JP2020096789A - Method for monitoring incontinence - Google Patents

Abstract

To provide a method for monitoring incontinence.SOLUTION: A method for monitoring incontinence of a user comprises the steps of:using a urine detection circuit 410 which is provided in an absorbent article and exhibits a changed electric nature when being exposed to urine to determine whether or not a user has discharged urine into the absorbent article; using a measurement circuit 420 for performing a measurement of a bladder to in order determine a parameter which varies according to a saturation level of the bladder; using a sensor attached to the user to determine a posture and/or motion of the user; and in response to determination that the user has discharged urine into the absorbent article, recording data indicating the parameter, an estimated motion and/or posture of the user based on the posture and/or motion determined by the sensor, and an estimation of a urine volume discharged onto the urine detection circuit, by a processing circuit 430.SELECTED DRAWING: Figure 4

Description

The concept of the present invention relates to a method of monitoring incontinence.

Urinary incontinence or dysfunction of urinary control is a common problem affecting both men and women of all ages. Many feel embarrassed and do not dare to go to a doctor for help. This can lead to chronic incontinence. In the prior art, a common way to manage incontinence is to use absorbent articles such as diapers, sanitary napkins or pads, or even catheters. However, this only reduces the inconvenience to the wearer when an incontinence event occurs.

Common types of urinary incontinence include stress and urge incontinence. There are also mixed types of incontinence, including both stress and urge incontinence. Stress incontinence may be caused by loss of urethral support, usually as a result of birth, overweight or/and damage to the pelvic support structure as a result of some medication. Stress urinary incontinence is typically a relatively small amount of urine leakage during an activity that increases coughing, sneezing and lifting, or abdominal pressure, such as rapid movement during sports activities. Is characterized by. The main treatment for stress urinary incontinence is pelvic floor exercises. Another possibility would be surgery or drug prescription to tighten or support the bladder outlet. On the other hand, urinary incontinence may be caused by abnormal bladder contractions. It is also sometimes referred to as an "overactive" bladder. Urge urinary incontinence is typically characterized by a relatively large urine leak associated with insufficient warning to reach the toilet in time. Potential treatments for urge incontinence are pelvic floor exercises to retrain the bladder, or prescription of drugs to relieve the bladder.

Various systems are known in the prior art, for example relying on electrical sensors for detecting the presence of urine in diapers. Such prior art systems, however, can often only detect when the diaper is damp and signal, for example, the wearer or caregiver of the diaper, of the need to change the diaper. However, this only provides limited help to those suffering from incontinence, primarily in that it makes it easier for the wearer or caregiver to determine when it is time to change diapers. ..

The inventor has realized that it would be advantageous to provide a system that allows for improved urinary incontinence monitoring. More specifically, the present inventor has a system for incontinence monitoring that provides, for many people suffering from incontinence and similar problems, aspects of monitoring other than just the need to change diapers. I found that would be useful.

According to one aspect of the invention, there is provided a system for monitoring incontinence, the system comprising a urine sensing circuit configured to exhibit altered electrical properties upon exposure to urine and varying levels of bladder filling. A measurement circuit configured to perform a measurement of the bladder of the wearer to determine at least one parameter of: a sensor configured to determine orientation and/or movement of the sensor; and a urine detection circuit. Determined by the measurement circuit in response to determining whether it is exposed to urine, estimating the amount of urine released to the urine detection circuit, and determining that the urine detection circuit is exposed to urine Record the data representative of the at least one parameter, the estimated movement and/or posture of the wearer based on the orientation and/or movement determined by the sensor and the estimated amount of urine released to the urine detection circuit. And a processing circuit configured to.

The system detects the actual detection of an involuntary micturition event (hereinafter synonymously referred to as micturition event or incontinence event) and a parameter indicating bladder filling level, an estimate of the wearer (indicating the wearer's current activity). It is possible to correlate the movements and/or postures that have been taken and the estimated amount of urine released by the wearer. This type of correlation is particularly useful for monitoring stress urinary incontinence, which, as mentioned above, is usually characterized by a relatively small leakage of urine during activities that increase abdominal pressure. Information on the bladder filling level, movement/posture and the amount of urine released is thereby helpful in understanding which activities cause incontinence and the severity of incontinence during these activities. However, it should be noted that this system is also useful for monitoring urgency and mixed type incontinence.

By triggering the recording of data in response to the urine sensing circuit detecting or determining exposure to urine, a parameter indicative of bladder filling level and the wearer's estimated movement and/or posture may be an incontinence event. Accurate monitoring is provided to address conditions that are sometimes common. This accuracy would be difficult to achieve with any manual monitoring method.

According to one embodiment of the invention, the processing circuitry is responsive to determining that the urine detection circuitry is exposed to urine, the at least one parameter determined by the measurement circuitry, the estimated motion and/or Or further configured to record an association between posture and estimated amount of urine released to the urine detection circuit. In other words, the processing circuit is configured to logically link the at least one parameter determined by the measurement circuit, the estimated movement/posture and the estimation of the amount of urine released to the urine detection circuit. ..

The processing circuit is further configured to record in the data an indication that the urine detection circuit is exposed to urine. The processing circuit therefore provides an indication that the urine detection circuit is exposed to urine, and the at least one parameter determined by the measurement circuit, the estimated movement/posture and the urine released to the urine detection circuit. It is configured to correlate volume estimates (or link them with an indication that the urine detection circuit is exposed to urine).

The processing circuit is configured to record the data in the memory.

According to one embodiment of the present invention, the processing circuit is configured to determine that the urine detection circuit is exposed to urine based on the changed electrical characteristic. More specifically, the processing circuit can determine that the urine detection circuit is exposed to urine by detecting the changed electrical characteristic of the urine detection circuit.

According to one embodiment of the invention, the urine detection circuit is configured to exhibit an electrical response when exposed to urine, and the processing circuit detects the electrical response of the urine detection circuit to detect urine. Configured to determine that the circuit is exposed to urine.

According to one embodiment of the present invention, the altered electrical characteristic of the urine sensing circuit is indicative of/proportional to the amount of urine released into the urine sensing circuit.

According to one embodiment of the present invention, the electrical response of the urine detection circuit is indicative of the amount of urine released to the urine detection circuit/proportional to the amount of urine released to the urine detection circuit and the processing circuit It is configured to estimate the amount of urine released to the urine detection circuit based on the electrical response of the detection circuit.

According to one embodiment of the invention, the changed electrical characteristic or electrical response of the urine detection circuit is generated by a changed resistance, a changed capacitance, a changed inductance, a changed impedance, a changed resonance frequency, a urine detection circuit. A changed voltage, a changed current generated by the urine detection circuit, and a changed resonance frequency of the urine detection circuit.

According to one embodiment of the invention, the processing circuit is configured to estimate the amount of urine released to the urine detection circuit by determining the magnitude of the change.

According to one embodiment of the invention, the urine detection circuit has a portion configured to generate an electric current when exposed to urine to power the transmission of a signal from the urine detection circuit. In response to receiving the signal from the circuit, the processing circuit is configured to record this data. Thus, a micturition event directly triggers the recording of data by the processing circuitry. Furthermore, no additional power supply in the urine detection circuit is required, since the current that powers the transmission of signals is generated by the urine. The urine detection circuit can thereby be manufactured at a reasonably low cost.

According to one embodiment of the present invention, the signal transmitted from the urine detection circuit is indicative of the amount of urine released to the urine detection circuit and the processing circuit is based on the signal received from the urine detection circuit to the urine detection circuit. It is configured to estimate the amount of urine released.

According to one embodiment of the invention, the current generated by this portion is proportional to the surface area of this portion exposed to urine.

According to one embodiment of the invention, the portion comprises a first conductive path or electrode configured to function as an anode and a first portion configured to function as a cathode when the portion is exposed to urine. 2 conductive paths or electrodes. The anode-cathode pair enables the rational and relatively inexpensive manufacture of reliable, self-generating urine detection circuits.

According to one embodiment of the invention, the urine detection circuitry is configured to generate a current when exposed to urine to power a counter increment stored in the memory of the urine detection circuit. Have parts. Information regarding the amount of water resulting from a plurality of subsequent micturitions is thereby gathered by the reduced amount of signal transmission between the processing circuit and the urine detection circuit.

As such, the processing circuit is configured to estimate the amount of urine released to the urine detection circuit based on the counter.

According to one embodiment of the invention, the processing circuitry is further configured to record the time data in response to determining that the urine detection circuitry is exposed to urine. As a result, the time of the incontinence event is recorded.

According to an embodiment of the invention, the processing circuit is further configured to estimate the bladder filling level based on the at least one determined parameter, ie by using the at least one determined parameter. An estimate of bladder filling level may be included in this recorded data.

According to one embodiment of the invention, the processing circuitry is configured to provide a signal indicative of bladder filling level based on the determined parameter. The signal may be used, for example, to provide the user with information about the bladder filling level. The signal indicates the filling level in a relative or absolute representation. Based on this information, the system user can determine if it is time to go to the toilet.

According to one embodiment of the invention, the processing circuitry is configured to provide a warning signal in response to determining that the urine sensing circuit is exposed to urine. Thus, the user is informed that a urine leak has occurred which may otherwise have gone unnoticed. This can make it easier for the user to understand which situation results in involuntary urination.

According to one embodiment of the invention, the system further comprises at least one of a microphone, a temperature sensor, an accelerometer, or an altimeter, or a combination thereof. The additional sensor allows more parameters to be recorded in the data that have an effect on the micturition event. Therefore, the parameters measured by these sensors may be included in the data recorded by the processing circuitry in response to a micturition event.

According to one embodiment of the invention, the measuring circuit and the processing circuit are galvanically connected. This allows easy communication between the measuring circuit and the processing circuit.

According to one embodiment of the present invention, the processing circuit and the urine detection circuit are galvanically separated. This simplifies the use of the system as the urine detection circuit may be handled without the need to handle any wiring. It also allows the urine detection circuit to be used as a disposable component of a system that is easily replaced after an incontinence event.

According to one embodiment of the invention, the measurement circuit is configured to measure the impedance of the bladder and/or perform an ultrasonic measurement of the size of the bladder. These types of measurements allow accurate estimation of bladder filling levels.

According to one embodiment of the invention, the processing circuit is further configured to determine the threshold value based on the at least one determined parameter represented by the recorded data. Therefore, a threshold value corresponding to the bladder filling threshold value is determined. Since the threshold value is based on at least one determined parameter, the threshold value is determined to correspond to a bladder filling level above and above which the risk of an incontinence event increases. Further, the threshold is adjusted as needed for the particular individual, based on the at least one determined parameter being the measured parameter(s).

According to one embodiment of the invention, the processing circuit is further configured to determine the threshold value based on the at least one determined parameter represented by the recorded data and the previously determined threshold value. The advantages mentioned in connection with the previous embodiments likewise apply to this embodiment. In addition, the threshold determination is based on previously determined thresholds so that the thresholds are better adjusted over time to better address the incontinence problem of a particular individual.

According to one embodiment of the invention, the processing circuitry is further configured to determine the threshold value based on the at least one determined parameter represented by the recorded data and the estimated movement and/or pose. Since the movement and/or posture of the wearer affects both the determination of the parameter(s) by the measurement circuit and also the risk of an incontinence event, this embodiment describes that the wearer had it at the time of the incontinence event. Allows a threshold to be determined based on the estimated motion and/or pose. Therefore, the threshold is related to movement and/or posture.

According to one embodiment of the present invention, the measurement circuit is configured to repeatedly determine at least one parameter that varies with bladder filling level, and the processing circuit compares the repeatedly determined parameter with one or more bladder filling thresholds. And each threshold is associated with an orientation or movement determined by the sensor. The advantages of this embodiment are understood from the previous embodiments.

According to one embodiment of the invention, after detecting a micturition event, the processing circuit records the urine event in response to detecting the micturition event (eg, by detecting that the urine detection circuit is exposed to urine). It is further configured to perform a comparison between the at least one parameter represented by the captured data and the parameter determined by the measurement circuit in the case after detection of a micturition event. Urinary retention problems can be identified by comparing the filling levels before and after urination.

Also, according to one embodiment, which is intended to form an aspect of the individual invention, it exhibits a first electrical property or response when in proximity to the user's skin and is remote from the user's skin. A skin proximity sensor configured to exhibit a second electrical characteristic or response, and configured to perform a measurement of the wearer's bladder to determine a parameter that varies with bladder filling level. And a first parameter determined by the measurement circuit in response to detecting the separation between the skin proximity sensor and the user's skin based on the changed electrical property or response of the skin proximity sensor. Data is recorded indicating the bladder filling level at the first time point in the detection of the separation or before the detection of the separation, representing the second parameter determined by the measuring circuit, and the second time point after the first time point. And a processing circuit configured to record data indicative of bladder filling level at.

The processing circuit is configured to perform the comparison between the first and second parameters.

The second time point is delayed with respect to the first time point by a predetermined time interval (eg, the expected duration of normal urination). Alternatively, the second time point corresponds to a time point after or at which the processing circuit detects the restored proximity of the skin proximity sensor to the skin.

The skin proximity sensor may be, for example, an absorbent article worn by the user (eg, diaper/diaper or underwear/underwear) or the upper edge of clothing (eg, pants, shorts, skirt or the like worn by the user). Is configured to be attached to. When the user pulls down the absorbent article or clothing to urinate in the toilet, the skin proximity sensor loses proximity to the skin. When the user pulls up the absorbent article or clothing after urinating, the skin proximity sensor regains proximity to the skin. Identify urinary retention problems by comparing the filling level before and after urination.

As well as further objectives, the features and advantages of the above inventive concept will be explained through the following illustrative and non-limiting detailed description of preferred embodiments of the inventive concept with reference to the accompanying drawings. It will be better understood and the same reference numbers will be used for similar elements.
1 is a schematic diagram of a system according to an embodiment of the present invention. 3 illustrates an embodiment of a urine detection circuit. 7 illustrates another embodiment of a urine detection circuit. FIG. 6 is a schematic diagram of a system according to a further embodiment.

Detailed embodiments of each aspect of the present invention will now be described with reference to the drawings.

FIG. 1 schematically illustrates an embodiment of a system 100 for monitoring incontinence. The system 100 comprises a urine detection circuit 110, a measurement circuit 120 and a processing circuit 130. The urine detection circuit 110 is configured to exhibit altered electrical characteristics when exposed to urine. In other words, the urine detection circuit 110 exhibits altered electrical properties or properties in response to being exposed to urine. As described in more detail below, the altered electrical characteristic of the urine detection circuit 110 is indicative of the amount of urine released into the urine detection circuit 110 or is proportional to the amount of urine released into the urine detection circuit 110. To do. In use, the urine sensing circuit 110 is typically in the wearer's crotch region, for example, an absorbent article (eg, a diaper/diaper, a sanitary napkin/pad or some other article for absorbing urine). Or in relation to underwear or underwear. The wearer is also referred to as the user of system 100. When an incontinence event occurs, urine is released into the absorbent article or undergarment of the wearer and the urine sensing circuit 110 is exposed to urine.

The processing circuit 130 is configured to determine if the urine detection circuit 110 is exposed to urine. As described in more detail below, the processing circuit 130 communicates with the urine detection circuit 110 (eg, over a wireless or wired interface) and detects urine detection by detecting a change in electrical characteristics of the urine detection circuit 110. The circuit 110 is configured to determine that it is exposed to urine. The processing circuit 130 also saturates absorbent articles (eg, over a wireless or wired interface) to the user (eg, diapers/diapers, sanitary napkins/pads or some other article for absorbing urine). And signal that it must be replaced. This will avoid leakage of the absorbent article. Meanwhile, the measurement circuit 120 is configured to perform a measurement of the wearer's bladder to determine at least one parameter that varies with bladder filling level. The parameter(s) determined by the measurement circuit 120 may be, for example, ultrasound measurements of bladder impedance and/or bladder size. Further examples are given below. The measurement circuit 120 is typically located at or near the wearer's bladder area. The measuring circuit 120 is provided, for example, in a unit that is fixed to the skin of the bladder area (for example by means of glue), fixed to the wearer by means of straps or fixed to the edge of a diaper or undergarment.

The system 100 further comprises a sensor 140 attached to the wearer and configured to determine the orientation and/or movement of the sensor 140. The sensor 140 may include, for example, an accelerometer and/or a gyroscope in the form of a MEMS device. The accelerometer may be a single axis accelerometer, a two axis accelerometer or a three axis accelerometer. The accelerometer provides orientation and/or motion measurements, for example by storing the measurements in a memory or buffer accessible by the processing circuitry 130. The sensor 140 is configured to store a predetermined number of measurements and to start discarding the oldest measurement when the predetermined number is exceeded. This may conveniently be implemented, for example, using a first in first out buffer (ie a FIFO buffer). The processing circuit 130 estimates motion and/or posture of the wearer of the sensor 140 based on the orientation and/or motion measurements. By comparing the motion measurements during the time interval, the processing circuitry 130 determines if the wearer was moving during the time interval and/or estimates the wearer's posture. The processing circuitry 130 also optionally characterizes the type of movement as walking, running, or changing the orientation or posture of the wearer. As a non-limiting example, if the axis of the accelerometer is oriented along the length of the body, the accelerometer will provide a signal corresponding to the acceleration due to gravity when the user is standing and when the user is lying. Provides a signal near zero. This concept is extended to identify additional poses.

The wearer's motion pattern and posture of the sensor 140 further influences whether the current bladder filling level signifies an increased risk of an involuntary voiding event. It also affects the parametric measurement(s), in particular the impedance measured by the measuring circuit 120.

Therefore, the processing circuit 130 estimates the amount of urine released to the urine detection circuit 110 in response to determining that the urine detection circuit 110 is exposed to urine, and the determination is made by the measurement circuit 120. To record data representative of the at least one parameter, the estimated motion and/or posture of the wearer based on the orientation or motion determined by the sensor 140, and the estimated amount of urine released to the urine detection circuit 110. Further configured. Since the occurrence of an incontinence event is correlated with both the wearer's movement pattern or posture (ie, activity) and bladder filling level, data representing parametric measurement(s), urine estimator and movement/posture combinations. Enables a more accurate and extensive analysis of wearer's incontinence events.

The processing circuit 130 is configured in the same unit as the measurement circuit 120 and is DC-connected to the measurement circuit 120. The sensor 140 is provided in the same unit as the measurement circuit and/or the processing circuit 130. In addition, the measurement circuit 120, the processing circuit 130, and the sensor 140 are configured on different carriers (for example, different circuit boards or different boards), and the measurement circuit 120 and the sensor 140 are processed by wiring or a corresponding plug-socket interface. 130 can be connected. Further, the measurement circuit 120, the processing circuit 130, and the sensor 140 are configured on the same carrier, and the circuits 120, 130 and the sensor 140 are connected by a set of conductive paths.

When the amount of urine exposure increases (ie, due to an incontinence event), the electrical characteristics of urine sensing circuit 110 change from a first characteristic to a second characteristic. The altered electrical property occurs as a result of the urine sensing circuit 110 changing from a relatively dry state (eg, prior to the occurrence of an incontinence event) to a relatively wet state (eg, when an incontinence event occurs). It will be understood. Also, the altered characteristic may be such that the urine detection circuit 110 is already wet (eg, as a result of the first incontinence event) and is even wetter (eg, of a second incontinence event after the first incontinence event). Occurs as a result of changing to. Therefore, the electrical characteristics change in a manner that is proportional to the amount of urine that the urine detection circuit 110 is exposed to. In other words, the altered electrical characteristic of the urine detection circuit 110 is indicative of the amount of urine released into the urine detection circuit 110 or is proportional to the amount of urine released into the urine detection circuit 110.

Furthermore, exposure to urine with respect to the urine detection circuit 110 does not necessarily mean direct contact with urine in the present context. In fact, the urine sensing circuit 110 may be embedded within the absorbent material, so that no direct contact with the urine released by the wearer may occur. However, the presence of urine in close proximity to the urine sensing circuit nevertheless causes altered electrical properties.

According to some embodiments, the urine detection circuit 110 is configured to exhibit an electrical response when exposed to urine, and the processing circuit 130 detects the electrical response of the urine detection circuit 110 to detect the urine detection circuit 110. Is configured to determine that the is exposed to urine. Further, the electrical response of the urine detection circuit is indicative of the amount of urine released to the urine detection circuit 110 or is proportional to the amount of urine released to the urine detection circuit 110, and the processing circuit 130 is It is configured to estimate the amount of urine released into the urine detection circuit 110 based on the electrical response of 110.

The altered electrical characteristic or electrical response of the urine sensing circuit 110 may include, for example, a varied electrical parameter of the urine sensing circuit 110. The particular type of electrical parameter that changes depends on the actual design of the urine sensing circuit 110 (eg, which circuit elements are included in the circuit 110), eg, changed resistance, changed inductance, changed It may include one or a combination of capacitance or altered impedance. Also, as described in detail below, the altered electrical characteristic or response may result in altered energy absorption of the received high frequency signal and/or (eg, altered resonant frequency of the urine sensing circuit 110 and/or urine sensing). It may include altered energy of the high frequency signal transmitted from the urine detection circuit 110 (due to signal attenuation due to absorption of transmitted/received high frequency signal by urine in circuit 110). Also, as described in detail below, the altered electrical property may also include an altered voltage at a pair of electrodes (eg, an anode-cathode pair) of the urine sensing circuit 110.

Also, as described below in this regard, the processing circuit 130 is configured to estimate the amount of urine released to the urine detection circuit by determining the magnitude of the change.

FIG. 2 illustrates one embodiment of urine detection circuit 210 that may be used as urine detection circuit 110 in system 100. The urine detection circuit 210 has a portion 212 configured to generate an electric current when exposed to urine. The urine detection circuit 210 has first and second electrodes 214 and 215. When urine is between the electrodes 214, 215, the first electrode 214 is configured to act as an anode and the second electrode 215 is configured to act as a cathode. Therefore, urine may act as an electrolyte, producing a voltage between the first and second electrodes 214,215. Therefore, the urine detection circuit 210 is configured to exhibit changed voltage characteristics and current characteristics when exposed to urine. The magnitude of the generated current is proportional to the surface area of portion 212 exposed to urine. Various material combinations for the electrodes 214, 215 are possible. For example, the first electrode 214 may include copper and the second electrode 215 may include magnesium. The first electrode 214 may include copper and the second electrode 215 may include zinc. The first electrode 214 may include carbon and the second electrode 215 may include magnesium.

In the illustrated embodiment, each one of the first electrode 214 and the second electrode 215 has four elongated or finger-shaped electrode portions arranged in a comb-like structure. The electrode portions of the first and second electrodes 214, 215 are alternately arranged as shown. Such a structure of the electrodes 214 and 215 is called a comb-shaped electrode structure. The number of electrode portions of the first and second electrodes 214, 215 may be varied to produce a current within a desired range for a particular application, thus making the sensitivity of the urine sensing circuit 210 a application specific requirement. It should be noted that it may be adapted accordingly. As can be appreciated, the maximum current produced in the portion 212 depends, inter alia, on the electrode dimensions (eg length), the amount of overlap between adjacent anode-cathode electrode portions and also the electrolyte concentration (ion) in the urine. Concentration). The current produced is therefore increased by supplying salt (eg sodium chloride) in portion 212. Further, the maximum current is proportional to the number of electrode parts of the electrodes 214 and 215. Although more electrodes result in greater generated current, a single electrode portion of each electrode 214, 215 (eg, a single "finger portion") may be sufficient in some applications. .. It should also be appreciated that a greater number of electrode portions provide a larger urine sensing area for urine sensing circuit 210.

Optionally, a polymer coating such as polyvinyl chloride (PVC) or polyurethane is applied at portion 212 and/or to electrodes 214,215. More generally, the polymer may be a polymer that reacts with one or more specific analytes present in urine (eg, creatine, calcium or uric acid). Upon exposure to urine (and the analyte present in the urine), the current produced in portion 212 is thereby increased.

The first and second electrodes 214, 215 can be galvanically connected to the transmitter 216 of the urine detection circuit 210. Therefore, the current generated at the electrodes 214, 215 powers the transmitter 216 for transmitting the wireless signal from the urine detection circuit 210. As described further below in this regard, the wireless signal can be received by a receiver connected to the processing circuit 130, which can determine that the urine detection circuit 210 is exposed to urine.

The larger current generated in portion 212 means the larger power delivered to transmitter 216. Thus, the power of the wireless signal transmitted from transmitter 216 is indicative of the amount of urine released into portion 212 or is proportional to the amount of urine released into portion 212. The processing circuit 130 thus estimates the amount of urine released to the urine detection circuit 210 by determining the strength of the received wireless signal (eg, absolute strength or relative strength associated with a predetermined reference value). To do. The processing circuit 130 can, for example, measure the power of the received signal and look up the measured power with a predetermined (eg, established by a calibration procedure) power level and different amounts of urine exposure. It can be compared with a table (LUT).

The transmitter 216 may generally have LC or RLC circuits. Optionally, the antenna element can be connected to an LC or RLC circuit to enhance the range of transmitter 216. Alternatively, the electrodes 214, 215 are designed to function as antenna elements. According to a specific example, the transmitter 216 may be a near field communication type (NFC) or a radio frequency identification type (RFID).

As shown in FIG. 2, the urine detection circuit 210 is provided on the substrate 218. The substrate may generally be a relatively thin flexible substrate. The urine detection circuit is provided by means of a current carrying element provided on the substrate 218, according to processes which are known per se to the person skilled in the art, for example by depositing the conductive material on the substrate or by masking and etching the conductive material from the substrate. The circuit elements forming 210 may be formed. Substrate 218 may be, for example, a thin plastic foil such as PET foil (polyethylene terephthalate). An adhesive may be provided on one surface of the substrate 218. Therefore, the urine detection circuit 210 may be configured in a patch-like structure. The adhesive surface allows easy attachment and removal of the urine detection circuit 210 on the absorbent article or undergarment. Advantageously, the substrate 218 is biocompatible and environmentally compatible, and is provided with a shape and size that minimizes wearer inconvenience throughout the wearer's daily activities. The substrate 218 may also contain or be made from absorbent materials such as paper, cloth, cotton or absorbent polymers. Therefore, the substrate itself absorbs urine, and the absorbed urine subsequently causes a change in the electrical characteristics of the urine detection circuit 210. The substrate 218 having the urine detection circuit 210 is disposed on the inside of the absorbent article (eg, diaper or undergarment) and the urine detection circuit 210 faces the absorbent article (the substrate is between the urine detection circuit 210 and the skin). Pinched) or facing the wearer's skin. The urine detection circuit 210 may alternatively be located outside the absorbent article and the urine detection circuit 210 is exposed to urine absorbed by the absorbent article. According to a further option, the urine detection circuit 210 may alternatively be integrated in the absorbent article, for example in the absorbent material of a diaper or sanitary napkin.

FIG. 3 illustrates another embodiment of a urine detection circuit 310 that may be used as the urine detection circuit 110 in the system 100. The urine detection circuit 310 has first and second electrodes 314 and 315. In contrast to the urine sensing circuit 210, the first and second electrodes 314, 315 may be made of the same conductive material, eg copper. The first and second electrodes 314, 315 are constructed in an antenna configuration. The first and second electrodes 314 and 315 are connected to the LC or RLC circuit 316, and the urine detection circuit 310 resonates according to the input high frequency signal. When urine is present at the first and second electrodes 314, 315, the resonant frequency of the urine sensing circuit 310 is (of the resistance or capacitance in the urine sensing circuit 310, such as between the first and second electrodes 314, 315). Change). The high frequency signal is transmitted by a transmitter coupled to the processing circuit 130, as described in detail below. Therefore, the processing circuit 130 determines that the urine detection circuit 310 is exposed to urine based on the changed response to the transmitted high frequency signal.

The change in the resonance frequency of the urine detection circuit 310 is influenced by the amount of urine released to the urine detection circuit 310. In other words, the presence of urine changes the environment around the first and second electrodes 314, 315, which changes the resonance conditions for the urine detection circuit 310. The greater the change in environment, the greater the change in resonance conditions. Changes in the environment may cause, for example, shifts, broadenings and/or spectral changes in the resonance conditions, and the amount of urine determined from the resonance conditions affected thereby. Therefore, the processing circuit 130 estimates the amount of urine released to the urine detection circuit 310. The processing circuit 130 can measure, for example, the power of the received response or the duration of the received response, and the measured power can be the predetermined power (eg, established by a calibration procedure) or duration and urine. Can be compared to a look-up table (LUT) that associates different amounts of exposure.

Referring to FIG. 3, the number of “finger-like” electrode portions of each electrode 314, 315 may be greater than or less than two. As mentioned above, a greater number of electrode portions provide a larger urine detection area for the urine detection circuit 310. Furthermore, the design and dimensions of the electrodes 314, 315 may be modified to obtain sufficient coupling to the incoming RF field on the one hand and, on the other hand, the desired sensitivity to urine for a particular application.

Also, according to an alternative embodiment described in connection with FIG. 2, instead of powering the transmission of wireless signals, the current generated in portion 212 is stored in the memory of urine detection circuit 210. Used to power the counter increments. For purposes of the following discussion, element 216 of FIG. 2 represents both memory and transmitter-receiver circuitry. The processing circuit is further configured to estimate the amount of urine released to the urine detection circuit based on the counter.

The memory of the urine detection circuit 210 may include, for example, an N-bit register, and the current/voltage in the memory (may be specific to a particular type and memory implementation, as will be appreciated by those skilled in the art). It is configured to shift some bits in the register from a "0" to a "1" when the current/voltage level required to power it is exceeded. The number of bits shifted is proportional to the voltage/current provided by portion 212. As a non-limiting example, the release of 1 ml of urine into portion 212 may result in a shift of one bit in the register from "0" to "1". The release of an additional 1 ml of urine into portion 212 may result in a doubling of the current/voltage generated in portion 212, thus causing another bit in the register to shift from "0" to "1". May bring. Preferably, the memory is a non-volatile memory and the state of the bit register will be maintained even when the memory is not powered. Thereby, the state of the bit register (and thus the value of the counter) is preserved even if part 212 is prior to the subsequent release of urine or a memory read is being performed.

The transmitter-receiver circuit of the urine detection circuit 210 is responsive to receiving a wireless readout signal from a readout unit (eg, a processing circuit 130 that transmits a wireless signal using a transmitter connected to the processing circuit 130). , The counter value is encoded into a response signal and the response signal is wirelessly transmitted to the readout unit using techniques well known to those skilled in the art. Optionally, the counter in the memory of urine detection circuit 210 is reset to zero after reading. The read signal is preferably transmitted at a fixed repetition rate (every 5-30 seconds, every 1-5 minutes, etc.). The operation of the transmitter-receiver circuit and the memory during reading is powered by the energy of the radio signal received from the reading unit, using well known circuit designs. Also, the operation is powered by a small battery.

The logic that governs memory update, read and initialization as well as transmitter-receiver operation may be implemented, for example, in an integrated circuit connected to electrodes 214, 215. To avoid or reduce possibly unwanted shifts in the resonant frequency of the urine sensing circuit 210, a fluid impermeable layer or encapsulation (eg, plastic) is configured to cover the urine sensing circuit 210, but the electrodes The portion 212 having 214, 215 is exposed. Thereby, exposure of other parts of the urine detection circuit 210 to the urine other than the part 212 is avoided or minimized. As well as avoiding electrical artifacts from the environment for the urine detection circuit 210, an insulating layer from, for example, a metallic material (the same or different material as used for the electrodes of the urine detection circuit 210) can be used to form the circuit 210. Is formed on the lower surface of the substrate 218 opposite to the surface provided with.

The urine detection circuit 210 may further include a timer, and the value of the timer at each increment of the counter can be recorded in the memory together with the value of the counter. Also, the recorded timer value can be encoded in the response signal sent to the reading unit. The reading unit thereby determines the relative timing of the counter increments. The timer is powered by the same battery as the transmitter-receiver circuitry and memory. The timer is also powered by an energy storage element such as a capacitor that is charged by the current generated in portion 212. Preferably, the energy stored in the energy storage element is sufficient to power the timer for a duration equal to or greater than the repetition rate of the wireless read signal from the read unit. Optionally, the timer (in addition to the counter in the memory of urine detection circuit 210) is reset to zero after reading.

Referring to FIG. 1, measurement circuit 120 is configured to perform bladder measurements to determine parameters that vary with bladder filling level. According to one embodiment, the measurement circuit 120 is configured to measure the impedance of the bladder of the wearer of the measurement circuit 120. Generally, as the amount of urine in the bladder increases (ie, the level of bladder filling increases), the impedance measured across the bladder will increase. Thus, the determined impedance forms a measurable parameter that varies with bladder filling level. The measurement circuit 120 (referred to herein as the impedance measurement circuit 120) is configured to transmit an electrical measurement signal through the bladder of the wearer. The measurement signal may be an AC signal. As a non-limiting example, the frequency may be, for example, in the range of 5 kHz to 200 kHz. As a non-limiting example, the current may be in the range of 10 μA to 1000 μA.

The processing circuitry 130, for example, compares the measured impedance with a look-up table (LUT) that associates a predetermined (eg, established by a calibration procedure) impedance value with different bladder filling levels.

The measurement circuit 120 is configured to perform a two-terminal measurement of impedance. The measurement circuit 120 includes a first skin electrode configured to be attached via the bladder to a wearer's skin on a first side of the bladder (advantageously generally the opposite of the first side). A measurement signal, the impedance of the bladder being transmitted, configured to transmit a measurement signal to a second skin electrode configured to be attached to the skin of the wearer on a second side of the bladder And the measurement signal received by the second skin electrode. Alternatively, the measurement circuit 120 is configured to perform a four-terminal measurement of impedance. Thereby the contribution of the electrode-skin contact resistance is compensated. In any case, the electrodes may be of the dry type, or of the gel type or of the wet type in order to improve the contact between the electrode and the skin.

The measurement circuit 120 is configured to repeatedly measure the impedance of the bladder. The measured impedance is digitized by the analog-to-digital converter of the measurement circuit 120 and stored in a memory or buffer accessible by the processing circuit 130. The measurement circuit 120 is configured to store a predetermined number of measured impedances, and to start discarding the oldest impedance measurement when the predetermined number is exceeded. This may conveniently be implemented, for example, using a first in first out buffer (ie a FIFO buffer).

Instead of the measuring circuit 120 for digitizing the measured impedance, an analog signal representing the measured impedance is provided to the processing circuit 130 and the analog signal received using the analog-to-digital converter of the processing circuit 130 is converted into an analog signal. The digitized and digitized signal can be stored in a memory or buffer accessible by the processing circuit 130.

According to an alternative embodiment, the measurement circuit 120 is configured to perform ultrasound measurements of the bladder. More specifically, the measurement circuit 120 determines or estimates the size of the bladder. This dimension may be, for example, the width of the bladder. Normally, as the amount of urine in the bladder increases (ie, the bladder filling level increases), the bladder will expand and the width dimension of the bladder will increase. The defined width thus forms a measurable parameter that varies with bladder filling level. The measurement circuit 120 (in this case referred to as the ultrasonic measurement circuit 120) is configured to have an ultrasonic transducer configured to transmit ultrasonic signals and receive ultrasonic echo signals. The ultrasonic transducer is configured to face a skin portion in the bladder region of the wearer when using the measurement circuit 120. As the bladder expands, the time between the echo signal resulting from the reflection in the bladder wall closest to the transducer and the echo signal resulting from the reflections in the remote and contralateral bladder walls will increase. As with the impedance measurement described above, the transducer is arranged to store the time difference between these two echo signals in a memory or buffer accessible by the processing circuit 130, for example a FIFO buffer as described above. Is composed of. To improve the accuracy of ultrasound measurements, the measurement circuit 120 can be provided by an array of ultrasound transducers to provide a more accurate estimation of bladder inflation based on the bladder width dimension at multiple locations. It is possible to obtain.

Although described as an alternative above, it would be possible to design the measurement circuit 120 to perform impedance measurements along with ultrasound measurements of the bladder. By determining and correlating both of these two different types of parameters, the accuracy of bladder filling level is improved.

In addition to the above measurements of bladder filling level, the measurement circuit 120 may perform one or a combination of bladder magnetic field measurements, bladder light reflectance measurements or bladder size or bladder pressure mechanical measurements (impedance and impedance). Instead of or in addition to ultrasonic measurements).

For magnetic measurements, the measurement circuit 120 may include an inductor circuit that creates an oscillating magnetic field through the bladder. As the bladder filling level increases, the increased amount of urine in the bladder induces eddy currents in the inductor circuit, resulting in the increased energy being dissipated by the magnetic field. A parameter proportional to this change is determined and digitized by the analog-to-digital converter of the measurement circuit 120. In light of the above description of the measurement circuit 120, the determined parameters are stored in a memory or buffer accessible by the processing circuit 130, for example in a FIFO buffer as described above.

For light reflectance measurements, the measurement circuit 120 may include optical transducers (eg, light emitting diodes and photodetectors). As a non-limiting example, the wavelength of light may be in the infrared region or in the near infrared region. The optical transducer is configured to face a skin portion in the bladder region of the wearer when using the measurement circuit 120. As the bladder expands, the blood flow characteristics of the bladder will change. This will affect the reflected optical energy received by the photodiode. The reflected light detected by the photodetector thus forms a parameter representative of bladder filling level. The power detected by the photodetector is digitized by the analog-to-digital converter of the measuring circuit 120. In light of the above description of the measuring circuit 120, the detected power value is stored in a memory or buffer accessible by the processing circuit 130, for example in a FIFO buffer as described above.

For mechanical measurements, the measurement circuit 120 is a strain gauge integrated into a flexible belt that is adhesively attached to the skin in the bladder region or provided around the waist of the wearer. It is configured to measure resistance. As the bladder expands, the electrical resistance of the strain gauge increases. Thus, resistance forms a parameter that is representative of bladder filling level. The resistance of the strain gauge measured by the measurement circuit 120 is digitized by the analog-digital converter of the measurement circuit 120. In light of the above description of the measuring circuit 120, the resistance value is stored in a memory or buffer accessible by the processing circuit 130, for example in a FIFO buffer as described above. The measurement circuit 120 optionally samples and records an accelerometer signal configured on the wearer's skin (close to the strain gauge or more generally on the wearer's ventral region) and caused by breathing. Compensate for the effect of strain on the strain gauge.

As described above, the processing circuit 130 estimates the amount of urine released to the urine detection circuit 110 in response to determining that the urine detection circuit 110 is exposed to urine, and the measurement circuit 120 causes the urine detection circuit 110 to estimate the amount of urine released. Data representative of the determined at least one parameter, the estimated motion and/or posture of the wearer based on the orientation or motion as determined by the sensor 140, and of the urine released to the urine detection circuit 110. And an estimated amount and are configured to be recorded. More specifically, the processing circuit 130 obtains the parameter stored last as determined by the measurement circuit 120 from the memory or buffer accessible by the processing circuit 130, for example, so that the urination event It is configured to record data representative of the parameter(s) as determined by the measurement circuit 120 immediately prior to detection. Further, the processing circuitry 130 estimates the wearer's movement/posture based on the movement and/or orientation measurements by the sensor 140, as described above. Thereby, the recorded data may be used to correlate the bladder filling level with the occurrence of a voiding or incontinence event, the wearer's movement and/or posture, and the amount of urine released. The data can be recorded in the memory of the processing circuit 130. The recorded data is stored for transmission to an external unit or for further analysis.

More specifically, the processing circuit 130 detects the at least one parameter as determined by the measurement circuit 120, the estimated motion/posture and the estimated amount of urine released to the urine detection circuit 110 detected urination event. Data can be recorded in a data structure that is linked to. The data is stored in, for example, an array data structure or as an entry in a database and released to at least one parameter as estimated by the measurement circuit 120, estimated motion/posture, and urine detection circuit 110. The estimated amount of urine is associated with the detected micturition event. Along with the data, an indication that the urine detection circuit is exposed to urine is stored, for example using a single bit binary flag. Optionally, system 100 may have a timer and the time of detection of a micturition event may be recorded in a data structure. The stored time corresponds to the time of day, for example.

The processing circuit 130 is also configured to continuously or repeatedly data representing the parameter(s) as determined by the measurement circuit 120 and compare it to a corresponding threshold. For example, if the measurement circuit 120 is configured to determine the impedance of the bladder, the threshold may be an impedance threshold that corresponds to a bladder filling level at which the risk of an involuntary voiding event is significantly increased. Therefore, the impedance threshold is referred to as the bladder filling threshold. The threshold value is stored in a memory accessible to the processing circuit 130. If the processing circuit 130 determines that the threshold is met or exceeded, an alarm signal (ie, a warning signal) is provided to the wearer to indicate an increased risk of an involuntary voiding event. Advantageously, the processing circuit 130 is adapted such that the difference between the determined impedance and the threshold value gives the wearer time to, for example, go to the toilet (eg, an incontinence event is expected to occur). A signal may be provided to the wearer when it is already below a predetermined amount (either 10 or 20 minutes in advance). The signal may be visual, audible and/or generated by a visual indicator (eg, display or LED), an audible indicator (eg, speaker) connected to the processing circuit 130 or a tactile indicator (eg, vibrator). It may be a tactile signal. Alternatively, the signal is provided by the processing circuit 130 to an external device (eg, a mobile phone, tablet computer or personal computer) that presents an alert or produces an audible alert on its display.

Also, the impedance-based threshold comparisons described above may be performed in a corresponding manner for the other parameter types described above, as determined by the measurement circuit 120. Therefore, each type of parameter threshold is referred to as a bladder filling threshold. The processing circuit 130 is configured to provide a warning signal in response to any one of the determined parameter(s) meeting or exceeding its associated threshold value.

The threshold(s) is predetermined, for example, during the calibration phase of system 100. According to an alternative embodiment, the processing circuit 130 is configured to determine the threshold(s). The processing circuit 130 sets or configures each threshold value based on the parameter(s) represented by the data recorded by the processing circuit 130 in response to detecting the incontinence event as determined by the measuring circuit 120. The processing circuit is configured to set or configure each threshold, for example in response to the first detected urination event. Optionally, the processing circuitry sets or configures each threshold based on both the parameter(s) determined by the measurement circuit 120 and the previously determined threshold. For example, if the data recorded by the processing circuit 130 represents a parameter value smaller than the previous threshold in response to the detection of a urination event, the new threshold may be configured to be smaller than the previous threshold. Conversely, if the data recorded by the processing circuit 130 represents a parameter value greater than the previous threshold in response to the detection of a urination event, the new threshold may be configured to be greater than the previous threshold. Thereby the threshold(s) are adapted based on the bladder filling level at the actual occurrence of the micturition event.

Optionally, processing circuit 130 is configured to repeatedly provide a signal indicative of bladder filling level. The signal indicates, for example, one or more values of the parameter(s) most recently determined by the measurement circuit 120. The signal also indicates a ratio or ratios between the value or values of the parameter or parameters most recently determined by the measurement circuit 120 and the associated parameter threshold. The signal is provided, for example, to a display that provides information that allows the bladder filling level to be a determined parameter. The value(s) and/or the ratio(s) are, for example, presented on a display connected to the processing circuit 120. Alternatively, the signal is provided by the processing circuit 120 to an external device (eg, cell phone, tablet computer or personal computer) that presents the value(s) and/or ratio(s) on the display.

In the case where the processing circuit 130 is configured to perform a threshold comparison, as described above, the parameter threshold may preferably be associated with the corresponding movement or posture of the wearer. For example, a first impedance threshold may be used when the wearer is lying down and a second impedance threshold may be used when the wearer is upright or walking. As a non-limiting example, the bladder of a particular person has an impedance of 40 ohms when the bladder contains 350 mL of fluid and is 42 ohms when the person is seated upright. If the impedance is ohms or 38 ohms, it is pre-determined by the clinician to be half full. By determining the impedance of the bladder for different postures or movement types, multiple thresholds are determined, each associated with a particular posture or movement type. The threshold value is stored in a memory or buffer accessible to the processing circuit 130.

FIG. 4 illustrates a further embodiment of a system 400 for monitoring incontinence. The system 400 comprises a urine detection circuit 410. The urine detection circuit 410 may be implemented according to the urine detection circuit 210 or 310 described above. System 400 further comprises a measurement circuit 420 corresponding to measurement circuit 120 and a sensor 440 corresponding to sensor 140. The measurement circuit 420 can measure the impedance of the bladder using the skin electrode 422, for example. System 400 further comprises a processing circuit 430 corresponding to processing circuit 130. The processing circuitry 430 represents data representative of the parameter(s) associated with the bladder filling level determined by the measurement cycle 420, data representative of the wearer's movement and/or posture, and an estimated amount of urine released. It has a memory 434 for recording thresholds and data. The processing circuit 430 may further include, for example, an analog-to-digital converter 432 for digitizing the measurement signals from the measurement circuit 420, the sensor 440 and the additional sensor 460. The system 400 may further include a measurement circuit 420, a processing circuit 430, a transmitter 436, a receiver 438, a sensor 440, and a battery 430 for powering the optional additional sensors described below. The receiver 436 includes a transmitter portion to support communication with external devices or communication networks (eg, Bluetooth® protocol such as Bluetooth® low energy), as well as (eg, using NFC). It may have both a transmitter section for sending read or inquiry signals to the urine detection circuit. Similarly, receiver 438 includes a receiver portion for supporting communication with external devices or communication networks (eg, Bluetooth® protocol such as Bluetooth® low energy), as well as (eg, NFC). It may also have both a receiver section for receiving a signal from the urine detection circuit.

Optionally, system 400 may further comprise a user interface (not shown in Figure 4). The user interface may include user input devices such as buttons or keypads, lights, speakers and displays such as liquid crystal (LCD) displays or light emitting diode (LED) displays. As mentioned above, the speaker and/or display may be used to provide indications and alerts to the user. The user interface may also have tactile indicators such as vibrators that are used instead or as a complement to speakers and displays.

Elements 420-460 are configured on the same carrier, as shown schematically in FIG. The carrier is preferably relatively lightweight and discreet (eg, by adhesive) to the skin at the bladder area of the wearer, secured to the wearer by straps, or secured to the edges of a diaper or undergarment. It may be a unit.

The processing circuit 430 may include, for example, a microprocessor or a CPU. The logic that governs the operation of processing circuit 430 is stored, for example, as software instructions in a storage medium (usually in a non-transitory form), such as memory 434, as the instructions are executed by processing circuit 430. Configured to perform the operations of processing circuit 430 described in the text. The memory 434 may be volatile memory, such as random access memory (RAM) or flash memory. Memory 434 may include, for example, a program section and a data section, where the program section stores the software instructions described above and the data section stores data and variables used to perform the described operations. .. Alternatively, the functionality of processing circuit 430 may be implemented in one or more integrated circuits, or even one or more application specific integrated circuits (ASICs) or field programmable gate arrays (FPGAs).

As shown in FIG. 4, if the urine detection circuit 410 is implemented according to the urine detection circuit 210, the urine detection circuit 410 may be exposed to urine by a receiver 438 connected to the processing unit 430. Generate a current that powers the transmission of the received wireless signal. In response to detecting the wireless signal, the processing circuit 430 determines that a urination event has occurred and, therefore, (determined by the measurement circuit 420 immediately prior to or at the same time as the wireless signal detection. The data representing the parameter(s), the estimated amount of urine released into the urine detection circuit, and the estimated movement and/or posture of the wearer. Alternatively, if the urine detection circuit 410 is implemented according to the urine detection circuit 310, the processing circuit 430 causes the urination event to occur when the response from the urine detection circuit 410 to the wireless signal transmitted by the transmitter 436 changes. Determine that. The processing circuit 430 can control the transmitter 436 to repeatedly transmit a wireless signal to the urine detection circuit 410 at a predetermined repetition rate.

Optionally, system 400 may include additional sensors, generally shown as element 460 in FIG. For example, system 400 may include a microphone to monitor urine flow during controlled urination (commonly referred to as voiding). The system 400 may further include a skin proximity sensor (eg, a capacitance-based or resistance-based touch sensor for detecting skin proximity or contact as is well known in the art). The skin proximity sensor is configured to provide a signal to the processing unit 430 in response to detecting reduced proximity or loss of contact with the skin of the wearer. The signal indicates to processing circuit 430 the detection of a "pants down" event. The event can be recorded by the processing circuit 430 in the memory 434 and can be associated with the current measurement of the measurement circuit 420 for bladder filling level. A "pants down" event means that the wearer went to the toilet for an intended urination (also known as urination). For analytical and diagnostic purposes, it is useful to record the bladder filling level when going to the toilet. Optionally, a "pants down" event triggers microphone activation, and based on the acoustic signal from the microphone, processing circuit 430 analyzes the sound of urination, for example by analyzing the amplitude of the acoustic signal from the microphone. , Determine if the urine flow is continuous or intermittent. The processing circuitry 430 may record this information (eg, as a bit flag indicating either continuous or intermittent flow) in conjunction with the "pant down" event described above. Further, the processing circuit 430 can record the measurement of the measurement circuit 420 regarding the bladder filling level after urination is completed. If the amount of urine remaining in the bladder exceeds a certain predetermined (and user-specific) amount, eg, 100 mL or 150 mL, an alert signal is generated (eg, via the system user interface). In response to the processing circuit detecting an incontinence event (ie, by determining that the urine detection circuit 410 is exposed to urine), such a measurement of bladder filling level after voiding may be performed. Therefore, the system 400 may be used for detection of urine retention. Detection of urine retention leads to urinary tract infections. It is also believed that processing circuitry 430 can record this information in memory 434. Optionally, instead of a dedicated skin proximity sensor, a urine sensing circuit 410 that exhibits altered electrical properties upon proximity or contact with the skin may be used to detect a pant down event.

Also provided within system 400 are temperature sensors for measuring skin temperature and/or ambient temperature. The system 400 may also include an altimeter for measuring altitude. Also, the data associated with the measurements performed by these additional sensors 460 are recorded by the processing circuitry 430 in the memory 434 in response to detecting the incontinence event. This additional data correlates the occurrence of incontinence events with additional parameters that have an impact on the occurrence of involuntary voiding events, thus allowing an even more accurate and comprehensive analysis of wearer incontinence events. You can

The recorded data is transmitted, if repeated or requested, by a transmitter 436 to an external device or communication network generally indicated by element 470 of FIG. The transmitter 436 uses, for example, the Bluetooth® low energy protocol. The external device 470 is, for example, a wearer's mobile device, a medical staff mobile device, and/or a network server. The external device is a small, battery-powered portable device, such as a device intended to be installed adjacent to the bed or in the wearer's room, or that is always on the wearer of system 400 throughout day-to-day work. It may be. The external device has a simple user interface such as a button or keypad and a display or other visual indicator. As a further example, the external device may be a mobile phone. The transmitted data, in turn, provides the wearer or medical staff with an indication on the mobile device of an impending or already occurring incontinence event, an estimated bladder filling level and/or the amount of urine released. Can be used for The transmitted data can also be used to determine incontinence diagnoses and to perform analytical studies to suggest treatments that are best suited to the user's condition.

For analytical and diagnostic purposes, the data recorded by the processing circuitry 130, 430 may be used to establish a urination log or urination diary. For example, a diary can show the amount of urine reduction during the daytime (daytime) and nighttime (nighttime) and its time, the amount of urine in the bladder before urination (normal urination) and urination time, urine flow, movement in incontinence events. And/or posture and current bladder filling level prior to each incontinence event.

As mentioned above, the systems 100, 400 are particularly useful for monitoring stress incontinence. It is also useful for monitoring urgency and mixed type incontinence. However, it should be noted that some urge incontinence events may result in an estimated peak clipping of urine volume if the urine leak exceeds the sensitivity range of the urine detection sensors 110, 210, 310, 410. Is.

In the above, the inventive concept is mainly described with reference to a limited number of examples. However, as will be readily appreciated by those skilled in the art, other embodiments than the one disclosed above are equally possible within the scope of the inventive concept as defined by the appended claims. ..

For example, instead of being wirelessly connected (and thus galvanically isolated), the urine detection circuit 110 is galvanically connected to the processing circuit 130 by wiring. The wiring may be integrated, for example, in underwear or in an absorbent article. For example, a urine detection circuit similar to urine detection circuit 210 may be used without transmitter 216 and the current or voltage generated at electrodes 214, 215 may be processed using techniques well known in the art. Is directly detected and measured by. According to another embodiment, a urine detection circuit similar to urine detection circuit 310 can be used, and the altered impedance, resistance, or capacitance between electrodes 314, 315 can be detected and measured directly by processing circuit 130. It As such, the processing circuit 130 can measure, for example, the voltage or current generated in the portion 212, or the impedance, capacitance or resistance between the electrodes 314, 315, the measurement being predetermined (eg, by a calibration procedure). It can be compared to a lookup table (LUT) that correlates (established) current/voltage/impedance/capacitance/resistance levels with different amounts of urine exposure.

In these examples, the electrodes 214, 215, 314, 315 of the urine detection circuit 1 can be formed on the substrates 218, 318 as thin layers, for example. These layers may be, for example, 1 micrometer thick and the electrodes are flexible, thus minimizing wearer discomfort. To further reduce the weight of the electrodes 214, 215, 314, 315, they are perforated.

As an alternative or in addition to the above measurements on bladder filling level, it is further contemplated that data on other parameters may be recorded. Therefore, a urine sensing circuit configured to exhibit altered electrical characteristics when exposed to urine (eg, corresponding to circuit 110, 210, 310 or 410) and whether the urine sensing circuit is exposed to urine. And urine detection circuitry configured to record data representative of measured or user-provided parameters affecting bladder filling levels in response to determining that the urine detection circuit is exposed to urine. A system for monitoring incontinence of a user is provided that includes a processing circuit (eg, corresponding to processing circuit 130 or 430).

The user-provided parameter may be the volume of liquid intake by the user, the type of liquid, the glomerular filtration rate (GFR), or the time of the last toilet visit. This parameter is input, for example, by the user, for example, via the user interface or the user interface (for example, 470) of the external device, and is transmitted to the processing circuit (for example, 430). Based on the user's fluid intake knowledge and glomerular filtration rate, the bladder filling level can be accurately calculated by calculation without requiring direct measurement of the bladder. The clinician determines the GFR parameter and installs it in the memory of the processing unit (or alternatively in the memory of the external device). One way to determine GFR is to collect urine (usually 24 hours) to determine the amount of creatine cleared from the blood over a given time interval. For example, removing 1440 mg within 24 hours is equivalent to removing 1 mg/min. If the blood concentration is 0.01 mg/mL (1 mg/dL), then 100 mL/min of blood can be said to be “cleaned” from creatine. This is because 100 mL of blood containing 0.01 mg/mL needs to be cleaned in order to obtain 1 mg of creatine. The creatine measurement is then correlated with, for example, the user's age, gender and race to determine the user's GFR.

The measured parameter is the time elapsed since the last time the user went to the toilet (eg by determining the time elapsed since the last "pants down" event determined using the skin sensor above), (user Can represent temperature or time (when it is determined that is urinating on the absorbent article).

If the system comprises a sensor (eg, sensor 140 or 440) configured to determine the orientation and/or movement of the sensor, the recorded data is based on the orientation and/or movement determined by the sensor, Represents a wearer's estimated movement and/or posture. If the system comprises a measurement circuit (eg, measurement circuit 120 or 420), the recorded data is representative of the parameter(s) determined by the measurement circuit. If the processing circuit is configured to estimate the amount of urine released to the urine detection circuit in response to determining that the urine detection circuit is exposed to urine, the recorded data is It represents the estimated amount of urine released to the urine detection circuit.

When used in combination with the above embodiments comprising a measurement circuit configured to perform a measurement of a wearer's bladder to determine at least one parameter that varies with bladder filling level, the bladder filling level and The recording of both parameter(s), which has an effect on the parameter(s) that varies with the level of bladder filling, thus allows an even more detailed and complete analysis and diagnosis of incontinence.

Claims (22)

A method of monitoring user incontinence, comprising:
Using a urine detection circuit provided in the absorbent article and presenting changed electrical characteristics when exposed to urine, a step of determining whether or not the user has urinated the absorbent article,
Using a measurement circuit to perform a measurement of the bladder to determine a parameter that varies with bladder filling level;
Determining a posture and/or movement of the user using a sensor attached to the user;
A processing circuit is responsive to the determination that the user urinates into the absorbent article and a processing circuit estimates the user's estimated movement and/or posture based on the parameter and the posture and/or movement determined by the sensor. And recording data representative of an estimate of the amount of urine released into the urine detection circuit. The method further comprises recording, by the processing circuit, the data and an indication that the user has urinated the absorbent article in response to the determination that the user has urinated the absorbent article. The method described in. Using the measurement circuit to perform a plurality of measurements of the bladder to determine a parameter that varies with the bladder filling level;
The method of claim 1, further comprising the step of recording, by the processing circuit, an association between each determined parameter and an indication indicating whether the user has urinated the absorbent article. The method of claim 1, wherein the amount of urine is estimated based on the magnitude of the altered electrical characteristic of the urine sensing circuit. Performing a plurality of measurements of the bladder using the measurement circuit to measure a parameter that varies with the filling level of the bladder;
The method of claim 1, further comprising: comparing each of the determined parameters with one or more thresholds respectively associated with motion and/or pose by the processing circuitry. Estimating the bladder filling level based on the determined parameters by the processing circuit;
Providing a signal indicative of the estimated bladder filling level. A method of monitoring user incontinence, comprising:
Using a urine detection circuit provided in the absorbent article and presenting changed electrical characteristics when exposed to urine, a step of determining whether or not the user has urinated the absorbent article,
Determining a posture and/or movement of the user using a sensor attached to the user;
In response to determining that the user urinates the absorbent article, a processing circuit measures a measured or user-provided parameter that affects bladder filling levels, and the posture and/or the determination of the sensor. Recording data representative of an estimated pose and/or movement of the user based on movement and an estimate of the amount of urine released to the urine detection circuit. The data represents parameters provided by the user,
8. The method of claim 7, wherein the user-provided parameter represents a volume of fluid intake by the user, a type of fluid, a glomerular filtration rate (GFR), or a last time to go to the bathroom. The data represents the measured parameters,
8. The method of claim 7, wherein the measured parameters represent time, temperature, time of day, movement or posture of the user since the last time he went to the bathroom. The at least one parameter represented by the data recorded in response to the detection of the urination event by the processing circuit after the urine detection circuit detects the exposure to urine; The method of claim 1, further comprising performing a comparison between the parameter determined by the measurement circuit. In response to detecting a micturition event by detecting that the urine detection circuit has been exposed to urine, the data is provided with the at least one parameter determined by the measurement circuit, the estimated pose and/or 2. The method of claim 1, further comprising recording movement and an estimated amount of urine released to the urine sensing circuit in a data structure that links a detected voiding event. The method of claim 11, wherein the data is recorded in an array data structure or as an entry in a database. The method of claim 1, further comprising the step of characterizing the type of movement by the processing circuitry as walking, running, or changing the orientation or posture of the user. The changed electrical characteristic is changed resistance, changed capacitance, changed inductance, changed impedance, changed resonance frequency, changed voltage generated by the urine detection circuit, change generated by the urine detection circuit. 2. The method of claim 1, comprising one or more selected from the group consisting of an applied current, an altered resonant frequency of the urine sensing circuit. The method of claim 1, wherein the measurement circuit measures the impedance of the bladder or performs an ultrasonic measurement of the size of the bladder. The measurement circuit is located at or near the bladder region of the user,
The method according to claim 1, wherein the sensor is provided in the same unit as the measuring circuit. The method of claim 1, wherein the urine detection circuit is located in association with underwear or underwear. 18. The method of claim 17, wherein the measurement circuit is secured to the edge of the undergarment or undergarment. 8. The method of claim 7, further comprising calculating the bladder filling level based on fluid intake and glomerular filtration rate (GFR) by the user. Using a measurement circuit to perform a measurement of the bladder to determine a parameter that varies with the filling level of the bladder;
8. The method of claim 7, further comprising: recording, by the processing circuitry, data representative of at least one of the parameters in response to the user urinating the absorbent article. The urine detection circuit is located in relation to underwear or underwear,
The measuring circuit is fixed to an edge of the undergarment or undergarment at or near the bladder region of the user,
The method according to claim 20, wherein the sensor is provided in the same unit as the measuring circuit. 21. The method of claim 20, wherein the measurement circuit measures the impedance of the bladder or performs an ultrasonic measurement of the size of the bladder.

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