METHOD FOR OPERATING A HEARING AID AND HEARING AID

Abstract

A method is indicated for operating a hearing aid, wherein the hearing aid is switchable between a usage state, in which a signal processing unit of the hearing aid is activated, and an idle state, in which the signal processing unit is deactivated. The hearing aid has a time measuring unit, which has a first timer and a second timer. The first timer is activated in the usage state and is deactivated in the idle state, for time measurement during the usage state. The second timer is activated in the idle state for time measurement during the idle state. Furthermore, a corresponding hearing aid is indicated.

Claims

1. A method for operating a hearing aid having a time measuring unit with a first timer and a second timer, which comprises the steps of: switching the hearing aid between a usage state, in which a signal processing unit of the hearing aid is activated, and an idle state, in which the signal processing unit is deactivated; activating the first timer in the usage state and deactivating the first timer in the idle state for a time measurement during the usage state; and activating the second timer in the idle state for a time measurement during the idle state.

2. The method according to claim 1, wherein for continuous time measurement, the time measuring unit updates a hearing aid time in the usage state using the first timer and in the idle state using the second timer.

3. The method according to claim 1, which further comprises calibrating the time measuring unit by means of real time, which is provided by a secondary device, which is connected to the hearing aid for data exchange.

4. The method according to claim 1, wherein: the first timer has a greater accuracy than the second timer; and the second timer has a lower energy consumption than the first timer.

5. The method according to claim 1, wherein the first timer is a quartz oscillator.

6. The method according to claim 1, wherein the second timer is an RC oscillator or LC oscillator.

7. The method according to claim 1, wherein the hearing aid has a shift register, which is activated by the second timer such that a duration of the idle state is stored in the shift register.

8. The method according to claim 1, wherein the second timer is formed untrimmed and is calibrated using the first timer.

9. The method according to claim 1, wherein: the second timer is not temperature stabilized; and the hearing aid has a temperature sensor for measuring a temperature and for calibrating the second timer.

10. The method according to claim 1, wherein the second timer is charged once using energy from a battery of the hearing aid upon activation and is then subsequently not further supplied with energy from the battery as long as the idle state is activated.

11. The method according to claim 1, which further comprises repeatedly charging the second timer in the idle state from a battery of the hearing aid.

12. The method according to claim 11, wherein: a duration of the idle state is only measured up to a maximum duration; and the second timer is only charged in the idle state when the maximum duration is not yet reached.

13. The method according to claim 11, wherein the second timer is only supplied with energy from the battery in the idle state when a charge level of the battery at least corresponds to a minimum charge level.

14. A hearing aid, comprising: a controller configured to carry out the method according to claim 1.

Description

BRIEF DESCRIPTION OF THE FIGURES

[0041] FIG. 1 is an illustration of a hearing aid;

[0042] FIG. 2 is a block diagram showing a part of an interconnection of the hearing aid from FIG. 1; and

[0043] FIG. 3 is a chart showing a hearing aid time and a real time.

DETAILED DESCRIPTION OF THE INVENTION

[0044] A method for operating a hearing aid 2 is described hereinafter on the basis of FIGS. 1 to 3, which is shown in FIG. 1 together with a secondary device 4 and in detail in FIG. 2 as a pseudo-circuit diagram. The hearing aid 2 shown here is solely by way of example a so-called RIC device, the following statements also apply similarly to all other hearing aid types, however. The hearing aid 2 is switchable between a usage state, in which a signal processing unit 6 of the hearing aid 2 is activated for the intended use, i.e., the hearing aid 2 is switched on, and an idle state, in which the signal processing unit 6 is deactivated, i.e., the hearing aid 2 is switched off. The usage state is used to operate the hearing aid 2 when it is used by a user (not explicitly shown). In contrast, the idle state is used to operate the hearing aid 2 when it is presently not being used by the user.

[0045] The hearing aid 2 has a time measuring unit 8, which has a first timer 10 and a second timer 12. The two timers 10, 12 are each designed as an oscillator and accordingly each generate a cyclic or periodic signal and thus oscillations, by the counting of which a time measurement is carried out. The first timer 10 is activated in the usage state and deactivated in the idle state, for time measurement during the usage state, but not in the idle state. For example, the first timer 10 is activated at the beginning of the usage state and deactivated again at its end. In contrast, the second timer 12 is activated in the idle state, for time measurement during the idle state. The second timer 12 is presently deactivated in the usage state. For example, the second timer 12 is activated at the beginning of the idle state and deactivated again at its end. Overall, a time measurement both in the usage state and also in the idle state is thus possible using the two timers 10, 12, for example, a measurement of the duration of the respective state, namely by means of a corresponding timer 10, 12 in each case. In the present case, the two time measurements are combined to form a continuous time measurement.

[0046] The hearing aid 2 has, for example, as recognizable in FIG. 1, one or more input transducers 14 (two microphones here), a signal processing unit 6, and an output transducer 16 (a receiver here). The hearing aid 2 shown by way of example here is used to care for a hearing-impaired user and to compensate for hearing loss. The input transducer 14 generates an input signal which is supplied to the signal processing unit 6. The signal processing unit 6 modifies the input signal and thus generates an output signal, which is thus a modified input signal. The output signal is finally output by means of the output transducer 16 to the user.

[0047] In the usage state, the hearing aid 2 is activated and then carries out a processing and output of signals as described above. In other words: upon switching on of the hearing aid 2, the usage state is activated, upon switching off of the hearing aid 2, the usage state is deactivated. The time period between a beginning and a following end of the usage state is also referred to as the usage phase pn. During activated usage state, thus during a usage phase pn, sound signals from the surroundings are converted using the input transducer 14 into an input signal. Alternatively or additionally, an electrical input signal is received directly by the hearing aid 2 by means of another input transducer, for example, from another device, for example, the secondary device 4, which transmits the electrical input signal via a data connection to the hearing aid 2. In the signal processing unit 6, the input signal, however it is obtained, is then processed and an output signal is generated therefrom and this is then output via the output transducer 16 to the user.

[0048] In the idle state, in contrast, the hearing aid 2 is switched off, the signal processing unit 6 is deactivated, and the described processing and output of signals is not carried out. The time period between a beginning and a subsequent end of the idle state is also referred to as an idle phase pr. In the present case, the signal processing unit 6 and the input transducer 14 and the output transducer 16 are deactivated during an idle phase pr and in this way do not consume energy. The hearing aid 2 is thus essentially deactivated, but not completely deactivated, rather the hearing aid 2 has one or more idle state functions which—if required—are executed in the idle state and accordingly consume energy. However, the essential functionality for the processing and output is deactivated. The time measurement using the second timer 12 is such an idle state function and the second timer 12 is accordingly activated in the idle state. The energy consumption is drastically reduced in the idle state in comparison to the usage state, however, above all in that processing and output of signals do not take place. The idle state is thus an operating state in which the hearing aid 2 is not used by the user and is also not worn by the user.

[0049] The usage state and the idle state mutually exclude one another, at a given point in time only one of the two states can always be activated. The usage state and the idle state mutually alternate, so that a chronological sequence of usage phases pn, in which the usage state is activated, and idle phases pr, in which the idle state is activated, results.

[0050] Due to the use of two timers 10, 12, in the present case a time measurement is possible both in the usage state and in the idle state. An absolute and continuous time measurement is thus also possible overall independently of the operating state of the hearing aid 2, which is not interrupted by repeatedly turning the hearing aid 2 on and off. A real-time synchronization is not primarily required, but is optionally carried out. Independently thereof, a continuous time measurement is carried out using the time measuring unit 8, by means of which usage points in time, usage events, and usage situations of various usage phases pn (and possibly also idle phases pr) can then also be linked with one another and are also linked. In this way, a common continuous time frame is provided over multiple usage and idle phases pr, which is also referred to as hearing aid time th. This hearing aid time th is so to speak an internal time of the hearing aid 2 and is relative insofar as it does not necessarily correspond to the real time te, i.e., the actually presently existing time, but rather is measured relative to a starting point. An update of the hearing aid time th beyond a single usage phase pn is now possible using the two timers 10, 12. This then enables a data analysis using the hearing aid 2, which is improved in relation to a data analysis oriented only to a relative time measurement. However, the details of this data analysis are not relevant in the present case, it is primarily important solely that the hearing aid 2 has an absolute time measurement and is not dependent for this purpose on an additional external device. The hearing aid 2 accordingly does not require the secondary device 4 for the absolute time measurement.

[0051] In the present case, for the continuous time measurement, the time measuring unit 8 updates the hearing aid time th in the usage state using the first timer 10 and in the idle state using the second timer 12. This is illustrated in FIG. 3, which shows the hearing aid time th beginning from a starting point S (the starting point S is, for example, temporarily t=0 until an optional calibration using the real time te has taken place). Alternating usage and idle phases pn, pr are also indicated. During a usage phase pn, the first timer 10 is then activated and during an idle phase pr, the second timer 12 is then activated. The two timers 10, 12 thus together form a common hearing aid clock, which specifies the continuously measured hearing aid time th, for example, as a combination of date and time. Upon switching on and off, the timer 10, 12 which is used to update the hearing aid time th is accordingly changed.

[0052] In addition, in the present case the time measuring unit 8 is calibrated by means of a real time te, which is also shown in FIG. 3 and which is provided here by a secondary device 4. The secondary device 4 is connected for this purpose to the hearing aid 2 for data exchange. Due to this synchronization of the hearing aid 2 with the secondary device 4, the hearing aid time th then corresponds to the real time te, so that not only an absolute time measurement takes place, but also a time measurement in the time frame of the real time te. The time measuring unit 8 then insofar represents a real time clock of the hearing aid 2. However, it is to be emphasized that such a calibration of the hearing aid time th using a real time te is not required for a continuous time measurement as such, because a lack of calibration ultimately only results in an offset between hearing aid time th and real time te, which is not necessarily relevant for the data analysis, however.

[0053] The secondary device 4 is, for example, a computer, for example, at an audiologist and operated using fitting software, a smartphone, or the like and is connectable in a wireless or wired manner to the hearing aid 2 for data exchange, for example, via Bluetooth or WLAN. The secondary device 4 has a real-time clock (not explicitly shown), which specifies the real time te (also referred to as system time, for example, UTC, i.e., coordinated universal time), which is then transmitted to the hearing aid 2 for calibrating the hearing aid time th and thus for calibrating the time measuring unit 8. For example, the hearing aid time th is calibrated each time the hearing aid 2 is connected to a suitable secondary device 4.

[0054] In the delivery state, the hearing aid time th is generally uncalibrated, so that upon the first startup of the hearing aid 2, i.e., upon the first switching on and thus upon beginning the first usage phase pn, a point in time has to be arbitrarily specified or estimated as the starting point. For example, during the production of the hearing aid 2, the day of the production or a date lying several days or weeks in the future is selected as the starting point S. The time of day at the starting point S is, for example, 00:00 AM. Depending on the actual time upon startup, an offset then results. The hearing aid 2 is already capable in principle due to the time measuring unit 8 of carrying out a time measurement over a full day, i.e., over 24 hours, for example, in that a counter is simply incremented at regular time intervals until 24 hours are reached; directly thereafter, a new day is then counted. It is primarily unimportant whether these days correspond to actual days, the hearing aid 2 is at least capable of monitoring usage points in time, usage events, and usage situations, especially switching on and off of the hearing aid 2, in the course of a day and in this aspect of determining an absolute and continuous time frame for the usage state. Up to the first calibration using a secondary device 4, an absolute time measurement then takes place, however, this is regularly shifted by an offset (thus a fixed value) with respect to the real time te. This is then corrected accordingly upon a later calibration and the time measurement up to this point is then converted. The original starting point S is then accordingly provided with the correct real time te. If 00:00 AM was used as the starting point S, for example, but the hearing aid 2 was actually switched on for the first time at 7:15 AM, a time difference of 7 hours 15 minutes exists up to the first calibration, which is then corrected (an offset in the date is similarly corrected if necessary). The previous data analysis is then corrected accordingly.

[0055] The two timers 10, 12 are optimized in the present case toward the respective operating state. In the design shown, for this purpose, the first timer 10 has a greater accuracy than the second timer 12 and the second timer 12 has—when activated—a lower energy consumption than the first timer 10—when activated. “Accuracy” is understood here as “chronological accuracy” or “frequency stability”, i.e., how accurately the timer 10, 12 measures the time and how frequency stable the timer 10, 12 is. The higher the accuracy, the more uniformly the timer 10, 12 measures successive units of time and/or the lower the deviation (“drift”) accumulated with time is from the real time te. The first timer 10 is therefore also referred to as a precision timer, in contrast the second timer 12 is referred to as a low-energy timer. The most accurate possible time measurement is now implemented using the first timer 10 and, on the other hand, the lowest possible energy consumption is implemented by the second timer 12 in the idle state. The absolute accuracy and absolute energy consumption of the two timers 10, 12 are primarily not important, energy consumption and accuracy of the two timers 10, 12 relative to one another are more important, and that the conflict of goals between accuracy and energy consumption is thus resolved differently in the different operating states. The first timer 10 is selected in the present case with respect to the accuracy and the second timer 12 is selected with respect to the energy consumption. Accordingly, the possible occurrence of a deviation of the hearing aid time th from the real time to is tolerated in the idle state and is insofar also unproblematic as it can be recognized accordingly upon a calibration using a secondary device 4 or upon a calibration of the second timer 12 using the first timer 10 and—if necessary—can be corrected again.

[0056] In the exemplary embodiment of FIG. 2, the first timer 10 is a quartz oscillator, which uses an oscillating quartz 18 for the clock generation and thus for the time measurement and therefore has a high accuracy, i.e., is particularly frequency stable. The quartz oscillator is also used in one possible embodiment as a clock generator for operating the signal processing 6 and/or as a clock generator for other functions.

[0057] In the exemplary embodiment of FIG. 2, the second timer 12 is an RC oscillator, alternatively an LC oscillator is also possible. The second timer 12 is also a freewheeling oscillator, i.e., in contrast to a quartz oscillator is especially not particularly frequency stable, so that the second timer 12 has a clock frequency possibly varying over time. The RC oscillator has one or more resistors 20 and capacitors 22 for clock generation, which are suitably interconnected with one another to generate an oscillation and thus enable a time measurement. In FIG. 2, only one resistor 20 and one capacitor 22 are shown solely by way of example; other designs are also conceivable. An LC oscillator similarly has one or more inductors and capacitors for clock generation in order to generate an oscillation for the time measurement. In each case, the second timer 12 thus has at least one capacitor 22, which is repeatedly charged and discharged to generate the oscillations. The capacitor 22 also determines here with which energy the second timer 12 is charged at the beginning of the idle state.

[0058] The second timer 12 is integrated in the present case in an analog IC 24 (i.e., an analog integrated circuit) of the hearing aid 2. The analog IC 24 is formed separately from the signal processing unit 6 in the exemplary embodiment shown. The signal processing unit 6 is implemented here as part of a digital signal processor 26 (abbreviated: DSP). The analog IC 24 and also the signal processor 26 and therefore also the signal processing unit 6 are all parts of a control unit 28 of the hearing aid 2. The analog IC 24 is embodied, for example, as a microcontroller, ASIC, or the like; a design is also suitable in which the entire control unit 28 is designed as a microcontroller, ASIC, or the like, wherein then the analog IC 24 forms a section of the control unit 28, for example, as shown in FIG. 1. In addition to the second timer 12, still further analog functions 30, which are not of further relevance here, are also integrated in the analog IC 24 in FIG. 2.

[0059] In the exemplary embodiment of FIG. 2, the hearing aid 2 has a shift register 32, which is activated by the second timer 12 in such a way that the duration of the idle state is stored in the shift register 32. In the present case, for this purpose the shift register 32 is integrated in the analog IC 24 and connected to the second timer 12. A time measurement of the second timer 12 is stored in the shift register 32, for example, in that the shift register 32 is simply used as a counter which is progressively increased by the second timer 12 if the second timer 12 is activated.

[0060] In addition, the analog IC 24 in FIG. 2 has a main memory 34, which is connected to the above-mentioned shift register 32 in order to store a time measurement of the second timer 12 and then carry out a new time measurement using the shift register 32 without discarding the prior time measurement. In this way, the durations of various idle phases pr are measured and stored separately in the main memory 34, in the present case especially for continuous time measurement and for a data analysis. As soon as the idle state is deactivated and the usage state is activated, the shift register 32 is read out and the time measurement stored therein is stored in the main memory 34, to be combined, for example, added there with a time measurement of the first timer 10 from the preceding or the now following usage phase pn, and in this way to update the hearing aid time th. Accordingly, the first timer 10 in FIG. 2 is also connected to the main memory 34 in order to store a time measurement of the first timer 10 therein, for example, a duration of a usage phase pn.

[0061] As is recognizable in FIG. 2, the first timer 10 is at least partially integrated therein in the analog IC 24 in that the associated oscillating quartz 18 is not integrated in the analog IC 24, but rather formed as a separate component and then connected to the analog IC 24.

[0062] In the present case, the second timer 12 is formed untrimmed, i.e., uncalibrated. The second timer 12 is then calibrated using the first timer 10, i.e., a calibration is carried out. Since the first timer 10 is more accurate than the second timer 12, the latter may accordingly be calibrated using the former, so that a separate trimming during the production is omitted. For example, the hearing aid 2 has a zero crossing detector or flank detector (not explicitly shown) and a slide register as a counter for the calibration and the second timer 12 is calibrated in that its oscillations (also referred to as cycles) within a fixed time period and also the oscillations of the first timer 10 in the same time period are counted using the shift register and then compared to one another. In this way, a parameter is determined using which a time measurement of the second timer 12 is converted. The parameter is, for example, the ratio of number of cycles of the two timers per unit of time or the number of cycles of the second timer 12 per single cycle of the first timer 10 or the like. The parameter is stored, for example, in the main memory 34. The calibration and/or the determination of the parameter only takes place, for example, upon a first startup of the hearing aid 2 or alternatively or additionally repeatedly whenever the usage state is activated.

[0063] In the exemplary embodiment shown, the second timer 12 is moreover also not temperature stabilized. The hearing aid 2 then has a temperature sensor 36 which is already provided in any case, for example, for one or more other functions of the hearing aid 2. A temperature is measured using the temperature sensor 36, using which the second timer 12 is calibrated, i.e., a calibration is carried out (additionally or alternatively to the above-described calibration using the first timer 10). A linear relationship between temperature and deviation during the time measurement is assumed here, for example, or a calibration curve, function, or table is used, which is stored, for example, in the main memory 34. The temperature is either measured directly during the idle state or at the beginning and/or end of an idle phase pr, thus upon activation or deactivation of the idle state.

[0064] The hearing aid 2 shown here furthermore has an energy management unit 38 for controlling the energy supply of the diverse components of the hearing aid 2 and especially of the analog IC 24 and optionally further parts of the control unit 28. The energy supply is carried out using a battery 40 of the hearing aid 2. In the present case, the energy management unit 38 is integrated in the analog IC 24. Furthermore, the hearing aid 2 has a safety switch 42 to prevent a deep discharge of the battery 40 in that it is galvanically separated from the remaining hearing aid 2 below a minimum charge level. The safety switch 42 is also integrated in the analog IC 24 in FIG. 2. The safety switch 42 is formed open during the production of the hearing aid 2 and is opened during the delivery to the user and is only closed upon the first startup of the hearing aid 2. In this way, a deep discharge of the battery 40 is avoided before the startup. In the present case, the safety switch 42 is moreover a reversible switch, so that a deep discharge of the battery 40 is also still avoided after the first startup, for example, if the duration of a single idle phase pr is sufficiently long that the charge state of the battery 40 sinks below the minimum charge level. The safety switch 42 is then opened again by the energy management unit 38 when the charge level of the battery 40 sinks below the minimum charge level. Otherwise, the safety switch 42 also remains closed when the idle state is activated, however, so that the second timer 12 is supplied with energy.

[0065] The energy management unit 38 also controls a supply of the second timer 12 with energy from the battery 40. For example, the second timer 12 is charged once with energy from a battery 40 upon activation and then subsequently is not supplied further with energy from the battery 40 as long as the idle state is activated. Alternatively, the second timer 12 is repeatedly charged from the battery 40 of the hearing aid 2 in the idle state. Especially in the case of an RC or LC oscillator, one or more capacitors 22 are charged for the time measurement and then do not require further energy for a specific time. However, the charged energy is consumed with time so that renewed charging can be necessary if this lasts longer than the idle state is activated, however, a single charge at the beginning of an idle phase pr is sufficient. If the second timer 12 is repeatedly charged during the idle state, this takes place, for example, whenever the second timer 12 falls below a minimum charge level.

[0066] A design is also possible in which the duration of the idle state is only measured up to a maximum duration and the second timer 12 is only charged in the idle state when the maximum duration is not yet reached. In this way, a deep discharge of the battery 40 is prevented in that the time measurement using the second timer 12 is only carried out until reaching the maximum duration, for example, 7 days, and then the second timer 12 is also deactivated, so that energy is no longer consumed. Alternatively or additionally, a deep discharge of the battery 40 is avoided in that the second timer 12 is only supplied with energy from the battery 40 in the idle state when a charge level of the battery 40 at least corresponds to a minimum charge level. The charge level is determined, for example, on the basis of the voltage of the battery 40 or this is used directly as a measure for the charge level.

[0067] The following is a summary list of reference numerals and the corresponding structure used in the above description of the invention: [0068] 2 hearing aid [0069] 4 secondary device [0070] 6 signal processing unit [0071] 8 time measuring unit [0072] 10 first timer [0073] 12 second timer [0074] 14 input transducer [0075] 16 output transducer [0076] 18 oscillating quartz [0077] 20 resistor [0078] 22 capacitor [0079] 24 analog IC [0080] 26 signal processor [0081] 28 control unit [0082] 30 further analog functions [0083] 32 shift register [0084] 34 main memory [0085] 36 temperature sensor [0086] 38 energy management unit [0087] 40 battery [0088] 42 safety switch [0089] S starting point [0090] to real time [0091] th hearing aid time [0092] pn usage phase [0093] pr idle phase