CN217546294U - Hearing system with hearing device and charging station - Google Patents

Abstract

The invention relates to a hearing system having a hearing device and a charging station which can be connected to the hearing device for energy transmission, the hearing device having a plurality of sensors for collecting first sensor data which enable the body state of a hearing device wearer to be inferred in a first period of time, and the hearing device further having a first memory in which the first sensor data are recorded, the charging station having a second memory, wherein the hearing device and the charging station can be connected in a data-technical manner and the first sensor data can be transmitted from the first memory of the hearing device to the second memory of the charging station, the charging station further having an evaluation device which is designed to compare the first sensor data with at least one predetermined reference value for at least one data category and to output a display command for an optical display of the deviation as a function of the deviation of the first sensor data of each data category from the associated predetermined reference value.

Description

Hearing system with hearing device and charging station

Technical Field

The utility model relates to a hearing system, it includes hearing equipment and can be connected so that the charging station of energy transmission with this hearing equipment, and the hearing system sets up to, through a plurality of sensors of hearing equipment collect and record first sensor data in first time quantum after the first time quantum, be connected hearing equipment and charging station on data technology, and will first sensor data transmission is to the memory of charging station.

Background

Many elderly people are helped by nursing or nursing staff in their daily lives. This is particularly applicable to the elderly who are cared for by caregivers in nursing homes, and also to the elderly who are under circuit care such as help in taking medicines at home or the elderly who are cared for by family members and are helped in daily life.

The caregiver often cannot immediately tell whether the person being cared for feels well overall, or whether there is a certain discomfort, which may even be caused by clinical signs. Particularly when only the overall comfort level is concerned, the caregiver relies on the information given by the caregiver, which is purely subjective and also depends on the communication ability of the caregiver. However, especially the elderly are often difficult to fully express this information, possibly due to purely phonetic problems, and possibly also due to the mental capacity that diminishes in some cases when assessing their own situation.

SUMMERY OF THE UTILITY MODEL

The object of the invention is therefore to provide a system by means of which data from which the comfort of a person can be inferred can be detected as objectively and automatically as possible and provided to the nursing staff for a better care and evaluation of the comfort.

The hearing device has at least one sensor for collecting first sensor data which enable an inference of the physical state of a wearer of the hearing device (also referred to below as a user of the hearing device), and a first memory for storing the first sensor data, wherein the charging station has at least one second memory which is provided for storing the first sensor data when the hearing device is connected to the charging station in a data-related manner, wherein the charging station also has an evaluation device which is provided for comparing the first sensor data with a predefined reference value for at least one data category, and for outputting a display command for an optical display of the deviation as a function of the deviation of the first sensor data of the or each relevant data category from the associated predefined reference value. Advantageous embodiments which are considered inventive in part per se are the subject matter of the dependent claims and the following description.

Preferably, the charging station of the hearing system also has a display device which generates a corresponding optical display in response to the display command. In particular, the display performed by the auxiliary device receiving and executing the display command can be omitted. In particular, the charging station has a detection device which detects when the hearing instrument is arranged in the charging position and can then initiate the energy transmission.

A hearing device is generally understood to be any device worn by a person on the ear in order to assist hearing or to compensate for hearing impairment. In particular, the hearing device has one or more input transducers, each of which converts ambient sound into a corresponding input signal, wherein the or each input signal is processed in accordance with the individual requirements of the hearing device wearer in order to compensate for the hearing impairment and is amplified and/or compressed here, in particular the video band. The hearing instrument also has at least one output transducer arranged to convert the or each processed input signal into a corresponding output sound signal which is input to the wearer's ear.

A charging station is to be understood here as any device which is provided as specified and which is structurally provided for charging a rechargeable power source (i.e. for example a battery or a battery) arranged in the hearing instrument by means of the hearing instrument. For this purpose, the hearing device is preferably arranged in or at the charging station in a charging position, characterized in that in the charging position energy can be transferred from the charging station to the hearing device, for example by inserting the hearing device into a charging housing provided for this purpose of the charging station in the case of wireless, in particular inductive, or RF high-frequency transmission, or by connecting a charging cable of the charging station with the hearing device in the case of wired energy transmission. In particular, the energy transfer can also be effected via the galvanic connection via the charging contacts themselves.

The hearing instrument can be connected to a charging station in data technology, so that the first sensor data stored in the first memory of the hearing instrument can be transmitted to the charging station via the data connection established in this way, in order to be stored there in the second memory. In the case of a charging cable for the energy transmission, the data connection can be established in particular via the charging cable. In the case of energy transmission of current, the data connection can be established via the current connection for energy transmission by modulating the transmission signal to form an alternating current for the charging process. In particular, however, wireless connections, for example by RF high-frequency transmission or inductive transmission, can also be used here for data transmission. For RF high-frequency transmissions, preferably in the frequency range from 100MHz to 10GHz, particularly preferably in the frequency range from 300MHz to 3GHz, it is possible in particular to use so-called electric antennas, which are coupled predominantly to the electric component of the high-frequency electromagnetic alternating field, and/or so-called magnetic antennas, which are coupled predominantly to the magnetic component of the high-frequency electromagnetic alternating field.

In particular, the energy transmission and the data transmission can take place in different ways, i.e. for example the data transmission takes place via bluetooth, while the energy transmission takes place via galvanic, capacitive or inductive coupling or via RF high-frequency transmission in other frequency bands than the frequency band used for bluetooth.

Possible sensors of the hearing instrument include, inter alia, a temperature sensor for determining the body temperature, a pulse sensor for determining the pulse rate, an acceleration sensor for determining the movement of the wearer, a magnetic field sensor and one or more input transducers of the hearing instrument. In this case, the first sensor data can comprise, as separate data categories, in particular the measured body temperature and/or the pulse rate and/or the movement activity determined by means of the signals of the acceleration sensor and/or the time profile for a telephone call determined by means of the magnetic field sensor and the time profile for the speech in the wearer environment (or surroundings) and/or the time profile and/or the level profile and/or the frequency profile of the own speech activity determined on the basis of the input signals and by means of a corresponding signal processing.

The first sensor data are therefore collected directly as data from the sensor or sensors which generate them, or are derived by preprocessing, in particular in the case of input signals generated by input transducers. The preprocessing can be based on purely creating a time profile, for example a movement activity of the wearer distributed over the course of the day, determined by means of the signals of the acceleration sensors, or the preprocessing can also be based on further processing and in particular deriving further variables, for example with regard to the dwell of the wearer in a speech-rich environment in the case of creating a time profile. In this case, one or more input signals (generated from ambient sound by one or more input transducers of the hearing instrument) are subjected to speech recognition, in particular a banded analysis is used for the speech recognition and a corresponding time profile is then established.

Based on the first mentioned sensor data, the physical state and in particular the comfort of the wearer of the hearing device can be inferred at least indirectly in a manner yet to be described.

The first sensor data generated on the basis of the signal of at least one sensor of the hearing instrument is here preferably collected over a first period of time, i.e. for example over the entire day from the beginning of the morning on which the hearing instrument is put on for a predetermined run until the evening takes off and the day-related run ends. The first sensor data is here stored on a first memory of the hearing instrument, which may be implemented as a volatile memory or a non-volatile memory powered by a battery. In this case, the removal can be performed in particular together with connecting the hearing instrument to a charging station for charging the power supply.

After the end of the first time period for collecting the first sensor data, a data connection for transmitting the first sensor data to a second memory arranged in the charging station is established between the hearing instrument and the charging station, and the first sensor data is transmitted accordingly. This is preferably done during a charging process of the power supply of the hearing instrument, which is charged by a charging station. The second memory, which is arranged in the charging station, for storing the transmitted first sensor data is in particular a non-volatile memory, in order to make the first sensor data also available for long-term analysis in a time-resolved manner. The second memory may also be formed by a battery-powered volatile memory, wherein the power supplied by the battery ensures that a charge representing the data state is received.

The reference values for the data classes can be predefined by predetermined values in general, in particular by the factory, and stored in the charging station, or can be adjusted by user input. Especially with regard to data categories relating to habits and daily life of the hearing device wearer, such as time distribution in a speech-enabled environment, meaningful predetermined values for the reference value may be related to said habits and may preferably be taken into account by a corresponding user input. The or each reference value is preferably stored in a memory of the charging station, wherein said memory for one or more reference values may be physically implemented on the same storage medium as the second memory for storing the first sensor data transmitted from the hearing instrument.

The evaluation device of the charging station is provided, in particular, by means of at least one processor and by means of a working memory addressable by the processor, for comparing the first sensor data with an associated reference value for at least one data category. In particular, the evaluation device can be implemented on a central control unit of the charging station, which also controls the charging process.

Deviations of reference values may be considered herein to be significant in only one direction, i.e., reference values are defined herein as limits. In particular, it is also possible to predetermine a plurality of reference values for each data category, so that, for example, an interval is formed by two reference values and, in the event of a deviation from this interval, the first sensor data is offset. In particular, a plurality of such intervals can also be defined for one or each data category by reference values, wherein the individual intervals can be assigned, for example, characteristic values that differ with respect to the degree of criticality, for example, for body temperatures up to 37.4 ℃: is not critical; [37.5 ℃,38.0 ℃): the temperature is raised; [38.1 ℃,39.0 ℃): fever is caused; [39.1 ℃,39.9 ℃): high-temperature roasting; not less than 40.0 ℃: very high heat, etc.

If a deviation from the reference value is detected, in particular in the form of exceeding the reference value defined as a limit value, the optical display can be generated by a display device provided on the charging station itself or a display command can be issued by the evaluation device via the communication device of the charging station, so that the caregiver can see the optical display generated in response to the deviation on an auxiliary device, for example a smartphone or tablet computer, as a result of the display command.

The display device of the charging station may be formed here on the one hand by a screen which is provided in particular for displaying text, so that the display may for example comprise a specific numerical indication of the deviation of the first sensor data from the reference value. On the other hand, the display device may also comprise at least one LED, preferably with one LED display per data category or with the aid of the same LED showing different colors for different data categories, so that a luminous signal is generated in the case of a deviation defined as critical. This may be combined with the screen output described above, among other things.

As reference values in the individual data categories of the first sensor data, in particular:

for the data category of daily wear time, which may be determined, for example, based on the running time and on the temperature determined by the temperature sensor of the hearing instrument, using a value of, for example, eight or ten or twelve hours (individually adjusted in particular according to the habits of the wearer);

using a value of 2 minutes per day or 5 minutes per day for a data category of a wearing time difference between a right unit and a left unit of a binaural hearing device;

for the data category of the pulse rate, for example using a value of 80 times per minute or 90 times per minute or 95 times per minute, which value may be further increased if necessary to, for example, 100 times per minute if the wearer is known to have hypertension;

for the data category of body temperature, a value is used, for example, between 37.0 ℃ and 37.5 ℃, for example 37.4 ℃;

for data categories for periods of time without significant motion, values of, for example, 30 minutes or 60 minutes are used;

for data categories of time periods that the hearing device wearer spends in a voiced environment (including watching television and listening to radio), values of e.g. 10 or 14 or 20 hours per week or 1.5 or 2 or 3 hours per day are used;

for the data category of the time period spent by the wearer of the hearing device in the environment with loudspeakers (the person speaking can be distinguished from the television or radio program by means of the audio signal transmitted directly from the television or radio device or alternatively by means of the hearing device wearer's own voice activity or by means of the WLAN signal of the television or radio device), a value of 5 or 7 or 10 hours per week or 1 or 1.5 hours per day is used;

for the data category of the time period spent by the hearing device wearer on the phone (which time period is identified by direct transmission of the audio signal of the phone to the hearing device or by a magnetic field sensor), a value of, for example, 1 or 3 hours per week or 15 or 30 minutes per day is used;

for the data category of the center frequency of the wearer's own voice, a value related to the corresponding previously measured wearer center frequency is used.

In particular, the individual adjustment for the reference value can be carried out for data categories relating to the habits and daily life of the wearer, but the factory presets are preferably selected from the mentioned value ranges.

If the wearer removes the hearing instrument at night (whereby the first time period ends) and connects the hearing instrument to the charging station for charging the battery, for example by inserting the hearing instrument into a provided charging housing of the charging station, a data connection between the hearing instrument and the charging station can also be established at this time, so that the first sensor data are transmitted from the first memory of the hearing instrument to the second memory of the charging station, and the first sensor data are transmitted accordingly and immediately subjected to said analysis in the analysis means with respect to the respective reference value.

At this time, if the first sensor data deviates from the reference value, the caregiver can identify by means of a corresponding optical display whether the health condition or the general comfort condition of the wearer is likely to deteriorate, so that the wearer's behavior can be monitored more accurately and the doctor notified (e.g. when fever occurs) if necessary. For example, if the wearer is moving significantly less than usual, or has significantly longer periods of inactivity than usual, or is averted from a talking environment, this may indicate a condition, increased social isolation, or tired state that requires more careful examination, depending on the age and other status of the wearer. The caregiver may be prompted to notify the physician via the optical display so that the physician may perform a detailed examination for a particular diagnosis.

In this case, the caregiver can see the optical display, in particular, on the display unit of the charging station, for example, on the screen as described above or on his smartphone or tablet, wherein, for the latter case, the smartphone or tablet is preferably configured to automatically connect to the charging station when the smartphone or tablet is sufficiently close to the charging station (for example, automatically "pairing" by bluetooth) in order to automatically transmit the display command for the optical display and, particularly preferably, in order to automatically display it.

Preferably, the hearing system has an establishable data-technology connection between the hearing device and the charging station when the hearing device is arranged in the charging position with respect to the charging station. Thus, the time at which the power supply of the hearing instrument is charged by the charging station is also used for the data transmission of the first sensor data. In this case, the charging position preferably has the features as described above.

Advantageously, the charging station also has a display device which generates a corresponding optical display in response to a display command. The display device may comprise a screen and/or a plurality of LEDs, which are provided in particular for displaying text and/or characters. In particular, in the case of the use of LEDs, different displays for different data categories, for example different colors of the LED display or different displays realized by different LEDs, are provided and provided for the respective deviation of the first sensor data from the associated reference value. The display device on the charging station eliminates the need for an optical display to be output by the auxiliary device, so that the nursing staff does not need to carry such auxiliary device with him.

Suitably, the hearing system is further arranged to collect and record the first sensor data in at least one of the following data categories: the wearing time of the hearing device, the difference in wearing time on the right or left ear, the pulse rate, the body temperature, the duration without significant movement, the time spent by the wearer in an environment with speech and/or speakers, the duration of the call, the frequency of the wearer's own voice. The above-mentioned data categories allow the collection of objective first sensor data that are already able to draw sufficient conclusions about possible changes in the wearer's state, without specific medical diagnostics being required in this case. If the optical display suggests consulting a physician, the medical diagnosis may be provided by the physician at the time of a detailed examination. The first sensor data can be presented to the physician by an optical display in order to make the most accurate diagnosis.

It has proven advantageous if the hearing system is configured to display the numerical deviation of the first sensor data from the reference value for at least one data category and/or to graphically display the deviation of the first sensor data from the reference value for at least one data category discretely on a criticality value grid and to display the corresponding criticality value. In this case, the indication of the deviation of the value is to be understood in particular as meaning that, for the data category concerned in which the deviation of the first sensor data from the associated reference value is determined, the value of the first sensor data is indicated together with at least one reference value, wherein in particular the value of the deviation can be indicated together. In particular, numerical deviations can also be shown separately. However, for at least one data category, deviations from at least one reference value can also be plotted discretely on the criticality value grid.

Thus, a reference value of, for example, 37.4 ℃ can be predetermined for the body temperature, and negative deviations can be classified substantially as non-critical, while positive deviations are classified as gridlike incrementally critical according to a single degree of Celsius (e.g., a deviation of less than 0.6 ℃ C.: not yet critical, but noteworthy; a deviation from 0.6 ℃ to less than 1.6: critical but not yet critical; a deviation from 1.6 ℃ is critical; etc.), wherein the maximum category that is open upwards can be defined if necessary. Similar gridding can be done for other data categories, especially for biometric data such as pulse rate (e.g. reference value 90 times/min for a certain age; negative deviation: not critical; from 90 times/min to less than 100 times/min: not critical but noteworthy; from 100 times/min to less than 120 times/min: critical but not yet dangerous; from 120 times/min to less than 180 times/min: dangerous; more than 180 times/min: very dangerous; etc.). The display here includes the assigned criticality value (i.e. for body temperature, for example "fever"), and may also include a numerical deviation and/or the value of the first sensor data and/or the reference value itself for a better overview.

The gridding of the first sensor data of the data category can thus be realized on the one hand by a plurality of reference values and the intervals formed therefrom having possibly different criticalities and, on the other hand, by gridding deviations from a single predetermined reference value and gridding deviations from the gridding with different criticalities. This may result in equivalent classification according to the data class, if necessary.

Preferably, the hearing system is configured to output an action recommendation and/or an action recommendation at least for the highest critical level value. For example, if the highest critical value (i.e. for example "very high fever" or a pulse rate rated as "very dangerous") is reached in the data category "body temperature" or "pulse rate", a consultant may be immediately recommended. As such, a period of time classified as critical motionless (e.g., no athletic activity exceeds a limit, measured by an acceleration sensor) may indicate that there is a physical problem with the wearer and it is also recommended here to consult a doctor or ask the wearer whether he is in pain or the like.

Advantageously, the charging station has a communication device, wherein the hearing system is also configured to output a medical warning message via the communication device of the charging station to a recipient remote from the charging station via the communication link, at least for the highest critical distance value. Especially for first sensor data from a category of biometric data such as body temperature or pulse rate, it may be advantageous for the doctor to receive the above-mentioned alarm prompt at the receiver, for example by email or other network-based message, directly and automatically by means of a charging station, without the work of a nursing staff (who first has to see and react to the optical output) being required in this case.

Advantageously, the hearing system is further arranged to collect and record the first sensor data in at least three of the following data categories: pulse rate, body temperature, blood pressure, blood oxygen saturation, and respiratory rate. The hearing system is further configured to form an Early Warning Score (EWS) based on the first sensor data recorded in at least three of the data categories, the early warning score having a value range that includes non-negative integer values, and wherein a corresponding optical display of the EWS is generated in accordance with the EWS by means of the charging station. EWS is used to estimate the severity of a possible illness in a person in a simple manner without the need for a specific diagnosis. For this purpose, the EWS uses the first mentioned sensor data, which are respectively represented as integers ≧ 0 for each individual data class, for example, a zero value is assigned to the temperature range from 36.0 ° to 37.9 ° for body temperature (or a slightly similar range). The individual values for the different data classes are then preferably added and the EWS is formed by the resulting sum.

On the one hand, the EWS thus produced can be displayed directly by means of a display device of the charging station. On the other hand, the EWS can also be monitored in time, in particular by means of a charging station, in order to generate a display when the EWS has reached a limit value (for example 2 or 3) in the meantime (even if the EWS is then below the limit value again), or when it is recorded that the EWS continues to increase (in particular compared to a previous hearing instrument data reading), for example from 0 to 1. In these cases it is suggested that the described embodiments of the method may advantageously indicate the measures by monitoring the comfort of the hearing device user and in particular the health status of the user in more detail by means of further measures.

It has proved to be further advantageous here if the hearing system is provided for additionally collecting electroencephalographic signals (EEG signals) as first sensor data, for estimating an attention value relating to the mental state of the wearer of the hearing device on the basis of the electroencephalographic signals, and for forming the early warning score also on the basis of the attention value. In this case, the attention value can be given in particular by a value which enables a classification of the consciousness of the wearer, i.e. for example by so-called AVPU values ("alert, veral, pain, nonresponsive"). In this category, the user is fully alert ("alert"), or he reacts only to speech ("verbal"; the reaction may be verbal or motor), or he reacts only to a set painful stimulus ("pain"), or he no longer exhibits any reaction ("unresponsive," unconscious state). The EEG sensor is here preferably arranged in the hearing device. The classification, i.e., for example, into the AVPU table, can be carried out in particular using a previously determined EEG signal with a corresponding response to a set stimulus, wherein, for example, an EEG signal generated in the hearing device can be compared with a previously determined signal value characterizing the EEG signal.

In a further advantageous embodiment, the hearing system is configured to preset a predetermined reference value for at least one data category, the preset being formed on the basis of an expected value of the first sensor data for the relevant data category, and/or wherein the reference value is individually adapted to the wearer of the hearing device. The general presetting can be carried out in particular at the factory, wherein the expected value of the first sensor data for the data category concerned can be queried, for example, from a health database. For the individual adjustment of the reference value to the wearer, the reference value can be determined in particular by means of one or more measurements in conjunction with the wearer (for example recording his voice in order to determine the center frequency, a heating measurement or a pulse measurement, etc.).

Preferably, the hearing system is configured such that, for at least one data category, the reference value is initially predefined by a general preset, wherein the reference value is individually adapted to the wearer of the hearing device, in particular by input of the hearing device acoustician and in particular within the range of adjustment of the hearing device, and the general preset of the reference value is overlaid by the individually adapted reference value. This can be done in particular by the hearing device acoustician within the scope of the adjustment of the hearing device, so that the wearer first lets the hearing device acoustician make an adjustment before the hearing device and the hearing system are actually put into operation, and the hearing device acoustician during the adjustment overrides the general preset of the reference value with a new value of the reference value, which has been determined individually for the wearer depending on the physical state of the wearer, in particular the health state and age of the wearer. For example, if the wearer has a known, slightly elevated hypertension, the preset reference value for the pulse rate may also be slightly increased.

But it is also possible to perform the personalized matching after a longer period of time (e.g. several weeks) when the hearing system is put into operation and used. In particular, reference values which constantly exceed a particular data class can be considered here, if this exceeding proves to be of no concern.

Preferably, the hearing system is configured such that the individual adaptation of the reference value is performed by remote adjustment via an internet connection to the charging station. This includes, among others: the hearing device acoustician can access the charging station via the internet connection within the scope of the remote adjustment, in which the wearer of the hearing device is not present in the space of the hearing device acoustician, and can therefore, via this access, overwrite the preset reference value with the reference value that is individually adapted to the wearer.

Suitably, the hearing system is configured such that the personalized matching of the reference values is carried out such that an electronic health record of the wearer is accessed for this purpose, wherein health data of the wearer is obtained from the electronic health record of the wearer, said health data being associated with data of at least one data category, such that the personalized matching is carried out on the basis of said health data of the wearer. For example, such an association may exist, for example, between health data about the wearer's blood pressure and a data category "pulse rate", or a previously known mental condition that causes the wearer to avoid a crowd, such that health data about the mental condition is associated with the data category "time spent in an environment with speakers". In this case, access can be effected within the scope of the above-described remote adjustment, preferably after the hearing device acoustician has obtained a corresponding authorization of the hearing device wearer or in the case of a "live" adjustment of the hearing device acoustician, or else by means of an automation service without any intervention by the hearing device acoustician.

Drawings

Embodiments of the invention are explained in more detail below with the aid of the figures. In the drawings, schematically:

fig. 1 shows a wiring diagram of a hearing system with a hearing instrument and a charging station with a memory for storing data of the hearing instrument;

fig. 2 shows a block diagram of a method for operating the hearing system according to fig. 1, in which data stored on the hearing device are transmitted to a charging station;

fig. 3 shows a longitudinal section through a hearing device and a charging station provided for carrying out the method according to fig. 2;

fig. 4 shows a schematic diagram of an alternative hearing system with a hearing device and a charging station, which hearing system is arranged for using data stored in the hearing device; and

fig. 5 shows a block diagram of the personalization of the reference values stored in the charging station according to fig. 2 for the wearer of the hearing device.

The components and dimensions corresponding to one another are provided with the same reference symbols in each case in all the figures.

Detailed Description

In fig. 1, a hearing system 1 comprising a hearing device 2 and a charging station 4 is schematically shown in a circuit diagram. In the present case, the hearing instrument 2 is designed as a monaural device. The hearing instrument 2 could equally easily be a binaural hearing instrument with a left unit and a right unit. The hearing instrument 2 has a first input transducer 6 and a second input transducer 8, which in the present case are provided by a microphone and are arranged for generating a first or a second input signal 12, 14 from ambient sound 10, respectively. The first and second input signals 12, 14 are each supplied to a control unit 16, in which the two input signals 12, 14 are processed in order to compensate for a hearing impairment of the wearer of the hearing device 2 and in this case in particular to enhance the two input signals in frequency bands. In this case, an output signal 18 is generated in the control unit 16, which output signal is converted by an output transducer 20 of the hearing device 2, which output transducer is provided by a loudspeaker in the present case, into an output sound signal 22, which output sound signal is provided to the ear of the wearer of the hearing device 2 when the hearing device 2 is operated as intended.

The hearing instrument 2 further comprises a temperature sensor 24, an acceleration sensor 26 and a pulse meter 28 arranged for measuring the pulse rate of the wearer. The temperature sensor 24, the acceleration sensor 26 and the pulse measuring device 28 are connected to the control unit 16 in order to transmit the respective measured values to the control unit 16. A first memory 30 is implemented on the control unit 16, which stores the measured values of the mentioned sensors in a manner to be described. For energy supply, the hearing instrument 2 also has a rechargeable battery 32, which supplies energy to the control unit 16, in particular when the hearing instrument 2 is in operation. For charging the battery 32, the hearing instrument 2 has an energy receiving means 34, which will be described below.

The charging station 4 has an energy output device 36 which, depending on its type and construction, is compatible with the energy receiving device 34 of the hearing instrument 2 for energy transmission. This means in particular that the energy receiving means 34 and the energy output means 36 can each be provided by an induction coil for inductive energy transfer or by metal contacts for a galvanic connection, by means of which an alternating current can be conducted from the charging station 4 to the hearing device 2. Likewise, the energy receiving means 34 and the energy output means 36 can be provided by electrodes, through which energy can be transmitted by means of capacitive coupling, or by receiving or transmitting antennas for high-frequency transmission. Inductive energy transfer is also possible. Electronic components, such as transformers and/or converters, for example, for the pretreatment and/or preparation of the network current 38 supplied to the charging station 4 prior to the transmission are understood here as components of the energy output 36 and are therefore not shown in detail.

The charging station 4 also has a non-volatile second memory 40, on which the data of the hearing devices 2 are to be stored in a manner to be described further below. The second memory 40 is connected to an evaluation device 42, which in particular has at least one processor (not shown in detail) and a working memory addressable by the processor, and the analysis means are arranged to evaluate data transferred from the hearing instrument 2 to the second memory 40. The evaluation device 42 is connected to a display device 44 of the charging station 4, which display device comprises in the present case a screen 46 and an LED 48. In this case, the screen 46 is provided, inter alia, for displaying text symbols, and the LED 48 is provided for outputting an optical signal. The evaluation device 42 is also connected to a communication device 50 of the charging station 4, which is provided for establishing an internet connection and for transmitting a message accordingly to a previously predefined internet address or other network-based service.

Fig. 2 shows a block diagram of a method for operating the hearing system according to the invention according to fig. 1 in order to explain the operating principle of the hearing system. The first time period 52, during which the first sensor data 54 is continuously collected in the hearing device 2, is given in the present case by the time period during which the wearer of the hearing device 2 is wearing the hearing device 2 during the day. This collection is carried out on the one hand directly by means of the sensor signals of the temperature sensor 24 and of the pulse meter, so that for the respective data category 56 of body temperature and pulse rate the first sensor data can be given directly from the sensor signals (over time). On the other hand, the signal of the acceleration sensor 26 and the first and second input signals 12, 14 may also be further processed in the control unit 16. The signal from the acceleration sensor 26 may, for example, determine a duration for the "inactive" data category 56 during which no significant motion activity is present. When the movement is determined to be significant, the intensity of the movement is not important here, in which case only movement pauses are taken into account.

By means of the input signals 12, 14 it can be recognized in the control unit whether the wearer of the hearing device is in an environment with speech at a given point in time, wherein it is also possible to distinguish whether the speech originates from a television program or a radio program. This differentiation can be effected, for example, by means of recognition of the wearer's own voice activity (and monitoring of the wearer's speech pauses) or else by means of a sufficiently strong WLAN signal emitted by a television (not shown) and detected by the hearing device 2. It is thus also possible to indirectly identify whether the wearer is in an environment with loudspeakers. It is thus possible to determine, for example, within the first time period 52, the total duration of time during which the wearer is subjected to speech during the first duration (i.e. distributed over the day), or the time during which the wearer is subjected to, for example, a television or radio program. The mentioned duration is then recorded as the first sensor data 54 for the respective data category 56 "in an environment with speech" or "in an environment with loudspeakers". The first sensor data 54 thus determined indirectly by means of the input signals 12, 14 are shown in fig. 2 as signal arrows from the control unit 16 (even if the entire signal processing and the processing of all sensor data can be carried out physically in the control unit 16).

The described first sensor data determined during the first time period 52 is stored in the hearing instrument 2 on the first memory 30.

After the end of the first time period 52, the hearing device 2 is arranged in a charging position of the charging station 4, which is characterized in that in the charging position a transfer of energy from the energy output means 36 of the charging station 4 to the energy receiving means 34 of the hearing device 2 is enabled in order to charge the battery 32 of the hearing device 2. This may for example be done in case the wearer takes off the hearing device 2 at night.

Here, when the hearing instrument 2 is arranged in the charging position, a data connection 58 is established between the hearing instrument 2 and the charging station 4. The data connection can preferably be established via the energy receiving device 34 of the hearing instrument 2 and the energy output device 36 of the charging station 4 according to fig. 1, for example in that the hearing instrument 2 modulates a weak alternating current (in the case of galvanic coupling) or an alternating field (in the case of inductive or capacitive coupling) preferably of high frequency in the case of energy reception to form a transmission signal for the energy transmission, which can be detected in the energy output device 36 and decoded accordingly.

The first sensor data 54 are transmitted via the data connection 58 established in this way to the second memory 40 of the charging station 4. For each individual data category 56, the evaluation device 42 compares the stored first sensor data 54 with a predefined reference value 60. If deviations, in particular reference values 60a defined as limit values, are found to be exceeded for one or more data categories 56a, the evaluation device 42 supplies corresponding display commands 62 to the display device 44 and displays the deviations for the relevant data category 56a as numerical values on the screen 46, preferably simultaneously specifying the data category 56a to which the deviation relates and particularly preferably simultaneously specifying the actual value given by the first sensor data 54 of the data category 56a and the associated reference value 60a.

This may be the case, for example, for body temperatures, wherein the reference value 60a is determined, for example, as 37 ℃, and each exceeding of the actually measured body temperature recorded in the first sensor data 54 is recorded as a deviation worth reporting and displayed on the screen 46 accordingly. Here, the deviations can also be plotted on a discrete grid of critical degree values, and additional instructions are provided for the deviations depending on the respective critical degree value. For example, for body temperature as data category 56, when a reference value of 37℃ is exceeded, an alarm prompt may be displayed on screen 46 with increasing risk levels for each increase of one degree Celsius. Furthermore, an alarm can be output at least for the highest critical value (in the case of a body temperature of, for example, above 40 ℃), which alarm is displayed by the LED 48 in the present case. Likewise, medical alert prompts are in this case output directly to the doctor via the communication device 50, for example via email or other web-based service on the doctor's smartphone or smartwatch.

Fig. 3 schematically shows a hearing device 2 designed as an ITE device ("in-ear") and a charging station 4 in longitudinal section. The hearing instrument 2 has a rechargeable battery 32. Here, an induction coil 66 is arranged in the housing 64 around the battery 32, which induction coil is provided on the one hand for receiving the charging signal and on the other hand for transmitting data stored in the hearing instrument. The charging station 4 belonging to the hearing instrument 2 has an induction coil 68 which is arranged such that the induction coils 66 and 68 of the hearing instrument 2 and the charging station 4 are directly opposite each other when the hearing instrument 2 is arranged in the charging position, i.e. positioned as prescribed for the charging process. Subsequently, the induction coil 68 of the charging station 4 provides a charging signal from which the induction coil 66 of the hearing instrument 2 derives energy for the charging process. The induction coil 66 can be modulated on its side upon the extraction of energy to form a signal, by means of which a data connection to the charging station 4 is made and which can transmit the first sensor data 14 stored on the hearing instrument 2 to the charging station 4, in particular, according to fig. 2. Alternative, not shown in detail forms of combined energy and data transmission between the hearing device and the charging station include, for example, current contacts arranged at corresponding positions on the hearing device 2 and on the charging station 4 or antennas for high-frequency transmission arranged in the hearing device 2 and in the charging station 4.

Another possibility of using the data collected during operation of the hearing instrument is shown by means of fig. 4. Fig. 4 shows, similarly to fig. 1, a hearing system 1, which comprises a hearing instrument 2 and a charging station 4, schematically in a circuit diagram. The hearing instrument 2 here has, in particular, a first memory 30 in which data 70 are stored continuously during operation of the hearing instrument 2. In this case, the data 70 may on the one hand comprise the first sensor data according to fig. 2, but may also contain further data, such as operating data, which relates to the direct operation of the hearing instrument. When the hearing instrument 2 is arranged in a charging position relative to the charging station 4 (e.g. by being inserted into a charging housing of the charging station 4 or pushing the hearing instrument 2 into a charging bay or the like provided in the charging station 4), the data 70 is also transmitted to the second memory 40 of the charging station 4. While a charging process for charging a battery (not shown) of the hearing device 2 may be performed.

The data 70 may include, in particular (the first sensor data 54 according to fig. 2 is not shown separately here):

a) User data relating to interaction with the hearing instrument 2: program changes, volume changes, manual restarts, length of use, frequency of hearing device removal during the day, etc.

b) User data relating to interaction with the environment: own voice activity, voice activity of the interlocutor, distance variation with respect to an effective signal source or an interfering signal source;

c) Environmental data: listening conditions (e.g., speech in quiet environments, speech with background noise, music, cocktail party, etc.), absolute loudness, signal-to-noise ratio (SNR), type of ambient noise;

d) Sensor data: GPS profiles, sensor data of geometric sensors (e.g., brain activity, blood glucose, pulse rate), user's athletic activity, body temperature, pedometer;

e) Other interactive and social information: user commands to a digital assistant ("Alexa", "Siri", etc.), time-dependent counts of questions (e.g. repeat command: "please repeat", "please say again"), social behaviors recognized in a time by means of a conversation, spoken language numbers.

Further data may be collected by the charging station 4 itself or may relate to other devices located in the environment of the charging station or the hearing device 2, such as:

f) Data of the charging station: time data (start, duration and end of the charging process), room temperature during the charging process and further sensor data of the charging station (if available), battery status (i.e. charge level) of the hearing device 2 at the start and/or end of the charging process;

g) Data of other connected devices: transmitter statistics of a television or other multimedia device (in particular television, radio) are in particular related to the duration of use of the multimedia device and the frequency of program changes.

An internet connection can be established via the communication device 50 of the charging station, so that the data 70 stored in the second memory 40 are transmitted to the cloud server 72 either in their entirety or as a function of previous analyses and corresponding selections by means of the analysis device 42, and are stored there in a personalized manner (for example under the account number of the user). On the one hand, the new data 70 can always be transmitted from the hearing device 2 into the second memory 40 of the charging station 4 (i.e. in particular during each charging process) or after a predetermined number of charging cycles (e.g. 10, 50 or 100). However, the transmission may also take place at a predetermined point in time, for example at a particular time on a particular working day, etc.

The analysis carried out beforehand can be carried out in this case in particular by means of user input with regard to the user's satisfaction with the hearing program proposed by the hearing device 2 or with regard to presettings or the like for a particular listening situation or the like, or with regard to the speech intelligibility or the like evaluated for the proposed algorithm for signal processing, but also by means of objective data, for example the number of program changes (in particular in relation to the respective listening situation) or the percentage time in certain listening situations. The user input for the analysis performed beforehand can also be stored as a function of a) as data 70 in the first memory 30 of the hearing instrument 2 and correspondingly transmitted to the cloud server 72 for availability there.

If the hearing system is also designed for the embodiment according to fig. 1 or fig. 2, the analysis can also be implemented in the embodiment according to fig. 4, in particular physically, in an analysis unit 42, which evaluates the first sensor data 54 with respect to the respective reference value 60 for the method according to fig. 2.

The data 70 of the wearer of the hearing device 2 stored in the cloud server 72 (in particular for the user account of the wearer) can then be accessed after a corresponding authentication or authorization check, in particular including an authorization by the hearing device acoustician or doctor (in particular an otolaryngologist, a general practitioner or a neurologist, etc.), in order to use the data 70 for the adjustment process of the hearing device 2 or, if necessary, for the diagnosis and/or treatment of the wearer, of the hearing device 2. In this case, the access can also be filtered in that a person who queries the cloud server 72 in order to access the data 70 stored in the cloud server for a specific wearer of the hearing device 2 is only transmitted with data from a specific data category, wherein the corresponding opening can be determined beforehand by means of the usage of the querying person. For example for hearing device acousticians, the transmission may be limited to the above types a), b), and c) of data, which contain the broadest sense of acoustic information.

The general practitioner can obtain additional information for diagnosis, for example, by means of data which record the motor activity or social activity (conversation, etc.) of the wearer of the hearing device 2 over a relevant period of time (for example, the last two weeks before the visit).

Fig. 5 shows the block diagram of a possibility for individually adapting the reference value 60 stored in the charging station 4 according to fig. 2 to the wearer of the hearing device 2. In the case shown, the hearing instrument 2 is connected to the cloud server 72 via the internet via the mobile telephone 74 by means of an application installed on the mobile telephone 74 and provided and set up in particular for this purpose. The cloud server 72 itself is also connected to a computer 76 of a hearing device acoustician 78. In this case, the computer 76 should be considered particularly generically as the entire analysis instrument available to the hearing device acoustician 78 for adjusting the hearing device 2.

Programs for remotely adjusting the hearing instrument 2 are run on the computer 76 in a manner not shown in detail, which programs communicate with the hearing instrument 2, in particular via the cloud server 72 and the mentioned application installed on the mobile phone 74, in order to adjust the acoustic parameters and/or other operating parameters of the hearing instrument 2 to the needs of the wearer of the hearing instrument 2 (for example according to a preset evaluation of the hearing instrument 2 by the wearer via the application). In the case of remote adjustment, the hearing device acoustician 78 can now override the reference value 60 of the charging station 4 preset at the factory delivery, for example when the preset value is found to be unsuitable for the wearer's situation, with the reference value 60 being a personalized match for the wearer of the hearing device 2 (for example, if the wearer is known to have a frequently rising blood pressure and/or pulse, and/or if the reference value 60 for a particular data category is frequently exceeded, without this having a significant effect on the physical state of the wearer, the reference value 60 in the data category "pulse" is raised).

In order to implement the described coverage of the reference value 60, an internet connection to the cloud server 72 is established via the communication device 50 of the charging station 4, via which the hearing instrument acoustician 78 can access the charging station 4 and the reference value 60 stored there. However, charging station 4 can also be connected to mobile telephone 74 via its communication device 50 and thus establish a connection to cloud server 72 using an application installed on the mobile telephone. In this case, the application installed on the mobile phone 74 acts as an interface for the entire hearing system 1 with respect to the cloud server 72.

The cloud server 72 may also establish a connection with a health database 80 in which an electronic health profile 82 of the wearer of the hearing device 2 is stored. After corresponding authorization and authentication, the cloud server 72 may obtain limited access to the electronic health profile 82 and here download from the health database 80 certain specific health data 84 that are closely associated with the data of the data category 56 transmitted from the hearing device 2 for storage on the charging station 4. The personalized adjustment of the reference values 60 previously stored on the charging station 4 can also be carried out here on the basis of the health status data 84 respectively associated with the respective data category 56. This can be done fully automatically by means of an algorithm executed for this purpose, in particular on the cloud server 72, or by a corresponding interaction of the hearing instrument acoustician 78, by which the hearing instrument acoustician is suggested, for example, with a new individualized reference value 60, wherein the hearing instrument acoustician 78 can also confirm or, if necessary, also change the suggested reference value 60 for covering the presettings on the charging station 4 within the corridor.

Although the invention has been illustrated and described in detail with respect to the details of the preferred embodiments, the invention is not limited to the disclosed examples, and various other modifications can be derived therefrom by those skilled in the art without departing from the scope of the invention.

List of reference numerals

1. Hearing system

2. Hearing device

4. Charging station

6. First input converter

8. Second input converter

10. Ambient sound

12. First input signal

14. Second input signal

16. Control unit

18. Output signal

20. Output converter

22. Outputting sound

24. Temperature sensor

26. Acceleration sensor

28. Pulse measuring instrument

30. First memory

32. Battery with a battery cell

34. Energy receiving device

36. Energy output device

38. Network current

40. Second memory

42. Analysis device

44. Display device

46. Screen

48 LED

50. Communication device

52. A first period of time

54. First sensor data

56. Data classes

56a data class

58. Data connection

60. Reference value

Reference value of 60a

62. Display command

64. Shell body

66. Induction coil

68. Induction coil

70. Data of

72. Cloud server

74. Mobile telephone

76. Computer with a memory card

78. Hearing device acoustics worker

80. Health condition database

82. Electronic health status file

84. Health condition data

Claims (15)

1. A hearing system (1) having a hearing instrument (2) and a charging station (4), wherein the hearing instrument (2) has at least one sensor (6, 8, 24, 26, 28) for collecting first sensor data (54) which enable the physical state of a wearer of the hearing instrument (2) to be inferred, and a first memory (30) for storing the first sensor data (54), wherein the charging station (4) has at least one second memory (40) which is provided for storing the first sensor data (54) when the hearing instrument (2) is data-technically connected to the charging station (4),

wherein the charging station (4) further comprises an evaluation device (42) which is provided for comparing the first sensor data (54) with a predefined reference value (60, 60 a) for at least one data category (56, 56 a) and for outputting a display command (62) for an optical display of the deviation as a function of the deviation of the first sensor data (54) of the or each relevant data category (56, 56 a) from the associated predefined reference value (60, 60 a).

2. The hearing system (1) as claimed in claim 1, characterised in that it has an establishable data-technical connection between the hearing device (2) and a charging station (4) when the hearing device (2) is set in a charging position with respect to the charging station (4).

3. The hearing system (1) of claim 1 or 2, characterized in that the charging station (4) further has a display device (44) which generates a corresponding optical display in response to the display command (62).

4. The hearing system (1) according to claim 1 or 2, characterized in that the hearing system is arranged to collect and record the first sensor data (54) in at least one of the following data categories (56, 56 a): -the wearing time of the hearing device (2), -the difference in wearing time on the right or left ear, -the pulse rate, the body temperature, the duration without significant movement, the time spent by the wearer in an environment with speech and/or loudspeakers, -the duration of a phone call, -the frequency of the wearer's own voice.

5. The hearing system (1) according to claim 4, characterised in that it is provided for the numerical deviation of the first sensor data (54) from the reference value (60, 60 a) to be displayed for at least one data category (56, 56 a) and/or for the deviation of the first sensor data (54) from the reference value (60, 60 a) for at least one data category (56, 56 a) to be plotted discretely on a criticality value grid and for the corresponding criticality value to be displayed.

6. The hearing system (1) as claimed in claim 5, characterized in that the hearing system is arranged to output action counseling and/or action advice at least for the highest critical degree value.

7. The hearing system (1) according to claim 5 or 6, characterised in that, wherein the charging station (4) has a communication device (50), and wherein the hearing system (1) is provided to output, at least for the highest critical degree value, a medical warning cue by the communication device (50) of the charging station (4) via a communication link to a recipient remote from the charging station (4).

8. The hearing system (1) according to claim 5 or 6, characterised in that it is arranged to collect and record first sensor data (54) in at least three of the following data categories (56, 56 a): pulse rate, body temperature, blood pressure, blood oxygen saturation and respiratory rate,

the hearing system is further configured to form an early warning score based on the first sensor data (54) recorded in at least three of the data categories, the early warning score having a value range that includes non-negative integer values, and to generate a corresponding optical display of the early warning score by means of the charging station (4) depending on the early warning score.

9. The hearing system (1) as claimed in claim 8, characterized in that the hearing system is provided to additionally collect electroencephalographic signals as first sensor data (54), to estimate attention values relating to the mental state of the wearer of the hearing device (2) on the basis of the electroencephalographic signals and to form the early warning score also on the basis of the attention values.

10. The hearing system (1) according to claim 9, characterised in that the hearing system is arranged to, for at least one data category (56, 56 a), preset predetermined reference values (60, 60 a) that are generally pre-set, which pre-set is formed on the basis of expected values of the first sensor data (54) for the relevant data category (56, 56 a), and/or to individually match the reference values (60, 60 a) to the wearer of the hearing device (2).

11. The hearing system (1) according to claim 10, characterised in that the hearing system is arranged to initially have a generally preset predetermined reference value (60, 60 a) for at least one data category (56, 56 a) and to have the reference value (60, 60 a) individually matched to the wearer of the hearing device (2), and that the generally preset for the reference value (60, 60 a) is overlaid by the individually matched reference value (60, 60 a).

12. The hearing system (1) according to claim 10, characterised in that the hearing system is arranged to initially preset a predetermined reference value (60, 60 a) for at least one data class (56, 56 a) by a general preset and to individually match the reference value (60, 60 a) to the wearer of the hearing device (2) by input of a hearing device acoustician (78) and within the scope of adjustment of the hearing device (2), and that the general preset for the reference value (60, 60 a) is covered by the individually matched reference value (60, 60 a).

13. The hearing system (1) according to claim 11, characterised in that it is provided for the individualized matching of the reference value (60, 60 a) to be carried out by remote adjustment via an internet connection with the charging station (4).

14. The hearing system (1) according to claim 12, characterised in that it is arranged to perform the individualized matching of the reference value (60, 60 a) by remote adjustment via an internet connection with the charging station (4).

15. The hearing system (1) according to one of the claims 11 to 14, characterised in that the hearing system is configured to access an electronic health record (82) of the wearer for the purpose of personalised matching of the reference values (60, 60 a) and to retrieve health data (84) of the wearer from the electronic health record (82) of the wearer, which health data is associated with data of at least one data category (56, 56 a) and to personalised matching is performed on the basis of the health data (84) of the wearer.

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