System and Method for Monitoring Hydration Status of a Human Body

Abstract

A system for monitoring hydration status of a human body is provided. The system comprises a plurality of sensors adapted to perform bio-impedance measurements at predefined locations on the body, thereby generating respective measurement data. The system further comprises a processing unit adapted to receive and to process the measurement data in order to estimate a body composition parameter for the respective locations on the body. In this context, at least one sensor is adapted to perform bio-impedance measurement at the throat region or esophagus region in order to detect a swallowing or fluid intake event.

Claims

1. A system for monitoring hydration status of a human body comprising: a plurality of sensors configured to perform bio-impedance measurements at predefined locations on the body and generate respective measurement data; and a processing unit configured to receive and to process the measurement data and estimate a body composition parameter for the respective locations on the body based on the respective measurement data, wherein one sensor of the plurality of sensors is adapted to perform bio-impedance measurement at the throat region or esophagus region and detect a swallowing event or a fluid intake event.

2. The system according to claim 1, wherein the processing unit is further configured to control remaining sensors of the plurality of sensors based on the detected swallowing or fluid intake event.

3. The system according to claim 1, wherein the body composition parameter includes an estimation of fluid volume, fat mass, or lean mass.

4. The system according to claim 1, wherein the one sensor of the plurality of sensors is a first sensor, and wherein a second sensor of the plurality of sensors is configured to perform bio-impedance measurement at a predefined location capable of capturing the impedance changes of the stomach and generate measurement data for estimating a fluid volume in the stomach.

5. The system according to claim 1, wherein the one sensor of the plurality of sensors is a first sensor, and wherein a second sensor is adapted to perform bio-impedance measurement at a predefined location configured to capture the impedance changes of the bladder and generate measurement data for estimating a fluid volume in the bladder.

6. The system according to claim 1, wherein the plurality of sensors are interchangeable with respect to their respective locations on the body.

7. The system according to claim 1, wherein the plurality of sensors are integrated in clothing.

8. The system of claim 7, wherein the plurality of sensors are linked to their respective locations on the body.

9. The system according to claim 1, wherein the system is operable in an idle mode wherein at least one sensor of the plurality of sensors is continuously active and the rest of the sensors are in sleep mode.

10. The system according to claim 9, wherein the continuously active sensor performs bio-impedance measurement at the throat region or esophagus region and is configured to transmit a trigger signal towards the processing unit upon detecting a swallowing or fluid intake event.

11. The system according to claim 10, wherein the processing unit is configured to generate control signals based on the trigger signal in order to perform wakeup control of the sensors that are in sleep mode.

12. The system according to claim 1, wherein the processing unit configures the plurality of sensors based on predefined time settings in order to define a measurement duration and a measurement rate of recurrence for the respective sensors.

13. The system according to claim 1, wherein the plurality of sensors are further adapted to transmit the respective measurement data to the processing unit upon detecting a variation with respect to a reference value or to a value from an immediate preceding measurement.

14. The system according to claim 1, wherein the system further comprises at least one additional sensor adapted to perform galvanic skin response measurement or sweat composition measurement at a predefined location on the body, thereby generating measurement data for fluid loss estimation.

15. The system according to claim 1, wherein the system further comprises at least one additional sensor adapted to perform photoplethysmogram measurement at a predefined location on the body, thereby generating measurement data in order to increase the accuracy for the fluid estimation.

16. The system according to claim 1, wherein the processing unit is implemented on a cloud environment.

17. The system according to claim 1, wherein the system further comprises a user interface and whereby the processing unit is further adapted to configure the plurality of sensors based on control commands received from a user via the user interface.

18. A method for monitoring hydration status of a human body comprising the steps of: performing bio-impedance measurements at predefined locations on the body by a plurality of sensors, thereby generating respective measurement data; and receiving and processing the measurement data by a processing unit in order to estimate a body composition parameter for the respective locations on the body, wherein at least one sensor is adapted to perform bio-impedance measurement at the throat region or esophagus region in order to detect a swallowing or fluid intake event.

19. A computer program with program code configured to monitor hydration status of a human body according to the method of claim 14.

20. The computer program wherein the program code runs on a system according to claim 1.

Description

BRIEF DESCRIPTION OF THE FIGURES

[0044] The above, as well as additional, features will be better understood through the following illustrative and non-limiting detailed description of example embodiments, with reference to the appended drawings.

[0045] FIG. 1 shows the prospective body locations for compartment based monitoring approach by way of an example;

[0046] FIG. 2 shows an example embodiment of the system according to the first aspect of the disclosure;

[0047] FIG. 3 shows an example process flow chart for controlling the sensors;

[0048] FIG. 4 shows an example model for measurement data processing and feedback;

[0049] FIG. 5A shows an example correlation analysis of Thorax measurement for a heart failure patient;

[0050] FIG. 5B shows an example correlation analysis of Foot measurement for a heart failure patient; and

[0051] FIG. 6 shows an example embodiment of the method according to the second aspect of the disclosure.

[0052] All the figures are schematic, not necessarily to scale, and generally only show parts which are necessary to elucidate example embodiments, wherein other parts may be omitted or merely suggested.

DETAILED DESCRIPTION

[0053] Example embodiments will now be described more fully hereinafter with reference to the accompanying drawings. That which is encompassed by the claims may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein; rather, these embodiments are provided by way of example. Furthermore, like numbers refer to the same or similar elements or components throughout.

[0054] Reference will now be made in detail to the embodiments of the present disclosure, examples of which are illustrated in the accompanying drawings. However, the following embodiments of the present disclosure may be variously modified and the range of the present disclosure is not limited by the following embodiments.

[0055] In FIG. 1, the prospective body locations for compartment based monitoring approach are illustrated by way of an example. Considering the frequency response of bio-impedance and the dielectric/conductive properties of the different tissues, it is possible to estimate the diverse compartments of the human body, i.e., intracellular and extracellular water, lean mass, fat mass, etc. Measurement of total body bio-impedance is the most commonly used method for estimating whole body compartments. Many of the whole body bio-impedance instruments apply three approaches for impedance measurement: hand-to-foot method, foot-to-foot method and hand-to-hand method. The hand-to-foot one is the most commonly used method.

[0056] The aforementioned methods perform either a single measurement (e.g., whole body measurement) or multiple measurements (e.g., segmented approach) in order to estimate the total body water or composition. A continuous monitoring of current fluid status of a body cannot be achieved by a single whole body measurement or by the traditional segmented approach. With the idea of having sensors performing bio-impedance measurement, which can be placed anywhere on the body, the proposed disclosure introduces a novel compartment based monitoring in order to monitor the fluid status of the body continuously and further allowing feedback to the user.

[0057] Therefore, instead of measuring whole body bio-impedance (e.g., the hand-to-foot method), the disclosure proposes to perform multiple localized bio-impedance measurements by using multiple sensors. Each sensor will give localized fluid information, and the combined sensor network will provide overall fluid information and actionable information.

[0058] For example, the perspective locations for bio-impedance measurements on the body 1 can be defined based on patient's health conditions. In general, fluid intake can be estimated from measurements performed at throat region or at esophagus region 2 and at upper abdomen region or stomach 3. The volume of fluid output can be estimated from measurements performed at lower abdomen region or bladder 7. Additionally, with the help of galvanic skin response (GSR) and/or sweat composition measured at any location on the skin, e.g., 6, fluid loss through sweat can also be estimated.

[0059] These additional measurements provide a complete picture of the overall estimation for fluid output. In order to monitor the current fluid status, bio-impedance measurements can be performed at torso 4 as well as at peripheries 5. Hence, by means of the proposed compartment based measurement, multiple measurements on multiple locations of the body 1 can be performed, for example in a sequence, thereby facilitating a continuous monitoring of the fluid status of the whole body 1.

[0060] In FIG. 2, an example embodiment of the system 10 according to the first aspect of the disclosure is illustrated. The system 10 comprises a plurality of sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4 that perform bio-impedance measurement at specific locations on the body 1, thereby forming a sensor network. The system 10 further comprises a processing means 13 that is able to communicate with the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4, for example in a bi-directional manner. The sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4 can be remote sensors, where the processing unit 13 communicates with the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4 wirelessly.

[0061] In some example implementations, the processing unit 13 is realized in a cloud environment in order to incorporate the high degree of mobility and reliability of cloud based processing to access and to further process the measurement data. A user interface 15 is also incorporated into the system 10, through which a user can manipulate or expedite the measurement configuration as well as processing. The user interface 15 can be a smartphone, where the user can configure the system 10, e.g., via an application. Additionally or alternately, the user interface 15 can be a web-based graphical user interface (web-GUI), executable in a personal computer where the computer is connected to the cloud via internet.

[0062] As already mentioned above, the prospective measurement locations of the body are defined on the basis of a patient's health condition. For instance, a patient with congestive heart failure, measurements at pulmonary area and peripheral area provides a complete estimation of accumulated fluid in both lung and peripherals. Upon determining the locations, a user may link the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4 and the respective measurement locations through the user interface 15, e.g., via the application. Another possible implementation of the sensor network includes the integration of the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4 in clothing, either with adapters/holders on the clothing or fully integrated in clothing, thereby linking the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4 to the positions automatically. In one implementation, the processing unit 13 is able to collect measurement data continuously from the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4. Depending on the sensor location, measurement instances and intervals could be every 5-10 minutes for approximately 5-60 seconds. Particularly for this implementation, the processing unit 13 is not required to communicate bi-directionally with the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4. In this regard, the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4 are incorporated with on-sensor processing to detect a change in the measured data, either respect to a defined threshold or to the data from immediate preceding measurement. An if-statement would suffice to implement the detection algorithm. As a consequence, the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4 will only send the measurement to the processing unit 13 only when a change is observed.

[0063] In an example implementation, the processing unit 13 initiates the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4 to perform bio-impedance measurements, e.g., for 60 seconds, at the respective locations in order to collect initial measurement data as base or reference values. After the initial data collection, all but one sensor 11.sub.1 of the plurality of sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4 remain in a sleep mode. This configuration is hereafter referred to as the idle mode. During this mode of operation, one sensor or the throat sensor 11.sub.1 remains active and continuously monitors at the throat region or at esophagus region 2. The throat sensor 11.sub.1 performs bio-impedance measurement at throat or at esophagus region in order to detect a swallowing or fluid intake event.

[0064] Upon detecting a swallowing or fluid intake event, e.g., by means of valley detection or by detecting contraction at the esophagus tube mentioned before, the throat sensor 11.sub.1 transmits a trigger signal towards the processing unit 13. In response, the processing unit 13 generates control signals for wakeup control of the rest of the sensors 11.sub.2,11.sub.3,11.sub.4, thereby initiating bio-impedance measurements at other body locations. The sensors 11.sub.1,11.sub.2,11.sub.3, 11.sub.4 are further configured with respect to the measurement duration and the measurement rate of recurrence, for example by a user through the processing unit, so as to take the delays between fluid input and distribution into account.

[0065] For instance, upon initiating the sensors 11.sub.2,11.sub.3,11.sub.4 after detecting a swallowing or fluid intake event, data collection starts immediately at the stomach. In the beginning, the measurement rate of recurrence at the stomach is approximately every 10 seconds, later every 5 minutes and the measurement duration is typically 2 hours. Other sensors are also triggered immediately after the detection of a swallowing or fluid intake event, where data collection is performed in every 5-10 minutes. In this case, the processing unit 13 communicates with the sensors 11.sub.1,11.sub.2,11.sub.3, 11.sub.4 in a bi-directional manner and based on the trigger signal, the processing unit 13 sends control signal to dedicated sensors, which will then start/stop data collection with these sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4.

[0066] Alternately, it is further possible to configure the sensor network in a master-slave fashion, where the throat sensor 11.sub.1 operates as the master sensor and the rest are slave sensors. Upon detecting a swallowing or fluid intake event, instead of sending the trigger signal to the processing unit 13, the throat sensor 11.sub.1 uses the trigger signal for wakeup control of the rest of the sensors 11.sub.2,11.sub.3,11.sub.4, thereby initiating measurements at different body locations. In this case, the processing unit 13 is not exclusively required to communicate with the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4 in a bi-directional manner, especially if a user externally provides the base or reference values. The processing unit 13 is further able to send feedback to the user based on the processed data/results from respective measurements. Such a user can be an individual or a caregiver, where the feedback can be a trend or the actual values/thresholds. Such feedback can be categorized into short-term feedback and long-term feedback. Examples of short-term feedback may include health status of the heart failure patient for acute trend monitoring. The basis of this is to monitor fluid removal from the lungs or peripherals based on a change in treatment or follow up of the buildup of fluid after treatment changes.

[0067] Another example of short-term feedback may regard to monitoring of the total body water to provide feedback to the user if the subject is over-hydrated or dehydrated. Especially for kidney patients, this could relate to dialysis treatment or the amount of water they can still drink. Athletes or elderly persons can also use this to monitor dehydration or over-hydration. Examples of long-term feedback may include long-term trend monitoring in disease progression, either based on the time constants of transport between compartments or based on the status of one compartment.

[0068] Furthermore, in addition to the bio-impedance measurement sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4, the sensor network comprises additional sensors for estimating different physiological parameters in some example implementations. For example, a galvanic skin response (GSR) measurement sensor can provide measurement data from skin response in order to estimate fluid loss through sweat. A sweat patch can collect sweat at the surface of the skin and can measure different compositions, thereby providing measurement data from sweat analysis in order to estimate fluid loss through sweat. A photoplethysmogram (PPG) measurement sensor can provide insights on blood volume changes in the microvascular bed of tissue. Hence, fluid intake, distribution and output can be effectively estimated in order to model the fluid map for the whole body 1, whereby facilitating a continuous monitoring of hydration status for the whole body 1 or of a specific location on the body 1.

[0069] In FIG. 3, an example process flow chart for controlling the sensors is illustrated. The process flow chart corresponds to the implementation where the processing unit 13 utilizes a swallowing or fluid intake detection event as a control parameter for the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4. After commencing the measurement 30, the processing unit 13 initiates 31 the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4, for example in a predefined sequence (e.g., based on a certain health condition to be monitored) and collects data with the sensors 11.sub.1,11.sub.2,11.sub.3,11.sub.4 for approximately 60 seconds in order to gather reference values. Once the reference data are collected, the system 10 maintains an idle mode 32 where only the throat sensor 11.sub.1 is active and is continuously monitoring and the rest of the sensors 11.sub.2,11.sub.3,11.sub.4 are inactive.

[0070] If the throat sensor 11.sub.1 detects a swallowing or fluid intake event, it transmits 33 a trigger signal towards the processing unit 13. The processing unit 13 further generates control signals based on the trigger input in order to sequentially activate the rest of the sensors 11.sub.2,11.sub.3,11.sub.4, thereby initiating an active mode 34. All sensors 11.sub.2,11.sub.3,11.sub.4 are therefore activated in sequence and start to collect data immediately after trigger. However, it is possible that the swallowing event does not correspond to an actual drinking incident, e.g., swallowing without actually drinking water, and therefore the trigger signal would be a false indication for commencing data collection with the sensors 11.sub.2,11.sub.3,11.sub.4.

[0071] In order to detect such false positive triggers, the processing unit 13 performs additional checks 35 on data collected at stomach. If the collected data do not show any significant discrepancy for a certain period after trigger, for instance, if the stomach sensor does not detect anything within 5-10 minutes after trigger, the measurement is terminated and the system resumes back to its idle mode 32. If the collected data at the stomach show sufficient change within this duration, the trigger is considered as positive trigger and the processing unit 13 continues with data processing 36 and with further feedback 37 to the user.

[0072] In FIG. 4, an example model for measurement data processing and feedback is illustrated. The model processing can be performed in the cloud environment. The rate and clearance constants (e.g., k.sub.12 and k.sub.ref_12) are in per minute and volumes are in liters. However, the model parameters can be personalized by a user with respect to a standard model. Additionally, the model parameters can be personalized based on calibration or on over time adaptation. The model processing can be automated based on a drinking activity, which is used as the calibration event. Bio-impedance measurement at throat (esophagus measurement) confirms the drinking activity where the stomach data is processed to estimate the volume of fluid intake.

[0073] With bio-impedance measurement and additional PPG and BP data processing result in the blood volume estimation (total blood equilibrium). Moreover, intra and extracellular volumes can further be estimated from the bio-impedance measurement. In this context, an alternative modeling between blood and extravascular space and between extravascular space and intracellular space can be based on osmotic pressure differences. The fluid output can be estimated from the bladder, e.g., by estimating the volume of fluid loss through urine, as well as from the estimation of fluid loss through sweat.

[0074] Standard model processing can be incorporated herein in order to get references and/or thresholds for data collection and processing. For instance, with respect to the delay between fluid intake and distribution, it takes typically 5 minutes for water to show up in the blood after drinking and 11-13 minutes before half of the water is absorbed. Generally, it takes 75-120 minutes before all water is absorbed into the body. The water is detected initially in the central compartment (blood and extravascular with rapid uptake) and next is spread to peripheral compartment (extravascular with slow uptake).

[0075] In terms of fluid removal, kidney produces an average of 30-50 ml urine per hour, where the normal range per day is 0.6-2.6 liters. This is also vastly dependent on hydration status. Bladder can hold 300-400 ml for up to 2-5 hours. Fluid removal through sweat is dependent on any ongoing activity as well as on the ambient temperature. Any field activity result in higher fluid loss through sweat, e.g., playing cricket typically results in a fluid loss of 0.5 liters per hour, playing rugby results in 2.6 liters per hour. Moreover, the average amount of fluid loss for a healthy person during sleep, e.g., through sweat and through exhale, is approximately 25 ml per hour.

[0076] It is to be noted that, in order to estimate fluid amount (or TBW) fit function using metadata (such as, but not limited to, gender, age and weight) from the subject and 30 data from the bio-impedance measurement as an input to reference fluid measurements. To obtain the bio-impedance parameters, the bio-impedance measurement should be pre-processed and for some of the parameters a human tissue model should be fitted.

[0077] Along FIG. 5A and FIG. 5B, example correlation analysis between fluid balance and bio-impedance for a heart failure patient are illustrated. In particular, FIG. 5A shows the correlation between fluid balance and bio-impedance on thorax, and FIG. 5B shows the correlation between fluid balance and bio-impedance on foot. In both illustrations, the left vertical axis denotes measured bio-impedance in ohm, the right vertical axis denotes fluid balance in liter and the bottom horizontal axis denotes elapsed time in hour.

[0078] Heart failure often only affects the left or right side of the heart, but can affect both. In the case of left-sided heart failure, the left ventricle of the heart no longer pumps enough blood around the body. As a result, blood builds up in the pulmonary veins (i.e., fluid accumulated in the lung). In the case of right-sided heart failure, the right ventricle of the heart is too weak to pump enough blood to the lungs. This causes fluid buildup in the peripherals. In the case of biventricular heart failure, both sides of the heart are affected, which leads to the combined effects as both left-sided and right-sided heart failure.

[0079] Moreover, if the monitoring is performed only on the thorax, e.g., a single/dedicated sensor measurement system, it can have better sensitivity to the fluid in the lung, especially compared to the whole-body bio-impedance, but it cannot detect the fluid balance from the other body part. Having multiple bio-impedance sensors forming a sensor network resolves the foregoing limitation, which can be implemented for monitoring patients' conditions with either one-sided heart failure or biventricular heart failure.

[0080] The correlation analysis along FIG. 5A and FIG. 5B are performed on a patient with right-sided heart failure. It can be seen that, for thorax measurement (FIG. 5A), no correlation between fluid balance and measured bio-impedance is present since there is no pulmonary congestion. By contrast, for foot measurement (FIG. 5B), high (negative) correlation between fluid balance and measured bio-impedance is observed, especially due to peripheral congestion. Such high correlation is expected since the patient is suffered from right-sided heart failure. Therefore, thorax measurement (e.g., with a single or dedicated sensor) is desirable for left-sided heart failure but not for right-sided heart failure or for biventricular heart failure. A sensor network with multiple sensors can evidently provide more insights about the whole body fluid map.

[0081] Furthermore, the present disclosure can also be implemented for monitoring patients with chronic kidney disease. Generally, patients with kidney disease accumulate the fluid in their whole body in-between two dialysis sessions. The proposed compartment based measurement approach can provide the information about fluid status of the patient in real-time, so that they know how much they can drink more or how much they have to remove during dialysis. In addition to the current fluid status, fluid intake and output are also monitored continuously for generating complete feedback to the caregiver.

[0082] The present disclosure is not limited to patient monitoring with certain health conditions, it can further be implemented for general hydration monitoring for athletes or elderly people. Elderly people or people undergoing extreme sport can experience extreme dehydration and only monitoring the amount of water consumption is can be problematic, since it does not show where the fluid goes after consuming. The present disclosure models a whole body fluid map using compartmental sensor network in order to monitor drinking, absorbing into the body, increase in total body water, excretion and decrease in total body water. Such an intense model can determine whether the person is in dehydration status or not in a superior manner.

[0083] In FIG. 6, an example embodiment of the method according to the second aspect of the present disclosure is illustrated. In a first step 100, bio-impedance measurements are performed by a plurality of sensors at predefined locations on the body, thereby generating respective measurement data. In a second step 101, the measurement data are received by a processing unit. In a third step 102, the measurement data are processed by the processing unit in order to estimate a body composition parameter for the respective locations on the body. The embodiments of the present disclosure can be implemented by hardware, software, or any combination thereof. Various embodiments of the present disclosure may be implemented by one or more application specific integrated circuits (ASICs), digital signal processors (DSPs), digital signal processing devices (DSPDs), programmable logic devices (PLDs), field programmable gate arrays (FPGAs), processors, controllers, microcontrollers, microprocessors, or the like.

[0084] While various embodiments of the present disclosure have been described above, it should be understood that they have been presented by way of example only, and not limitation. Numerous changes to the disclosed embodiments can be made in accordance with the disclosure herein without departing from the spirit or scope of the disclosure. Thus, the breadth and scope of the present disclosure should not be limited by any of the above described embodiments. Rather, the scope of the disclosure should be defined in accordance with the following claims and their equivalents.

[0085] Although the disclosure has been illustrated and described with respect to one or more implementations, equivalent alterations and modifications will occur to others skilled in the art upon the reading and understanding of this specification and the annexed drawings. In addition, while a particular feature of the disclosure may have been disclosed with respect to only one of several implementations, such feature may be combined with one or more other features of the other implementations as may be desired for any given or particular application.

[0086] While some embodiments have been illustrated and described in detail in the appended drawings and the foregoing description, such illustration and description are to be considered illustrative and not restrictive. Other variations to the disclosed embodiments can be understood and effected in practicing the claims, from a study of the drawings, the disclosure, and the appended claims. The mere fact that certain measures or features are recited in mutually different dependent claims does not indicate that a combination of these measures or features cannot be used. Any reference signs in the claims should not be construed as limiting the scope.