KR100545128B1 - System for detecting uroflow information and method therefore - Google Patents

Abstract

The present invention provides a urination information detection system and method that can be utilized as clinical information for diagnosing diseases of the urinary system by detecting urination time, urination volume, urination rate and urination pattern by using the weight change during urination of the subject. do.

To this end, the present invention detects the body weight during urination of the test subject and the weight sensing means for generating a weight signal, the urine signal detection for detecting the weight signal indicating a slight weight change during urination of the subject from the weight signal from the weight sensing means Means and control processing means for extracting urination pattern information indicating urination time, urination amount and urination rate from the body weight signal from the urination signal detecting means.

Description

System for detecting uroflow information and method therefore}

1 is a block diagram showing the configuration of the urination information detection system according to the present invention;

FIG. 2 is a detailed view illustrating a configuration block for extracting urination information of the microprocessor illustrated in FIG. 1;

Figure 3 is a graph showing an exemplary curve state approximated by the urination signal and polynomial according to a preferred embodiment of the present invention,

4 is a graph illustrating an example of detecting a starting point and an end point of urination from the urination signal of FIG. 3 according to a preferred embodiment of the present invention;

5A to 5C are graphs illustrating an example of extracting a urination pattern by low-pass filtering and first differentiating the urination signal of FIG. 3 according to a preferred embodiment of the present invention;

6 is a flowchart for explaining the operation of the urination information detection method according to the present invention.

<Description of the symbols for the main parts of the drawings>

2,4,6: load cell, 8,10,12: operational amplifier,

14: adder, 16: 5Hz low pass filter,

18: 0.1Hz lowpass filter, 20: 1Hz lowpass filter,

22: sample / hold circuit, 24: differential amplifier,

26: microprocessor, 28: analog-to-digital converter,

30: polynomial calculation unit, 32: local curvature application unit,

34: urination time detection unit, 36: urination amount detection unit,

38: average urination rate detection unit, 40: 0.25 Hz low pass filter,

42: 1 first differential treatment unit, 44: highest urination rate detection unit.

The present invention relates to a urinary information detection system and a method thereof, and more particularly, to the urinary time, the voided volume, the urinary flow rate, and the urine pattern clinically necessary for diagnosing diseases of the urinary system. The present invention relates to a urination information detection system and a method for detecting a (Uroflow Pattern).

As is well known, the urinary system of the human body is susceptible to various diseases such as prostate hypertrophy and incontinence of urine, and most of the diseases of the urinary system are in the urinary processing state of the human body. It is closely related to.

Therefore, in recent years, the disease of the urinary system is predicted in advance, and the fundamental prevention is performed, and as a method for accurately diagnosing the disease occurring in the urinary system, the analysis of the components obtained by taking the urine of the subject, of course, Data on the weight change of the subject measured during urination is to be used for prevention and treatment.

However, in order to accurately obtain the data of the weight change obtained during urination of the subject in order to prevent the disease of the urinary system, it is necessary to exclude the influence of the weight change caused by unnecessary movement or heartbeat of the subject due to urination. There is a disadvantage in that it is difficult to use as an appropriate data for the prevention and treatment of diseases of the urinary system, because a method of efficiently removing unnecessary signal components detected during urination and extracting only a signal of urination is not developed. .

Accordingly, the present invention has been made in view of the above-described conventional circumstances, and an object thereof is to detect urination time, urination amount, urination rate and urination pattern by using a weight change during urination of a test subject, thereby diagnosing diseases of the urinary system. It is to provide a urination information detection system and method that can be used as clinical information.

According to the system of the present invention to achieve the above object, the weight sensing means for detecting the weight during urination of the test subject to generate a weight signal, and the weight change during the urination of the test subject from the weight signal from the weight sensing means A urination signal detection means for detecting a weight signal indicated by the urination signal detection means and a control processing means for extracting urination pattern information indicating urination time, urination amount and urination rate from the body weight signal from the urination signal detection means To provide.

According to the method of the present invention to achieve the above object, the weight of the subject having a weight change value generated during the urination in the subject body weight of detecting the subject at the time of performing urination, the detected body weight signal Detecting a starting point and end point of urination from the body weight signal, and extracting a urination pattern signal having a urination time, urination amount and urination rate from the start point and end point of urination; Provides a method of detecting urination information.

Hereinafter, the present invention configured as described above will be described in detail with reference to the accompanying drawings.

That is, Figure 1 is a block diagram showing the configuration of the urination information detection system according to the present invention.

As shown in FIG. 1, the urination information detection system according to the present invention includes first to third load cells 2, 4 and 6, first to third operational amplifiers 8, 10 and 12, and an adder 14. ), A 5 Hz low pass filter 16, a 0.1 Hz low pass filter 18, a 1 Hz low pass filter 20, a sample / hold circuit 22, a differential amplifier 24, and a microprocessor 26. .

In the figure, the first to third load cells 2, 4, and 6 are respectively installed at positions (i.e., toilet seats) where the test subject can rest upon urination, and thus detect the weight of the test subject performing urination. do.

Here, in the embodiment of the present invention, three load cells (2, 4, 6) are applied, but the number of load cells is less than three or four in order to increase the accuracy of the change in the installation position of the load cell or the weight of the subject. It is possible to apply more than that.

The first to third operational amplifiers 8, 10 and 12 are connected so as to correspond to the first to third load cells 2, 4 and 6, respectively, and the weights from the load cells 2, 4 and 6 respectively. The detected signal is amplified by a predetermined amplification.

The adder 14 adds the weight sensing signals amplified by the first to third operational amplifiers 8, 10, and 12, respectively, and outputs the weight sensing signals added through the adder 14. The weight of the subject includes a change in the heart rate of the test subject or a signal change by the minute movement, so that the weight change due to urination cannot be accurately detected.

The 5 Hz low pass filter 16 performs a low pass filtering on the weight detection signal from the adder 14 in a frequency band of 5 Hz, and a non-inverting input terminal of the differential amplifier 24 as a weight signal of a test subject including urination information. Will be entered in (+).

The 0.1 Hz low pass filter 18 low-pass filters the weight detection signal from the adder 14 in a frequency band of 0.1 Hz, and the sample / hold circuit 22 performs the 0.1 Hz low pass filter 18. The low-pass filtered weight detection signal is sampled and held through the input signal, and is input to the inverting input terminal (-) of the differential amplifier 24 as an average weight signal of the test subject.

The 1 Hz low pass filter 20 low pass filters the weight detection signal from the adder 14 in the frequency band of 1 Hz and inputs the same to the microprocessor 28.

In the figure, the differential amplifier 20 is input through the non-inverting input terminal (+) to the average weight signal of the test subject from the sample / hold circuit 22 input through the inverting input terminal (-). The body weight signal including urination information is differentially amplified to output the urination signal according to the minute weight change during urination to the microprocessor 26.

That is, the differential amplifier 24 subtracts the average weight value from the small weight change value to exclude the peripheral influence caused by the minute movement and the heartbeat during the urination, which is unnecessary for the detection of the urination pattern. As a result, only the urination value (that is, 1/200 to 1/400) which is relatively small compared to the weight value is output.

The microprocessor 26 detects the start point and the end point of urination by digitally converting the weight signal from the differential amplifier 24 through its analog-to-digital converter 28 to perform a software operation. The urination time, urination amount and urination rate are detected based on the start point and the end point.

Here, as shown in FIG. 2, the microprocessor 26 includes a polynomial calculator 30, a low power curvature applying unit 32, a urination time detector 34, a urination amount detector 36, and an average urination rate detector ( 38), the 0.25 Hz low-pass filter 40, the first differential processing section 42, and the highest urination rate detection section 44 is configured.

In FIG. 2, the polynomial calculator 30 extracts the urination signal by removing the influence of body weight and motion (Motion Artifact) from the weight signal from the differential amplifier 24. The regression curve according to the polynomial ( Polynomial Regression) can be used to remove noise components from the urination signal including the weight change by the subject's movement. As shown in FIG. 3, the 20th order is considered in consideration of the maximum proximity to the urination signal. Use polynomials to detect baseline in three steps.

In addition, the local curvature applying unit 32 applies a local curvature to detect the start and end point of urination in the urination signal detected by the polynomial calculation unit 30, the local curvature is a limited curve The range shows the curvature according to the scan length, and the larger the curvature of the curve increases the value, the smaller the curvature decreases the value.

As shown in FIGS. 4A to 4D, the curvature of the starting point and the ending point of the regional curvature applied to the regional curvature applying unit 32 is large, and the maximum value is calculated at the starting point. And the end point represents the minimum value.

Thus, by applying the regional curvature to the detected baseline according to the definition of the regional curvature, it is possible to detect the starting point and the end point of urination, and the three-stage baseline detected by the regression curve using the urination signal and polynomial of the subject, and the The scan length of the local curvature with respect to the baseline (the scan lengths of 50, 100, and 150 are applied in FIGS. 4B, 4C, and 4D, respectively) is set to detect the start point of the maximum value and the end point of the minimum value.

In FIG. 2, the urination time detector 34 detects the time difference from the start point to the end point as the urination time, based on the start point and the end point of the urination signal detected by the local curvature application part 32.

The urination amount detection unit 36 is based on the start point and the end point of the urination signal detected by the local curvature applying unit 32, after the urination detected by the voltage and the end point before the urination baseline detected by the start point The voltage difference between the voltage on the base line is obtained, and the amount of urination is calculated by averaging the voltage difference on the base line for a predetermined time (for example, 5 seconds) at the start point and the end point. This is to exclude the error of unnecessary movement of the subject if the voltage difference before and after the urination is calculated as one instantaneous data.

In addition, the average urination rate detection unit 38 calculates the urination time detected by the urination time detection unit 34 and the urination amount detected by the urination amount detection unit 36 to detect an average urine flow rate. . In Equation 1 below, the average urination rate (Q _mean ) is calculated by calculating the urination time and the urination amount.

Here, V.V represents urination volume, and V.T represents urination time.

The 0.25 Hz low pass filter 40 extracts a signal unique to urination by low pass filtering a urination signal having a starting point and an end point detected by the regional curvature applying unit 32 at a frequency band of 0.25 Hz. It is to detect the urination pattern.

Here, the 0.25 Hz low pass filter 40 performs low pass filtering in a frequency band of 0.25 Hz for the intrinsic urine signal as shown in FIG. 5A, thereby unnecessary movement of the test subject as shown in FIG. 5B. Only signals unique to urination that have been removed (Motion Artifact) can be extracted.

The first differential processor 42 detects the instantaneous urinary flow rate (Uroflow Rate) by first processing the low-pass filtered urination signal through the 0.25 Hz low-pass filter 40, which detects a baseline. When the regression curve using the polynomial is used, even the inherent urination signal cannot be ignored, so that the first derivative can proceed to detect the instant urination rate.

The highest urination rate detection unit 44 converts the highest value among the urination patterns detected by the first derivative of the first differential treatment unit 42 into the maximum urinary rate.

Here, as shown in FIG. 5C, the first differential processing unit 42 may extract the urination pattern signal having the highest value by first differentiating the low pass filtered urination signal.

Next, the operation of the present invention made as described above will be described in detail with reference to the flowchart of FIG. 6.

First, when the first to third load cells (2, 4, 6) generates a weight detection signal that detects the weight of the subject performing urination, the first to third operational amplifier (8, 10, 12) The weight detection signal is amplified, and each signal amplified signal is added by the adder 14 and output.

In this state, the 5 Hz low pass filter 16, the 0.1 Hz low pass filter 18, and the 1 Hz low pass filter 20 transmit the weighted signals added by the adder 14 at frequencies of 5 Hz, 0.1 Hz, and 1 Hz, respectively. Low-pass filtering in the band, the differential amplifier 24 is low-pass filtered from the 5Hz low-pass filter 16 receives a signal representing the weight of the test subject including the urination information to the non-inverting input terminal (+) On the other hand, the amplified by receiving a signal representing the average weight of the test subject by the sample / hold processing by the 0.1Hz low-pass filter 18 and the sample / hold circuit 22 to the inverting input terminal (-) As a result, the weight signal according to the minute weight change of the test subject is output (step S10).

Accordingly, the microprocessor 26 digitally converts the weight signal output from the differential amplifier 24 by the analog / digital converter 28 and removes noise by the regression curve using the polynomial in the polynomial calculator 30. In addition to detecting only the urination signal, the local curvature application unit 32 detects the start point and the end point of urination using the local curvature (step S11).

Then, the urination time detection unit 34 of the microprocessor 26 detects the urination time from the difference between the start point and the end point of urination detected by the regional curvature applying unit 32 (step S12), and the amount of urination The detector 36 calculates the voltage difference between the baseline before urination and the baseline after urination according to the start point and end point of urination, and calculates the voltage difference as an average value for a predetermined time such as 5 seconds to detect the amount of urination. (Step S13).

Accordingly, the average urination rate detection unit 38 of the microprocessor 26 detects the average urination amount by calculating the urination time value detected by the urination time detection unit 34 and the urination amount value detected by the urination amount detection unit 36. (Step S14).

Meanwhile, the 0.25 Hz low pass filter 40 of the microprocessor 26 extracts a signal unique to urination by performing low pass filtering in a frequency band of 0.25 Hz, and the first derivative processor 42 performs low pass filtering. The first step of differentially processing the unique signal of urination is to detect the urination pattern of the urination signal, while the maximum urination rate detection unit 44 detects the highest urination rate by converting the highest value among the urination patterns (step S15). .

It is a matter of course that the present invention having the above-described embodiments can be variously modified and implemented without departing from the technical spirit of the present invention without departing from the embodiments.

As described above, according to the present invention, the urine pattern information such as urination time, urination amount and urination rate can be accurately detected by efficiently removing noise components such as unnecessary movement and heartbeat from the weight change state detected during urination of the subject. As a result, the data of the urination pattern can be detected more accurately and simply, and the urination pattern information can be appropriately used for diseases and treatment of the urinary system.

Claims (12)

A weight sensing means for detecting a weight during urination of the test subject and generating a weight signal; Urination signal detection means for detecting a weight signal indicating a slight weight change during urination of the test subject from the weight signal from the weight detection means, and a urination pattern indicating urination time, urination amount and urination rate in the body weight signal from the urination signal detection means; In the urination information detection system having a control processing means for extracting information, The control processing means may include a polynomial calculation unit detecting only a urination signal from which noise during urination is removed from the weight signal by a regression curve using a polynomial; A local curvature applying unit which detects a start point and an end point of urination by applying a local curvature to the urination signal;  An average urination rate extraction unit for extracting data of an average urination rate from the start point and the end point of the urination; And a urination rate extracting unit configured to extract data of the highest urination rate from the start point and the end point of the urination. According to claim 1, wherein the weight sensing means are each installed in a position seated at the time of urination of the test subject to a plurality of load cells for sensing the weight of the subject, and amplifying the weight signals respectively detected from the plurality of load cells And a plurality of operational amplifiers, and an adder for adding and processing the respective weight signals amplified by the plurality of operational amplifiers. The low-pass filter of claim 1, wherein the urination signal detecting means outputs the body weight signal as a body weight signal of a test subject including urination information by low-pass filtering the body weight signal in a frequency band of 5 Hz. 0.1Hz lowpass filter for lowpass filtering in frequency band and output as the average weight signal of the subject, 1Hz lowpass filter for lowpass filtering the body weight signal in frequency band of 1Hz, weight signal from the 0.1Hz lowpass filter A sample / hold circuit for sample / hold processing, and differentially amplify the weight signal from the 5 Hz low pass filter with respect to the weight signal from the sample / hold circuit to output a weight signal having only a minute change value during urination. Urination information detection system comprising a differential amplifier. delete According to claim 1, wherein the average rate of urination extraction unit urination time detection unit for detecting the urination time by the difference value from the start point to the end point of urination, baseline and urination before urination determined by the start point and end point of the urination A urination information detection system comprising a urination amount detection unit for detecting the urination amount by the voltage difference between the baseline and the average urination rate detection unit for calculating data of the urination time and urination amount to detect the data of the average urination rate . 6. The urination information detection system according to claim 5, wherein the urination amount detecting unit is configured to calculate a baseline value during a set time with respect to the voltage difference before and after urination. The method of claim 1, wherein the maximum urination rate extraction unit 0.25Hz low-pass filter for low-pass filtering the urination signal having a starting point and the end point in the frequency band of 0.25Hz, and first differential processing the low-pass filtered urination signal And a first differential processing unit for extracting a urination pattern signal having the highest value, and a maximum urination rate detection unit for converting a maximum value of the urination pattern signal extracted by the first differential processing to detect a maximum urination rate. Urination information detection system. Detecting the weight of the test subject at the time when the test subject performs urination; Detecting a body weight signal having a weight change value generated at the time of urination in the sensed body weight signal; Detecting a start point and an end point of urination from the body weight signal; In the urination information detection method comprising: extracting a urination pattern signal having a urination time, urination amount and urination rate from the start and end of the urination; Detecting the start point and end point of urination from the weight signal, Extracting only the urination signal from which noise is removed by a regression curve using a twentieth polynomial; And applying a local curvature to the urination signal to detect a baseline showing a strong curvature as a start point and an end point. The method of claim 8, wherein the sensing of the weight of the test subject comprises: Detecting weight by a plurality of load cells respectively installed at positions where the test subject rests upon urination, Urination information detection method comprising the step of amplifying and adding the weight signal respectively detected by a plurality of load cells. The method of claim 8, wherein the detecting of the weight signal having the weight change value comprises: Lowpass filtering the weight signal by a 5Hz lowpass filter, a 0.1Hz lowpass filter and a 1Hz lowpass filter, respectively; Sample / hold processing the low pass filtered body weight signal by the 0.1 Hz low pass filter; A weight signal having a minute change value is differentially amplified by differentially amplifying a weight signal output as an average weight signal of a subject by a sample / hold process and a weight signal of a subject including urination information by a 5 Hz low-pass filter. Urination information detection method comprising the step of generating. delete The method of claim 8, wherein the step of extracting the urination pattern signal having the urination time, urination amount and urination rate, Detecting the urination time according to the difference between the start point and the end point of the urination; Detecting the amount of urination by the voltage difference between the baseline before urination and the line after urination by the starting point and the end point, Detecting an average urination rate by calculating the urination time and urination amount; Extracting a signal unique to urination by low pass filtering of a 0.25 Hz low pass filter with respect to the urination signal having a starting point and an end point, Extracting a urination pattern signal by first differentiating the urination characteristic signal; The urination pattern detection method comprising the step of detecting the highest rate of urination by converting the highest value among the signal pattern.

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