Method for operating a hearing device and hearing device

Abstract

A method for operating a hearing device (2) is provided, wherein the hearing device (2) can be switched between a use state and a sleep state, wherein a signal processing device (6) of the hearing device (2) is activated in the use state and deactivated in the sleep state, wherein the signal processing device (6) is deactivated, wherein the hearing device (2) has a time measurement unit (8) having a first timer (10) and a second timer (12), wherein the first timer (10) is activated in the use state and deactivated in the sleep state for measuring time during the use state, wherein the second timer (12) is activated in the sleep state for measuring time during the sleep state. A corresponding hearing device (2) is also provided.

Description

Technical Field

[0001] The present invention relates to a method for operating a hearing instrument and a hearing instrument. Background Art

[0002] Hearing devices typically include an input converter, a signal processing device, and an output converter. Hearing devices are used, for example, to provide hearing-impaired users with hearing loss and to compensate for hearing loss. The input converter generates an input signal, for example, from an ambient sound signal. The input signal is fed to a signal processing device, which modifies the input signal to generate an output signal. To compensate for hearing loss, the input signal is amplified with a frequency-dependent amplification factor, for example, based on the user's audiogram. Finally, the output signal is typically output to the user as an audio signal via the output converter.

[0003] Hearing devices benefit from the ability to measure time in various ways. For example, time measurement can be used to determine the duration of use of a hearing device, for example, to monitor a user's regular use of the hearing device. It is also possible to determine the duration of use of various settings, for example, to identify and specifically improve user preferences. It is also conceivable to use time measurement to identify the time and duration of different environmental situations, thereby, for example, identifying recurring usage situations and then specifically offering the user the appropriate settings for the hearing device at a given time. Numerous other possible applications of time measurement in hearing devices are also conceivable.

[0004] EP 1 746 861 A1 describes the use of frequency-stable components, such as quartz, in hearing instruments. However, these components disadvantageously have high power consumption and require a large amount of space. Furthermore, a hearing instrument is described that has a free-wheeling oscillator, which can be tuned via a supply current or a switchable capacitor and provides the basic clock for a signal processing device. To tune the oscillator, an external transmitter sends a special signal to the hearing instrument. This makes it possible to dispense with frequency-stable components, such as quartz, in hearing instruments. Summary of the Invention

[0005] Against this background, the technical problem to be solved by the present invention is to improve time measurement in a hearing instrument. To this end, a corresponding method for operating a hearing instrument and such a hearing instrument are to be specified.

[0006] According to the present invention, the aforementioned technical problem is solved by a method having the features according to the present invention and by a hearing device having the features according to the present invention. Advantageous embodiments, developments, and variants are the subject of the following description. The description of the method also applies to the hearing device, and vice versa. With respect to the method steps explicitly or implicitly described below, advantageous embodiments of the hearing device result from the hearing device having a control unit that is configured to perform one or more of these method steps.

[0007] The core idea of ​​the present invention is in particular to use two different timers in the hearing instrument in order to enable continuous time measurement even when the hearing instrument is switched off, in particular independently of an external timer.

[0008] The method is used to operate a hearing instrument. The hearing instrument can be switched between an active state and a sleep state. In the active state, a signal processing device of the hearing instrument is activated, in particular for normal use, i.e., the hearing instrument is switched on. In the sleep state, the signal processing device is deactivated, i.e., the hearing instrument is switched off. The active state is used, in particular, to operate the hearing instrument while the user is using the hearing instrument. Conversely, the sleep state is used, in particular, to operate the hearing instrument when the user is not using the hearing instrument.

[0009] A hearing instrument includes a time measurement unit having a first timer and a second timer. The two timers are each designed, in particular, as oscillators, and thus each generates a cyclic or periodic signal, thereby generating oscillations, and time measurement is performed by counting the oscillations. The first timer is activated in a use state and deactivated in a sleep state, for measuring time during the use state. The first timer is preferably used to measure usage time, such as the duration of a use state or the duration of a usage event or usage scenario. Thus, time measurement is performed in the use state using the first timer, but not in the sleep state. In one suitable embodiment, the first timer is activated at the beginning of the use state and deactivated again at the end of the use state. Conversely, the second timer is activated in the sleep state for measuring time during the sleep state. The second timer is preferably deactivated in the use state. Preferably, the second timer is used to measure the duration of the sleep state. In one suitable embodiment, the second timer is activated at the beginning of the sleep state and deactivated again at the end of the sleep state. Thus, both timers, i.e., corresponding timers, are used to measure time in both the use state and the sleep state. Advantageously, the two time measurements are combined to produce a continuous time measurement.

[0010] Hearing devices typically have an input converter, a signal processing device, and an output converter. The input converter is typically a microphone. The output converter is typically an earpiece, also known as a loudspeaker or receiver. A hearing device is typically associated with a single user and used only by that user. Hearing devices are preferably used to serve hearing-impaired users and to compensate for hearing loss. The input converter generates an input signal, which is fed to a signal processing device. The signal processing device modifies the input signal to generate an output signal, which is therefore the modified input signal. To compensate for hearing loss, the input signal is amplified with a frequency-dependent amplification factor, for example, based on the user's audiogram. Finally, the output signal is output to the user using the output converter. In hearing devices with a microphone and earpiece, the microphone generates the input signal from the ambient sound signal, and the earpiece generates the sound signal from the output signal. The input and output signals are electrical signals and are therefore also referred to as signals. In contrast, the ambient sound signal and, if necessary, the sound signal output by the earpiece are acoustic signals.

[0011] In the use state, the hearing device is active and signals are processed and output as described above. In other words, the use state is activated when the hearing device is turned on and deactivated when the hearing device is turned off. When the use state is active, i.e., when the hearing device is turned on, acoustic signals from the environment are converted into input signals using an input converter. Alternatively or additionally, the electrical input signal of the hearing device can be directly received using a suitable input converter, for example, from another device that transmits the electrical input signal to the hearing device via a data connection, and used as the input signal. The input signal is then processed in a signal processing device, and an output signal is generated from the input signal. The output signal is then output to the user via the output converter. Therefore, the use state is the operating state of the hearing device, intended for regular use by a user, who typically also wears the hearing device during the use state. The period between the start and subsequent end of the use state is also referred to as a use phase.

[0012] In contrast, in the sleep state, the hearing device is turned off, the signal processing device is deactivated, and the described signal processing and output are not performed. In particular, the signal processing device, as well as the input and output converters, are deactivated and, in this manner, consume no energy. The hearing device is thus essentially deactivated, but not completely. Rather, the hearing device has one or more sleep-state functions that, if necessary, are performed in the sleep state and consume energy accordingly. However, the main processing and output functions are deactivated. Time measurement using a second timer is one such sleep-state function, and the second timer is correspondingly active in the sleep state. However, energy consumption in the sleep state is significantly reduced compared to the active state, particularly because no signal processing or output is performed. The sleep state is therefore an operating state in which the user is not using the hearing device, and in particular, not wearing it. For example, the hearing device in the sleep state may be placed in a storage case or connected to a charging device. The period between the start and subsequent end of the sleep state is also referred to as the sleep phase.

[0013] The active state and the dormant state are mutually exclusive, and only one of the two states can be active at a given time point. The active state and the dormant state alternate with each other, thereby generating a time sequence of active phases of the active state and active phases of the dormant state.

[0014] The present invention is primarily based on the observation that time measurements in hearing devices can, in principle, be performed relative to specific events. For example, the switching on of the hearing device, i.e., the start of a usage phase, can be marked as time t=0, and then counting can be performed in suitable time units starting from this time. At each renewed start of the usage phase, i.e., at each new usage phase, the count starts again at time t=0. Usage times, usage events, and usage situations can then be determined relative to the start of the usage phase. However, these cannot be linked to usage times, usage events, and usage situations of another usage phase, since a continuous time measurement is not possible.

[0015] Correspondingly, absolute time measurement offers further advantages: multiple temporally separated periods of use of the hearing device can be linked to one another. Advantageously, the actual time of day and, if necessary, the current date are also known to the hearing device, in particular for identifying recurring usage patterns in everyday life and for controlling the hearing device in a time-dependent manner. While relative time measurement only allows for the measurement of durations (i.e., elapsed time), absolute time measurement allows for the acquisition of additional, specific time information, such as specific points in time and also from multiple different periods of use.

[0016] It has been observed that hearing devices typically only perform relative time measurements. This is due to historical reasons, as zinc-air batteries were often used, and some still are, for energy supply to hearing devices. When the hearing device is turned off, these batteries are electrically isolated from all electronic components of the hearing device and thus do not supply energy to the timer, which is an electronic component. Therefore, time measurement is not possible in the sleep state, and relative time measurement is the only option in active mode. However, in newer hearing devices using lithium-ion batteries or equivalent, this limitation generally does not apply, and energy can also be supplied in the sleep state. However, it is desirable to minimize energy consumption in the sleep state to ensure that the active mode lasts as long as possible.

[0017] A major advantage of the present invention results from the use of two timers, and in particular, from the fact that time measurements can be performed not only in use but also in sleep mode, i.e., not only during use phases but also during sleep phases. This allows for continuous, absolute time measurement, independent of the hearing instrument's operating state, that is not interrupted by repeated switching on and off. Real-time synchronization is not required, although it is advantageous. Advantageously, continuous time measurement is now performed independently of this using the time measurement unit. Using this continuous time measurement, usage points, usage events, and usage situations from different use phases (and, if necessary, sleep phases) can be linked, and advantageously so. In this way, a common, continuous time frame is formed across multiple use phases and sleep phases, also referred to as hearing instrument time. This internal time can be considered internal to the hearing instrument. However, it should not be confused with the relative time measurement described above. Rather, hearing instrument time is relative only in that it does not necessarily correspond to real time, i.e., the currently existing time, but is measured relative to a starting point. However, unlike relative time measurement, hearing instrument time has only a single time t=0 as its starting point and does not restart for each individual usage phase. If multiple time t=0s are used, at least their relative positions relative to one another are known. One advantage of two timers is that the hearing instrument time can be adjusted after individual usage phases, and therefore absolute time measurement is also possible. This allows for improved data analysis using hearing instruments compared to data analysis focused solely on relative time measurement. However, the details of this data analysis are irrelevant here; the main point is that the hearing instrument is equipped with absolute time measurement and does not rely on additional external equipment.

[0018] In a preferred embodiment, the time measurement unit adjusts the hearing instrument time using a first timer in the active state, i.e., during the active phase, and adjusts the hearing instrument time using a second timer in the inactive state, i.e., during the inactive phase. In other words, the two timers together form a common hearing instrument clock that provides continuously measured hearing instrument time, for example, as a combination of date and time. Thus, the timer used to adjust the hearing instrument time changes when the hearing instrument is switched on and off. This has the advantage that, depending on the operating state, a timer optimally tuned for that operating state can be used.

[0019] The time measurement unit is preferably calibrated using the real-time time provided by a second device, which is connected to the hearing instrument for data exchange. As already described, real-time time is, in particular, the currently existing time. Through the described synchronization of the hearing instrument with the second device, the hearing instrument time corresponds to real-time time, thereby enabling not only absolute time measurement but also time measurement within the real-time timeframe. In this respect, the time measurement unit is thus a real-time clock of the hearing instrument. However, it should be noted that such calibration of the hearing instrument time with real-time time is not inherently necessary for continuous time measurement, as the absence of calibration ultimately only results in a shift between the hearing instrument time and the real-time time, which does not necessarily lead to improved data analysis.

[0020] The second device is, for example, a computer, smartphone, or equivalent running fitting software, such as at the audiologist's location, and can be connected to the hearing instrument wirelessly or wired, such as via Bluetooth or WLAN, for data exchange. The second device has a real-time clock that provides real-time time (also known as system time, such as UTC, Coordinated Universal Time). This real-time time is then transmitted to the hearing instrument for calibrating the hearing instrument time and, therefore, the time measuring unit. The hearing instrument time is preferably calibrated each time the hearing instrument is connected to a suitable second device.

[0021] In the delivered state, hearing devices are typically uncalibrated. Therefore, when a hearing device is first put into operation, i.e., when it is first switched on, and therefore at the beginning of the first usage phase, a time point must be arbitrarily predetermined or estimated as the starting point. For example, during the manufacture of the hearing device, the manufacturing date or a date several days or weeks in the future is selected as the starting point. The clock time at the starting point is, for example, 00:00. This is then shifted according to the actual time of commissioning. Due to the time measurement unit, the hearing device can advantageously measure time throughout the entire day, i.e., around the clock. For example, this can be accomplished by simply incrementing a counter at regular intervals until 24 hours have been reached, and then simply counting a new day at the end. Whether these days correspond to the actual number of days is initially unimportant; the hearing device can at least monitor usage times, usage events, and usage situations, particularly switching the hearing device on and off, over the course of a day and, in this regard, determine both absolute and continuous time frames for the usage state. Before the first calibration with the second device, an absolute time measurement is then performed. However, this absolute time measurement is usually offset by a certain shift (i.e., a fixed value) relative to the real time. This is then calibrated accordingly during the subsequent calibration, and the time measurements to date are appropriately converted. The correct real time is then set to the original starting point accordingly. For example, if 00:00 was used as the starting point, but the hearing device was actually connected for the first time at 7:15, there was a time difference of 7 hours and 15 minutes before the first calibration, which is then calibrated (and the date shift is similarly calibrated, if necessary). The data analysis to date is then calibrated accordingly.

[0022] As already explained, the two timers can now be optimized based on the respective operating states. To this end, in a preferred embodiment, the first timer has higher accuracy than the second timer, and the second timer (when activated) has lower energy consumption than the first timer (when activated). "Accuracy" is understood to mean, in particular, "temporal precision" or "frequency stability," that is, how accurately a timer measures time and how stable its frequency is. The higher the accuracy, the more evenly the timer measures successive time units and / or the smaller the accumulated time deviation ("drift") from real time. Therefore, the first timer is also referred to as a precise timer, and the second timer as a low-energy timer. This embodiment is based on the considerations that, on the one hand, it is desirable to measure time as accurately as possible, which is now achieved with the first timer, and, on the other hand, the least energy should be consumed in the dormant state, which is now achieved with the second timer. The absolute accuracy and absolute energy consumption of the two timers are initially unimportant; what is more important is the energy consumption and accuracy of the two timers relative to each other, and thus, the conflict between accuracy and energy consumption is resolved differently in different operating states. The first timer is selected based on accuracy, and the second timer is selected based on energy consumption. A possible occurrence of a deviation between the hearing device time and the real time in the sleep state is accordingly tolerated, and in this respect, such a possible occurrence of a deviation is not a problem, because when calibrating with the second device or when calibrating the second timer with the first timer, such a possible occurrence of a deviation can be correspondingly identified and, if necessary, calibrated again.

[0023] In one suitable embodiment, the first timer, i.e., the precision timer, is a quartz oscillator. Quartz oscillators use oscillating quartz for clock generation and, therefore, for time measurement, and therefore have high precision. Precision is defined, in particular, by the deviation of the oscillator's actual frequency from its nominal frequency, or equivalently, by the deviation of the actual elapsed time relative to the time measured by the oscillator, in particular the quotient thereof. This deviation is typically specified in parts per million, or ppm. For quartz oscillators, the deviation is typically better than 100 ppm. In other words, quartz oscillators are particularly frequency-stable, i.e., they have a very constant clock frequency and therefore generate oscillations that vary very little relative to one another. The oscillating quartz itself consumes no energy; however, to control it, the oscillator has circuitry that typically consumes 10 μW to 100 μW, although the energy consumption may also vary from these values. The quartz oscillator is preferably also used as a clock generator for operating the signal processing device. Since the first timer is only used when the signal processing device is also active, it is advantageous to use as the first timer a clock generator which, in the operating state, also serves as a clock generator for other functions, for example for the signal processing device.

[0024] In one suitable embodiment, the second timer, i.e., the low-energy timer, is an RC oscillator or an LC oscillator. RC oscillators and LC oscillators are also referred to as oscillator circuits. An example of an RC oscillator is a phase-shift oscillator. Examples of LC oscillators are LC parallel circuits or LC series circuits. The second timer is preferably a free-running oscillator, meaning that, unlike a quartz oscillator, it is not particularly frequency-stable, and thus has a clock frequency that may vary over time. Accordingly, a deviation occurs in the clock frequency, which can be quantified, for example, by a statistical metric such as variance.

[0025] To generate a clock pulse, an RC oscillator has one or more resistors and capacitors that are connected to each other in a suitable manner to generate oscillations, thereby enabling time measurement. Similarly, an LC oscillator has one or more inductors and capacitors to generate oscillations for time measurement. Therefore, in each case, the second timer has at least one capacitor that is repeatedly charged and discharged to generate the oscillations. The capacitor thus also determines, in particular, the energy level with which the second timer is charged at the beginning of the sleep state. The accuracy of an RC or LC oscillator is typically at least one order of magnitude lower than that of a quartz oscillator. For example, a deviation of 10,000 ppm (i.e., three orders of magnitude greater than the value given above for a quartz oscillator) corresponds to a deviation of 1% from the nominal frequency of the RC oscillator. In contrast, energy consumption is typically at least one order of magnitude lower than with a quartz oscillator and is generally dependent on the nominal frequency and the required circuitry.

[0026] The second timer is suitably integrated into an analog IC (i.e., analog integrated circuit) of the hearing instrument. The analog IC is preferably designed separately from the signal processing device. The signal processing device is suitably implemented as part of a digital signal processor (abbreviated as "DSP," i.e., "digital signal processor"). Not only the analog IC, but also the signal processor, and therefore the signal processing device, are part of the control unit of the hearing instrument. The analog IC is implemented, for example, as a microcontroller, ASIC, etc., and a design is also suitable in which the entire control unit is designed as a microcontroller, ASIC, etc., wherein the analog IC then forms a sub-area of ​​the control unit. In addition to the second timer, one or more other electronic components having corresponding functions are also suitably integrated into the analog IC, as further explained below. In principle, designs are also possible in which other analog functions, not further relevant here, are integrated into the analog IC.

[0027] The hearing instrument preferably includes a shift register, and the second timer controls the shift register so that the duration of the sleep state, in particular the duration of an individual sleep phase, is stored in the shift register (also referred to as a time register). In one suitable embodiment, the shift register is integrated into an analog IC and connected to the second timer. For example, if the second timer is active, the second timer continuously increments the counter by simply using the shift register as a counter, and the time value measured by the second timer is stored in the shift register.

[0028] The analog IC preferably includes a main memory. The main memory is advantageously connected to the aforementioned shift register so that the time measurement values ​​of the second timer can be stored in the main memory. A new time measurement can then be performed using the shift register without discarding the previous time measurement values. In this way, the durations of different sleep phases are measured and stored separately in the main memory, in particular for continuous time measurement or, for example, for data analysis. In a particularly simple embodiment, once the sleep state is deactivated and the active state is activated, the shift register is read out and the time measurement value stored therein, i.e., the duration of the recently concluded sleep phase, is stored in the main memory to be combined there with, in particular, added to, the time measurement value of the first timer from the preceding or subsequent active phase, thereby adjusting the hearing device time. Correspondingly, the first timer is also advantageously connected to the main memory so that its time measurement values, such as the duration of the active phase, are stored there.

[0029] In a suitable design, the first timer is also at least partially integrated in the analog IC. In particular, in the case of a quartz oscillator, the relevant oscillating quartz is not integrated in the analog IC for reasons of principle, but is constructed as a separate component and connected to the analog IC in a suitable manner.

[0030] In a particularly simple embodiment, the second timer is designed to be untrimmed, i.e., uncalibrated. In particular, in the case of RC or LC oscillators, manufacturing-related inaccuracies arise, which are typically eliminated by trimming the RC or LC oscillator. One or more additional capacitors are added to achieve the desired oscillation behavior, in particular a specific clock frequency. This trimming can be conveniently omitted, making manufacturing simpler and more cost-effective overall. Alternatively, the second timer is calibrated using the first timer, i.e., the second timer is calibrated using the first timer. Because the first timer is particularly more accurate than the second timer, the second timer can be calibrated using the first timer, thus eliminating separate trimming during manufacturing. For example, for calibration, the hearing instrument may include a zero crossing or edge detector and a shift register as a counter. The second timer is calibrated by counting the oscillations of the second timer within a fixed time period (also called cycles) and the oscillations of the first timer within the same time period using the shift register, and then comparing them. In this way, a characteristic number is determined, which is used to convert the time measurement value of the second timer. A suitable characteristic number is, for example, the ratio of the number of cycles of the two timers per time unit, or the number of cycles of the second timer per individual cycle of the first timer, or the like. The characteristic number is preferably stored in a main memory. The characteristic number is calibrated, in particular determined, for example, only when the hearing device is first put into operation, or alternatively or additionally, it is repeatedly performed upon activation of the use state. In particular, in the latter case, temperature instabilities of the second timer are preferably also automatically taken into account during calibration.

[0031] In one suitable design, the second timer is not temperature-stable, which is advantageously particularly cost-effective. It is generally desirable to design the timer to be as temperature-stable as possible to avoid temperature-related deviations in the time measurement. However, this is omitted here for the sake of achieving the simplest possible design. Alternatively, the hearing instrument advantageously includes a temperature sensor, which is, for example, already provided for one or more other functions of the hearing instrument. The temperature is then measured using the temperature sensor, and the second timer is calibrated using the temperature, i.e., calibrated (in addition to or as an alternative to the calibration using the first timer described above). In one suitable design, a linear relationship between temperature and deviation is assumed in the time measurement. Alternatively or additionally, a calibration curve, calibration function, or calibration table is used, which is typically stored in a main memory and determined, for example, through trial and error. The temperature is measured directly during the sleep state, or at the beginning and / or end of the sleep phase, i.e., when the sleep state is activated or deactivated. The latter method has the advantage of consuming less energy in the sleep state, while the former method provides higher calibration accuracy. The actual calibration is then performed, for example, in the operating state, to adjust the hearing instrument time as accurately as possible after the sleep phase ends.

[0032] The hearing device preferably includes an energy management unit for controlling the energy supply to various components of the hearing device, in particular the analog integrated circuit (IC), and, if necessary, other parts of the control unit, using a battery. The energy supply is thus provided by the hearing device's battery. The battery is preferably a lithium-ion battery, also known as a lithium-ion secondary battery. The energy management unit is preferably integrated into the analog integrated circuit (IC). The energy management unit is also referred to as a PMIC, or "power management integrated circuit." Furthermore, the hearing device preferably includes a safety switch for preventing deep discharge of the battery by electrically isolating the battery from the rest of the hearing device below a minimum state of charge. The safety switch is preferably also integrated into the analog integrated circuit. In one preferred embodiment, the safety switch is a one-shot switch that is open during manufacturing of the hearing device and upon delivery to the user, and is closed once and permanently when the hearing device is first put into operation. This prevents deep discharge of the battery before commissioning. However, a particularly advantageous embodiment is one in which the safety switch is a reversible switch. This prevents deep discharge of the battery even after initial operation, for example if a single sleep phase lasts long enough to cause the battery's state of charge to fall below a minimum state of charge. The safety switch is then configured to be open during manufacture of the hearing device, open during delivery to the user, and closed only during initial operation of the hearing device. It is then reversible, i.e., it is opened again, in particular by the energy management unit, when the battery's state of charge falls below the minimum state of charge. However, in other cases, the safety switch remains closed even when the sleep phase is activated, thereby supplying energy to the second timer.

[0033] The energy management unit preferably also controls the supply of energy from the battery to the second timer. In one suitable embodiment, the second timer is charged once with energy from the hearing device's battery upon activation, and then subsequently no longer supplied with energy from the battery as long as the sleep state is active. Alternatively, the second timer is repeatedly charged from the hearing device's battery during the sleep state. In particular, in the case of an RC or LC oscillator, the second timer, for fundamental reasons, includes one or more capacitors that are charged for time measurement and then require no further energy for a specific period of time. However, over time, the charged energy is consumed, and recharging may be necessary. However, if this lasts longer than the duration of the active sleep state, a single charge at the beginning of the sleep phase is advantageously sufficient. If the second timer is repeatedly charged during the sleep state, this is preferably always performed below the second timer's minimum charge state.

[0034] A suitable design is also one in which the duration of the sleep state is measured only before a maximum duration, and the second timer is charged in the sleep state only if the maximum duration has not yet been reached. In this way, deep discharge of the battery is prevented by measuring time using the second timer only before reaching a maximum duration, for example, seven days, and then also deactivating the second timer so that no energy is consumed. The safety switch described above is then also opened in a suitable manner.

[0035] Alternatively or additionally, deep discharge of the battery is avoided by, in an advantageous embodiment, powering the second timer with energy from the battery in the sleep state only when the battery's state of charge corresponds to at least a minimum state of charge. For example, the state of charge is determined based on the battery voltage, or the battery voltage is directly used as a measure of the state of charge.

[0036] The hearing device according to the present invention has a control unit, in particular a control unit as described above, which is designed to carry out the method as described above. BRIEF DESCRIPTION OF THE DRAWINGS

[0037] The embodiments of the present invention are described in detail below with reference to the accompanying drawings, wherein:

[0038] Figure 1 The hearing device is schematically shown accordingly,

[0039] Figure 2 The corresponding schematic diagram Figure 1 a part of an electrical circuit in a hearing device,

[0040] Figure 3 The hearing device time and the real time are schematically shown accordingly. DETAILED DESCRIPTION

[0041] Next, with the help of Figures 1 to 3 To describe a method for operating a hearing device 2, Figure 1 The hearing device 2 is shown together with the second device 4 in FIG. Figure 2A hearing device 2 is partially shown in FIG as a pseudo-circuit diagram. The hearing device 2 shown here is merely an example of a so-called RIC device; however, the following description applies similarly to any other type of hearing device. The hearing device 2 can be switched between an active state and a sleep state. In the active state, the signal processing device 6 of the hearing device 2 is activated for normal use, i.e., the hearing device 2 is switched on. In the sleep state, the signal processing device 6 is deactivated, i.e., the hearing device 2 is switched off. The active state allows the hearing device 2 to operate while a user (not explicitly shown) is using the hearing device 2. Conversely, the sleep state allows the hearing device 2 to operate when the user is not using the hearing device 2.

[0042] The hearing instrument 2 includes a time measurement unit 8 having a first timer 10 and a second timer 12. Each of the two timers 10 and 12 is configured as an oscillator, thus generating a cyclic or periodic signal, thereby generating oscillations. Time measurement is performed by counting the oscillations. The first timer 10 is activated in the active state and deactivated in the sleep state, and is used to measure time during the active state, but not in the sleep state. For example, the first timer 10 is activated at the beginning of the active state and deactivated again at the end of the active state. In contrast, the second timer 12 is activated in the sleep state and is used to measure time during the sleep state. The second timer 12 is deactivated in the active state. For example, the second timer 12 is activated at the beginning of the sleep state and deactivated again at the end of the sleep state. Thus, using both timers 10 and 12, that is, using the corresponding timer 10 and 12, time measurements can be performed both in the active state and in the sleep state, for example, the duration of the respective state. Advantageously, the two time measurements are combined into a continuous time measurement.

[0043] For example, in Figure 1 As can be seen in the figure, the hearing device 2 includes one or more input transducers 14 (here, two microphones), a signal processing device 6, and an output transducer 16 (here, an earpiece). The hearing device 2 shown here as an example is used to provide hearing-impaired users with compensation for hearing loss. The input transducer 14 generates an input signal, which is fed to the signal processing device 6. The signal processing device 6 modifies the input signal to generate an output signal, which is thus the modified input signal. Finally, the output signal is output to the user via the output transducer 16.

[0044] In the use state, the hearing device 2 is active and signals are processed and output as described above. In other words, the use state is activated when the hearing device 2 is turned on, and deactivated when the hearing device 2 is turned off. The period between the start and the end of the use state is also referred to as the use phase pn. During the active use state, i.e., during the use phase pn, sound signals from the environment are converted into input signals using the input converter 14. Alternatively or additionally, the electrical input signal of the hearing device 2 is directly received via another input converter, for example, from another device, such as the second device 4, which transmits the electrical input signal to the hearing device 2 via a data connection. The received input signal is then processed in the signal processing device 6, and an output signal is generated therefrom. The output signal is then output to the user via the output converter 16.

[0045] In contrast, in the sleep state, the hearing device 2 is turned off, the signal processing device 6 is deactivated, and the described signal processing and output are not performed. The period between the start and subsequent end of the sleep state is also referred to as the sleep phase pr. During this sleep phase pr, the signal processing device 6, as well as the input converter 14 and the output converter 16, are deactivated and, in this manner, do not consume energy. The hearing device 2 is thus essentially deactivated, but not completely. Rather, the hearing device 2 has one or more sleep-state functions that, if necessary, are performed in the sleep state and accordingly consume energy. However, the main functions of processing and output are deactivated. Time measurement using the second timer 12 is such a sleep-state function, and the second timer 12 is correspondingly active in the sleep state. However, energy consumption in the sleep state is significantly reduced compared to the active state, particularly because no signal processing or output is performed. The sleep state is therefore an operating state in which the user is not using or wearing the hearing device 2.

[0046] The active state and the dormant state are mutually exclusive, and only one of the two states can be active at a given time point. The active state and the dormant state alternate with each other, thereby generating a time sequence of active phases pn of the active state and active phases pr of the dormant state.

[0047] Due to the use of two timers 10 and 12, time measurement can be performed not only in the active state but also in the sleep state. This allows for continuous, absolute time measurement regardless of the operating state of the hearing device 2, uninterrupted by repeated switching on and off of the hearing device 2. Real-time synchronization is not required, although it is optional. Continuous time measurement is now performed independently of this using the time measurement unit 8. Using this continuous time measurement, usage times, usage events, and usage situations of different usage phases pn (and, if necessary, sleep phases pr) can be linked, and advantageously so. In this way, a common, continuous time frame is formed across multiple usage phases and sleep phases pr, also referred to as the hearing device time th. This hearing device time th is, so to speak, an internal time of the hearing device 2 and is relative in that it does not necessarily correspond to the real time te, i.e., the currently existing time, but is measured relative to a starting point. Using the two timers 10 and 12 , the hearing device time th can now be adjusted after a single usage phase pn, thus also allowing for absolute time measurement. This allows for improved data analysis using the hearing device 2 compared to data analysis focused solely on relative time measurement. However, the details of this data analysis are irrelevant here; the main point is that the hearing device 2 is capable of absolute time measurement and does not rely on additional external devices. Therefore, the hearing device 2 does not require a second device 4 for absolute time measurement.

[0048] In order to perform continuous time measurement, the time measurement unit 8 adjusts the hearing instrument time th using a first timer 10 in the use state and adjusts the hearing instrument time th using a second timer 12 in the sleep state. Figure 3 As shown in Figure 3 The hearing instrument time th is shown starting from a starting point S (for example, temporarily t=0 until an optional calibration with the real time te has been performed). Alternating use and rest phases pn, pr are also shown. During the use phase pn, the first timer 10 is active, and during the rest phase pr, the second timer 12 is active. In other words, the two timers 10, 12 together form a common hearing instrument clock that outputs the continuously measured hearing instrument time th, for example, as a combination of date and time. Therefore, the timers 10, 12 used to adjust the hearing instrument time are changed during switching on and off.

[0049] Additionally, here, with the help of Figure 3The time measurement unit 8 is calibrated with the real-time time te shown in FIG, provided here by the second device 4. To this end, the second device 4 is connected to the hearing instrument 2 for data exchange. This synchronization of the hearing instrument 2 and the second device 4 causes the hearing instrument time th to correspond to the real-time time te, thereby enabling not only absolute time measurement but also time measurement within the framework of the real-time time te. In this sense, the time measurement unit 8 thus represents the real-time clock of the hearing instrument 2. However, it should be noted that this calibration of the hearing instrument time th with the real-time time te is not necessary for continuous time measurement, as the absence of calibration ultimately only results in a shift between the hearing instrument time th and the real-time time te, which is not necessarily relevant for data analysis.

[0050] The second device 4 is, for example, a computer, smartphone, or the like, running fitting software, such as at an audiologist's office, and can be connected to the hearing device 2 wirelessly or by wire, such as via Bluetooth or WLAN, for data exchange. The second device 4 has a real-time clock (not explicitly shown) that generates the real-time time te (also called system time, such as UTC, i.e., Coordinated Universal Time). This real-time time te is then transmitted to the hearing device 2 for calibration of the hearing device time th and, therefore, of the time measurement unit 8. For example, the hearing device time th is calibrated each time the hearing device 2 is connected to a suitable second device 4.

[0051] In the delivery state, the hearing device time th is typically uncalibrated. Therefore, when the hearing device 2 is first put into operation, i.e., when it is first switched on, and therefore at the beginning of the first usage phase pn, a time point must be arbitrarily predetermined or estimated as the starting point. For example, when the hearing device 2 is manufactured, the manufacturing date or a date several days or weeks in the future is selected as the starting point S. The clock time at the starting point is, for example, 00:00. This time point is then shifted according to the actual time of commissioning. Due to the time measurement unit 8, the hearing device 2 can, in principle, already perform time measurement throughout the entire day, i.e., 24 hours. For example, this can be achieved by simply incrementing a counter at regular intervals until 24 hours are reached and then simply counting a new day at the end. Whether these days correspond to the actual number of days is initially unimportant; the hearing device 2 can at least monitor usage times, usage events, and usage situations, particularly the switching on and off of the hearing device 2, over the course of a day and, in this regard, determine both absolute and continuous time frames for the usage state. Before the first calibration with the second device 4, an absolute time measurement is then performed. However, this absolute time measurement is usually offset by a certain shift (i.e., a fixed value) relative to the real time te. This is then calibrated accordingly during a later calibration, and the time measurements to date are then converted. The correct real time te is then set to the original starting point S accordingly. For example, if 00:00 is used as the starting point S, but the hearing device 2 is actually first connected at 7:15, there is a time difference of 7 hours and 15 minutes before the first calibration. This time difference is then calibrated (and the date shift is similarly calibrated, if necessary). The data analysis to date is then calibrated accordingly.

[0052] Here, the two timers 10 and 12 are optimized according to the corresponding operating state. To this end, in the design shown, the first timer 10 has a higher accuracy than the second timer 12, and the second timer 12 (when activated) has a lower energy consumption than the first timer 10 (when activated). Here, "accuracy" is understood to mean "precision in time" or "frequency stability", that is, how accurately the timers 10 and 12 measure time, and how high the frequency stability of the timers 10 and 12 is. The higher the accuracy, the more evenly the timers 10 and 12 measure consecutive time units, and / or the smaller the accumulated time deviation (English "drift") from the real time te. Therefore, the first timer 10 is also called a precise timer, and the second timer 12 is, on the contrary, called a low-energy timer. Now, the first timer 10 is used to achieve the most accurate time measurement possible, and on the other hand, the second timer 12 is used to achieve the least possible energy consumption in the sleep state. Initially, the absolute accuracy and absolute energy consumption of the two timers 10 and 12 are unimportant; rather, the energy consumption and accuracy of the two timers 10 and 12 relative to one another are more important, and thus, the conflict between accuracy and energy consumption is resolved differently in different operating states. Here, the first timer 10 is selected for accuracy, and the second timer 12 for energy consumption. Accordingly, any possible deviation of the hearing instrument time th from the real-time time te in the sleep state is tolerated. This is also not a problem, as any such deviation can be detected during calibration with the second device 4 or during calibration of the second timer 12 with the first timer 10 and, if necessary, can be corrected again.

[0053] exist Figure 2 In the embodiment of the present invention, the first timer 10 is a quartz oscillator. For clock generation and therefore for time measurement, the quartz oscillator uses an oscillating crystal 18. Therefore, the quartz oscillator has a high precision, i.e., the quartz oscillator is particularly frequency-stable. In one possible embodiment, the quartz oscillator is also used as a clock generator for operating the signal processing device 6 and / or as a clock generator for other functions.

[0054] exist Figure 2 In the embodiment of the invention, the second timer 12 is an RC oscillator, but it can also be an LC oscillator. The second timer 12 is also a self-excited oscillator, that is, unlike a quartz oscillator, the second timer 12 is not particularly frequency-stable, so that the second timer 12 has a clock frequency that can vary over time. For clock generation, the RC oscillator has one or more resistors 20 and capacitors 22, which are connected to each other in a suitable manner to generate oscillations, thereby enabling time measurement. Figure 2 Only one resistor 20 and one capacitor 22 are shown as examples, but other designs are also conceivable. Similarly, an LC oscillator has one or more inductors and capacitors for clock generation, thereby generating oscillations for time measurement. Therefore, in each case, second timer 12 has at least one capacitor 22, which is repeatedly charged and discharged to generate oscillations. Capacitor 22 also determines the energy level with which second timer 12 is charged at the start of the sleep state.

[0055] Here, the second timer 12 is integrated into an analog IC 24 (i.e., an analog integrated circuit) of the hearing instrument 2. In the illustrated embodiment, the analog IC 24 is constructed separately from the signal processing device 6. Here, the signal processing device 6 is implemented as part of a digital signal processor 26 (abbreviated as "DSP" for "digital signal processor"). Not only the analog IC 24, but also the signal processor 26, and therefore the signal processing device 6, are also part of the control unit 28 of the hearing instrument 2. The analog IC 24 is implemented, for example, as a microcontroller, an ASIC, etc., and a design is also suitable in which the entire control unit 28 is constructed as a microcontroller, an ASIC, etc., wherein, for example, as in Figure 1 As shown in FIG, the analog IC 24 thus forms a sub-area of ​​the control unit 28. In addition to the second timer 12, Figure 2 In the embodiment, further analog functions 30 which are not further relevant here are also integrated in the analog IC 24 .

[0056] exist Figure 2 In the embodiment of the present invention, the hearing instrument 2 has a shift register 32, and the second timer 12 controls the shift register 32 so that the duration of the sleep state is stored in the shift register 32. Here, for this purpose, the shift register 32 is integrated into the analog IC 24 and is connected to the second timer 12. For example, if the second timer 12 is active, the second timer 12 continuously increments the counter by simply using the shift register 32 as a counter, and the time measured by the second timer 12 is stored in the shift register 32.

[0057] also, Figure 2The analog IC 24 in has a main memory 34, which is connected to the shift register 32 already mentioned, in order to store the time measurement values ​​of the second timer 12 and then to perform a new time measurement using the shift register 32 without discarding the previous time measurement value. In this way, the duration of the different sleep phases pr is measured and stored separately in the main memory 34, in particular for continuous time measurement and for data analysis. As soon as the sleep state is deactivated and the use state is activated, the shift register 32 is read out and the time measurement value stored therein is stored in the main memory 34 in order to be combined there with the time measurement value of the first timer 10 from the previous use phase pn or the now subsequent use phase pn, for example, to be added, and in this way the hearing device time th is adjusted. Correspondingly, Figure 2 The first timer 10 in the main memory is also connected to the main memory 34 in order to store therein time measured values ​​of the first timer 10 , for example the duration of the usage phase pn.

[0058] As in Figure 2 As can be seen in FIG. 1 , the first timer 10 is at least partially integrated in the analog IC 24 by virtue of the associated oscillating quartz 18 not being integrated in the analog IC 24 but being constructed as a separate component and then connected to the analog IC 24 .

[0059] Here, the second timer 12 is designed to be untrimmed, i.e., uncalibrated. The second timer 12 is then calibrated using the first timer 10. Because the first timer 10 is more accurate than the second timer 12, the first timer 10 can be used to calibrate the second timer 12, eliminating the need for separate calibration during manufacturing. For example, for calibration, the hearing device 2 includes a zero-crossing or edge detector (not explicitly shown) and a shift register as a counter. The second timer 12 is calibrated by using the shift register to count the oscillations (also called cycles) of the second timer 12 within a fixed time period and the oscillations of the first timer 10 within the same time period, and then comparing them. In this way, a characteristic number is determined, which is used to convert the time measurement value of the second timer 12. For example, the characteristic number is the ratio of the number of cycles of the two timers per time unit, or the number of cycles of the second timer per individual cycle of the first timer, or the like. The characteristic number is stored, for example, in the main memory 34. The calibration and / or determination of the characteristic number is performed, for example, only when the hearing instrument 2 is first put into operation, or alternatively or additionally, is always repeated when a usage state is activated.

[0060] Furthermore, in the illustrated embodiment, the second timer 12 is not temperature-stabilized. The hearing instrument 2 then has a temperature sensor 36, which is already provided for one or more additional functions of the hearing instrument 2. The temperature is measured using the temperature sensor 36, and the second timer 12 is calibrated, i.e., calibrated, using the temperature (in addition to or as an alternative to the calibration using the first timer 10 described above). For example, a linear relationship between temperature and deviation is assumed in the time measurement, or a calibration curve, calibration function, or calibration table, for example, stored in the main memory 34, is used. The temperature is measured directly during the sleep state, or at the beginning and / or end of the sleep phase pr, i.e., when the sleep state is activated or deactivated.

[0061] The hearing device 2 shown here also has an energy management unit 38 for controlling the energy supply to various components of the hearing device 2, in particular the analog IC 24 and, if necessary, other parts of the control unit 28. The energy supply is provided by a battery 40 of the hearing device 2. In this case, the energy management unit 38 is integrated into the analog IC 24. The hearing device 2 also has a safety switch 42 for preventing deep discharge of the battery 40 by electrically isolating the battery 40 from the rest of the hearing device 2 below a minimum state of charge. Figure 2 In the present embodiment, a safety switch 42 is also integrated into the analog IC 24. The safety switch 42 is designed to be open during manufacturing of the hearing device 2, open upon delivery to the user, and closed only when the hearing device 2 is first put into operation. This prevents deep discharge of the battery 40 before commissioning. Furthermore, the safety switch 42 is a reversible switch, thus preventing deep discharge of the battery 40 even after the first commissioning, for example, if the duration of a single sleep phase pr is long, causing the battery 40's state of charge to fall below a minimum state of charge. When the battery 40's state of charge falls below the minimum state of charge, the energy management unit 38 opens the safety switch 42 again. However, in other cases, even when the sleep phase is activated, the safety switch 42 remains closed, thereby supplying energy to the second timer 12.

[0062] The energy management unit 38 also controls the energy supply from the battery 40 to the second timer 12. For example, upon activation, the second timer 12 is charged once using energy from the battery 40, and then subsequently, as long as the sleep state is active, no further energy is supplied to the second timer 12 from the battery 40. Alternatively, the second timer 12 is repeatedly charged from the battery 40 of the hearing device 2 during the sleep state. In particular, in the case of an RC or LC oscillator, one or more capacitors 22 are charged for time measurement, and these capacitors 22 then require no further energy for a specific period of time. However, over time, the charged energy is consumed, and recharging may be necessary. However, if this lasts longer than the duration of the active sleep state, a single charge at the beginning of the sleep phase pr is sufficient. If the second timer 12 is repeatedly charged during the sleep state, this is done, for example, always below the minimum charge level of the second timer 12.

[0063] A design is also possible in which the duration of the sleep state is measured only before a maximum duration, and second timer 12 is charged in the sleep state only when the maximum duration has not yet been reached. In this way, deep discharge of battery 40 is prevented by measuring time using second timer 12 only before reaching a maximum duration, for example, seven days, and then deactivating second timer 12 so that no energy is consumed. Alternatively or additionally, deep discharge of battery 40 can be avoided by powering second timer 12 with energy from battery 40 in the sleep state only when the charge state of battery 40 corresponds to at least a minimum charge state. For example, the charge state can be determined based on the voltage of battery 40, or the voltage of battery 40 can be directly used as a measure of the charge state.

[0064] Reference Signs List

[0065] 2 Hearing devices

[0066] 4 Second device

[0067] 6 Signal processing device

[0068] 8 Time measurement unit

[0069] 10 First Timer

[0070] 12 Second timer

[0071] 14 Input Converter

[0072] 16 output converter

[0073] 18 oscillating quartz

[0074] 20 resistors

[0075] 22 capacitors

[0076] 24 Analog ICs

[0077] 26 Signal Processor

[0078] 28 control unit

[0079] 30 Other simulation functions

[0080] 32 shift registers

[0081] 34 Main memory

[0082] 36 Temperature Sensor

[0083] 38 Energy Management Unit

[0084] 40 batteries

[0085] 42 Safety switch

[0086] S starting point

[0087] te real time

[0088] th hearing device time

[0089] pn use phase

[0090] pr dormant stage

Claims

1. A method for operating a hearing instrument (2), -in, The hearing device (2) is capable of switching between a use state and a sleep state, wherein the signal processing device (6) of the hearing device (2) is activated in the use state and the signal processing device (6) is deactivated in the sleep state. - wherein the hearing instrument (2) has a time measurement unit (8) having a first timer (10) and a second timer (12), - wherein the first timer (10) is activated in the use state and deactivated in the sleep state to measure time during the use state, - wherein the second timer (12) is activated in the sleep state to measure time during the sleep state, In order to perform continuous time measurement, the time measurement unit (8) adjusts the hearing device time (th) using the first timer (10) in the use state and adjusts the hearing device time using the second timer (12) in the sleep state.

2. The method according to claim 1, in, The time measuring unit (8) is calibrated with the aid of real time (te), which is provided by a second device (4) which is connected to the hearing instrument (2) for data exchange.

3. The method according to claim 1 or 2, in, The first timer (10) has a higher accuracy than the second timer (12), The second timer (12) has lower energy consumption than the first timer (10).

4. The method according to claim 1 or 2, in, The first timer (10) is a quartz oscillator.

5. The method according to claim 1 or 2, in, The second timer (12) is an RC oscillator or an LC oscillator.

6. The method according to claim 1 or 2, in, The hearing instrument (2) has a shift register (32) which is controlled by the second timer (12) such that the duration of the sleep state is stored in the shift register (32).

7. The method according to claim 1 or 2, in, The second timer (12) is configured to be untrimmed and is calibrated using the first timer (10).

8. The method according to claim 1 or 2, in, the second timer (12) is not temperature stable, The hearing device (2) has a temperature sensor (36), which is used to measure the temperature and to calibrate the second timer (12).

9. The method according to claim 1 or 2, in, The second timer (12) is charged once with energy from a battery (40) of the hearing device (2) upon activation and then subsequently no further energy is supplied to the second timer (12) from the battery (40) as long as the sleep state is active.

10. The method according to claim 1 or 2, in, The second timer (12) is repeatedly charged by the battery (40) of the hearing device (2) in the sleep state.

11. The method according to claim 10, in, The duration of the sleep state is measured only before the maximum duration, The second timer (12) is charged in the sleep state only when the maximum duration has not been reached.

12. The method according to claim 10, in, The second timer (12) is supplied with energy from the battery (40) in the sleep state only when the charge state of the battery (40) corresponds to at least one minimum charge state.

13. A hearing instrument (2) having a control unit (28) which is designed to carry out the method according to any one of claims 1 to 12.

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