KR102415949B1 - Apparatus for bladder condition measurement based on near infrared - Google Patents

Abstract

Disclosed is an apparatus for measuring a bladder condition based on near-infrared rays (NIR). The apparatus for measuring the bladder condition based on the NIR comprises: a first measurement unit, in order to analyze the bladder condition in a time domain (TD) method and a frequency domain (FD) method among optical analysis methods of biological tissues, including one light source for measurement irradiating the bladder of a patient with light for measurement which is multi-wavelength NIR, and one light sensor measuring the first optical characteristics of an optical signal reflected and diffused from the bladder; a second measurement unit, in order to analyze the bladder condition in a multi-distance continuous wave (MD-CW) method among optical analysis methods, including at least one light source for measurement irradiating the bladder with light for measurement, and a plurality of optical sensors disposed to be sequentially away from the light source for measurement to measure the second optical characteristics of an optical signal reflected and diffused from the bladder; and a control unit calculating a first light absorption coefficient and a first light scattering coefficient of the bladder by using the measured first optical characteristics, calculating first physiologic information of the bladder by using the calculated first light absorption coefficient, calculating a second light absorption coefficient and a second light scattering coefficient of the bladder by using the measured second optical characteristics, and calculating second physiologic information of the bladder by using the calculated second light absorption coefficient. The present invention can monitor the bladder condition of the patient in real time.

Description

Apparatus for bladder condition measurement based on near infrared

The present invention relates to a near-infrared-based bladder condition measurement device.

In patients with Spinal Cord Injury, Alzheimer's Disease, Parkinson's Disease, etc., it is difficult to determine when to urinate on your own. Prior to catheterization using a catheter (Catheterization) is performed. Since more than 90% of urine must be excreted in a normal state, catheterization should be performed approximately 4 to 6 times a day, and accordingly, catheterization more than 2000 times a year can be performed.

If such proper catheterization is not performed, 100% of recurrent UTIs occur at least once a year. In addition, bladder stones 49%, sleep neurosis 47%, and vesicoureteral reflux 33% occurred. Furthermore, the main cause of death caused by the failure of proper catheterization was Renal Failure.

If patients with geriatric diseases such as neurogenic bladder and urinary incontinence, or geriatric diseases such as Alzheimer's and Parkinson's, do not feel or feel unclear, catheterization using a catheter can be performed at an appropriate time. can These patients are often unable to self-urethane themselves, so family members have to help, and sometimes they have to wear a urinal. However, if the urinal is kicked, the risk of urinary tract infection increases, and self-catheterization is the method with the least medical side effects. It can be like this, and life becomes a hellish situation, especially for young patients. Self catheterization is performed 4 to 6 times at a regular time, but the amount eaten each day is different for each person, and water intake is different every day.

Even if the number of times catheterized catheterization is reduced to 1 or 2 times a day for these patients, the quality of life of the patient and their family can be surprisingly improved, and the risk of urinary tract infection of the patient can be lowered. It can also be of great help in reducing the complications and mortality of In addition, it is possible to prevent complications that may occur if the nursing hospital fails to manage it on time, and in the case of female diseases such as urinary incontinence, the quality of life of incontinence patients can be improved by predicting the time that may occur when the bladder is somewhat full. It can also be improved.

Therefore, catheter catheterization for patients with neurogenic bladder and female diseases such as urinary incontinence and geriatric diseases such as Alzheimer's Parkinson's is not performed at a set time, but appropriate catheterization according to the amount of urine in the bladder of the patient. In order to inform the timing of self catheterization, a method for monitoring the patient's bladder condition in real time is required.

Republic of Korea Patent Publication No. 10-1431051 (2014.08.11.)

The present invention is an optical analysis method of living tissue, a time domain (TD: Time Domain) method, a frequency domain (FD: Frequency Domain) method, a multi-distance continuous wave (MD-CW) method and a continuous light wave ( By using the Continuous Wave (CW) method in a complex manner, it is possible to measure the amount of residual urine and physiological information in real time, and to provide monitoring information of the bladder according to the measured information in real time in various ways such as alarm or health status information. An object of the present invention is to provide a near-infrared-based bladder condition measurement device.

According to one aspect of the present invention, a near-infrared-based bladder condition measurement device is disclosed.

Near-infrared-based bladder state measuring apparatus according to an embodiment of the present invention, in order to analyze the bladder state in a time domain (TD: Time Domain) method and a frequency domain (FD: Frequency Domain) method among the optical analysis methods of biological tissue, the patient's A first light source for measurement irradiating multi-wavelength near infrared (NIR) measurement light to the bladder, and one optical sensor for measuring the first optical characteristics of the optical signal reflected and diffused from the bladder 1 measurement unit, at least one light source for measurement that irradiates the measurement light to the bladder in order to analyze the bladder condition in a multi-distance continuous wave (MD-CW) method among the optical analysis methods, and the A second measuring unit including a plurality of photosensors disposed sequentially away from the light source for measurement and measuring second optical properties of the optical signals reflected and diffused from the bladder and the measured first optical properties are used. Calculating a first light absorption coefficient and a first light scattering coefficient of the bladder, calculating first physiological information of the bladder using the calculated first light absorption coefficient, and using the measured second optical characteristic and a control unit calculating a second light absorption coefficient and a second light scattering coefficient of the bladder, and calculating second physiological information of the bladder using the calculated second light absorption coefficient.

The physiological information includes content of oxygenated hemoglobin (O2Hb), reduced hemoglobin (HHb), body water (Water), and fat (Lipid).

The first measuring unit irradiates the light for measurement of a preset fast pulse to the bladder, and measures the reflected signal intensity over time from the light signal reflected and diffused from the bladder.

The control unit calculates the first light absorption coefficient and the first light scattering coefficient in a time domain method by using the reflected signal intensity according to the measured time.

The first measuring unit irradiates the measurement light modulated in the form of a sine wave with a light source of 50 to 1,000 MHz frequency to the bladder, and from the optical signal reflected and diffused from the bladder, the phase shift, the modulation depth, and the DC component versus the AC component measure the ratio of

The controller calculates the first light absorption coefficient and the first light scattering coefficient in a frequency domain method using the measured phase shift, modulation depth, and ratio of the DC component to the AC component.

The second measurement unit measures the reflected signal intensity for each wavelength for each of the plurality of optical sensors.

The control unit calculates the second light absorption coefficient and the second light scattering coefficient using an equation using the second light absorption coefficient, the second light scattering coefficient, and the system parameter as unknowns, wherein the second measurement unit includes the unknown In order to generate three equations for the calculation of the solution of

The near-infrared-based bladder condition measuring device includes a plurality of light sources for measurement that irradiate the light for measurement to the bladder and reflection from the bladder in order to analyze the condition of the bladder in a continuous wave (CW) method among the optical analysis methods. and a third measuring unit including a plurality of optical sensors for measuring a third optical characteristic of the diffused optical signal.

The third measurement unit is arranged such that four optical sensors correspond to each light source for measurement to form a plurality of channels.

The control unit calculates a third light absorption coefficient and a third light scattering coefficient of the bladder using the measured third optical characteristic, and obtains third physiological information of the bladder using the calculated third light absorption coefficient Calculate.

The apparatus for measuring bladder status based on near-infrared rays according to an embodiment of the present invention is an optical analysis method of a living tissue, and includes a time domain (TD) method, a frequency domain (FD) method, and a multi-distance continuous light wave (MD-CW) method. : By using the Multi-Distance Continuous Wave method and the Continuous Wave (CW) method in combination, it measures the amount of residual urine and physiological information in real time, and sends the bladder monitoring information according to the measured information to an alarm or health By providing the status information in real time in various ways, it is possible to monitor the bladder status of a patient who does not feel the need to urinate in real time.

1 is a view schematically illustrating the configuration of a near-infrared-based bladder state measuring device according to an embodiment of the present invention.
2 to 18 are views for explaining a near-infrared-based bladder state measuring apparatus according to the embodiment of the present invention of FIG.

As used herein, the singular expression includes the plural expression unless the context clearly dictates otherwise. In this specification, terms such as "consisting of" or "comprising" should not be construed as necessarily including all of the various components or various steps described in the specification, some of which components or some steps are It should be construed that it may not include, or may further include additional components or steps. In addition, terms such as "...unit" and "module" described in the specification mean a unit that processes at least one function or operation, which may be implemented as hardware or software, or a combination of hardware and software. .

Hereinafter, various embodiments of the present invention will be described in detail with reference to the accompanying drawings.

1 is a diagram schematically illustrating the configuration of a near-infrared-based bladder condition measuring device according to an embodiment of the present invention, and FIGS. 2 to 18 are a near-infrared-based bladder condition measuring device according to an embodiment of the present invention in FIG. It is a drawing for explanation. Hereinafter, an apparatus 100 for measuring a bladder state based on near-infrared rays according to an embodiment of the present invention will be described with reference to FIG. 1 , with reference to FIGS. 2 to 18 .

Referring to FIG. 1 , an apparatus 100 for measuring a bladder state based on near-infrared rays according to an embodiment of the present invention includes a first measuring unit 110 , a second measuring unit 120 , a third measuring unit 130 , and an output unit. 140 , the input unit 150 , the communication unit 160 , and the control unit 170 may be included.

The first measurement unit 110 irradiates light for measurement to the bladder of a patient in order to analyze the bladder state in a time domain (TD) method and a frequency domain (FD) method among optical analysis methods of biological tissues. and measure the optical signal reflected and diffused from the patient's bladder.

At this time, for the time domain method, the first measurement unit 110 irradiates light for measurement of a preset fast pulse (eg, 100ps) to the bladder, and reflects over time from the light signal reflected and diffused from the bladder. Signal strength can be measured. In addition, for the frequency domain method, the first measuring unit 110 irradiates a light source of 50 to 1,000 MHz frequency modulated in the form of a sine wave to the bladder, and a phase shift from the optical signal reflected and diffused from the bladder, It is possible to measure the modulation depth and the ratio of the AC component to the DC component.

For example, referring to FIG. 2 , the first measurement unit 110 is formed to completely cover the bladder, and a plurality of measurement elements including one light source 111 for measurement and one optical sensor 115 are arranged. can be formed. Here, the light source for measurement 111 is a light source for measurement 121 is composed of LD (Laser Diode), LED (Light-Emitting Diode) or OLED (Organic Light-Emitting Diode), and the optical sensor 115 is PD ( Photodiode), IR enhanced PD, APD (Avalanche Photodiode), CCD, or CMOS can be configured.

As shown in FIG. 3 , the second measuring unit 120 analyzes the bladder condition by using a multi-distance continuous wave (MD-CW) method among the optical analysis methods of living tissue. At least one light source for measurement 121 irradiating multi-wavelength near infrared (NIR) and the light source 121 for measurement are sequentially disposed away from each other, and the bladder is irradiated by the light source 121 for measurement The wavelength near-infrared light may include a plurality of optical sensors 125 for measuring the reflected signal intensity for each wavelength of the reflected and diffused optical signal from the bladder.

Here, the light source 121 for measurement may irradiate near-infrared rays having a preset irradiation signal intensity for each wavelength according to the control of the controller 170, which will be described later.

For example, the at least one light source for measurement 121 may include a laser diode (LD), a light-emitting diode (LED), or an organic light-emitting diode (OLED). In addition, the plurality of optical sensors 125 may be configured to be sequentially disposed away from the light source 121 for measurement, and each optical sensor 125 may be a photodiode (PD), an IR enhanced PD, an avalanche photodiode (APD) or It can be composed of CCD or CMOS.

For example, referring to FIG. 3 , the second measurement unit 120 according to an embodiment of the present invention may be attached to the skin of the patient's abdomen where the bladder is located. In addition, the light source 121 for measurement provided in the second measurement unit 120 is disposed in the center of the second measurement unit 120, and a plurality of optical sensors ( 125) can be arranged. Thus, as shown in FIG. 3 , the second measurement unit 120 may receive light reflected and diffused from the bladder for measurement.

In order to analyze the bladder condition in a continuous wave (CW) method among the optical analysis methods of biological tissues, the third measurement unit 130 is a multi-wavelength near-infrared (NIR: NIR: A plurality of measurement light sources 131 for irradiating Near Infrared) and a plurality of measurement light sources 131 for measuring the reflected signal intensity for each wavelength of an optical signal reflected and diffused from the bladder by the multi-wavelength near-infrared rays irradiated to the bladder by the measurement light source 131 It may include an optical sensor 135 .

For example, as shown in FIG. 4 , the plurality of light sources for measurement 131 and the plurality of optical sensors 135 are arranged such that a plurality of optical sensors 135 correspond to each other for each light source 131 for measurement. of the channel 133 may be formed. That is, in the third measurement unit 130 shown in FIG. 4 , one channel 133 may be formed by disposing four photosensors 135 around one photosensor 135 as a center. Here, the light source for measurement 131 is composed of a laser diode (LD), a light-emitting diode (LED), or an organic light-emitting diode (OLED), and the light sensor 135 is a PD ( Photodiode), IR enhanced PD, APD (Avalanche Photodiode), CCD, or CMOS can be configured.

The output unit 140 outputs an audible or visual signal. For example, the output unit 140 may display a status indicator lamp and/or a buzzer for displaying operating states such as driving start, measurement, and measurement completion of the near-infrared-based bladder state measurement apparatus 100 according to an embodiment of the present invention. may include

In addition, the output unit 140 may further include a display module (not shown) for displaying and outputting information received or processed by the near-infrared-based bladder state measuring apparatus 100 according to an embodiment of the present invention. That is, the display module includes an analysis result (physiological information, etc.) of the control unit 170, which will be described later, for diffuse optics detected by the optical sensors 115, 125, 135 of the measurement units 110, 120, 130. ) can be printed.

For example, the display module may be implemented as a liquid crystal display or the like. In addition, when the display module and the sensor sensing a touch operation form a layered structure (ie, a touch screen), the display module may be used as an input device in addition to an output device. Hereinafter, when a touch screen is used as a display module, a sensor for detecting a touch operation will be referred to as an input unit 150 to be described later.

The input unit 150 is a user interface for receiving various commands from a user, and there is no particular limitation in its implementation method. For example, the input unit 150 may include a plurality of manipulation units, and these manipulation units may be manufactured as a key pad, a touch pad (static pressure/capacitance), a wheel key, a jog switch, or the like.

The communication unit 160 performs wired/wireless communication with the user terminal.

For example, the communication unit 160 may include a USB (Universal Serial Bus) module, a Bluetooth module, a Wi-Fi module, etc., and may include short-range wireless communication such as Bluetooth or Wi-Fi. Data can be transmitted to a user terminal such as a smart phone or a desktop PC using short-distance wired communication such as USB.

The controller 170 basically controls the overall operation of the near-infrared-based bladder state measuring apparatus 100 according to an embodiment of the present invention.

That is, in the controller 170 , the first measuring unit 110 , the second measuring unit 120 , and the third measuring unit 130 irradiate multi-wavelength near-infrared rays to the bladder of the patient, and the reflected and diffused light from the bladder. A signal is received, and the optical characteristics of the received optical signal are measured for each time domain method, frequency domain method, multi-distance continuous light wave method, and continuous light wave method. Here, the optical characteristics of the received optical signal are measured by the first measuring unit 110 over time, the reflected signal strength, the phase shift, the modulation depth, and the ratio of the AC component to the DC component, and the second measuring unit 120 measures it. It may include the reflected signal intensity for each wavelength, and the reflected signal intensity for each wavelength measured by the third measuring unit 130 .

Then, the control unit 170 calculates the physiological information of the bladder through the analysis of the optical characteristic value of the measured optical signal. Here, the physiological information may include contents of oxygenated hemoglobin (O2Hb), reduced hemoglobin (HHb), body water (Water), and fat (Lipid).

5 shows a concept of analysis of a bladder condition using a time domain method. Referring to FIG. 5 , the time domain method irradiates a preset fast pulse (eg, 100ps) of light for measurement to the bladder, and measures the reflected signal intensity over time from the light signal reflected and diffused from the bladder to measure the medium. A way to understand the characteristics of This method has the advantage of being able to separate the optical characteristics of the bladder (light absorption coefficient μ _a , light scattering coefficient μ' _s ) through a single measurement (one detection element), but the circuit is complicated and expensive, and medical equipment above the handheld level can be implemented with

For example, referring to FIGS. 5 and 6 , the controller 170 may calculate the optical characteristics of the bladder (light absorption coefficient μ _a , light scattering coefficient μ' _s ) according to the time domain method using the following equation. have.

이고,

이고, R_eff는 유효 프레넬 계수이고,

이고, c는 광속으로,

이고, n은 매질의 굴절율이고, ρ는 광원과 광센서 간의 거리이다.Here, z is the distance normal to the boundary,

ego,

and R _eff is the effective Fresnel coefficient,

and c is the speed of light,

, n is the refractive index of the medium, and ρ is the distance between the light source and the photosensor.

7 shows a concept of analyzing a bladder condition using a frequency domain method. Referring to FIG. 7 , in the frequency domain method, a light source with a frequency of 50 to 1,000 MHz irradiates light modulated in the form of a sinusoid to the bladder, and contrasts the phase shift, modulation depth, and DC component from the optical signal reflected and diffused from the bladder. By measuring the ratio of the AC component, optical properties (light absorption coefficient μ _a , light scattering coefficient μ' _s ) can be calculated. This method has the advantage of being able to implement a system at an appropriate cost compared to the time domain method, but it is still complicated and expensive and can be implemented with medical equipment above the handheld level.

For example, referring to FIGS. 7 and 8 , the controller 170 can calculate the optical characteristics of the bladder (light absorption coefficient μ _a , light scattering coefficient μ' _s ) according to the frequency domain method using the following equation. have.

이고,

이고,

이고,

이고,

이고, ρ는 광원과 광센서 간의 거리이다.here,

ego,

ego,

ego,

ego,

and ρ is the distance between the light source and the photosensor.

9 shows an analysis concept of a bladder condition using a multi-distance continuous light wave method. Referring to FIG. 9 , the multi-distance continuous light wave method is similar to the continuous light wave method to be described later, but has a feature that can calculate the optical characteristics of the bladder (light absorption coefficient μ _a , light scattering coefficient μ' _s ) through multiple distances. . This method has the advantage of being able to implement a system at a relatively low cost compared to the time domain method and the frequency domain method, and can be developed as a wearable product because of its simple circuit and easy miniaturization.

For example, referring to FIG. 9 , the controller 170 may calculate the optical characteristics (light absorption coefficient μ _a , light scattering coefficient μ' _s ) of the bladder according to the multi-distance continuous light wave method using the following equation. .

Here, R(ρ) is the reflectance, ρ=(x, y), a' is the albedo indicating the reflectance at the surface, a' = μ' _s / (μ _a + μ' _s ), and , μ _a is the light absorption coefficient, μ' _s is the light scattering coefficient, z ₀ is the distance from the region of interest (ROI) to the measurement surface (the skin surface of the bladder region), z ₀ = (μ _a + μ' _s ) ^-1 , μ _eff is the effective attenuation coefficient, μ _eff = [3 μ _a (μ _a + μ' _s )] ^1/2 , r ₁ is positive from the region of interest As the distance to the positive impulse source of , r ₁ = [(z - z ₀ ) ² + ρ ² ] ^1/2 , and z _b is the core of the Extrapolate boundary condition, which assumes that the flux of photons disappears. is the value of the virtual boundary, r ₂ is the distance from the region of interest to the negative impulse source, r ₂ = [(z + z ₀ + 2z _b ) ² + ρ ² ] ^1/2 , R _exp (ρ) is the experimental value (experimental R) of the reflectance measured in the physiological tissue using the experimental system, and α is the system parameter set in the experimental system.

In Equation 3, the light absorption coefficient μ _a , the light scattering coefficient μ′ _s and the system parameter α are unknown. Since at least three equations are required to calculate the solutions of these three unknowns, at least one light source for measurement 121 and at least three optical sensors 125 are required. That is, by using the reflected signal intensity measured at three points, from Equation 3, three equations for the three unknowns of the light absorption coefficient μ _a , the light scattering coefficient μ' _s and the system parameter α can be generated, From the generated three equations, the values of the unknown light absorption coefficient μ _a , the light scattering coefficient μ′ _s and the system parameter α can be calculated.

On the other hand, in the continuous light wave method, like the time domain method, the frequency domain method, and the multi-distance continuous light wave method described above, the optical characteristics of the bladder (light absorption coefficient μ _a , light scattering coefficient μ′ _s ) cannot be calculated as specific values. That is, since it is impossible to distinguish between the optical properties of the light absorption coefficient μ _a and the light scattering coefficient μ' _s , the bladder condition can be measured with the amount of change, that is, the trend, based on the initial measured value.

For example, referring to FIG. 10 , the controller 170 may calculate the optical characteristics (light absorption coefficient μ _a , light scattering coefficient μ′ _s ) of the bladder according to the continuous light wave method using the following equation.

where r ₁ = [z ₀ ² + ρ ² ] ^1/2 , r ₂ = [(z ₀ + 2z _b ) ² + ρ ² ] ^1/2 , z ₀ = (μ _a + μ' _s ) ^-1 and μ _eff = [3 μ _a (μ _a + μ' _s )] ^1/2 .

As shown in Equation 4, in the continuous light wave method, it is impossible to distinguish between the light absorption coefficient μ _a and the light scattering coefficient μ _{' s} , which are optical properties. As a reference, the light absorption coefficient μ _a can be calculated.

In addition, the controller 170 may calculate physiological information by using the light absorption coefficient μ _a among the optical characteristics (light absorption coefficient μ _a , light scattering coefficient μ′ _s ) of the bladder calculated as described above. That is, the controller 170 may calculate physiological information from the calculated light absorption coefficient μ _a using the following equation.

,

,

및

는 각각 산소 헤모글로빈(O2Hb), 환원 헤모글로빈(HHb), 체수분(Water) 및 지방(Lipid)의 파장별 광소멸계수(extinction rate)이고, [O2Hb], [HHb], [water] 및 [lipid]는 각각 산소 헤모글로빈(O2Hb), 환원 헤모글로빈(HHb), 체수분(Water) 및 지방(Lipid)의 함량이고,

는 파장별 광흡수계수이다.here,

,

,

and

are the extinction rates for each wavelength of oxygenated hemoglobin (O2Hb), reduced hemoglobin (HHb), body water (Water) and fat (Lipid), [O2Hb], [HHb], [water] and [lipid] are the contents of oxygenated hemoglobin (O2Hb), reduced hemoglobin (HHb), body water (Water) and fat (Lipid), respectively,

is the light absorption coefficient for each wavelength.

In Equation 3, the contents of oxygenated hemoglobin (O2Hb), reduced hemoglobin (HHb), body water (Water), and fat (Lipid) can be calculated using the least squares method, and oxygenated hemoglobin (O2Hb) and reduced hemoglobin (HHb) The content of is calculated as an absolute value in mol unit, and the content of body water (Water) and fat (Lipid) can be calculated as a relative value in % unit.

Referring to FIG. 11 , in the near-infrared band, there is a light absorption peak of 85% or more of biological tissue components such as collagen, body water, fat, reduced hemoglobin (HHb), and oxygen hemoglobin (O2Hb). do. Here, reduced hemoglobin (HHb) and oxygen hemoglobin (O2Hb) are blood flow indicators. Therefore, it is possible to measure the amount of urine filled in the bladder by measuring the water content in the bladder, and the blood flow in the bladder can be calculated by measuring the amount of reduced hemoglobin (HHb) and oxygen hemoglobin (O2Hb) in the bladder.

For example, since the light absorption peak of water exists at wavelengths such as 960 nm, 1180 nm, and 1440 nm among the near infrared wavelengths, as shown in FIG. The measuring units 110 , 120 , 130 may be controlled to irradiate.

The controller 170 may output the bladder monitoring information according to the physiological information calculated in this way through the output unit 140 in real time, and transmit it to the user terminal through the communication unit 160 .

For example, FIGS. 12 to 15 show monitoring information on bladder urine volume in the time domain method, the frequency domain method, and the multi-distance continuous light wave method. Referring to FIG. 12 , the plurality of optical sensors 115 and 125 may be divided into a plurality of zones (Zone1 to Zone 8) such that at least one optical sensor overlaps. And, as shown in the table below, the body water content of the bladder indicating the amount of urine for each divided area may be calculated, output, and transmitted.

The controller 170 may display and output whether the bladder is half or completely filled with urine as shown in FIG. 13 by using the body water content calculated for each region.

The table below shows the body water content calculated for each area when the bladder is half full of urine.

The table below shows the body water content calculated for each area when the bladder is completely filled with urine.

And, FIG. 14 is a 3D analysis graph of the bladder according to Table 2, and FIG. 15 is a 3D analysis graph of the bladder according to Table 3. Referring to FIG. 14 , when the bladder is moderately filled with urine, it can be seen that the upper value is low and the lower value is high based on the patch of the graph of FIG. 14 . Through this, it is possible to estimate the shape of the bladder inflated. And, referring to FIG. 15 , when the bladder is full of urine, it can be seen that both the upper and lower values of the patch in the graph of FIG. 15 are high, but the upper one is lower than the lower one.

Meanwhile, FIGS. 16 to 18 show monitoring information on the amount of urine in the bladder in the case of the continuous light wave method. Monitoring information for bladder urine output in the case of continuous light wave method, as shown in FIGS. 16 to 18, monitoring of bladder urine volume in the time domain method, frequency domain method, and multi-distance continuous light wave method described above It can be expressed similarly to information. That is, in the case of the continuous light wave method, the body water content of the bladder indicating the amount of urine for each channel is calculated, and a figure and/or a three-dimensional analysis graph of the bladder can be calculated from this. Here, FIG. 16 shows a case where the bladder is slightly filled with urine, FIG. 17 shows a case where the bladder is half full of urine, and FIG. 18 shows a case where the bladder is completely filled with urine.

The above-described embodiments of the present invention have been disclosed for purposes of illustration, and various modifications, changes, and additions will be possible within the spirit and scope of the present invention by those skilled in the art having ordinary knowledge of the present invention, and such modifications, changes and additions should be regarded as belonging to the following claims.

100: near-infrared based bladder condition measurement device
110: first measuring unit
120: second measurement unit
130: third measurement unit
140: output unit
150: input unit
160: communication department
170: control unit

Claims (11)

In the near-infrared-based bladder condition measurement device,
Among the optical analysis methods of biological tissue, to analyze the bladder condition in the time domain (TD) method and the frequency domain (FD) method, for measuring multi-wavelength near infrared (NIR) to the patient's bladder a first measuring unit including one measuring light source irradiating light and one optical sensor measuring a first optical characteristic of an optical signal reflected and diffused from the bladder;
In order to analyze the bladder condition in a multi-distance continuous wave (MD-CW) method among the optical analysis methods, at least one light source for measurement that irradiates the light for measurement to the bladder and the light source for measurement a second measurement unit disposed to be apart in sequence and including a plurality of optical sensors for measuring second optical characteristics of the optical signal reflected and diffused from the bladder;
In order to analyze the bladder condition in a continuous wave (CW) method among the optical analysis methods, a plurality of light sources for measurement irradiating the light for measurement to the bladder and a third optical signal reflected and diffused from the bladder a third measuring unit including a plurality of photosensors for measuring characteristics; and
A first light absorption coefficient, a first light scattering coefficient, a second light absorption coefficient, a second light scattering coefficient, and a third light absorption coefficient of the bladder using the measured first optical characteristic, the second optical characteristic, and the third optical characteristic and calculating a third light scattering coefficient, and using the calculated first light absorption coefficient, the second light absorption coefficient, and the third light absorption coefficient, the bladder first physiological information, the second physiological information, and the third physiological information Including a control unit for calculating academic information,
The control unit is
Calculating the first light absorption coefficient and the first light scattering coefficient according to the time domain method using the following equation,

Here, z is the distance normal to the boundary,

ego,

and R _eff is the effective Fresnel coefficient,

and c is the speed of light,

, n is the refractive index of the medium, and ρ is the distance between the light source and the photosensor
Calculating the first light absorption coefficient and the first light scattering coefficient according to the frequency domain method using the following equation,

here,

ego,

ego,

ego,

ego,

and ρ is the distance between the light source and the light sensor
Calculating the second light absorption coefficient and the second light scattering coefficient according to the multi-distance continuous light wave method using the following equation,

Here, R(ρ) is the reflectance, ρ=(x, y), a' is the albedo indicating the reflectance at the surface, a' = μ' _s / (μ _a + μ' _s ), and , μ _a is the light absorption coefficient, μ' _s is the light scattering coefficient, z ₀ is the distance from the region of interest (ROI) to the measurement surface (the skin surface of the bladder region), z ₀ = (μ _a + μ' _s ) ^-1 , μ _eff is the effective attenuation coefficient, μ _eff = [3 μ _a (μ _a + μ' _s )] ^1/2 , r ₁ is positive from the region of interest As the distance to the positive impulse source of , r ₁ = [(z - z ₀ ) ² + ρ ² ] ^1/2 , and z _b is the core of the Extrapolate boundary condition, which assumes that the flux of photons disappears. is the value of the virtual boundary, r ₂ is the distance from the region of interest to the negative impulse source, r ₂ = [(z + z ₀ + 2z _b ) ² + ρ ² ] ^1/2 , R _exp (ρ) is the experimental value (experimental R) of reflectance measured in physiological tissues using the experimental system, and α is the system parameter set in the experimental system.
Calculating the third light absorption coefficient and the third light scattering coefficient according to the continuous light wave method using the following equation,

where r ₁ = [z ₀ ² + ρ ² ] ^1/2 , r ₂ = [(z ₀ + 2z _b ) ² + ρ ² ] ^1/2 , z ₀ = (μ _a + μ' _s ) ^-1 and μ _eff = [3 μ _a (μ _a + μ' _s )] ^1/2
The third measuring unit is arranged such that four optical sensors correspond to each light source for measurement to form a plurality of channels,
The third light absorption coefficient is a near-infrared-based bladder state measuring device, characterized in that calculated based on a third light scattering coefficient set to an arbitrary constant.
According to claim 1,
The physiological information is a near-infrared based bladder state measuring device, characterized in that it includes the content of oxygenated hemoglobin (O2Hb), reduced hemoglobin (HHb), body water (Water) and fat (Lipid).
According to claim 1,
The first measuring unit irradiates the measurement light of a preset fast pulse to the bladder, and measures the reflected signal intensity over time from the optical signal reflected and diffused from the bladder.
4. The method of claim 3,
The control unit calculates the first light absorption coefficient and the first light scattering coefficient in a time domain method using the reflected signal intensity according to the measured time.
According to claim 1,
The first measuring unit irradiates the measurement light modulated in the form of a sine wave with a light source of 50 to 1,000 MHz frequency to the bladder, and from the optical signal reflected and diffused from the bladder, the phase shift, the modulation depth, and the DC component versus the AC component Near-infrared-based bladder condition measuring device, characterized in that for measuring the ratio of.
6. The method of claim 5,
The control unit calculates the first light absorption coefficient and the first light scattering coefficient in a frequency domain method using the measured phase shift, modulation depth, and the ratio of the DC component to the AC component. Device.
According to claim 1,
The second measurement unit near-infrared-based bladder state measuring device, characterized in that for measuring the intensity of the reflected signal for each wavelength for each of the plurality of optical sensors.
According to claim 1,
The control unit calculates the second light absorption coefficient and the second light scattering coefficient by using an equation in which the second light absorption coefficient, the second light scattering coefficient, and the system parameter are unknown,
The second measuring unit, to generate three equations for calculating the solution of the unknown, near-infrared-based bladder state measuring device, characterized in that it comprises at least three optical sensors.
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