WO2014067248A1

WO2014067248A1 - Method of real-time monitoring of low urine volume in bladder and automatic alarm

Info

Publication number: WO2014067248A1
Application number: PCT/CN2013/072651
Authority: WO
Inventors: 刘官正; 蒋庆
Original assignee: 中山大学
Priority date: 2012-11-01
Filing date: 2013-03-14
Publication date: 2014-05-08
Also published as: CN102961152A; CN102961152B

Abstract

Disclosed is a method of real-time monitoring of low urine volume in the bladder and an automatic alarm, which includes the following steps: 1) tightly attaching multiple test electrodes to the test sites of a patient, and real-time monitoring of an electrical impedance value of the bladder with a bio-electrical impedance measurement device according to a bio-electrical impedance technique (101); 2) by means of a digital filter algorithm, selecting suitable parameters and removing interference signals to improve the signal-noise ratio of the electrical impedance, and real-time updating of the maximum value of the electrical impedance and calculating an impedance threshold value and change rate thereof (102); 3) according to medical knowledge and clinical experience, establishing an expert diagnostic system to approximately process the impedance threshold value and the change rate of the threshold value, deciding on an approximate rule and then effecting an automatic urination alarm according to the approximate rule so as to remind the patient of the need to urinate in time or to inform a medical worker (103). By employing this method, the urine volume in the bladder can be dynamically predicted accurately and in real time and a urination alarm is effected, so the patient can be reminded of the need to urinate in time, or the pathogenic conditions can be monitored remotely via a wireless network, which is more convenient and safer to operate and has a strong anti-interference capability.

Description

Real-time monitoring and automatic alarm method for low-load bladder urine volume

Technical field

The invention relates to a real-time monitoring method for bladder urine volume, in particular to a real-time monitoring and automatic urinating alarm method for low-load bladder urine volume based on bioelectrical impedance.

technical background

At present, the methods of detecting bladder conditions mostly adopt ultrasonic, pressure, displacement and other technical means, and all of them adopt static monitoring methods, which cannot grasp the urine volume of patients in time. For patients with urinary insufficiency such as urinary incontinence, cystitis, spinal cord injury, etc., it is necessary to monitor the bladder urine volume in real time, and promptly remind the patient to urinate, in order to prevent complications such as excessive urination, excessive urination or urinary incontinence; Remote monitoring is achieved by wired (or wireless) communication methods, and current methods of monitoring bladder urine volume do not meet the above requirements.

Bioelectrical impedance technology utilizes the electrical properties of biological tissues and organs to extract non-invasive detection techniques for human physiological and pathological information. Existing measurement methods and devices are unable to clearly and accurately determine the appropriate alarm points based on the measurement data, prompting the patient to urinate. In the prior art, a bioresistance-based bladder urine volume monitoring device is disclosed, and a linear method such as threshold value and curve fitting is used to predict the amount of urine. However, considering that the human bladder organ is an extremely complex adaptive system, the mathematical model between the electrical impedance change and the urine volume change is extremely complicated, and there are obvious individual and temporal and spatial differences, further complicating the model. In the prior art, a simple linear relationship is used to predict the amount of urine, which inevitably has a great error. Therefore, based on the in-depth discussion of the relationship between the bladder organ and its electrical impedance, the present invention proposes an adaptive prediction model based on fuzzy logic and expert knowledge to achieve more accurate urine volume prediction and urination alarm.

Summary of the invention

The object of the present invention is to overcome the deficiencies of the prior art, and to provide a non-invasive urinary prediction method based on bioelectrical impedance, combined with clinical expert experience and experimental data characteristics, and using fuzzy logic method to achieve more accurate bladder urine volume prediction and alarm. It is safer to operate, more resistant to interference, and more accurate to prompt patients to urinate in time and avoid the risk of excessive urination.

The present invention provides a real-time monitoring and automatic alarm method for low-load bladder urine volume, and the steps thereof include:

1) placing a plurality of test electrodes close to the test site of the patient, and measuring the electrical impedance value of the bladder in real time by a bioelectrical impedance measuring device according to the bioelectrical impedance technology;

2) Through the digital filtering algorithm, select appropriate parameters including cutoff frequency and order, remove interference signals including breathing, heartbeat, high frequency, power frequency, and improve the electrical impedance SNR; then, real time Update the maximum impedance, calculate the impedance threshold and its rate of change;

3) Based on medical knowledge and clinical testing experience, establish an expert diagnosis system, which blurs the impedance threshold and threshold change rate, and formulates fuzzy rules; then implements an automatic urination alarm according to the fuzzy rule criteria to prompt the patient to urinate in time. Or notify medical staff.

As a preferred embodiment of the technical solution of the present invention, the low-load bladder urine volume real-time monitoring and automatic alarm method of the present invention further includes part or all of the following technical features:

Preferably, the bioelectrical impedance measuring device comprises a test electrode, a lower position machine and a host computer, and a multi-way switch module connecting the two is arranged between the test electrode and the lower position machine, and the lower position machine is responsible for the electrical impedance data. The data is collected and wirelessly communicated with the host computer. The host computer is responsible for the electrical impedance data processing and automatic alarm.

Preferably, the lower computer main control board comprises a main control module and a power module connected to the main control module, an amplitude/phase measurement module, a measurement signal filtering module, an intermediate frequency sinusoidal signal generation module, a voltage controlled constant current source module, and a transmission. The module and the receiving module; the power module realizes long-time measurement through energy consumption management, the measurement signal filtering module is used to remove the interference signal, the voltage-controlled constant current source module is used to provide a stable excitation current, and the transmitter is used to be worn on the patient's lower abdomen The lower end corresponds to the test position of the bladder to input current excitation, and the receiver is used to collect the electrical impedance data of the human body and wirelessly transmit it to the upper computer.

Preferably, the data communication communication between the upper computer and the lower computer is realized by an RS232 wireless module set in the lower computer.

Preferably, in the step 2), the digital filtering algorithm is a low-pass point-by-point filtering algorithm with a very low cutoff frequency, which can effectively remove interference signals such as breathing, heartbeat, high frequency and power frequency in real time, and improve signal noise. ratio. Further, in a preferred embodiment of the present invention, in the step 2), the digital filtering algorithm is a low-pass point-by-point filtering algorithm using an extremely low cutoff frequency of less than or equal to 0.01. Considering that the physiological characteristics such as breathing and heartbeat also affect the measurement accuracy to a certain extent, this finding specifies that the low-pass filter cutoff frequency must be less than or equal to 0.01.

Preferably, in the step 2), updating the electrical impedance maximum means that the maximum impedance value is recorded and updated in real time, and the impedance maximum value <42> is recorded in the register in real time, if the current time impedance value is < Z ( k) > greater than the previous impedance maximum value < Max(Z) >, the current impedance value < Z (k, > is restarted into the register, the previous data is automatically discarded; otherwise, no data replacement work is done. .

Preferably, the step of calculating the impedance threshold and the rate of change in step 2) is based on subtracting the impedance maximum value from the current impedance value to obtain an impedance threshold and a rate of change thereof, and then performing a parameter blurring step according to the knowledge base:

The threshold and threshold rate of change are calculated according to the following formula:

TR(k) = Max(Z) - Z(k) , k = 0, 1,2,...

Where TR d, Max{k) respectively represent the impedance threshold at the current time, and the maximum resistance at the current time Resistance value, the impedance value of the current time. Qing) = — — D, k = 2,3,4,...

T

Where TR k-, , respectively represent the current rate of change of the threshold, the threshold of the previous moment, the sampling period;

Parameter fuzzification is to change the exact value of threshold and threshold change rate into fuzzy value. The threshold fuzzy value is divided into 4 levels such as positive (ΡΒ), center (ΡΜ), positive (PS), and zero (Z). . The threshold change rate fuzzy value is divided into five levels such as positive (PB), small (PS), zero (Z), negative (NS), and negative (NB).

Preferably, in the step 3), according to expert knowledge and clinical testing experience, the following fuzzy rules are formulated:

[1] IF threshold is positive (PB), THEN urinary alarm;

[2] The IF threshold is centered (PM) and the threshold change rate is zero (Z) / negative small (NS) / negative large (NB), THEN urination alarm;

[3] The IF threshold is positive (PS) and the rate of change of the threshold is positive (PB), THEN urinating alarm; In addition, if the test time reaches a certain time (such as 2.5 hours), there is still no alarm, the test system performs Urinary alarm, and check the test device and electrode.

Preferably, the low-load bladder urine volume real-time monitoring and automatic alarm method of the invention further comprises selecting an electrode placement position, adopting a multi-way switch module to perform measurement position switching, realizing multi-position measurement and comparison, finding an optimal measurement position, and reducing Measurement error caused by small individual differences. Considering that individual differences (such as fat, height, waist circumference, etc.) directly affect the choice of test electrode position, for this reason, this discovery has developed a multi-way switch circuit module (as shown in Figure 7), which can achieve different measurements. Position comparison (such as different height, test electrode width, relative distance between test electrode and stimulating electrode, etc.), to obtain the best electrode placement position for different subjects, to minimize the inherent interference caused by individual differences, improve measurement accuracy.

Compared with the prior art, the technical solution of the present invention at least includes the following beneficial effects:

1. Using fuzzy logic theory, it helps to shorten the distance between clinical experts' language and engineering data features, better learn clinical expert experience, more fully acquire impedance characteristics, and improve alarm accuracy.

2. Combined with the expert alarm method of threshold, threshold change rate, time and other characteristics, it can capture the physiological characteristics of urination more accurately, and more reasonable urination reminder and alarm!

3. The multi-way switch circuit module has been added to compare the measurement results at different positions to obtain the best electrode placement position, which can reduce the interference caused by individual differences.

DRAWINGS

1 is a flow chart of a real-time monitoring and automatic alarm method for low-load bladder urine provided by the implementation of the present invention Figure.

2 is a schematic view showing the wearing of the test electrode used in the embodiment of the present invention.

Fig. 3A is a diagram showing the structure of the impedance threshold membership function in the embodiment of the present invention.

Fig. 3B is a diagram showing the membership function of the impedance threshold change rate in the embodiment of the present invention.

4 is a flow chart of an alarm algorithm in an embodiment of the present invention.

Figure 5 is a comparison of sampled data in an embodiment of the present invention.

Figure 6 is a display interface in an embodiment of the present invention.

Figure 7 shows the system structure in the embodiment of the present invention.

detailed description

In order to make the objects, the technical solutions and the advantages of the present invention more comprehensible, the present invention will be described in detail with reference to the accompanying drawings.

As shown in FIG. 1, a real-time monitoring and automatic alarming method for low-load bladder urine volume provided by the present invention includes the following steps:

1. Select the best measurement position. As shown in Figure 2, the measurement position includes three adjustable parameters (the vertical height from the electrode to the navel, the distance from the measuring electrode to the center line, and the distance from the stimulating electrode to the center line). Considering the disturbance of the tissue around the bladder, the uncertainty of the flow of current in the human organs and the individual differences in the position of the bladder, we can use a multi-way switch (Figure 7) to compare the different positions to find the best electrode installation position. , to minimize the inherent interference of the human body and improve the signal to noise ratio. According to the anatomy and electric field distribution principle, the measuring electrode and the stimulating electrode are at the same horizontal line (Fig. 2).

2, through the real-time low-pass filtering algorithm, select the appropriate parameters including the cutoff frequency, order, etc., the cutoff frequency is generally lower than 0. 01Hz, to remove the interference signals such as breathing, heartbeat, high frequency, power frequency, improve the resistance Anti-signal to noise ratio. Real-time search and bubble method are used to obtain the maximum value of dynamic impedance and calculate the impedance threshold and its rate of change. The impedance threshold is the dynamic maximum value to reduce the current value of the impedance, and the threshold change rate is the current threshold minus the last time threshold.

3. Combine medical knowledge with clinical experimental data characteristics, establish an expert diagnosis system, that is, blur the threshold and threshold change rate, and turn into clinical language; formulate fuzzy rules and realize automatic alarm to remind patients to urinate in time. Figure 3 is a schematic diagram of the membership function of the threshold and threshold rate of change. The fuzzy inference rules are as follows:

[1] The IF threshold is positive (PB), THEN urinary alarm;

[2] The IF threshold is centered (PM) and the threshold change rate is zero (Z) / negative small (NS) / negative large (NB), THEN urination alarm; [3] IF threshold is positive (PS) and threshold change rate is positive (PB), THEN urinary report

[4] If the test time reaches a certain time (such as 2. 5 hours), there is still no alarm, and the test system performs a forced urination alarm to avoid the risk caused by the test error. And check the test equipment and electrodes in time.

[5] In addition, the alarm rules and threshold values can be corrected based on the knowledge of expert knowledge, and clinical test data and expert new knowledge are added as the main basis for knowledge update. As can be seen from Figure 1, this process mainly includes three parts: electrode wear and impedance data acquisition, data pre-processing and feature extraction, feature defuzzification and diagnostic alarm.

The wearing of the electrode includes the selection and placement of the electrode position. The position selection is based on the comparison of the multiplex switch to obtain the best placement position. Before the electrode is placed, it is best to shave the unclean substance on the skin surface and then rub the surface with alcohol. To reduce the impact on the measurement. Fig. 2 is a perspective view showing the wearing of the test electrode in the embodiment of the present invention. As shown in the schematic diagram, multiple test electrodes must be in the same horizontal plane, with two measuring electrodes inside and two stimulating electrodes outside, where multiple test electrodes must be symmetrical about the midline. This electrode wearing method conforms to the anatomical and electric field distribution principles and helps to obtain the best results.

The low-load bladder urine volume real-time monitoring and automatic alarm method includes the selection of the electrode placement position, uses the multi-way switch module to perform measurement position switching, realizes multi-position measurement and comparison, finds the best measurement position, and reduces individual differences. The resulting measurement error. Considering that individual differences (such as fat, height, waist circumference, etc.) directly affect the choice of test electrode position, for this reason, this discovery has developed a multi-way switch circuit module (as shown in Figure 7), which can achieve different measurements. Position comparison (such as different height, test electrode width, relative distance between test electrode and stimulating electrode, etc.), to obtain the best electrode placement position for different subjects, to minimize the inherent interference caused by individual differences, improve measurement accuracy.

In step 2) of the preferred embodiment of the present invention, the digital filtering algorithm is a low-pass point-by-point filtering algorithm using a very low cutoff frequency, which can effectively remove interference signals such as breathing, heartbeat, high frequency, and power frequency in real time, and improve Signal to noise ratio. Further, in a preferred embodiment of the present invention, in the step 2), the digital filtering algorithm is a low-pass point-by-point filtering algorithm using an extremely low cutoff frequency of less than or equal to 0.01. Considering that the physiological characteristics such as breathing and heartbeat will also affect the measurement accuracy to a certain extent, this finding specifies that the cutoff frequency of the low-pass filter must be less than or equal to 0.01. The updated resistance reactance maximum means that the maximum impedance value is recorded and updated in real time, and the impedance maximum value < ^(Z) > is recorded in the register in real time, if the current time impedance value <2( ) > is greater than the previous impedance maximum The value < Ϊ4Ζ) >, the current time impedance value <Z(fc) > is restarted into the register, and the previous data is automatically discarded; otherwise, no data replacement work is performed.

Wherein, the calculation of the impedance threshold and its rate of change in step 2) is based on the impedance maximum and the current impedance. The value is subtracted to obtain the impedance threshold and its rate of change, and then the parameter fuzzification step is performed according to the knowledge base: The threshold value and the threshold change rate are calculated according to the following formula:

TR(k) = Max(Z) - Z(k) , k = 0, 1,2,...

Where TR and Max(k) represent the current time impedance threshold, the maximum impedance at the current time, and the impedance at the current time. ) = just — — , k = 2,3,4,...

T

Fig. 3B is a diagram showing the membership function of the impedance threshold change rate in the embodiment of the present invention. Figure 3A shows the membership function of the impedance threshold. Considering that the impedance threshold is always greater than zero, its value is divided into three positive intervals, including positive (PS), medium (PM) and positive (PB), respectively. The function of triangle, ladder and unilateral trapezoids, the choice of value can be selected and optimized according to test experience.

Figure 3B is a threshold function of the threshold change rate. The threshold change rate is divided into five intervals according to the principle of symmetry, including negative large (NB), negative small (NS), zero (Z), positive small (PS) and positive (PB), respectively, using unilateral trapezoids and trapezoids. , triangles, trapezoids, and unilateral trapezoidal functions, whose value can be selected and optimized through test experience.

FIG. 4 is a flow chart of an alarm algorithm according to an embodiment of the present invention. First, the patient must be reminded to drain the urine before the measurement to ensure that the initial value of the urine in the bladder is close to zero.

The second step is to set the parameters, mainly including the setting of the electrode placement position. If the patient is using the instrument for the first time, the comparison test of the multi-way switch must be performed to obtain the best measurement position, and the electrode placement is completed, and the monitoring is started. instrument.

Next, pre-processing and feature extraction of impedance data such as dynamic acquisition and filtering are performed to obtain more accurate parameters such as maximum impedance value, impedance threshold, and impedance threshold change rate.

In the next step, the membership function and the fuzzy inference rule base provided in the database are used to perform impedance characterization (threshold and threshold change rate) to defuzzify and urinate event diagnosis, match the urinary alarm successfully, and store the data in the database. In, to update the database. If the match is unsuccessful, start the abnormal diagnosis program, and notify the engineer and the clinical expert to diagnose the fault together, and eliminate the interference factors such as battery power failure, electrode aging and falling off, and abnormal abnormal operation of the patient, and ensure the next measurement is correct.

At the same time, in order to avoid abnormal errors and affect the health of patients, this discovery participated in a strong Alarm measures to protect patients' health.

In addition, the new knowledge of clinical experts, the guiding situation of the testing process, the addition of new data, etc. can further improve the database and knowledge base, modify the membership function and inference rules, etc., so as to achieve an adaptive urinary alarm method to achieve the best. Precision. In step 3) of the embodiment of the present invention, based on expert knowledge and clinical testing experience, the following fuzzy rules are formulated:

[4] The IF threshold is positive (PB), THEN urinary alarm;

[5] The IF threshold is centered (PM) and the threshold change rate is zero (Z) / negative small (NS) / negative large (NB), THEN urination alarm;

[6] IF threshold is positive (PS) and threshold change rate is positive (PB), THEN urinary alarm; In addition, if the test time reaches a certain time (such as 2.5 hours), there is still no alarm, the test system performs Urinary alarm, and check the test device and electrode.

Figure 5 compares sampled data in an embodiment of the invention. The above figure shows the raw data of bladder bioelectrical impedance. The figure below shows the data after pre-processing such as low-pass filtering.

Figure 6 shows the display interface in the embodiment of the present invention. The invention adopts Labviw program design display interface, including motion button and serial channel selection, raw data and filtered dynamic data display, alarm indicator and abnormal condition indicator light, status display box (prompt whether normal monitoring), monitoring time and other information . Through the interface display, you can clearly understand the operating status of the instrument.

Figure 7 shows the system structure in the embodiment of the present invention. The system structure is the bioelectrical impedance measuring device, comprising a test electrode, a lower position machine and a host computer, wherein the test electrode and the lower position machine are provided with a multi-way switch module connecting the two, and the lower position machine is responsible for the resistance Anti-data acquisition, and wireless communication with the host computer, the host computer is responsible for electrical impedance data processing and automatic alarm. The multiplexer selection module is mainly used to compare the effects of different measurement positions to help the first-time patient to obtain the best measurement position and improve the measurement accuracy.

The main control board of the lower computer comprises a main control module and a power module connected to the main control module, an amplitude/phase measurement module, a measurement signal filtering module, an intermediate frequency sinusoidal signal generation module, a voltage controlled constant current source module, a transmitting module, and a receiving The power module manages long-term measurement through energy management, the measurement signal filtering module is used to remove the interference signal, the voltage-controlled constant current source module is used to provide a stable excitation current, and the transmitter is used to wear the bladder at the lower end of the patient's lower abdomen. The test electrode of the position is input with current excitation, and the receiver is used to collect the electrical impedance data of the human body and wirelessly transmit it to the upper computer. In the preferred embodiment of the present invention, the data communication communication between the upper computer and the lower computer is realized by the RS232 wireless module set in the lower computer.

The upper computer alarm algorithm module is mainly responsible for electrical impedance data preprocessing (filtering, detrending, etc.), feature extraction (impedance maximum, threshold, threshold change rate, etc.), feature fuzzification and diagnosis, etc. Correct the knowledge base and improve the accuracy of the alarm. Then, according to the diagnosis result of the alarm algorithm, the sound and light alarm is used to remind the patient to urinate in time.

It is to be noted that a number of modifications and variations can be made by those skilled in the art without departing from the principles of the invention. It should be noted that the method and the measuring device of the present invention can also measure the thickness of the fat, the condition of the ascites, the food retained in the stomach, and the respiratory condition, etc., which are all within the scope of the present invention.

Claims

1. A low-load bladder urine volume real-time monitoring and automatic alarm method, characterized in that it comprises the following steps:

1) placing a plurality of test electrodes close to the test site of the patient, and measuring the electrical impedance value of the bladder in real time by the bioelectrical impedance measuring device according to the bioelectrical impedance technology;

2) Through the digital filtering algorithm, select appropriate parameters including cutoff frequency and order, remove interference signals including breathing, heartbeat, high frequency, power frequency, and improve the impedance-to-noise ratio; then, update the electrical impedance in real time. Maximum value, calculate the impedance threshold and its rate of change;

2. The low-load bladder urine volume real-time monitoring and automatic alarm method according to claim 1, wherein: the bioelectrical impedance measuring device comprises a test electrode, a lower computer and a host computer, and the test electrode A multi-way switch module connecting the two is provided with the lower position machine, and the lower position machine is responsible for data collection of electrical impedance resistance, and performs data communication with the upper computer through wireless mode, and the upper computer is responsible for electrical impedance data processing and automatic reporting.

3. The method for real-time monitoring and automatic alarming of low-load bladder urine according to claim 2, wherein: the main control board of the lower computer comprises a main control module and a power module connected to the main control module, and an amplitude value thereof. / phase measuring module, measuring signal filtering module, intermediate frequency sinusoidal signal generating module, voltage controlled constant current source module, transmitting module, receiving module; said power module realizes long-term measurement through energy consumption management, and measuring signal filtering module is used for removing interference The signal, the voltage-controlled constant current source module is used to provide a stable excitation current, and the transmitter is used to input current excitation by a test electrode worn at the lower end of the patient's lower abdomen corresponding to the bladder position, and the receiver is used to collect the electrical impedance data of the human body and transmit it wirelessly to Host computer.

4. A low-load bladder urine volume real-time monitoring and automatic alarm method according to claim 2, wherein the data communication communication between the upper computer and the lower computer is realized by an RS232 wireless module set in the lower computer.

5. The low-load bladder urine volume real-time monitoring and automatic alarm method according to claim 1, wherein: in the step 2), the digital filtering algorithm is a low-pass point-by-point filtering algorithm using a very low cutoff frequency. It can effectively remove interference signals such as breathing, heartbeat, high frequency and power frequency in real time, and improve the signal to noise ratio.

The low-cut-off frequency of less than or equal to 0.01 is used in the step 2). Low pass point-by-point filtering algorithm.

7. The method for real-time monitoring and automatic alarming of low-load bladder urine according to claim 5, wherein: in the step 2), updating the maximum value of the electrical impedance refers to real-time recording and updating the maximum impedance value. The impedance maximum value < 4 > is recorded in the register in real time. If the current time impedance value <2> is greater than the previous impedance maximum value <M (Z)>, the current time impedance value <^)> is restarted. When writing to the register, the previous data is automatically discarded; otherwise, no data is replaced.

8. The method for real-time monitoring and automatic alarming of low-load bladder urine according to claim 1, wherein: calculating the impedance threshold and the rate of change in step 2) are based on the impedance maximum value and the current impedance value. Reduce the impedance threshold and its rate of change, and then perform the parameter fuzzification step according to the knowledge base:

TR(k)=Max(Z)-Z(k), k = 0,1,2,...

Where 7^), fer ), Z) respectively represent the current time impedance threshold, the maximum impedance value at the current time, and the impedance value at the current time; ) = just — — , k = 2, 3, 4,...

T

Where dTi and TRm respectively represent the current rate of change of the threshold, the threshold of the previous moment, and the sampling period;

Parameter fuzzification is to change the exact value of threshold and threshold change rate to fuzzy value. The threshold fuzzy value is divided into 4 levels such as Zhengda (PB), center (PM), positive (PS), and zero (Z). . The threshold change rate fuzzy value is divided into five levels such as positive (PB), positive (PS), zero (Z), negative (NS), and negative (NB).

9. A method for real-time monitoring and automatic alarming of low-load bladder urine according to claim 1, wherein: in the step 3), according to expert knowledge and clinical testing experience, the following fuzzy rules are formulated:

[1] The IF threshold is positive (PB), THEN urinary alarm;

[2] IF threshold is centered (PM) and threshold rate of change is zero (Z) / negative small (NS) / negative (NB), THEN urination alarm;

[3] IF threshold is positive (PS) and threshold change rate is positive (PB), THEN urinary alarm; In addition, if the test time reaches a certain time (such as 2.5 hours), there is still no alarm, the test system performs urination mandatory Alarm, and check the test device and electrode.

10. The method for real-time monitoring and automatic alarming of low-load bladder urine according to claim 1, further comprising: selecting an electrode placement position, and adopting a multi-way switch module to perform measurement position switching, thereby realizing multi-position measurement and comparison, Find the best measurement position and reduce the measurement error caused by individual differences.