a parameter value that measures the degree of offset of the excitation signal caused by the mutual migration of charges in the diaper and the migration of charges in urine to the electrodes. The larger the current shunt value, the more the mutual migration of charges in the diaper and the migration of charges in urine to the electrodes cause an offset to the excitation signal, that is, more excitation signals are diverted by the current loop. The smaller the current shunt value, the less the mutual migration of charges in the diaper and the migration of charges in urine to the electrodes cause an offset to the excitation signal, that is, fewer excitation signals are diverted by the current loop.

[0056] In some embodiments, refer to Figure 3 , which is an equivalent circuit diagram of intelligent urinary incontinence detection according to some embodiments of this application, and is specifically described as follows: In Circuit A, a capacitor is formed between each end of the electrode and the urine respectively (i.e., Capacitor C1 and Capacitor C2 in the figure). Due to the mutual migration of charges in urine and the migration of charges in urine to the electrodes, a capacitor is formed (i.e., C3 in the figure). The more urine there is in the diaper, that is, the more ions there are in the urine, the smaller the impedance value of Capacitor C3. When there is a lot of urine in the diaper, Capacitor C3 can be ignored. At this time, Circuit A can be equivalent to Circuit B. The less urine there is in the diaper, that is, the fewer ions there are in the urine, the weaker the ion adsorption ability, the lower the interfacial polarization effect, and the smaller the impedance values of Capacitor C1 and Capacitor C2. When there is very little urine in the diaper, Capacitor C1 and Capacitor C2 can be ignored. At this time, Circuit A can be equivalent to Circuit C.

[0057] In Step 106, the polarization effect value of all electrodes in the diaper is determined by combining the voltage division value and the current shunt value. When the polarization effect value is greater than the preset polarization threshold, it is recorded as one case of urinary incontinence.

[0058] It should be noted that in this application, the polarization effect value is a parameter value that measures the degree of polarization caused by the interaction between the electrodes and urine in the diaper. The larger the polarization effect value, the greater the degree of polarization caused by the interaction between the electrodes and urine in the diaper. The smaller the polarization effect value, the smaller the degree of polarization caused by the interaction between the electrodes and urine in the diaper. As a preferred embodiment, in this application, the polarization effect value of all electrodes in the diaper is determined by combining the voltage division value and the current shunt value, which can be achieved in the following manner: the ratio of the voltage division value to the current shunt value is used as the polarization effect value of all electrodes in the diaper.

[0059] In addition, it should be noted that the greater the polarization effect value, the greater the influence of the parasitic capacitance in the diaper and the smaller the influence of the current loop. The smaller the polarization effect value, the smaller the influence of the parasitic capacitance in the diaper and the greater the influence of the current loop.

[0060] It should be noted that the polarization threshold in this application can be determined through experiments. For example, in this application, a first excitation signal and a second excitation signal can be emitted to a dry diaper, and then the polarization effect value of the dry diaper can be determined. Then, the diaper is soaked in salt water for 30 seconds, and the first excitation signal and the second excitation signal are emitted to the soaked diaper, and then the polarization effect value after soaking is determined. Finally, the average value of the polarization effect value of the dry diaper and the polarization effect value after soaking is used as the polarization threshold.

[0061] In some embodiments, after recording one episode of urinary incontinence, the method further includes: stopping the emission of the first excitation signal and the second excitation signal, and after the resistance values at all locations on the diaper are greater than or equal to a preset resistance threshold, repeating the steps of step 101 to step 106.

[0062] In addition, on the other hand of this application, in some embodiments, this application provides an intelligent urinary incontinence detection system. Referring to Figure 4 , this figure is a schematic structural diagram of an intelligent urinary incontinence detection system according to some embodiments of this application. The intelligent urinary incontinence detection system 400 includes: a collection module 401, a processing module 402, and an execution module 403, which are described as follows: Collection module 401. In this application, the collection module 401 is mainly used to collect resistance signals at all locations on the diaper through the flexible fabric sensor; Signal emission module 402. In this application, the signal emission module 402 is mainly used to alternately emit a first excitation signal and a second excitation signal to the detection area of the diaper through the driving electrode when the resistance value of at least one resistance signal is less than a preset resistance threshold. Among them, the first excitation signal and the second excitation signal are used to analyze the impedance characteristics of the diaper; Signal reception module 403. In this application, the signal reception module 403 is used to collect a first response signal of the first excitation signal and a second response signal of the second excitation signal through the detection electrode; Processing module 404. In this application, the processing module 404 is used to compare the phase offset between the first excitation signal and the first response signal, and then identify the voltage division value when a parasitic capacitance is formed between the liquid on the surface of the diaper and the driving electrode; It should be noted that in this application, the processing module 404 is further used to compare the signal attenuation between the second excitation signal and the second response signal, and then identify the current shunt value when a current loop is formed between the liquid on the surface of the diaper and the diaper shunt layer; Execution module 405. In this application, the execution module 405 is mainly used to determine the polarization effect value of all electrodes in the diaper by combining the voltage division value and the current shunt value. When the polarization effect value is greater than a preset polarization threshold, it is recorded as one episode of urinary incontinence.

[0063] In addition, the present application also provides a computer device, which includes a memory and a processor. The memory stores code, and the processor is configured to obtain the code and execute the above-mentioned intelligent urinary incontinence detection method.

[0064] In some embodiments, referring to Figure 5 , this figure is a schematic structural diagram of a computer device for implementing the intelligent urinary incontinence detection method according to some embodiments of the present application. The intelligent urinary incontinence detection method in the above embodiments can be implemented by Figure 5 the computer device shown. The computer device 500 includes at least one processor 501, a communication bus 502, a memory 503, and at least one communication interface 504.

[0065] The processor 501 can be a general-purpose central processing unit (CPU) or an application-specific integrated circuit (ASIC).

[0066] The communication bus 502 can be used to transfer information between the above components.

[0067] The memory 503 can be a read-only memory (ROM) or other types of static storage devices that can store static information and instructions, a random access memory (RAM), or other types of dynamic storage devices that can store information and instructions. It can also be an electrically erasable programmable read-only memory (EEPROM), a compact disc read-only memory (CD-ROM), or other optical disc storage (including compressed optical discs, laser discs, optical discs, digital versatile discs, Blu-ray discs, etc.), a magnetic disk, or other magnetic storage devices, or any other medium that can be used to carry or store the desired program code in the form of instructions or data structures and can be accessed by a computer, but is not limited thereto. The memory 503 can exist independently and be connected to the processor 501 through the communication bus 502. The memory 503 can also be integrated with the processor 501.

[0068] Among them, the memory 503 is used to store the program code for executing the solution of this application, and is controlled by the processor 501 for execution. The processor 501 is used to execute the program code stored in the memory 503. The program code may include one or more software modules. The intelligent urinary incontinence detection method in the above embodiments can be implemented by one or more software modules in the processor 501 and the program code in the memory 503.

[0069] The communication interface 504, using any device such as a transceiver, is used to communicate with other devices or communication networks, such as Ethernet, radio access network (RAN), wireless local area networks (WLAN), etc.

[0070] In a specific implementation, as an embodiment, the computer device may include multiple processors, and each of these processors may be a single-core (single-CPU) processor or a multi-core (multi-CPU) processor. The processor here may refer to one or more devices, circuits, and / or processing cores for processing data (such as computer program instructions).

[0071] The above computer device may be a general-purpose computer device or a special-purpose computer device. In a specific implementation, the computer device may be a desktop computer, a laptop computer, a network server, a personal digital assistant (PDA), a mobile phone, a tablet computer, a wireless terminal device, a communication device, or an embedded device. The embodiments of this application do not limit the type of the computer device.

[0072] In addition, this application also provides a computer-readable storage medium, and the computer-readable storage medium stores a computer program, and when the computer program is executed by a processor, the above intelligent urinary incontinence detection method is implemented.

[0073] In summary, in the intelligent urinary incontinence detection method and system disclosed in the embodiments of the present application, first, resistance signals at various positions on the urine patch are collected by the flexible fabric sensor; when the resistance value of at least one resistance signal is less than a preset resistance threshold, a first excitation signal and a second excitation signal are alternately emitted into the detection area of the urine patch through the driving electrode, wherein the first excitation signal and the second excitation signal are used to analyze the impedance characteristics of the urine patch; the first response signal of the first excitation signal and the second response signal of the second excitation signal are collected by the detection electrode; the phase offset between the first excitation signal and the first response signal is compared to identify the voltage division value when a parasitic capacitance is formed between the liquid on the surface of the urine patch and the driving electrode; the signal attenuation between the second excitation signal and the second response signal is compared to identify the current shunt value when a current loop is formed between the liquid on the surface of the urine patch and the urine patch shunt layer; the polarization effect values of all the electrodes in the urine patch are determined by combining the voltage division value and the current shunt value, and when the polarization effect value is greater than a preset polarization threshold, it is recorded as one episode of urinary incontinence.

[0074] Thus, when the present application detects that there is liquid on the urine patch (i.e., when the resistance value is less than the resistance threshold), two excitation signals with different frequencies are alternately emitted, and the waveforms between each excitation signal and the corresponding response signal are compared to identify the voltage division of the electrical signal by the urine interface polarization capacitance in the urine patch and the shunt of the electrical signal by the capacitance formed by the charge migration (i.e., the voltage division value and the current shunt value). Furthermore, based on the magnitudes of the voltage division and the shunt, the polarization effect value caused by the urine between the two electrodes in the urine patch is determined, and finally, urinary incontinence is alarmed through this polarization effect value. In summary, the present application can perform confidence detection of urinary incontinence under the interference of the polarization effect.

[0075] Although the preferred embodiments of the present application have been described, those skilled in the art can make additional changes and modifications once they learn the basic creative concept. Therefore, the appended claims are intended to be construed to include the preferred embodiments as well as all changes and modifications falling within the scope of the present application.

[0076] Obviously, those skilled in the art can make various changes and modifications to the present application without departing from the spirit and scope of the present application. Thus, if these modifications and variations of the present application fall within the scope of the claims of the present application and their equivalent technologies, the present application also intends to include these changes and modifications.

Claims

1. An intelligent detection method for urinary incontinence, characterized in that, Including: Collecting resistance signals at various locations on the diaper through the flexible fabric sensor; When the resistance value of at least one resistance signal is less than a preset resistance threshold, alternately emitting a first excitation signal and a second excitation signal into the detection area of the diaper through the drive electrode, wherein the first excitation signal and the second excitation signal are used to analyze the impedance characteristics of the diaper; Collecting a first response signal of the first excitation signal and a second response signal of the second excitation signal through the detection electrode; Comparing the phase offset between the first excitation signal and the first response signal, and further identifying the voltage division value when a parasitic capacitance is formed between the surface liquid of the diaper and the drive electrode; Comparing the signal attenuation between the second excitation signal and the second response signal, and further identifying the current shunt value when a current loop is formed between the surface liquid of the diaper and the diaper shunt layer; Combining the voltage division value and the current shunt value to determine the polarization effect value of all electrodes in the diaper. When the polarization effect value is greater than a preset polarization threshold, it is recorded as one episode of urinary incontinence.

2. The method according to claim 1, wherein The frequency of the first signal is lower than the frequency of the second signal.

3. The method according to claim 1, characterized in that Alternately emitting a first excitation signal and a second excitation signal into the detection area of the diaper through the drive electrode specifically includes: Emitting an electrical signal with a first frequency into the detection area of the diaper through the drive electrode, and using the electrical signal with the first frequency as the first excitation signal; After the first excitation signal ends and a specified time interval elapses, emitting an electrical signal with a second frequency into the detection area of the diaper through the drive electrode, and using the electrical signal with the second frequency as the second excitation signal; After the second excitation signal ends and a specified time interval elapses, emitting an electrical signal with a first frequency into the detection area of the diaper through the drive electrode, and repeating the above steps to complete the alternate emission of the first excitation signal and the second excitation signal.

4. The method according to claim 1, characterized in that Comparing the phase offset between the first excitation signal and the first response signal, and further identifying the voltage division value when a parasitic capacitance is formed between the surface liquid of the diaper and the drive electrode specifically includes: Filtering the first response signal to obtain a first smoothed signal; Determining the phase angle of the first smoothed signal; Determining the phase offset according to the phase angle of the first smoothed signal and the phase angle of the first excitation signal; Determining the voltage loss according to the amplitude of the first smoothed signal and the amplitude of the first excitation signal; Determining the voltage division value when a parasitic capacitance is formed between the surface liquid of the diaper and the drive electrode according to the phase offset and the voltage loss.

5. The method according to claim 1, characterized in that Comparing the signal attenuation between the second excitation signal and the second response signal, and further identifying the current shunt value when a current loop is formed between the surface liquid of the diaper and the diaper shunt layer specifically includes: Filtering the second response signal to obtain a second smoothed signal; Determining the peak factor of the second smoothed signal and the peak factor of the second excitation signal; Determining the signal attenuation according to the peak factor of the second smoothed signal and the peak factor of the second excitation signal; Determine the current shunt value when the liquid on the surface layer of the diaper and the diaper shunt layer form a current loop in combination with the signal attenuation amount and the change rate of the alternating current.

6. The method according to claim 1, wherein Determining the polarization effect value of all electrodes in the diaper by combining the voltage division value and the current shunt value means taking the ratio of the voltage division value and the current shunt value as the polarization effect value of all electrodes in the diaper.

7. The method according to claim 1, wherein The diaper includes: a surface layer, a driving electrode layer, a nylon cloth isolation layer, a detection electrode layer, a diversion layer, an absorption core layer, and a bottom layer.

8. An intelligent urinary incontinence detection system, characterized in that, The urinary incontinence intelligent detection system includes: An acquisition module for acquiring resistance signals at various positions on the diaper through the flexible fabric sensor; A signal transmitting module for alternately transmitting a first excitation signal and a second excitation signal into the detection area of the diaper through the driving electrode when the resistance value of at least one resistance signal is less than a preset resistance threshold, wherein the first excitation signal and the second excitation signal are used to analyze the impedance characteristics of the diaper; A signal receiving module for acquiring a first response signal of the first excitation signal and a second response signal of the second excitation signal through the detection electrode; A processing module for comparing the phase offset between the first excitation signal and the first response signal, and further identifying the voltage division value when a parasitic capacitance is formed between the liquid on the surface layer of the diaper and the driving electrode; The processing module is further configured to compare the signal attenuation between the second excitation signal and the second response signal, and further identify the current shunt value when the liquid on the surface layer of the diaper and the diaper shunt layer form a current loop; An execution module for determining the polarization effect value of all electrodes in the diaper by combining the voltage division value and the current shunt value, and when the polarization effect value is greater than a preset polarization threshold, recording it as one episode of urinary incontinence.

9. A computer device, characterized in that, The computer device includes a memory and a processor, the memory stores code, and the processor is configured to obtain the code and execute the urinary incontinence intelligent detection method according to any one of claims 1 to 7.

10. A computer-readable storage medium storing a computer program, characterized in that, When the computer program is executed by the processor, it implements the urinary incontinence intelligent detection method according to any one of claims 1 to 7.

Images