JP2013039158A - Urination detecting device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a urination detecting device for highly accurately measuring urination quantity to an absorbent article such as a diaper and a urination collecting pad.SOLUTION: An electrostatic capacity sensor sheet 1 has a film 1a and a plurality of electrodes 1b formed in one surface of the film 1a. A plurality of sensor elements are constituted by connecting each of electrodes 1b by leads and having electrode rows arranged in a plurality of rows. The electrode distance in the row direction in the electrode rows is in the range of 20 to 55 mm, the electrodes has a rectangular shape present in a rectangular shape from 15 to 35 mm. Such an electrostatic capacity sensor sheet 1 is attached to the outside surface of the absorbent article. The absorbent part of the absorbent article has a polymer quantity capable of absorbing urine of a centrifugal holding quantity of at least 350 g. The electrostatic capacity sensor sheet 1 detects impedance change between the electrodes by each of the sensor elements and detects the urination in the absorbent article such as the urine collecting pad.

Description

  The present invention relates to a urination detection device, and more particularly, to a urine detection device that measures the amount of urination to an absorbent article such as a diaper and a urine collection pad.

  Diapers are used for care of bedridden caregivers and urinary incontinence, and diapers are used at predetermined times or every fixed time because the need for changing diapers cannot be communicated to caregivers. Have been replaced.

  However, since the interval between urinations and the amount of urination per time cannot be accurately grasped, caregivers need to change diapers at regular intervals, and the internal situation cannot be grasped without opening the diapers. Often, caregivers who are not fully urinating will also need to open and reapply diapers. For this reason, unnecessary work is generated for the caregiver, and the care receiver is more than necessary to check the diaper, which is a mental burden.

  On the other hand, Patent Document 1 describes an excretion monitoring device that detects an excretion state of a diaper based on a change in capacitance between a pair of conductors positioned outside a diaper absorber. Has been.

  Patent Document 2 proposes a technique for detecting the amount of excretion in an absorbent article based on a plurality of sensor outputs.

JP 2000-185067 A JP 2002-224093 A

  However, with the technique of Patent Literature 1, it is possible to detect the presence or absence of urination, but it is difficult to accurately grasp the amount of urination. On the other hand, in the technique of Patent Document 2, it is possible to detect the amount of urination (excretion amount), but it is considered to measure a plurality of times of urination at a normal adult urination amount of about 150 g. Therefore, when it is applied to an absorbent article that supports multiple urinations, there is a problem that the measurement accuracy of the urination amount is lowered. Even with the technique of Patent Document 2, it has been difficult to measure the urination interval, the amount of urination, the urination rate, etc. of the care recipient.

  On the other hand, in the aging society, self-support for the caregiver's excretion is required. However, it is difficult to support self-support only by detecting urination or simply detecting the amount of urination. Yes, there is a need for support such as grasping urination intervals, urination volume, number of urinations per day, etc., calling out for independence at an appropriate timing, and guiding to the toilet. In addition, if the care recipient's urination rate, urination interval, etc. can be grasped, the cause of dysuria can be diagnosed, and the means for supporting independence of excretion can be improved. Therefore, there is a need for a urination detection device that can measure the urination amount to the absorbent article with high accuracy, which can measure the urination rhythm and urination history, instead of simply detecting the urination timing and urination amount.

  An object of the present invention is to provide a urine detection device that measures the amount of urination to an absorbent article such as a diaper and a urine collecting pad with high accuracy.

  One aspect of the present invention is an absorbent article that absorbs urination, and includes a plurality of electrode rows in which a plurality of electrodes are arranged on the outer surface opposite to the side that touches the user's skin, and impedance between the plurality of electrodes An urination detection device for detecting urination based on a change, wherein the absorbent part of the absorbent article has a polymer amount capable of absorbing urine of a centrifugal holding amount of 350 g or more, and electrodes in the column direction in the electrode array The interval is 20 to 55 mm.

  As described above, by using an appropriate combination of the electrode spacing in the column direction and the polymer amount in the electrode row, even if the amount of urination increases, the measurement accuracy is high, so not only the amount of urination once but also the urination interval It is possible to measure urination time and urine flow rate (urination rate), and to evaluate bladder function and dysuria.

  The electrode has a shape in a rectangle of 15 to 35 mm. Thereby, the amount of urination can be detected with high accuracy.

The centrifugal holding amount per unit area of the absorbent part of the absorbent article is 5000 to 8000 g / m ² . As a result, the measurement accuracy is high even when the amount of urination increases while making it possible to measure multiple urinations. Therefore, not only can the interval between urinations be measured, but also the urination time and urine flow rate (urination rate) can be measured more accurately. The amount of urination can be detected.

  The length from one end of the electrode array to the other end is 75% or more and 100% or less of the length in the longitudinal direction of the absorbent portion of the absorbent article. Thereby, the amount of urination can be detected with high accuracy.

  ADVANTAGE OF THE INVENTION According to this invention, the urination detection apparatus which measures the amount of urination to absorbent articles, such as a diaper and a urine picking pad, with high precision can be provided.

It is a figure which shows the structural example of the electrostatic capacitance sensor sheet | seat which concerns on this invention. It is a block diagram which shows the structural example of the urination detection apparatus to which this invention is applied. It is a block diagram which shows the detailed structural example of a data collection part. It is a block diagram which shows the detailed structural example of an information processing part. It is a figure for demonstrating the mounting method of the diaper to which the electrostatic capacitance sensor sheet was attached. It is a figure which shows the cross section of the user who mounted | wore with the diaper. It is a figure explaining the principle of the urination sensor of an electrostatic capacitance sensor sheet. It is a figure which shows a mode that artificial urine spreads when artificial urine is inject | poured for every fixed amount. It is a scatter diagram which shows the relationship between a capacitance sensor output variation | change_quantity and an artificial urine spreading area. It is a figure which shows typically artificial urine spread at the time of inject | pouring artificial urine for every fixed amount. FIG. 11 is a scatter diagram showing the relationship between the artificial urine injection amount and the capacitance sensor output change amount under the measurement conditions in FIGS. 10 (a) and 10 (b). FIG. 11 is a scatter diagram showing the relationship between the artificial urine injection amount and the capacitance sensor output change amount under the measurement conditions in FIGS. 10 (b) and 10 (c). It is a figure which shows the example of an electrode pattern. It is a figure which shows the example of another electrode pattern. It is a scatter diagram which shows the relationship between the amount of artificial urine injection using several electrode patterns, and an electrostatic capacitance sensor output variation | change_quantity. It is a figure which shows some Examples which measured the electrostatic capacitance sensor output variation | change_quantity using the electrode pattern. It is a figure which shows the measurement result obtained by the measuring method of the centrifugal holding amount of an absorbent article. It is a scatter diagram which shows the relationship between the artificial urine injection amount in the measurement conditions in FIG. 16, and an electrostatic capacitance sensor output variation | change_quantity. It is a scatter diagram which shows the relationship between an electrode space | interval and the amount of centrifugation holding | maintenance. It is a figure which shows arrangement | positioning of the electrode used when examining the definition of an electrode space | interval. It is a figure which shows an example of electrode space | interval d '. It is a figure which shows another example of electrode space | interval d '. It is a scatter diagram which shows the relationship between a capacitance sensor output variation | change_quantity at the time of performing the measurement which inject | pours artificial urine every 5g or 10g in 1 second using the measurement conditions of Example 1. FIG. It is a scatter diagram which calculates the urine flow rate per second using the measured value in FIG. 23, and shows the relationship between the calculated urine flow rate and time.

  The present invention includes a plurality of electrode rows in which a plurality of electrodes are arranged on the outer surface of the absorbent article opposite to the side touching the user's skin. The plurality of electrode rows may be provided on the outer surface opposite to the side that touches the user's skin of the absorbent part of the absorbent article. However, as shown in FIG. The sensor sheet is preferably provided on the outer surface opposite to the side of the absorbent part of the absorbent article that touches the user's skin.

  The capacitance sensor sheet 1 has a film 1a and a plurality of electrodes 1b provided on one surface of the film 1a. The plurality of electrodes 1b may be bonded to one surface of the film 1a, may be sewn, and preferably fixed. Each of the plurality of electrodes 1b is connected by a conductive wire, and includes a plurality of arranged electrode rows to constitute a plurality of sensor elements. Each sensor element detects an impedance change between the positive electrode and the negative electrode. It should be noted that the number of sensor elements may or may not correspond to the number of positive electrodes.

ここで、ａ１／２は、一つの電極において、列方向に直行する直線によって、電極の面積を分割した場合の一方の領域における重心から、列方向における近接する端部までの距離を意味する。電極の形状が矩形の場合には、列方向における長さの１／４に相当する。なお、離間距離ｄは、電極列の列方向における隣り合う電極の端部同士の距離であって、電極の形状によらず、０より大きい距離であって、５０ｍｍより小さい距離である。電極の形状が概ね矩形である場合には、複数回の排尿や多量の排尿に対する測定精度向上の観点から１０〜４５ｍｍであることが好ましく、１２〜４０ｍｍであることがより好ましい。 In the present invention, the electrode spacing in the column direction in the electrode rows is 20 to 55 mm, and more preferably 25 to 55 mm, from the viewpoint of improving measurement accuracy for multiple urinations and large amounts of urination. The electrode interval d ′ of the present invention has an area of 4 or the like by a straight line perpendicular to the electrode row as shown in FIG. 20 when the distance between the opposing ends of adjacent electrodes in the column direction is a separation distance d. In this case, when the distance from the electrode end to the straight line having an area of ¼ is a1 / 2 and a2 / 2, respectively, the sum of these is defined as the electrode interval d ′.
That is, the electrode interval is expressed by the following formula (1).

Here, a1 / 2 means a distance from the center of gravity in one region to the adjacent end in the column direction when the area of the electrode is divided by a straight line orthogonal to the column direction in one electrode. When the shape of the electrode is rectangular, it corresponds to ¼ of the length in the column direction. The separation distance d is the distance between the ends of adjacent electrodes in the column direction of the electrode rows, and is a distance greater than 0 and less than 50 mm regardless of the shape of the electrodes. When the shape of the electrode is generally rectangular, it is preferably 10 to 45 mm, more preferably 12 to 40 mm, from the viewpoint of improving measurement accuracy for multiple urinations or a large amount of urination.

  In the example of FIG. 1, the electrodes 1b are two-dimensionally arranged in 6 rows × 2 columns, and each electrode has a rectangular shape. The electrodes adjacent to each other in the column direction in the electrode rows are arranged in the order of positive electrode, negative electrode, positive electrode, and so on. On the other hand, it may be disposed in a positive electrode relationship, or may be disposed in a positive electrode with respect to the positive electrode and a negative electrode with respect to the negative electrode. From the viewpoint of reducing errors due to operation, it is preferable to dispose the positive electrode with respect to the positive electrode and the negative electrode with respect to the negative electrode. A positive potential is applied to the positive electrode, and the negative electrode is grounded.

  The material of the capacitance sensor sheet 1 is not limited to the film 1a, and may be, for example, a nonwoven fabric or a flexible substrate.

  The capacitance sensor sheet 1 having the above-described configuration is an outer surface of an absorbent article such as a urine absorbing pad (herein referred to as a urine removing pad) that absorbs excrement such as urine or stool of an elderly person or an infant. The excretion amount of excrement attached to the film side and absorbed by the urine collecting pad (in the present embodiment, in particular, the urination amount due to urination) is detected by a plurality of sensor elements. Note that the output interval of data detected by the sensor element is preferably 0.1 second to 3 minutes, more preferably less than 3 seconds, and even more preferably 1 second or less. Moreover, it is preferable that it is 5 to 10 hours, it is preferable that it is 6 to 9 hours, and it is 6 to 8 hours. Is more preferable. By measuring the measurement interval and measurement time, it is possible to measure multiple urinations, and the data of urination frequency, urination volume and rate, and urination interval related to the user's urination pattern can be obtained. It can be obtained more accurately.

  The urine removing pad is inserted into a tape diaper (a diaper to which a magic tape (registered trademark) is attached) inside (excretion site), and is used in an overlapping manner. That is, as described above, the capacitance sensor sheet 1 is attached to the outer surface opposite to the side of the urine removing pad that touches the user's skin. Therefore, when replacing the urine removal pad, it is only necessary to remove the capacitance sensor sheet 1 from the urine collection pad after use, and it is easy to attach it to a new urine collection pad. Yes, environmental impact is reduced. Examples of the user include a cared person, a subject for urination pattern inspection, a subject for urination support, and the like.

  The capacitance sensor sheet 1 can be fixed to the inside of the tape diaper or sandwiched between the urine removing pad and the tape diaper. It is preferable to attach or fix to the urine absorbing pad from the viewpoint of maintaining and improving the target positional relationship.

[Configuration of urination detection device of the present invention]
FIG. 2 is a block diagram illustrating a configuration example of the urination detection device 10 to which the present invention is applied. The urination detection device 10 includes a capacitance sensor sheet 1, data collection means 11, and information processing means 12. A usage example of the capacitance sensor sheet 1, the data collection unit 11, and the information processing unit 12 will be described later with reference to FIG.

  The entire circuit including the capacitance sensor sheet 1 is applied with a rectangular wave voltage of 400 to 600 kHz from the voltage control means 21 (FIG. 3), and the impedance change between the electrodes by each sensor element is the voltage control means 21. Detected by. Then, the impedance change between the electrodes per unit time is converted into a capacitance sensor output proportional to the voltage value in the voltage control means 21.

  The data collection means 11 is connected to the capacitance sensor sheet 1 via a cable (not shown), and is attached to the outer surface on the opposite side to the skin side of the user of the tape diaper. The voltage control means 21 (FIG. 3) of the data collection means 11 collects the change in impedance detected via the capacitance sensor sheet 1 as a capacitance sensor output proportional to the voltage value.

  Moreover, the data collection means 11 of this invention has the acceleration sensor 22 (FIG. 3) with the voltage control means 21. FIG. The acceleration sensor 22 detects the posture of the user wearing the diaper by detecting (collecting) accelerations in the X-axis direction, the Y-axis direction, and the Z-axis direction due to the displacement of the user.

  The information processing means 12 is, for example, a computer and includes a CPU (Central Processing Unit), a ROM (Read Only Memory), a RAM (Random Access Memory), a HDD (Hard Disk Drive), and the like. Collected data is acquired, and urination volume, urination rate, and urine flow rate are calculated. Details of the calculation method from the data collected by the data collection means 11 will be described later.

  FIG. 3 is a block diagram illustrating a configuration example of the function of the data collection unit 11. The data collection unit 11 includes a voltage control unit 21 and a data logger 23 and includes an acceleration sensor 22.

  The voltage control means 21 forms a bridge circuit with the impedance Zx between electrodes of the electrostatic capacitance sheet 1 and impedance elements Z1 to Z3 whose resistance values are known, and applies the output voltage of the oscillation circuit to the input terminal of the bridge circuit. Then, a differential voltage between the divided voltage by the impedance elements Z1 and Z2 and the divided voltage by the impedance element Z3 and the impedance Zx between the electrodes is detected, and a voltage signal having a voltage value corresponding to the magnitude of the impedance Zx is obtained. Output to the data logger 22. In the present invention, it is preferable to output and store the capacitance sensor output, which is a value proportional to the voltage signal of the voltage value corresponding to the magnitude of the impedance Zx, to the data logger 23 every unit time. The unit time is preferably 0.1 to 3 seconds, and more preferably 0.1 to 1 second.

  The acceleration sensor 22 detects the posture of the user wearing the diaper, and detects (collects) accelerations in the X-axis direction, the Y-axis direction, and the Z-axis direction, and the detection result is data collection means. 11 data loggers 23.

  The data logger 23 is an electronic measuring instrument that stores data acquired from the voltage control means 21 and the acceleration sensor 22. The data logger 23 transfers the stored data to the information processing means 12 in response to a request from the information processing means 12 or when it is detected that the data logger 23 is connected to the information processing means 12.

  FIG. 4 is a block diagram illustrating a configuration example of functions of the information processing means 12. The information processing unit 12 includes a data acquisition unit 31, a urination amount calculation unit 32, a urination rate calculation unit 33, and a urine flow rate calculation unit 34.

  When the data acquisition unit 31 is connected to the data collection unit 11 via a cable, the data acquisition unit 31 acquires the data stored in the data logger 23 of the data collection unit 11, and sends it to the urination amount calculation unit 32 and the urination rate calculation unit 33. Supply.

  The urine output calculating unit 32 calculates the urine output based on the data acquired from the data acquiring unit 31. The urination speed calculation means 33 calculates the urination speed based on the data acquired from the data acquisition means 31 and supplies the calculation result to the urine flow rate calculation means 34. The urine flow rate calculation unit 34 calculates the urine flow rate based on the calculated value of the urination rate acquired from the urination rate calculation unit 33.

  According to the urination detection device 1 configured as described above, when urination is present in the diaper, the impedance of the sensor element of the capacitance sensor sheet 1 corresponding to the portion where urination has occurred is significantly changed. Since the voltage control means 21 of the data collection means 11 outputs a voltage signal of the total amount of changes in impedance of the plurality of sensor elements, the urine output calculating means 32 of the information processing means 12 accurately calculates the urine output by calculation. Can be obtained.

<How to wear diapers>
FIGS. 5A to 5C are views for explaining a method of attaching the diaper to which the capacitance sensor sheet 1 is attached.

  As shown in FIG. 5 (a), the capacitance sensor sheet 1 has a urine collecting pad 41 that is the outer side of the urine removing pad 41 opposite to the side that touches the skin of the user (usually a cared person). It is preferable that the electrode 1b of the capacitance sensor sheet 1 is attached to the surface on the waterproof film side so as to contact. In this case, the urine collecting pad 41 to which the capacitance sensor sheet 1 is attached is, as shown in FIG. 5B, a holding means for the user, for example, a tape diaper 51 to which magic tapes 51a and 51b are attached. Arranged along the inner surface of the. At this time, the capacitance sensor sheet 1 is disposed so as to be sandwiched between the tape diaper 51 and the urine pad 41.

  As shown in FIG. 5C, the tape diaper 51 on which the capacitance sensor sheet 1 and the urine collecting pad 41 are arranged is attached to the user and is a velcro tape 51a, 51b which is a holding means for the user. Fixed. And the electrostatic capacitance sensor sheet | seat 1 and the data collection means 11 are connected via a cable, and the data collection means 11 is attached to the outer surface of the tape diaper 51. The method of attaching the data collecting means 11 is not particularly limited, but it is preferable that the data collecting means 11 is attached to the end of the tape diaper 51 near the abdomen by a fixing means such as a clip or a velcro tape.

  Since the acceleration sensor 22 is built in the data collecting means 11, it is important to correctly attach it to the tape diaper 51 with a fixing means such as a clip or a velcro tape, thereby correctly detecting the posture of the user. Can do.

  When the diaper is replaced, the data collecting unit 11 is connected to the information processing unit 12 so that the data can be transferred during the diaper replacement.

  FIG. 6 schematically shows the XX cross section of the user when the tape diaper 51 shown in FIG. 5 is mounted, and the positional relationship between the human body, the urine collecting pad 41, the capacitance sensor sheet 1, and the tape diaper 51. FIG.

  As shown in FIG. 6, the capacitance sensor sheet 1 is arranged outside the urine collecting pad 41, and the tape diaper 51 is arranged outside the capacitance sensor sheet 1. Thereby, it becomes possible for the tape diaper 51 to press the capacitance sensor sheet 1 and the urine collecting pad 41 to bring the urine collecting pad 41 into contact with the user and fix it, and the user stands or sits down. However, an error in the amount of change in impedance can be suppressed, and the measurement accuracy of the amount of urination can be further improved.

  As described above, by disposing the capacitance sensor sheet 1 on the outer surface of the urine collecting pad 41, it becomes possible to repeatedly measure the amount of urination and the like. Further, since the capacitance sensor sheet 1 is sandwiched between the urine pad 41 and the tape diaper 51, the capacitance sensor sheet 1 can be used repeatedly without touching the skin directly. Discomfort to the user can be reduced. Furthermore, it is preferable to provide a cut-out or cut-out portion in the center of the capacitance sensor sheet 1 so as not to touch the electrode from the viewpoint of reducing a sense of discomfort when the user's foot is closed. Further, since the data collection means 11 is not always connected to the information processing means 12, the user can move freely.

  In addition, although the tape diaper 51 was used, it does not necessarily need to be the tape diaper 51, for example, a pants-type wearing article may be sufficient.

  The total length of the electrode array of the present invention is preferably 75% or more, more preferably 78% or more of the length in the longitudinal direction of the absorption part from the viewpoint of detecting the spread of urination in the absorption part in a wider range. preferable.

The absorbent part of the absorbent article of the present invention (for example, the urine collecting pad 41) has a polymer amount capable of absorbing 350 g or more of urine, and preferably the amount of centrifugal retention per unit area of the absorbent part is a 5000~8000g / ^{m 2,} preferably 5000~7500g / ^{m 2.} In addition, the centrifugal retention amount (amount of urination that can be absorbed) of the absorption part of the present invention is 350 g or more and preferably 800 g or less.

<Principle of urination sensor>
FIG. 7 is a diagram for explaining the principle of the urination sensor of the capacitance sensor sheet 1.

  As shown in FIG. 7, capacitors C1 to C7 are formed between the electrodes 1b, respectively. That is, the capacitor C is formed between all the electrodes.

For example, when urine is discharged at the position of the urine collecting pad 41 corresponding to the position where the capacitor C4 is formed, the capacitance of the capacitor C4 changes (formed on the outer surface of the portion of the urine collecting pad 41 that has absorbed urine. The capacitance of the capacitor C4 to be changed changes). Here, the capacitance is expressed by the following equation (2). ε ₀ is the vacuum dielectric constant (constant: 8.854 × 10 ⁻¹² ), ε _S is the relative dielectric constant, A is the area of the electrodes, and d is the distance between the electrodes. The relative dielectric constant of air is 1, and the relative dielectric constant of water is 80.
Capacitance C = ε ₀ · ε _S · A / d (2)

  From the above equation (2) and the change in relative permittivity (change from 1 to 80), the capacitance of the capacitor C4 changes 80 times. Further, as shown at the end of the arrow A1, when urine is discharged at the position of the urine collecting pad 41 corresponding to the position where the capacitors C1 to C4 are formed, the capacitance of the capacitors C1 to C4 is increased by 80 times. Change.

  As described above, by measuring the change in the capacitance, the spread of urination in the urine collecting pad 41 can be calculated, and urine volume data can be obtained.

<Calculation of urine spreading area>
The present applicant attaches the capacitive sensor sheet 1 to the doll as shown in FIG. 5 and places the capacitive sensor sheet 1 on his / her back so that the urine collecting pad 41 on which the capacitive sensor sheet 1 is attached has a normal human urination part on the doll side surface. The discharge port of the tube was arranged in the region corresponding to, and the artificial urine spreading area was calculated when artificial urine (for example, physiological saline) was injected into the region corresponding to the urination part by a certain amount through the tube.

  FIGS. 8A to 8E are diagrams showing how artificial urine spreads when a certain amount of artificial urine is injected in the vicinity of the urination portion on the urine collecting pad 41. FIG. FIG. 8A shows the urine spread when 50 g of artificial urine is injected, FIG. 8B shows the artificial urine spread when 100 g of artificial urine is injected, and FIG. The urine spread when 150 g of artificial urine is injected is shown, FIG. 8 (d) shows the artificial urine spread when 200 g of artificial urine is injected, and FIG. 8 (e) is injected with 250 g of artificial urine. In case of artificial urine spread.

  As can be seen from FIGS. 8A to 8E, the artificial urine spreading area gradually increases as the artificial urine injection amount increases.

FIG. 9 is a scatter diagram showing the relationship between the capacitance sensor output change amount and the artificial urine spreading area. In FIG. 9, the vertical axis represents the capacitance sensor output change amount, and the horizontal axis represents the artificial urine spreading area (cm ² ). Capacitance sensor output change amount (total change amount of impedance change between electrodes by each sensor element) is the voltage output when there is no artificial urine amount obtained by the voltage control means 21 and the voltage when artificial urine is injected. The value related to the voltage output obtained by the control means 21 is represented.

  In FIG. 9, P1 is plotted based on the measured value of the change amount of the capacitance sensor output obtained from the artificial urine spreading area shown in FIG. 8A, and P2 is plotted in FIG. 8B. P3 is plotted based on the measured value of the capacitance sensor output change obtained by the artificial urine spreading area, and P3 is the capacitance sensor output change obtained by the artificial urine spreading area of FIG. P4 is plotted based on the measurement value of the capacitance sensor output change obtained by the artificial urine spreading area of FIG. 8 (d), P5 is plotted based on the measured value of the change amount of the capacitance sensor output obtained from the artificial urine spreading area of FIG.

  As can be seen from the relationship between the capacitance sensor output change amount and the artificial urine spread area shown in FIG. 9, the capacitance sensor output change amount increases in proportion to the increase in the artificial urine spread area.

  That is, if a change in the output amount of the capacitance sensor is detected, the urine spreading area can be calculated and converted into the urine output.

<Electrode pattern of urination sensor>
The present applicant prepares several electrode patterns of the capacitive sensor sheet 1, prepares several urine collecting pads 41 having different absorption performances, and attaches the capacitive sensor sheet 1 to the doll as shown in FIG. The discharge port of the tube is arranged in a region corresponding to a normal human urine discharge portion on the doll-side surface of the urine collecting pad 41 to which the capacitance sensor sheet 1 is attached, and artificial urine is passed through the tube. The amount of change in capacitance sensor output was measured when a fixed amount was injected into the region corresponding to the urination portion.

  FIGS. 10A to 10C show the doll-side surface of the urine pad 41 on which the capacitance sensor sheet 1 is mounted on the back and the capacitance sensor sheet 1 is attached to the doll. In the region corresponding to the normal human urination portion, the discharge port of the tube is arranged, and when the artificial urine is injected into the region corresponding to the urination portion by a certain amount through the tube, the artificial urine spreads in the urine collecting pad 41 It is a figure which shows a mode typically.

  FIG. 10A shows that the shape of the electrode 1b of the capacitance sensor sheet 1 is 25 mm × 25 mm, the separation distance in the column direction (lateral direction in the figure) in the electrode column is 50 mm, and between the electrode column and the electrode column (in the drawing) This is an electrode pattern in which the distance between the electrodes in the vertical direction is 20 mm. Here, the electrode separation distance refers to the distance from one end of the adjacent electrodes to the other end. In the present embodiment, the measurement results when artificial urine 50 g, 100 g, and 150 g are injected using the urine collecting pad 41 capable of absorbing urine equivalent to 150 g three times are shown. In the present embodiment, description will be made assuming that the amount of urination once is about 150 g.

  As shown in FIG. 10A, when 50 g of artificial urine is injected, the capacitance of the capacitor C provided between the four electrodes changes. When 100 g of artificial urine is injected, the capacitance of the capacitor C formed between the six electrodes changes. When 150 g of artificial urine is injected, the capacitance of the capacitor C formed between the eight electrodes changes.

  FIG. 10B shows that the shape of the electrode 1b of the capacitance sensor sheet 1 is 25 mm × 25 mm, the separation distance between the electrodes in the column direction in the electrode row is 50 mm, and the separation distance between the electrodes between the electrode row and the electrode row. Is an electrode pattern consisting of 20 mm, and using a urine collecting pad 41 capable of absorbing urine equivalent to 150 g for 6 times, the measurement results when the artificial urine was injected 50 times in a range of 50 g to 350 g and injected 7 times. Show.

  As shown in FIG. 10B, when 50 g of artificial urine is injected, the capacitance of the capacitor C provided between the four electrodes changes. When artificial urine is injected to 100 g to 250 g, the capacitance of the capacitor C provided between the six electrodes changes. When 300 g to 350 g are injected, the capacitance of the capacitor C provided between the eight electrodes changes.

  FIG. 10C shows that the shape of the electrode 1b of the capacitance sensor sheet 1 is 25 mm × 25 mm, the separation distance between the electrodes in the column direction in the electrode row is 12.5 mm, and between the electrodes between the electrode rows. Measurement results when the artificial urine was injected in increments of 50 g in a range of 50 g to 350 g and injected 7 times using the urine collecting pad 41 having an electrode pattern with a separation distance of 20 mm and capable of absorbing urination for 6 times. Is shown.

  As shown in FIG. 10C, when 50 g of artificial urine is injected, the capacitance of the capacitor C provided between the six electrodes changes. When 100 g of artificial urine is injected, the capacitance of the capacitor C provided between the 10 electrodes changes. When artificial urine is injected to 150 g to 250 g, the capacitance of the capacitor C provided between the 14 electrodes changes. When artificial urine is injected to 300 g to 350 g, the capacitance of the capacitor C provided between the 18 electrodes changes.

  FIG. 11 is a scatter diagram showing the relationship between the artificial urine injection amount and the capacitance sensor output change amount under the measurement conditions (electrode patterns) in FIGS. 10 (a) and 10 (b). In FIG. 11, the vertical axis represents the capacitance sensor output change amount, and the horizontal axis represents the artificial urine injection amount (g). That is, in the example of FIG. 11, by using the same electrode pattern, the capacitance sensor output change amount is compared between the urine collecting pad 41 with three absorption amounts and the urine collecting pad 41 with six absorption amounts. Yes.

In FIG. 11, the measured value of the capacitance sensor output change amount under the measurement conditions in FIG. 10A is plotted, and an approximate curve calculated from the measured value is indicated by y1. 10 approximate curve y1 that is calculated from the measured value at (a), the correlation coefficient ^{R 2} is expressed by the following equation (3).
y1 = 0.3276x ^0.9695
R ² = 0.899 (3)

Further, in FIG. 11, the measured value of the change amount of the capacitance sensor output under the measurement conditions in FIG. 10B is plotted, and an approximate curve calculated from the measured value is indicated by y2. 10 approximate curve y2 calculated from measurements at (b), the correlation coefficient ^{R 2} is expressed by the following equation (4).
y2 = 0.0777x + 4.9457
R ² = 0.8763 (4)

  FIG. 12 is a scatter diagram showing the relationship between the artificial urine injection amount and the capacitance sensor output change amount under the measurement conditions in FIGS. 10 (b) and 10 (c). In FIG. 12, the vertical axis represents the capacitance sensor output change amount, and the horizontal axis represents the artificial urine injection amount (g). That is, in the example of FIG. 12, the amount of change in the capacitance sensor output at the urine removing pad 41 for 6 absorptions is compared using different electrode patterns.

In FIG. 12, measured values under the measurement conditions in FIG. 10C are plotted, and an approximate curve calculated from the measured values is indicated by y3. 10 approximate curve y3 calculated from measurements at (c), the correlation coefficient ^{R 2} is expressed by the following Formula (5).
y3 = 2.8348x ^0.5236
R ² = 0.9216 (5)

  In FIG. 12, the measurement values under the measurement conditions in FIG. 10B are plotted, and an approximate curve (the above formula (4)) calculated from the measurement values is indicated by y2 (in FIG. 11). It is the same as the approximate curve y2.)

  From the above equations (3) to (5), the correlation coefficients (the square of R) representing the strength of correlation are 0.899, 0.8763, and 0.9216, respectively. That is, using the approximate curves y1 to y3, it is determined that the capacitance sensor output change value can be obtained with reliability of 89.9%, 87.63%, and 92.16%, respectively. Can do. Therefore, the electrode pattern in FIG. 10 (c) having the highest correlation coefficient and the capacitance sensor output under the measurement conditions using the urine collecting pad 41 with the absorption amount of 6 times give a highly accurate calculation result of the urine output. It can be determined that it can be obtained.

  In particular, the reliability of the approximate curves y2 and y3 can be determined from the positional relationship between the range of the artificial urine and the electrode of the capacitance sensor 1 in FIGS. 10 (b) and 10 (c). For example, when the cumulative amount corresponding to one urination amount (150 g) and the cumulative amount corresponding to two urination amounts (300 g) are compared, in FIG. The capacitance of the capacitor C provided between the electrodes changes, and when the cumulative amount is 300 g, the capacitance of the capacitor C provided between the eight electrodes changes, and the capacitance of the capacitor C for two capacitors changes. The capacity changes a lot. On the other hand, in FIG. 10C, the capacitance of the capacitor C provided between the 14 electrodes changes when the accumulation is 150 g, and the capacitor provided between the 18 electrodes when the accumulation is 300 g. The capacitance of C changes, and the capacitance of the four capacitors C changes a lot. That is, the condition of FIG. 10C has a higher resolution, so that the reliability of the obtained result is higher.

  As described above, according to the condition of FIG. 10C, it is possible to accurately measure a plurality of times of urination with a normal adult at a urine output of about 150 g.

<Specific example of electrode pattern>
Next, the applicant of the present invention made various electrode patterns by using the urine collecting pad 41 having an absorption amount of 6 times, and examined them.

  FIG. 13 shows that the shape of the electrode 1b of the capacitance sensor sheet 1 is 25 mm × 25 mm, the separation distance between the electrodes in the column direction (lateral direction in the figure) is 50 mm, the electrode interval in the column direction is 62.5 mm, The distance between the electrode rows between the electrode rows (vertical direction in the figure) is 20 mm, and the distance from the outermost one end to the other end in the row direction of the electrodes (the total length of the electrode rows) ) Shows the electrode pattern 1 of 400 mm.

  Here, the separation distance between the electrode ends facing each other between the electrode rows is the average of the separation distances between the opposing electrodes of the parallel electrode rows for all the electrodes constituting the electrode rows. Mean value. In the present invention, each electrode constituting the electrode array is preferably 5 mm or less, preferably 2 mm or less, even when there is a difference in the separation distance from the electrodes of the parallel electrode array. . The distance between the electrode rows is preferably 15 to 25 mm from the viewpoint of maintaining a predetermined distance between the electrode rows during use, preventing contact, and maintaining and improving measurement accuracy.

  FIG. 14 shows a list of specific examples of other electrode patterns. In the example of FIG. 14, in addition to the electrode pattern 1, the shape of the electrode 1b is 25 mm × 25 mm, the electrode interval in the column direction is 25 mm, the separation distance between the electrodes in the column direction in the electrode column is 12.5 mm, The distance between the electrode ends facing each other between the columns is 20 mm, the electrode pattern 2 has a total length of 400 mm, the shape of the electrode 1b is 25 mm × 20 mm, the electrode spacing in the column direction is 30 mm, the columns in the electrode column The distance between the electrodes in the direction is 20 mm, the distance between the electrode ends facing each other between the electrode rows is 20 mm, the total length of the electrode rows is 420 mm, and the shape of the electrode 1b is 5 mm × 40 mm, the electrode spacing in the column direction is 35 mm, the separation distance between the electrodes in the column direction in the electrode row is 15 mm, the separation distance between the opposite electrode ends between the electrode rows is 20 mm, The electrode pattern 4 has a total length of 425 mm, the shape of the electrode 1 b is 25 mm × 25 mm, the electrode spacing in the column direction is 16.5 mm, the separation distance between the electrodes in the column direction in the electrode column is 4 mm, The distance between the electrode ends facing each other is 20 mm, the electrode pattern 5 has an electrode row length of 402 mm, the shape of the electrode 1b is 25 mm × 15 mm, the electrode spacing in the row direction is 11.5 mm, the rows in the electrode row An electrode pattern 6 is shown in which the distance between the electrodes in the direction is 4 mm, the distance between the electrode ends facing each other between the electrode rows is 20 mm, and the total length of the electrode rows is 395 mm.

  FIG. 15 shows the electrode pattern 1, the electrode pattern 2, the electrode pattern 5, and the electrode pattern 6, and the capacitive sensor sheet 1 is placed on the back as shown in FIG. The discharge port of the tube is arranged in the area corresponding to the normal human urination part on the doll-side surface of the attached urine collecting pad 41, and artificial urine is injected through the tube into the area corresponding to the urination part. It is a scatter diagram which shows the relationship between the amount of artificial urine injection | pouring in the case of having performed, and an electrostatic capacitance sensor output variation | change_quantity. In FIG. 15, the vertical axis represents the capacitance sensor output change amount, and the horizontal axis represents the artificial urine injection amount (g).

In FIG. 15, the measured values of the change amount of the capacitance sensor output measured using the electrode pattern 1, the electrode pattern 2, the electrode pattern 5, and the electrode pattern 6 are plotted. In addition, an approximate curve calculated from the measured value of the change amount of the capacitance sensor output measured a plurality of times using the electrode pattern 1 is indicated by y11. Approximate curve y11, the correlation coefficient ^{R 2} is expressed by the following equation (6).
y11 = 0.0608x + 8.7965
R ² = 0.9149 (6)

Further, in FIG. 15, an approximate curve calculated from the measured value of the change amount of the capacitance sensor output measured a plurality of times using the electrode pattern 2 is indicated by y12. Approximate curve y12, the correlation coefficient ^{R 2} is expressed by the following equation (7).
y12 = 19.077Ln (x) -54.235
R ² = 0.941 (7)

Further, in FIG. 15, an approximate curve calculated from the measured value of the change amount of the capacitance sensor output measured a plurality of times using the electrode pattern 5 is indicated by y13. Approximate curve y13, the correlation coefficient ^{R 2} is expressed by the following equation (8).
y13 = 36.978Ln (x) -138.36
R ² = 0.9333 (8)

  From the above equations (6) to (8), the correlation coefficients are 0.9149, 0.941, and 0.9333, respectively. That is, it is determined that the value of the change amount of the capacitance sensor output can be obtained with the reliability of 91.149%, 94.1%, and 93.33% by using the approximate curves y11 to y13, respectively. Can do. Therefore, it can be determined that a highly accurate calculation result of the urine output can be obtained by the capacitance sensor output under the measurement condition using the electrode pattern 2 having the highest correlation coefficient.

  In FIG. 15, although the approximate curve y13 has a higher slope than the approximate curve y12, the reason why the correlation coefficient is lower than that of the approximate curve y12 is that the capacitance near the artificial urine injection amount 400 g. The measurement accuracy of the sensor output change amount may be low. In general, when a diaper is worn on a user, urine does not spread uniformly because it is curved rather than flat. That is, when urination is performed on the back, the spread of urine near the butt is less affected by gravity than the spread of urine near the urine portion of the urine collecting pad 41, and is delayed. For this reason, urine spreads not in the surface but in the depth direction of the urine collecting pad. The electrode pattern 5 is considered to have a low measurement accuracy because it is difficult to see the spread in the depth direction because the electrode interval is too narrow.

[Performance evaluation when the electrode pattern according to the present invention is applied]
The present applicant narrowed down several measurement objects (electrode patterns) from the measurement results as described above, measured the amount of urination a plurality of times using each electrode pattern, and determined their accuracy.

  FIG. 16 shows a urine collecting pad in which the capacitance sensor sheet 1 is attached to the doll using the electrode pattern of the capacitance sensor sheet 1 as shown in FIG. 41 is a diagram showing several examples in which the amount of change in capacitance sensor output was measured when artificial urine was injected using a tube in the vicinity of the urine portion on the doll side on 41.

  Examples 1-8 and Comparative Examples 1-9 are electrode shapes, electrode spacing in the column direction, separation distance between electrodes in the column direction, total length of the electrode column, length of the absorption part of the urine collecting pad 41, unit area The measurement results are shown when the polymer amount per unit, the centrifugal retention amount per unit area, and the centrifugal retention absorption amount are changed.

  In the examples and comparative examples, as described above, the total length of the electrode rows is the distance from the outermost one end to the other end in the row direction of the electrodes. Total length) / (length of the absorption part of the urine collecting pad 41), the centrifugal retention amount per unit area refers to the amount of water that the polymer absorbs per unit area, and the centrifugal retention absorption amount is the urine collecting pad. 41 refers to the amount of water absorbed. In addition, the measurement range refers to an artificial urine injection amount that provides a reliable measurement value of the capacitance sensor output change amount. In the embodiment, the measurement standard can be measured by injecting 150 g of artificial urine several times. In the comparative example, whether or not there is an artificial urine 150 g once is not measured.

  Before describing the determination result of FIG. 16, a method for measuring the centrifugal retention amount of the absorbent article and a method for measuring the polymer amount of the absorbent article will be described.

<Measurement method of centrifugal retention amount of absorbent article>
1. The product weight of the urine collecting pad 41 is measured.
2. The outer packaging material is cut leaving the absorber, and the weight after cutting (weight after cutting) is measured.
3. The cut sample is immersed in 0.9% physiological saline for 30 minutes.
4). Remove the sample and suspend for 30 minutes to get the correct amount of absorption.
5. Measure the weight of the sample (weight after saturation).
6). The sample is placed in a bag made of non-woven fabric or nylon mesh and closed with a clip.
7). In a centrifugal dehydrator, the bag containing the sample is rotated at 800 rpm for 10 minutes, and the weight of the subsequent sample (weight after dehydration) is measured.

  FIG. 17 is a diagram showing the measurement results obtained by the method for measuring the centrifugal holding amount of the absorbent article.

  In the example of FIG. 17, 100 g is obtained as the product weight of the urine collecting pad 41, 89 g is obtained as the weight after cutting, 983 g is obtained as the saturated weight after absorbing physiological saline, and 894 g ( 983 g-89 g), 446 g as a weight after dehydration, and 357 g (446 g-89 g) as a centrifugal retention amount.

<Measurement method of polymer amount of absorbent article>
1. Remove the pulp / polymer mixture from the product.
2. The mixture is sealed in a mesh bag and weighed (weight A).
3. Soak in ascorbic acid aqueous solution (vitamin C) for a whole day and night. This dissolves the polymer in vitamin C.
4). Sun dry the mesh bag until dry.
5. Weigh the mesh bag (weight B). That is, the polymer melts and flows out, and weight B = pulp + bag weight.
6). The amount of polymer is calculated by AB.

  By the measurement method as described above, the polymer amount per unit area and the centrifugal retention amount per unit area can be obtained.

  Returning to the description of FIG. 16, the determination result will be described. In Examples 1 to 3, the electrode spacing in the column direction of the capacitance sensor sheet 1 and the polymer amount per unit area are appropriate, and the amount of reliable change in capacitance sensor output is up to 350 g of artificial urine injection. Since the measurement value is obtained, it is possible to measure multiple times and to determine that the accuracy is high (indicated by “◯” in FIG. 16). In Examples 4 to 8, the electrode spacing in the column direction of the capacitance sensor sheet 1 and the polymer amount per unit area are appropriate, and the amount of change in the capacitance sensor output can be reliably measured up to an artificial injection amount of 400 g. Since a value is obtained, it is possible to measure multiple times and to determine that the accuracy is high (indicated by “◯” in FIG. 16).

  In Comparative Example 1, the amount of polymer per unit area is appropriate, but the electrode spacing in the column direction of the capacitance sensor sheet 1 is inappropriate. It cannot be obtained, and it can be determined that the accuracy is low (indicated by “x” in FIG. 16). In Comparative Examples 2 to 9, the electrode spacing in the column direction of the capacitance sensor sheet 1 and the polymer amount per unit area are inappropriate, and the change in the capacitance sensor output is reliable only from the artificial injection amount 200 g to 300 g. It is possible to determine that the measured value of the quantity cannot be obtained and the accuracy is slightly low (indicated by “Δ” in FIG. 16).

  18 (a) to 18 (c), the capacitance sensor sheet 1 is attached to the doll on the back as shown in FIG. 5 under the measurement conditions in FIG. Place the discharge port of the tube in the area corresponding to the normal human urination part of the doll side face on the urine collecting pad 41, and inject a certain amount of artificial urine into the area corresponding to the urination part through the tube It is a scatter diagram which shows the relationship between the amount of artificial urine injection | pouring in the case of having performed, and an electrostatic capacitance sensor output variation | change_quantity. 18A to 18C, the vertical axis represents the capacitance sensor output change amount, and the horizontal axis represents the artificial urine injection amount (g).

  FIG. 18A shows an electrode pattern no. When the artificial urine was injected in increments of 50 g from 50 g to 400 g using the urine collection pad 41 with 6 absorptions. 1-no. 7 is a scatter diagram showing the relationship between the artificial urine injection amount and the capacitance sensor output change amount in FIG.

  FIG. 18B shows an electrode pattern no. When the artificial urine was injected in increments of 50 g from 50 g to 400 g using the urine collection pad 41 having four absorptions. 2, no. 4-no. 7 is a scatter diagram showing the relationship between the artificial urine injection amount and the capacitance sensor output change amount in FIG.

  FIG. 18C shows an electrode pattern no. When the artificial urine was increased by 50 g from 50 g to 300 g using the urine collecting pad 41 having three absorptions. 1-no. 6 is a scatter diagram showing the relationship between the artificial urine injection amount and the capacitance sensor output change amount in FIG.

FIG. 19 is a scatter diagram showing the relationship between the electrode spacing in the column direction and the amount of centrifugal retention per unit area based on the measurement results of FIGS. 16 and 18A to 18C. In FIG. 19, the vertical axis represents the electrode spacing (mm) in the column direction, and the horizontal axis represents the centrifugal retention amount (g / m ² ) per unit area.

  In FIG. 19, P21 to P28 are plotted based on the measured values in Examples 1 to 8, respectively. P31 to P39 are plotted based on the measured values in Comparative Examples 1 to 9. Each is plotted.

  From the measurement results of FIG. 16 and FIG. 19, the electrode spacing in the column direction in the electrode row is an electrode pattern in the range of about 20 to 55 mm, and the absorbent part of the absorbent article (urine collecting pad 41) has an artificial part of 350 g or more. It can be judged that it is preferable to select a combination of polymer amounts capable of absorbing urine. Thereby, the amount of urination can be detected with high accuracy.

  Moreover, the amount of centrifugal retention per unit area of the absorbent part of the absorbent article (urine collecting pad 41) is approximately 5000 to 8000 g / m 2, and the electrode is in a shape of approximately 15 to 35 mm in a rectangle. It can be judged that it is preferable. Thereby, the amount of urination can be detected with high accuracy.

  Furthermore, it is determined that the distance from the outermost one end of the electrode array to the other end (the total length of the electrode array) is preferably approximately 75% or more of the length of the absorbent portion of the absorbent article (urine collecting pad 41). can do. Thereby, the amount of urination can be detected over a wide range.

<Definition of electrode spacing in the column direction in the electrode column>
The present applicant examined the definition of the electrode spacing in the column direction in the electrode row of the capacitance sensor sheet 1 from the scatter diagram shown in FIG.

  FIG. 20 is a diagram showing the arrangement of the electrodes 1b of the capacitance sensor sheet 1 according to the present embodiment. In FIG. 20, d represents the separation distance between the opposite ends of the electrodes adjacent in the column direction of the electrode row, and a1 represents the distance from the electrode end of the positive electrode to a straight line having an area of ½. The a2 represents the distance from the electrode end of the negative electrode to a straight line having an area of ½.

  In the figure, a range surrounded by A11 represents one electrostatic capacitance C, and consider this electrode area. In the present embodiment, since the positive electrode and the negative electrode are alternately arranged in the electrode 1b, from the positive electrode toward the negative electrodes on both sides in the directions (column direction) indicated by arrows A21 to A23 in the figure. The charge moves. As a result, the area of one electrostatic capacitance C is ½ of the electrode area.

Next, it is considered that the movement of electric charges moves in an arc shape from the arrangement of the electrodes. As a result, the average distance is from the position (a1 / 2) of half the distance a1 from the electrode end of the positive electrode to the straight line having an area of 1/2, from the electrode end of the adjacent negative electrode. It is considered to be a half of the circumference having a diameter up to a half position (a2 / 2) of the distance a2 to the straight line 2. That is, the distance d ′ between the average electrodes is expressed by the following equation (9).

Of the above formula (9), the following formula (1) excluding constants can be defined as the electrode spacing in the column direction of the electrode rows. The distance d ′ is preferably in the range of about 20 to 55 mm also from the measurement results described above.

<About electrode shape and electrode spacing>
The present applicant examined the relationship between the electrode shape and the electrode spacing in the column direction in the electrode column defined by the above equation (1).

  21A to 21H are diagrams illustrating an example of the electrode interval d ′. 21A to 21H, the solid line represents the position when the area of the electrode is halved.

  In FIG. 21A, two substantially square electrodes are arranged in parallel. In FIG. 21B, two parallelogram electrodes are arranged in parallel in the same direction. In FIG. 21C, two octagonal electrodes are arranged in parallel in the same direction. In FIG. 21D, two electrodes having a plurality of mountain shapes on one side are arranged in parallel in the same direction. In FIG. 21E, the arrangement positions of the two electrodes shown in FIG. In FIG. 21F, the arrangement positions of the two electrodes shown in FIG. In FIG. 21G, two triangular electrodes are arranged in parallel in the same direction. In FIG. 21 (h), electrodes each having a plurality of mountain shapes are arranged in parallel in the same direction on two parallel sides.

  22A and 22B are diagrams showing another example of the electrode interval d ′. In FIGS. 22A and 22B, the solid line represents the position when the area of the electrode is halved.

  In FIG. 22A, two triangular electrodes are arranged in parallel in different directions. In FIG. 22B, the deformed circle and two circular electrodes are arranged in parallel.

  As can be seen from FIGS. 21 and 22, in the electrode pattern in the present embodiment, in order to define the electrode interval d ′, it is necessary that electrodes having substantially the same shape are arranged in the same direction. That is, as shown in FIGS. 22E and 22F, when electrodes having different shapes are arranged, the electrode interval d ′ is not uniform, and the measurement results vary. In addition, when the separation distance d in the column direction in the electrode column becomes 0, the two electrodes are regarded as one and the measurement accuracy is deteriorated, so the shortest electrode interval d becomes a value larger than 0.

[Measurement of urination rate and urine flow rate by electrode pattern to which the present invention is applied]
<Measurement of urination rate>
The present applicant measured the amount of change in the capacitance sensor output when the artificial urine was injected at a constant rate at a constant rate using the measurement conditions of Example 1.

  FIG. 23 shows the capacitance when the measurement for injecting the artificial urine at 5 g per second under the measurement conditions of Example 1 is performed twice and the measurement for injecting the artificial urine at 10 g per second is performed three times. It is a scatter diagram which shows the relationship between sensor output variation | change_quantity and time. In FIG. 23, the vertical axis represents the capacitance sensor output change amount, and the horizontal axis represents time (sec).

  As shown in FIG. 23, the first and second measurement results when artificial urine is injected at 5 g per second, and the first to third measurement results when artificial urine is injected at 10 g per second. Are plotted respectively.

  As can be seen from this scatter diagram, the spread of urine can be grasped as the urination rate and can be used for evaluation of bladder function.

<Measurement of urine flow rate>
The applicant calculated the urine flow rate per second using the measured value of the micturition rate measured in FIG.

  24A to 24E are scatter diagrams showing the relationship between the calculated urine flow rate (g / sec) and time (sec) by calculating the urine flow rate per second using the measured values in FIG. It is. In FIG. 24, the vertical axis represents urine flow rate (g / sec), and the horizontal axis represents time (sec).

  FIG. 24A shows the relationship between the urine flow rate calculated from the first measurement result and the time when artificial urine is injected at 5 g per second.

  FIG. 24B shows the relationship between the urine flow rate calculated from the second measurement result and the time when artificial urine is injected up to 150 g for 30 seconds, 5 g per second.

  FIG. 24 (c) shows the relationship between the urine flow rate and time calculated from the first measurement result when artificial urine is injected up to 150g for 15 seconds, 10g per second.

  FIG. 24 (d) shows the relationship between the urine flow rate and time calculated from the second measurement result when artificial urine was injected up to 150g for 15 seconds, 10g per second.

  FIG. 24 (e) shows the relationship between the urine flow rate calculated from the third measurement result and the time when artificial urine was injected up to 150g for 15 seconds, 10g per second.

  Also, in FIGS. 24A to 24E, the moving averages (root mean square) of two sections are plotted.

  As can be seen from the scatter diagram in FIG. 24, the urine flow rate can be calculated by measuring the amount of urination at intervals of 1 second, and can be used for evaluating urination disorders.

<Correction by user posture>
The amount of urination, urination rate, and urine flow measured as described above can be corrected based on the posture information (X axis, Y axis, Z axis) of the user detected by the acceleration sensor 12. . Thereby, the detection accuracy of the urination volume, the urination speed, and the urine flow rate can be improved. In addition, the technique regarding correction | amendment of the amount of urination using attitude | position information (X-axis, Y-axis) is described in Unexamined-Japanese-Patent No. 2002-224093.

[Effects of the embodiment of the invention]
1. The electrode interval in the electrode row in the electrode row is in the range of approximately 20 to 55 mm, and the absorbent part of the absorbent article (urine collecting pad 41) absorbs the artificial urine having a centrifugal retention amount of 350 g or more. By selecting a combination of polymer amounts that can be measured, it is possible to measure urination multiple times with high accuracy. That is, if the amount of urination for one adult is 150 g, it can be measured accurately using multiple urinations, so urination interval, urination time and urine flow rate (urination rate) are measured more accurately. It is possible to evaluate bladder function and dysuria.

  2. By selecting a shape in which the electrodes of the electrode pattern are in a rectangle of approximately 15 mm to 35 mm, the urine output can be detected with high accuracy.

  3. By selecting a centrifugal holding amount per unit area of the absorbent part of the absorbent article that is approximately 5000 to 8000 g / m 2, measurement accuracy can be achieved even if the amount of urination increases while allowing urination multiple times. Since it is high, not only can the urination interval be measured, but also the urination volume can be detected with higher accuracy in terms of urination time and urine flow rate (urination rate).

  4). The distance from the outermost end of the electrode array to the other end (the total length of the electrode array) is approximately 75% or more of the length of the absorbent portion (urine collecting pad 41) of the absorbent article (tape diaper 51). By selecting, the amount of urination can be detected over a wide range.

[Modification]
In the above description, the electrode patterns of the capacitance sensor sheet 1 are arranged in two rows. However, the present invention is not limited to this, and the absorbent portion (urine collecting pad 41) of the three rows or the absorbent article (tape diaper 51) is used. If it can be covered, it may be more than that.

  The present invention is not limited to the above-described embodiment as it is, and in the implementation stage, the component may be modified and embodied without departing from the spirit of the invention, or a plurality of components disclosed in the above-described embodiment. Various inventions can be formed by appropriately combining the above. For example, some components may be deleted from all the components shown in the embodiment. Furthermore, you may combine the component covering different embodiment suitably.

DESCRIPTION OF SYMBOLS 1 Capacitance sensor sheet 11 Data collection means 12 Information processing means 21 Capacitance sensor 22 Acceleration sensor 23 Data logger 31 Data acquisition means 32 Urination amount calculation means 33 Urination speed calculation means 34 Urine flow rate calculation means

Claims (4)

An absorbent article that absorbs urine is provided with a plurality of electrode rows in which a plurality of electrodes are arranged on the outer surface opposite to the side that touches the user's skin, and the urination is performed based on an impedance change between the plurality of electrodes. A urination detection device for detecting
The absorbent part of the absorbent article has a polymer amount capable of absorbing the urination of a centrifugal retention amount of 350 g or more,
The urination detection device in which the electrode interval in the row direction in the electrode row is 20 to 55 mm.   The urination detection device according to claim 1, wherein the electrode has a shape within a rectangle of 15 to 35 mm. The urination detection device according to claim 1, wherein a centrifugal holding amount per unit area of the absorption part of the absorbent article is 5000 to 8000 g / m ² .   2. The urination detection device according to claim 1, wherein a length from one end to the other end of the electrode array is 75% or more and 100% or less of a length in a longitudinal direction of an absorbent portion of the absorbent article.

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