JP2016093209A - System for monitoring incontinence - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a system for monitoring incontinence.SOLUTION: A system for monitoring incontinence 400 comprises: a urine sensitive circuit 410 arranged to present a changed electrical characteristic when exposed to urine; a measurement circuit 420 arranged to perform a measurement on the urine bladder of a wearer to determine at least one parameter which varies with a fill level of the urine bladder; a sensor 440 arranged to determine an orientation or a movement of the sensor; and a processing circuit 430 arranged to determine whether the urine sensitive circuit has been exposed to urine, estimate the amount of urine released to the urine sensitive circuit, and in response to determining that the urine sensitive circuit has been exposed to urine, record data representing the at least one parameter determined by the measurement circuit, an estimated movement and/or posture of the wearer based on an orientation and/or a movement determined by the sensor, and an estimated amount of urine released to the urine sensitive circuit.SELECTED DRAWING: Figure 4

Description

  The inventive concept relates to a system for monitoring incontinence.

  Urinary incontinence or dysuria control function is a common problem affecting both men and women of all ages. Many people feel embarrassed and have no courage to go to the 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 wearer's inconvenience when an incontinence event occurs.

  Common types of urinary incontinence include stress and urge incontinence. There are also mixed types of incontinence that include both tension and urge incontinence. Stress urinary incontinence may be caused by loss of urethral support, usually as a result of childbirth, overweight or / and damage to the pelvic support structure as a result of some medication. Stress urinary incontinence typically involves a relatively small amount of urine leakage during an activity that increases abdominal pressure, such as coughing, sneezing and lifting, or rapid movement during sports activities, for example. It is characterized by. The main treatment for tension 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, urge incontinence may be caused by abnormal bladder contractions. This may also be referred to as an “overactive” bladder. Urinary urinary incontinence is typically characterized by a relatively large amount of urine leakage associated with insufficient warning to reach the toilet in time. Possible treatments for urge urinary 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 that rely on, for example, electrical sensors to detect the presence of urine in a diaper. Such prior art systems, however, can often only detect when the diaper is wet and signal the need to change the diaper, for example to the wearer or caregiver of the diaper. However, this only provides limited help to those suffering from incontinence, primarily in making 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 would allow improved monitoring of urinary incontinence. More specifically, the present inventor has a system for monitoring incontinence that provides for many people suffering from problems similar to incontinence, other than just the need to change diapers. Realized that would be useful.

  In accordance with one aspect of the present invention, a system for monitoring incontinence is provided, which system is configured to exhibit altered electrical characteristics when exposed to urine, and varies with bladder fill level. A measurement circuit configured to perform a measurement of the wearer's bladder to determine at least one parameter, a sensor configured to determine sensor orientation and / or movement, 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 Data representing this 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 To record and a processing circuit configured.

  The system detects actual involuntary urination events (hereinafter referred to as urination events or incontinence events), parameters indicating the level of bladder filling, and estimates of the wearer (indicating the wearer's current activity) It is possible to correlate the movement and / or posture and the estimated amount of urine released by the wearer. This type of correlation is particularly useful for monitoring tension urinary incontinence, which is typically characterized by a relatively small amount of urine leakage during activities that increase abdominal pressure, as described above. Information regarding bladder filling level, movement / posture and the amount of urine released is thereby useful for 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.

  The parameter indicating bladder filling level and the estimated movement and / or posture of the wearer are incontinence events by triggering the recording of data in response to detecting or determining that the urine detection circuit is exposed to urine Accurate monitoring is provided to accommodate conditions that are sometimes common. This accuracy will be difficult to achieve with any manual monitoring method.

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

  The processing circuit is further configured to record in this data an indication that the urine detection circuit is exposed to urine. The processing circuit thus has an indication that the urine detection circuit is exposed to urine and this 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 associate the quantity estimates (or link them with an indication that the urine detection circuit is exposed to urine).

  The processing circuit is configured to record 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 characteristics. More specifically, the processing circuit can determine that the urine detection circuit is exposed to urine by detecting the changed electrical characteristics of the urine detection circuit.

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

  According to one embodiment of the present invention, the altered electrical characteristics of the urine detection circuit indicate / proportional to the amount of urine released into the urine detection 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 into the urine detection circuit / proportional to the amount of urine released into the urine detection circuit, and the processing circuit is 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 present invention, the changed electrical characteristic or electrical response of the urine detection circuit is generated by the changed resistance, changed capacitance, changed inductance, changed impedance, changed resonant frequency, urine detection circuit. One or more selected from the group comprising: a changed voltage, a changed current generated by the urine detection circuit, 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 present invention, the urine detection circuit has a portion configured to generate a current when exposed to urine to provide power for transmission of a signal from the urine detection circuit, In response to receiving a signal from the circuit, the processing circuit is configured to record this data. Thus, a urination event directly triggers the recording of data by the processing circuit. Furthermore, no current is required in the urine detection circuit because the current that supplies power for signal transmission is generated by the urine. The urine detection circuit can thereby be manufactured at a reasonably relatively low cost.

  According to one embodiment of the present invention, the signal transmitted from the urine detection circuit indicates the amount of urine released to the urine detection circuit, and the processing circuit is directed to the urine detection circuit based on the signal received from 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 part is proportional to the surface area exposed to this part of urine.

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

  According to one embodiment of the present invention, the urine detection circuit unit is configured to generate a current when exposed to urine to supply power to an increment of a counter stored in the memory of the urine detection circuit. Has a part. Information regarding the amount of water resulting from multiple subsequent urinations is thereby gathered by the reduced amount of signal transmission between the processing circuit and the urine detection circuit.

  Therefore, 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 present invention, the processing circuit is further configured to record time data in response to determining that the urine detection circuit is exposed to urine. As a result, the time of the incontinence event is recorded.

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

  According to one embodiment of the present invention, the processing circuitry is configured to provide a signal indicative of a 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 relative or absolute representation. Based on this information, the user of the system can determine whether it is time to go to the toilet.

  According to one embodiment of the invention, the processing circuit is configured to provide a warning signal in response to determining that the urine detection circuit is exposed to urine. Thus, the user is informed that a urine leak has occurred that may otherwise have been missed without notice. This can make it easier for the user to understand which situations result in involuntary urination.

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

  According to one embodiment of the present invention, the measurement circuit and the processing circuit are connected in a direct current manner. This allows simple communication between the measurement circuit and the processing circuit.

  According to one embodiment of the present invention, the processing circuit and the urine detection circuit are separated in a DC manner. This simplifies the use of the system because the urine detection circuit may be handled without having to deal with wiring at all. 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 bladder dimensions. These types of measurements allow an accurate estimation of bladder filling level.

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

  According to an embodiment of the invention, the processing circuit is further configured to determine a threshold based on at least one determined parameter represented by the recorded data and a previously determined threshold. The advantages mentioned in connection with the previous embodiment apply to this embodiment as well. Further, the threshold determination is based on previously determined thresholds so that the thresholds are adjusted over time to better address a particular individual's incontinence issue.

  According to an embodiment of the present invention, the processing circuit is further configured to determine the threshold based on at least one determined parameter represented by the recorded data and the estimated motion and / or attitude. Since the wearer's movement and / or posture affects both the determination of the parameter (s) by the measurement circuit and the risk of incontinence events, this embodiment is assumed to have been present by the wearer during the incontinence event. Allows a threshold to be determined based on estimated motion and / or posture. Thus, 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 according to bladder filling level, and the processing circuit compares the repeatedly determined parameter to one or more bladder filling thresholds. Further configured, each threshold is associated with an orientation or movement determined by the sensor. The advantages of this embodiment can be understood from the previous embodiments.

  According to one embodiment of the present invention, after detecting a urination event (eg, by detecting that the urine detection circuit is exposed to urine), the processing circuit records in response to detecting the urination event. Is further configured to perform a comparison between the at least one parameter represented by the generated data and the parameter determined by the measurement circuit in the case after detection of the urination event. By comparing the level of fullness before and after urination, urinary retention problems can be identified.

  Also, according to one embodiment intended to form an individual inventive aspect, when in proximity to the user's skin, exhibits a first electrical characteristic or response 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 the level of bladder filling. And a first parameter determined by the measurement circuit in response to detecting a separation between the skin proximity sensor and the user's skin based on a changed electrical characteristic or response of the skin proximity sensor, Record data indicative of bladder filling level at a first time point at or prior to detection of separation, representing a second parameter determined by the measurement circuit, System and a processing circuit configured to record data indicating a bladder fill level is provided at a second time after the point.

  The processing circuit is configured to perform a 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 (for example, an assumed duration of normal urination). Alternatively, the second time point corresponds to a time point when the processing circuit detects or detects the restored proximity of the skin proximity sensor to the skin.

  The skin proximity sensor is an absorbent article worn by the user (such as diapers / diapers or underwear / underwear) or the upper edge of clothing (such as pants, shorts, skirts or the like worn by the user) It 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 its proximity to the skin. When the user pulls up the absorbent article or clothing after urination, the skin proximity sensor regains its proximity to the skin. Identify urinary retention problems by comparing the level before and after urination with the level of fullness.

As well as further objectives, the features and advantages of the inventive concept described above will become apparent from 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. 1 illustrates an embodiment of a urine detection circuit. 4 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 includes 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 characteristics or properties in response to being exposed to urine. As described in more detail below, the altered electrical characteristics of the urine detection circuit 110 indicate the amount of urine released to the urine detection circuit 110 or proportional to the amount of urine released to the urine detection circuit 110. To do. In use, the urine detection 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 to absorb urine). Or in relation to underwear or underwear. The wearer is also referred to as the user of the system 100. When an incontinence event occurs, urine is released to the absorbent article or the wearer's underwear, and the urine detection circuit 110 is exposed to the urine.

  The processing circuit 130 is configured to determine whether the urine detection circuit 110 is exposed to urine. As described in further detail below, the processing circuit 130 communicates with the urine detection circuit 110 (eg, over a wireless or wired interface) to detect urine detection by detecting that the electrical characteristics of the urine detection circuit 110 have changed. The circuit 110 is configured to determine that it is exposed to urine. The processing circuit 130 is also saturated with absorbent articles (eg, diapers / diapers, sanitary napkins / pads or some other article to absorb urine) to the user (eg, over a wireless or wired interface). And send a signal that it must be replaced. This will avoid leakage of the absorbent article. On the other hand, the measurement circuit 120 is configured to perform a measurement of the wearer's bladder to determine at least one parameter that varies with the level of bladder filling. The parameter (s) determined by the measurement circuit 120 may be, for example, an ultrasound measurement of bladder impedance and / or bladder size. Further examples are given below. The measurement circuit 120 is typically located in or near the wearer's bladder area. The measurement circuit 120 is provided, for example, in a unit that is secured to the skin in the bladder region (eg, with an adhesive), secured to the wearer with a strap, or secured to the edge of a diaper or undergarment.

  System 100 further comprises a sensor 140 attached to the wearer and configured to determine the orientation and / or movement of sensor 140. The sensor 140 may comprise an accelerometer and / or a gyroscope, for example in the form of a MEMS device. The accelerometer may be a single-axis accelerometer, a 2-axis accelerometer, or a 3-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 begin discarding the oldest measurement when the predetermined number is exceeded. This may be conveniently implemented using, for example, a first-in first-out buffer (ie, a FIFO buffer). The processing circuit 130 estimates the wearer's movement and / or posture of the sensor 140 based on the orientation and / or movement measurements. By comparing the motion measurements during the time interval, the processing circuit 130 determines whether the wearer was moving during the time interval and / or estimates the wearer's posture. The processing circuit 130 also optionally characterizes the type of movement as movement by walking, movement by running, or movement by the wearer changing orientation or posture. As a non-limiting example, if the axis of the accelerometer is oriented along the length of the body, the accelerometer is a signal corresponding to the acceleration due to gravity when the user is standing and when the user is lying Provides a signal close to zero. This concept is extended so that further postures can be specified.

  The wearer's movement pattern and posture of the sensor 140 further affects whether the current bladder filling level implies an increased risk of involuntary urination events. It also affects the parameter measurement (s), particularly the impedance measured by the measurement 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 is determined by the measurement circuit 120. To record data representing at least one parameter, an estimated movement and / or posture of the wearer based on the orientation or movement determined by the sensor 140, and an estimated amount of urine released to the urine detection circuit 110. Further configured. Since the occurrence of incontinence events is correlated to both the wearer's movement pattern or posture (ie activity) and bladder filling level, data representing parameter measurement (s), urine estimator and movement / posture combination Enables a more accurate and extensive analysis of wearer incontinence events.

  The processing circuit 130 is configured in the same unit as the measurement circuit 120 and is connected to the measurement circuit 120 in a direct current manner. 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. In addition, 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 exposed to urine increases (ie, due to an incontinence event), the electrical characteristics of the urine detection circuit 110 change from the first characteristic to the second characteristic. The altered electrical characteristics occur as a result of the urine detection circuit 110 changing from a relatively dry state (eg, before 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 that the urine detection circuit 110 is already wet (eg, as a result of the first incontinence event) to a much wetter state (eg, the second incontinence event after the first incontinence event). As a result of changing to (as a result). Accordingly, the electrical characteristics change in a manner that is proportional to the amount of urine to which the urine detection circuit 110 is exposed. In other words, the changed electrical characteristic of the urine detection circuit 110 indicates 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.

  Further, exposure to urine with respect to the urine detection circuit 110 may not necessarily mean direct contact with urine in this context. In fact, the urine detection circuit 110 may be embedded in the absorbent material so that direct contact with the urine released by the wearer may not occur. However, the presence of urine in proximity to the urine detection 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. Configured to be exposed to urine. Further, the electrical response of the urine detection circuit indicates 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 The urine detection circuit 110 is configured to estimate the amount of urine released to the urine detection circuit 110 based on the electrical response of 110.

  The changed electrical characteristic or electrical response of the urine detection circuit 110 may include, for example, a changed electrical parameter of the urine detection 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 changed impedance. Also, as described in detail below, the altered electrical characteristic or electrical response may be due to altered energy absorption of the received high frequency signal and / or (eg, altered resonant frequency and / or urine detection of the urine sensing circuit 110). It may contain altered energy of the high frequency signal transmitted from the urine detection circuit 110 (due to signal attenuation due to absorption of the transmitted / received high frequency signal by the urine in the circuit 110). Also, as described in detail below, the altered electrical characteristics may also include altered voltages at a pair of electrodes (eg, an anode-cathode pair) of the urine detection circuit 110.

  In addition, as will be described below, 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 a urine detection circuit 210 that may be used as the urine detection circuit 110 in the system 100. The urine detection circuit 210 has a portion 212 configured to generate an electrical current when exposed to urine. The urine detection circuit 210 has first and second electrodes 214 and 215. When urine is present between the electrodes 214, 215, the first electrode 214 is configured to function as an anode and the second electrode 215 is configured to function as a cathode. Thus, urine may function as an electrolyte and generate a voltage between the first and second electrodes 214, 215. Accordingly, the urine detection circuit 210 is configured to exhibit changed voltage and current characteristics when exposed to urine. The magnitude of the generated current is proportional to the surface area of the 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 contain copper, and the second electrode 215 may contain zinc. The first electrode 214 may contain carbon, and the second electrode 215 may contain magnesium.

  In the illustrated embodiment, each one of the first electrode 214 and the second electrode 215 has four elongated or finger-like electrode portions arranged in a comb-like structure. The electrode portions of the first and second electrodes 214 and 215 are alternately configured as shown. Such a configuration of the electrodes 214 and 215 is referred to as a comb electrode structure. The number of electrode portions of the first and second electrodes 214, 215 is varied to generate a current that is within a desired range for a particular application, thus making the sensitivity of the urine detection circuit 210 an application-specific requirement. It should be noted that it may be adapted accordingly. As can be appreciated, the maximum current generated in portion 212 is notably the electrode dimensions (eg, length), the amount of overlap between adjacent anode-cathode electrode portions, and the electrolyte concentration (ions) in the urine. Concentration). The current generated is thus increased by supplying salt (eg, sodium chloride) in portion 212. The maximum current is proportional to the number of electrode portions of the electrodes 214 and 215. Although more electrode portions result in a larger generated current, a single electrode portion of each electrode 214, 215 (eg, a single “finger”) may be sufficient in some applications. . It should also be understood that a greater number of electrode portions provides a larger urine detection area of the urine detection 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 the urine (eg, creatine, calcium or uric acid). When exposed to urine (and the analyte is present in the urine), the current generated in portion 212 is thereby increased.

  The first and second electrodes 214 and 215 can be connected to the transmitter 216 of the urine detection circuit 210 in a direct current manner. Thus, the current generated at electrodes 214 and 215 provides power to transmitter 216 for transmitting a radio signal from urine detection circuit 210. As will be further described below, a wireless signal can be received by a receiver connected to the processing circuit 130, and the processing circuit 130 can determine that the urine detection circuit 210 is exposed to urine.

  The larger current generated in portion 212 means more power supplied to transmitter 216. Thus, the power of the wireless signal transmitted from the transmitter 216 indicates the amount of urine released into the portion 212 or is proportional to the amount of urine released into the portion 212. The processing circuit 130 therefore 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 associating a predetermined level (eg, established by a calibration procedure) with a different amount exposed to the urine. It can be compared with a table (LUT).

  The transmitter 216 may generally have an LC circuit or an RLC circuit. Optionally, the antenna element can be connected to an LC or RLC circuit to improve the range of the 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 wireless automatic 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 a current-carrying part provided on the substrate 218 according to a process known per se to the person skilled in the art, for example by depositing a conductive material on the substrate or by masking and etching the conductive material from the substrate. Circuit elements forming 210 may be formed. The substrate 218 may be a thin plastic foil such as PET foil (polyethylene terephthalate). One surface of the substrate 218 can be provided with an adhesive. Therefore, the urine detection circuit 210 may be configured in a patch-like structure. The adhesive surface allows for 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 of 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. A substrate 218 having a urine detection circuit 210 is placed on the inside of an absorbent article (eg, a diaper or underwear) and the urine detection circuit 210 faces the absorbent article (the substrate is between the urine detection circuit 210 and the skin). Or face the wearer's skin. The urine detection circuit 210 may alternatively be disposed 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 shows 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 includes first and second electrodes 314 and 315. In contrast to the urine detection circuit 210, the first and second electrodes 314, 315 may be made of the same conductive material, for example copper. The first and second electrodes 314, 315 are configured in an antenna configuration. The first and second electrodes 314 and 315 are connected to an LC or RLC circuit 316, and the urine detection circuit 310 resonates in response to an input high frequency signal. When urine is present at the first and second electrodes 314, 315, the resonant frequency of the urine detection circuit 310 is the resistance or capacitance of the urine detection circuit 310, such as between the first and second electrodes 314, 315. Change). As described in detail below, the high frequency signal is transmitted by a transmitter connected to the processing circuit 130. 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 affected 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, thereby changing the resonance conditions for the urine detection circuit 310. As the environmental change increases, so does the change in resonance conditions. Changes in the environment can cause, for example, resonance conditions to shift, broaden and / or change in spectrum, so that the amount of urine can be determined from the affected resonance conditions. 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 measured with a predetermined power (eg, established by a calibration procedure) or duration and urine. Can be compared with a look-up table (LUT) that associates the different amounts exposed to.

  Referring to FIG. 3, the number of “finger-like” electrode portions of each electrode 314, 315 may be greater or less than two. As described above, a greater number of electrode portions provide a larger urine detection area of the urine detection circuit 310. Furthermore, the design and dimensions of the electrodes 314, 315 may be altered on the one hand to obtain sufficient coupling to the incoming RF field 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 supplying power to the transmission of the wireless signal, the current generated in the portion 212 is stored in the memory of the urine detection circuit 210. Used to power the counter increment. For the following discussion, element 216 in 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 current / voltage may be specific to the memory (as may be understood by those skilled in the art, may be specific to a particular type and memory implementation). It is configured to shift some bits in the register from “0” to “1” when the current / voltage level required to power is exceeded. The number of bits shifted is proportional to the voltage / current supplied from 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”. 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 shifting another bit in the register 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 hence the value of the counter) is preserved even if part 212 is before a subsequent urine discharge 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, 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 memory of urine detection circuit 210 is reset to zero after reading. The read signal is preferably transmitted at a fixed repetition rate (such as every 5-30 seconds, every 1-5 minutes, etc.). The operation of the transmitter-receiver circuit and memory during readout is powered by the energy of the radio signal received from the readout unit using well-known circuit designs. The operation is also powered by a small battery.

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

  The urine detection circuit 210 may further include a timer, and the timer value at each counter increment can be recorded in the memory together with the counter value. The recorded timer value can also be encoded into a response signal sent to the readout unit. Thereby, the readout unit determines the relative timing of the counter increment. The timer is powered by the same battery as the transmitter-receiver circuit 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 exceeding the repetition rate of the wireless readout signal from the readout unit. Optionally, the timer is reset to zero after reading (in addition to the counter in memory of urine detection circuit 210).

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

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

  Measurement circuit 120 is configured to perform a two-terminal measurement of impedance. The measurement circuit 120 (from the first skin electrode configured to be attached to the wearer's skin on the first side of the bladder via the bladder (advantageously generally opposite the first side). A measurement signal configured to transmit a measurement signal to a second skin electrode configured to be attached to the wearer's skin on the second side of the bladder (on the side), wherein the impedance of the bladder is transmitted And based on a 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 either case, the electrode may be a dry type, or may be a gel type or a wet type to improve contact between the electrode and the skin.

  Measurement circuit 120 is configured to repeatedly measure bladder impedance. 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. Measurement circuit 120 is configured to store a predetermined number of measured impedances and to begin discarding the oldest impedance measurement when the predetermined number is exceeded. This may be conveniently implemented using, for example, a first-in first-out buffer (ie, a FIFO buffer).

  Instead of the measurement circuit 120 digitizing the measured impedance, an analog signal representing the measured impedance is provided to the processing circuit 130, and the received analog signal using the analog-to-digital converter of the processing circuit 130. The 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 an ultrasound measurement of the bladder. More specifically, the measurement circuit 120 determines or estimates the bladder size. 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 bladder width dimension will increase. The defined width thus forms a measurable parameter that varies with bladder filling level. Measurement circuit 120 (in this case referred to as ultrasonic measurement circuit 120) is configured to have an ultrasonic transducer configured to transmit an ultrasonic signal and receive an ultrasonic echo signal. The ultrasonic transducer is configured to face the skin portion in the wearer's bladder region during use of the measurement circuit 120. As the bladder expands, the time between the echo signal resulting from the reflection at the bladder wall closest to the transducer and the echo signal resulting from the reflection at the remote and opposite bladder wall will increase. As in the case of measuring the impedance described above, the transducer is adapted to store the time difference between these two echo signals in a memory or buffer accessible by the processing circuit 130, for example in a FIFO buffer as described above. Configured. In order to improve the accuracy of ultrasound measurements, measurement circuit 120 can be provided by an array of ultrasound transducers to provide a more accurate estimate of bladder inflation based on bladder width dimensions at multiple locations. It is possible to obtain.

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

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

  For magnetic measurements, the measurement circuit 120 may include an inductor circuit that generates 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, with the result that the increased energy is 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. Based on 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 reflection 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 the skin portion in the wearer's bladder region during use of 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 representing the bladder filling level. The power detected by the photodetector is digitized by the analog-to-digital converter of the measurement circuit 120. In light of the above description of the measurement circuit 120, the detected power value is stored in a memory or buffer accessible by the processing circuit 130, eg, in a FIFO buffer as described above.

  For mechanical measurements, the measurement circuit 120 is a strain gauge integrated in a flexible belt that is glued to the skin in the bladder region or configured to be provided around the waist of the wearer. Configured to measure resistance. As the bladder expands, the electrical resistance of the strain gauge increases. Thus, resistance forms a parameter representing 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 measurement circuit 120, the resistance value is stored in a memory or buffer accessible by the processing circuit 130, eg, in a FIFO buffer as described above. Measurement circuit 120 optionally samples and records accelerometer signals configured on the wearer's skin (closer to the strain gauge or more generally on the wearer's ventral region) and caused by respiration. Compensate for strain gauge strain effects.

  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 Data representing the determined at least one parameter, an estimated movement and / or posture of the wearer based on the orientation or movement as determined by the sensor 140, and the urine released into the urine detection circuit 110. The estimator is configured to be recorded. Specifically, the processing circuit 130 obtains the last stored parameter as determined by the measurement circuit 120 from the memory or buffer accessible by the processing circuit 130, for example, by the processing circuit 130. It is configured to record data representing the parameter or parameters as determined by the measurement circuit 120 at the time immediately prior to detection. Further, the processing circuit 130 estimates the wearer's movement / posture based on movement and / or orientation measurements by the sensor 140 as described above. Thereby, the recorded data may be used to correlate bladder filling levels with the occurrence of urination or incontinence events, wearer movement and / or posture, and the amount of urine released. 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 at least one parameter as determined by the measurement circuit 120, the estimated movement / posture and the estimated amount of urine released to the urine detection circuit 110, and a urination event detected. Data can be recorded in the data structure linked to the. The data is stored, for example, in an array data structure or as an entry in the database and released to at least one parameter, estimated motion / posture, and urine detection circuit 110 as determined by measurement circuit 120 The estimated amount of urine is related to the detected urination 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 urination event can be recorded in the data structure. The stored time corresponds to the time, for example.

  The processing circuit 130 is also configured to compare data representing the parameter (s) as determined by the measurement circuit 120 continuously or repeatedly with a corresponding threshold value. For example, if the measurement circuit 120 is configured to determine bladder impedance, the threshold may be an impedance threshold that corresponds to a bladder filling level that greatly increases the risk of involuntary urination events. Thus, the impedance threshold is referred to as the bladder fullness 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 that the risk of involuntary urination events is increased. Advantageously, the processing circuit 130 is adapted so that the difference between the determined impedance and the threshold gives the wearer time to go, for example, to the toilet (eg, an incontinence event is expected to occur). A signal may be provided to the wearer when it is already less than a predetermined amount (in advance of 10 or 20 minutes before the time). The signal is generated by a visual indicator (eg, display or LED), an audible indicator (eg, a speaker) or a tactile indicator (eg, a vibrator) connected to the processing circuit 130, and / or It may be a tactile signal. Alternatively, the signal is provided by the processing circuit 130 to an external device (eg, mobile phone, tablet computer or personal computer) that presents a warning or generates an audible warning on its display.

  Also, the impedance-based threshold comparison described above may be performed in a corresponding manner for the other parameter types described above, as determined by the measurement circuit 120. Accordingly, 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.

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

  Optionally, the processing circuit 130 is configured to repeatedly provide a signal indicative of the 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 (s) 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 presented on a display connected to the processing circuit 120, for example. Alternatively, the signal is provided by the processing circuit 120 to an external device (eg, mobile phone, tablet computer or personal computer) that presents the value (s) and / or the ratio (s) on the display.

  As described above, in the case where the processing circuit 130 is configured to perform a threshold comparison, the parameter threshold may preferably be related to the wearer's corresponding movement or posture. For example, the first impedance threshold may be used when the wearer is lying, and the second impedance threshold may be used when the wearer is upright or walking. As a non-limiting example, a particular person's bladder is 42 if the bladder contains 350 mL of fluid, with 40 ohm impedance when the person is lying, and when the person sits upright. If the impedance is ohms or 38 ohms, it is pre-determined by the clinician to be half full. By determining bladder impedance for multiple 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 shows a further embodiment of a system 400 for monitoring incontinence. System 400 includes 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 includes 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. The system 400 further includes a processing circuit 430 corresponding to the processing circuit 130. The processing circuit 430 represents data representing the parameter (s) related to the bladder filling level determined by the measurement round 420, data representing the wearer's movement and / or posture, and the estimated amount of urine released. A memory 434 for recording threshold values and data is included. The processing circuit 430 may further include an analog-to-digital converter 432 for digitizing measurement signals from, for example, the measurement circuit 420, the sensor 440, and the additional sensor 460. The system 400 may further comprise 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. Receiver 436 includes a transmitter section to support communication with external devices or a communication network (eg, Bluetooth® protocol such as Bluetooth® low energy), and (eg, using NFC). You may have both the transmitter part for transmitting a reading or inquiry signal to a urine detection circuit. Similarly, the receiver 438 includes a receiver section for supporting communication with external devices or a communication network (eg, Bluetooth® protocol such as Bluetooth® low energy), and (eg, NFC). (Used) may have both receiver units for receiving signals from the urine detection circuit.

  Optionally, system 400 may further comprise a user interface (not shown in FIG. 4). The user interface may include a user input device such as a button or keypad, a light, a speaker, and a display such as a liquid crystal (LCD) display or a light emitting diode (LED) display. As described above, the speakers and / or displays 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 complements to speakers and displays.

  As shown schematically in FIG. 4, the elements 420-460 are configured on the same carrier. The carrier is preferably relatively lightweight and unobtrusive (eg, glued) to the skin in the wearer's bladder area, secured to the wearer with a strap, or secured to the edge 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 controls the operation of the processing circuit 430 is stored in a storage medium (usually in a non-transitory form) such as the memory 434, for example, as a software instruction, for example, when the instruction is executed by the processing circuit 430. Configured to perform the operations of the processing circuit 430 described in the document. The memory 434 may be a volatile memory such as a random access memory (RAM) or a 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 operations described. . Alternatively, the functions of the 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, when the urine detection circuit 410 is implemented according to the urine detection circuit 210, the urine detection circuit 410 is received by the receiver 438 connected to the processing unit 430 in response to being exposed to urine. A current is generated that supplies power to the transmission of the received radio 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 before or simultaneously with the detection of the wireless signal. 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, when the urine detection circuit 410 is implemented according to the urine detection circuit 310, the processing circuit 430 has caused a urination event when the response from the urine detection circuit 410 to the wireless signal transmitted by the transmitter 436 changes. Judge that. The processing circuit 430 can control the transmitter 436 to repeatedly transmit wireless signals to the urine detection circuit 410 at a predetermined repetition rate.

  Optionally, system 400 may comprise an additional sensor, generally shown as element 460 in FIG. For example, the system 400 may include a microphone for monitoring urine flow during controlled urination (usually referred to as urination). The system 400 may further comprise 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 per se). The skin proximity sensor is configured to provide a signal to the processing unit 430 in response to detecting a decrease in proximity or loss of contact with the wearer's skin. The signal indicates to the processing circuit 430 the detection of a “pants down” event. The event can be recorded in the memory 434 by the processing circuit 430 and can be associated with the current measurement of the measurement circuit 420 regarding the bladder filling level. The “pants down” event means that the wearer went to the bathroom for the intended urination (also known as urination). For analytical and diagnostic purposes, it is useful to record the level of bladder filling when going to the toilet. Optionally, the “pants down” event triggers the operation of the microphone, and based on the acoustic signal from the microphone, the 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. Processing circuit 430 may record this information (eg, as a bit flag indicating either continuous or intermittent flow) in conjunction with the “pants down” event described above. Furthermore, the processing circuit 430 can record the measurement of the measurement circuit 420 regarding the bladder filling level after the urination is finished. 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, determining that the urine detection circuit 410 is exposed to urine), such a measurement of bladder filling level after urination may be performed. Accordingly, system 400 may be used for detection of urine retention. Detection of urinary retention leads to urinary tract infections. It is also considered that the processing circuit 430 can record this information in the memory 434. Optionally, instead of a dedicated skin proximity sensor, an event that lowers the pants may be detected using a urine detection circuit 410 that exhibits an altered electrical characteristic when approaching or touching the skin.

  A temperature sensor for measuring skin temperature and / or ambient temperature is also provided in the system 400. The system 400 may also include an altimeter for measuring altitude. Also, data related to the measurements performed by these additional sensors 460 is recorded in memory 434 by processing circuit 430 in response to detecting an incontinence event. This additional data correlates the occurrence of incontinence events with additional parameters that have an impact on the occurrence of involuntary urination events, allowing for even more accurate and extensive analysis of wearer incontinence events Can do.

  The recorded data is transmitted by a transmitter 436 to an external device or communication network generally indicated by element 470 in FIG. 4 if repeated or requested. The transmitter 436 uses, for example, a Bluetooth (registered trademark) low energy protocol. The external device 470 is, for example, a wearer's mobile device, a medical staff's mobile device, and / or a network server. The external device is a small, battery-powered portable device that is intended to be installed next to the bed or in the wearer's room or that is always attached to the wearer of the system 400 throughout the day-to-day operation. There 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 of an imminent 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 an incontinence diagnosis and to perform an analytical study to suggest a treatment that best suits the user's condition.

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

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

  In the above, the inventive concept has mainly been described with reference to a limited number of embodiments. However, as will be readily appreciated by those skilled in the art, other embodiments than those 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 separated by DC), the urine detection circuit 110 is connected to the processing circuit 130 by DC. The wiring may be integrated, for example, in underwear or in an absorbent article. For example, a urine detection circuit similar to the urine detection circuit 210 can be used without the transmitter 216, and the current or voltage generated at the electrodes 214, 215 can be processed using techniques well known in the art. Is directly detected and measured. According to another embodiment, a urine detection circuit similar to the urine detection circuit 310 can be used, and the changed impedance, resistance or capacitance between the electrodes 314, 315 is directly detected and measured by the processing circuit 130. The Thus, 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, and the measurement can be determined in advance (eg, by a calibration procedure). Comparison can be made with a look-up table (LUT) that correlates the established (current) / voltage / impedance / capacitance / resistance levels with different amounts exposed to urine.

  In these embodiments, 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 drilled.

  It is further contemplated that data relating to other parameters can be recorded as an alternative or in addition to the above measurements relating to bladder filling level. Thus, a urine detection circuit configured to exhibit altered electrical characteristics when exposed to urine (eg, corresponding to circuit 110, 210, 310 or 410) and whether the urine detection circuit is exposed to urine Configured to record data representative of measured or user-supplied parameters that affect bladder filling level in response to determining that the urine detection circuit is exposed to urine. And a processing circuit (e.g., corresponding to processing circuit 130 or 430) is provided.

  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 last time that the user went to the toilet. This parameter is input by the user, for example, via the user interface or the user interface (eg, 470) of the external device, and transmitted to the processing circuit (eg, 430). Based on the user's knowledge of fluid intake and glomerular filtration rate, the bladder filling level can be accurately estimated by calculation without the need for direct measurement of the bladder. The clinician determines the GFR parameter and introduces 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 removed 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), it can be said that 100 mL / min of blood is “clean” from creatine. This is because in order to obtain 1 mg of creatine, 100 mL of blood containing 0.01 mg / mL needs to be clean. The measurement of creatine is then correlated, for example, with the user's age, sex, and race to determine the user's GFR.

  The measured parameter is (for example, by determining the time elapsed since the last “pants down” event determined using the skin sensor above), the time elapsed since the last visit to the toilet (user 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 sensor orientation and / or movement, the recorded data is based on the orientation and / or movement determined by the sensor; It represents the wearer's estimated movement and / or posture. If the system comprises a measurement circuit (eg, measurement circuit 120 or 420), the recorded data represents 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 into the urine detection circuit.

  When used in combination with the above embodiment comprising a measurement circuit configured to perform a measurement of the 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) having an effect on the parameter (s) that change with bladder filling level thus allows for a more detailed and complete analysis and diagnosis of incontinence.

Claims (15)

A urine detection circuit configured to exhibit altered electrical characteristics when exposed to urine;
A measurement circuit configured to perform a measurement of the wearer's bladder to determine at least one parameter that varies with the level of bladder filling;
A sensor configured to determine the orientation and / or movement of the sensor;
In response to determining whether the urine detection circuit 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 Data representing the at least one parameter determined by the measurement circuit, the estimated movement and / or posture of the wearer based on the orientation and / or movement determined by the sensor, and release to the urine detection circuit A system for monitoring incontinence comprising processing circuitry configured to record an estimate of the amount of urine that has been discharged.   The system of claim 1, wherein the altered electrical characteristic of the urine detection circuit indicates the amount of urine released into the urine detection circuit.   The urine detection circuit is configured to exhibit an electrical response indicative of the amount of urine released to the urine detection circuit when exposed to urine, and the processing circuit is configured to provide the electrical response of the urine detection circuit. To detect that the urine detection circuit is exposed to urine, and to estimate the amount of urine released to the urine detection circuit based on the electrical response of the urine detection circuit The system of Claim 1 or Claim 2 comprised by these.   The changed electrical characteristic or the electrical response of the urine detection circuit is a changed resistance, changed capacitance, changed inductance, changed impedance, changed resonance frequency, changed voltage generated by the urine detection circuit, The system according to any of claims 1 to 3, comprising one or more selected from the group comprising a changed current generated by the urine detection circuit and a changed resonance frequency of the urine detection circuit.   The system of claim 4, wherein the processing circuit is configured to estimate the amount of urine released to the urine detection circuit by determining the magnitude of the change.   The urine detection circuit has a portion configured to generate a current when exposed to urine to supply power for transmission of a signal from the urine detection circuit, and the signal from the urine detection circuit 6. A system according to any preceding claim, wherein the processing circuit is configured to record the data in response to receiving.   The signal transmitted from the urine detection circuit indicates the amount of urine released to the urine detection circuit, and the processing circuit releases to the urine detection circuit based on the signal received from the urine detection circuit. The system of claim 6, wherein the system is configured to estimate the amount of collected urine.   8. A system according to claim 6 or claim 7, wherein the current generated by the portion is proportional to the surface area of the portion exposed to urine.   The portion includes a first conductive path configured to function as an anode and a second conductive path configured to function as a cathode when the portion is exposed to urine. The system according to claim 8.   2. The urine detection circuit portion includes a portion configured to generate a current when exposed to urine to supply power to an increase in a counter stored in a memory of the urine detection circuit. The system according to claim 5.   The system of claim 10, wherein the processing circuit is configured to estimate the amount of urine released to the urine detection circuit based on the counter.   12. A system according to any preceding claim, wherein the processing circuit is further configured to record time data in response to determining that the urine detection circuit is exposed to urine. .   13. A system according to any of claims 1 to 12, wherein the processing circuit is configured to provide a signal indicative of a bladder filling level based on the at least one determined parameter.   14. A system according to any preceding claim, wherein the processing circuit is configured to provide a warning signal in response to determining that the urine detection circuit is exposed to urine.   The system according to any one of claims 1 to 14, further comprising at least one of a microphone, a temperature sensor, an accelerometer, an altimeter, or a skin contact sensor, or a combination thereof.

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