CN104869516B - Resource manager - Google Patents
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- CN104869516B CN104869516B CN201510086785.3A CN201510086785A CN104869516B CN 104869516 B CN104869516 B CN 104869516B CN 201510086785 A CN201510086785 A CN 201510086785A CN 104869516 B CN104869516 B CN 104869516B
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Abstract
The present invention relates to resource managers. A hearing aid comprising a power supply connected to supply power to a hearing aid circuit, the hearing aid circuit having: a wireless communication unit configured to communicate with another device; and a scheduler configured to receive communication requests from the communication tasks and schedule each communication task based on the communication task priority and the state of the power supply.
Description
Technical Field
A new hearing aid is configured to communicate wirelessly with other devices while taking into account the power state of the hearing aid.
The wireless communication may be performed in a wireless network that facilitates interconnection of multiple devices in the network, such as hearing aids, remote controls, accessory devices, mobile phones, headsets, doorbells, alarm systems, broadcast systems, etc.
Background
WO2004/110099 discloses a hearing aid wireless network in which the communication protocol is single, so that only a small number of codes is required and the amount of power consumed during operation is low. In addition, the acquisition time is short and the delay time is small.
Disclosure of Invention
A new hearing aid is provided which is capable of performing wireless communication according to a plurality of different wireless communication protocols.
A new hearing aid is provided comprising a hearing aid circuit, the hearing aid having:
an input transducer configured to output an audio signal based on a signal applied to the input transducer and representative of sound;
a hearing loss processor configured to compensate for hearing loss of a user of the hearing aid and to output a hearing loss compensated audio signal, e.g. the hearing aid may be used to restore loudness such that the loudness of the applied signal as perceived by a normally heard listener substantially matches the loudness of the hearing loss compensated signal as perceived by the user;
an output transducer, e.g., a receiver, an implanted transducer, etc., configured to output an aural output signal based on the hearing loss compensated audio signal, the aural output signal receivable by the human auditory system to cause a user to hear sound; and
a wireless communication unit configured to communicate with another device.
A power supply is connected to supply power to the hearing aid circuitry.
The hearing aid may further comprise a processor with an operating system configured to manage hearing aid hardware and software resources, including for example a hearing loss processor and possibly other processors and associated signal processing algorithms, a wireless communication unit, memory resources, power supply, etc., and provide common services to tasks to be performed. The operating system may schedule tasks to efficiently use the hearing aid resources and also include computational software for cost allocation including power consumption, processor time, storage, wireless transmission, and other resources.
Although the application code of the task is typically executed directly by the appropriate hearing aid processing circuitry, for various tasks such as wireless communication and memory allocation, the operating system acts as an intermediary between the task and the hearing aid circuitry and will frequently cause the system to invoke or interrupt operating system functions.
The processor may be a hearing loss processor or the wireless communication unit may comprise a processor with an operating system or the operating system may be distributed between the processors, e.g. the hearing loss processor and the wireless communication unit processor and possibly one or more further processors.
In particular, the operating system may be configured to control the wireless communication unit to perform communication with other devices according to a plurality of communication protocols and priorities of communication tasks.
The operating system may include, or consist of, a scheduler. The scheduler may be configured to receive communication requests from communication tasks and may schedule each communication task based on task priority and a state of the power supply, e.g. a discharge state of a battery of the power supply and/or a capacitor of the hearing aid circuitry.
There is provided a new method of scheduling wireless communication for a hearing aid comprising a hearing aid circuit, the hearing aid having:
an input transducer configured to output an audio signal based on a signal applied to the input transducer and representative of sound;
a hearing loss processor configured to compensate for a hearing loss of a user of the hearing aid and to output a corresponding hearing loss compensated audio signal;
an output transducer configured to output an auditory output signal based on the hearing loss compensated audio signal, the auditory output signal receivable by the human auditory system to cause a user to hear sound;
a wireless communication unit configured to communicate with another device;
a power supply connected to supply power to the hearing aid circuitry, an
An operating system configured to control the wireless communication unit to communicate with other devices according to respective communication protocols and priorities.
The new method may include receiving a communication request from the communication task and scheduling the communication task based on task priority and a state of the power source.
A transducer is a corresponding output signal that converts a signal applied to the transducer in one form of energy into another form of energy.
The input transducer may comprise a microphone that converts an acoustic signal applied to the microphone into a corresponding analog audio signal, wherein the instantaneous voltage of the audio signal varies continuously with the sound pressure of the acoustic signal.
The input transducer may also include a telemetry coil that converts the changing magnetic field on the telemetry coil into a corresponding changing analog audio signal, wherein the instantaneous voltage of the audio signal varies continuously as the magnetic field strength on the telemetry coil changes. The telemetry coil may be used to add signals to the noise ratio of speech over a speaker used to look for a large number of people in a public place such as a church, a lecture hall, a theater, a movie theater, etc., or over an amplification system such as at a train station, airport, shopping center, etc. The speech from the loudspeaker is converted into a magnetic field with an induction coil system (also called "hearing coil"), and the remote sensing coil is used to magnetically pick up the speech signal carried by the magnetic field.
The input transducer may further comprise at least two spaced apart microphones, and a beamformer configured for combining microphone output signals of the at least two spaced apart microphones into directional microphone signals.
The input transducer may comprise one or more microphones, telemetry coils and switches, for example for selecting among omni-directional microphone signals, or telemetry coil signals, individually or in any combination, as audio signals.
Typically, an analog audio signal is adapted for digital signal processing by being converted into a corresponding digital audio signal by an analog-to-digital converter, such that the amplitude of the analog audio signal is represented by a binary number. In this manner, the discrete-time and discrete-amplitude digital audio signals in the form of a sequence of values represent continuous-time and continuous-amplitude analog audio signals.
Throughout this disclosure, an "audio signal" may be used to identify any analog or digital signal forming part of a signal path from the output of an input transducer to the input of a hearing loss processor.
Throughout this disclosure, a "hearing loss compensated audio signal" may be used to identify any analog or digital signal forming part of a signal path from the output of a hearing loss processor to the input of an output transducer, which may be via a digital-to-analog converter.
The wireless communication unit may include a transceiver.
The wireless communication unit may be a device or a circuit comprising a wireless transmitter and a wireless receiver. The transmitter and receiver may share a common circuit and/or a single housing. Alternatively, the transmitter and the receiver may not share a circuit, and the wireless communication unit may include separate devices having the transmitter and the receiver, respectively.
The wireless communication may be performed according to a frequency diversification or spread spectrum scheme, i.e. the frequency range utilized by the hearing aid is divided into a plurality of frequency channels, and the wireless transmission switches the frequency channels according to a predetermined scheme such that the transmission is distributed over the entire frequency range.
The frequency hopping algorithm may be arranged to allow devices in the network to calculate what frequency channel in the network will be used at any given point in time, independent of the history of the network, e.g. the pseudo-random number generator calculates the next frequency channel number based on the current frequency channel number. This facilitates the synchronization of a new device with the hearing aid, e.g. the new device comprises the same pseudo-random number generator as the hearing aid. Thus, once the current channel number is received during the request, the new device will calculate the same next channel number as the hearing aid.
Each device in the network has its own identification number, e.g., a 32-bit number. Since the possibility of having two users with hearing aids with the same identity is negligible, no globally unique identity is required.
Preferably, the new device is automatically recognized by the network and interconnected with the network.
An advantage of a network operating according to a spread spectrum scheme is that the communication will have a low sensitivity to noise since noise is typically present in a particular frequency channel, and the communication will only be performed in the particular frequency channel for a short period of time, after which the communication will be switched to another frequency channel.
Furthermore, since the probability of two networks using the same specific frequency channel at the same time is very low, several networks may be present closely together, e.g. two or more hearing aid users may be present in the same room without network intervention. Likewise, the hearing aid network may co-exist with other wireless networks utilizing the same frequency band, such as a bluetooth network or other wireless local area networks.
Advantageously, the hearing aids may be embedded in a binaural hearing aid system, wherein the two hearing aids are interconnected, e.g. via a wireless network, for digitally exchanging data, e.g. audio signals, signal processing parameters, control data such as identification of signal processing programs, etc., and optionally interconnected with other devices such as remote controls, etc.
Typically, only a limited amount of power is available from the power supply of the hearing aidAnd (6) obtaining. For example, power is typically supplied by conventional ZnO in hearing aids2A battery.
Size and power consumption are important considerations in the design of hearing aids. The size of the hearing aid depends on the size of the battery used and in order to ensure that the hearing aid is compact and unobtrusive, small battery sizes are used, such as "312" and "13" models. However, small batteries have a relatively large internal resistance. For example, a "312" battery typically has an internal resistance of 5 ohms, which is two orders of magnitude higher than that of an AA-type battery. The high internal resistance causes a significant drop in the output voltage with increasing output current. This may be particularly important for part of the operation of the hearing aid circuitry.
The wireless communication unit of the hearing aid may be included in a radio chip, such as the Nordic semiconductor radio chip "" nRF24I01 ", which is generally described above as conventional ZnO2Operating at the voltage supplied by the battery. Therefore, it may be necessary to provide power to the radio chip via a voltage doubler (voltage amplifier). In addition, the radio chip draws a large amount of current during transmission and reception. Conventional ZnO2The battery is only able to supply the required amount of current to be drawn by the wireless communication unit during transmission and reception for a limited period of time, typically 1 millisecond. In case the amount of current required by the battery is continuously supplied for a longer period of time, the supply voltage will drop and fall below a certain threshold value, and the hearing aid circuitry, in particular the digital part of the hearing aid circuitry, will not function properly.
Further, ZnO is provided even after current has been supplied to the radio chip during communication within a limited time period2The battery also requires time to recover. Typically, the radio chip duty cycle, i.e. the percentage of time the radio is on relative to the sum of the radio on and off times, must remain below 10%.
This problem can be alleviated by connecting the circuit with a resistor and a capacitor between the power supply of the hearing aid circuitry and the source voltage input of the wireless communication unit, e.g. between the output of the voltage doubler and the power supply input of the radio chip. The capacitor delivers the peak current to the wireless communication unit so that the peak current drawn from the power supply becomes small, and the resistor limits the current drawn from the power supply by the wireless communication unit during the capacitor voltage drop.
The scheduler may be configured to calculate the earliest possible start time for executing the next communication task based on the estimated power consumption of the current or most recent communication task, in order to provide a power source, such as the above mentioned battery and/or capacitor, for a recovery time period between the end of the current or most recent communication task and the start of the next communication task.
The recovery time period applied after the end of the communication task performed by the wireless communication unit may be calculated as an estimated duration or an actual duration of the communication task performed by the wireless communication unit multiplied by a constant.
The estimated duration may consist of a time period increased by pre-processing, transmitting, receiving and post-processing of the communication task.
The actual duration may consist of a time period increased by the period during which the wireless device is actually powered while performing the communication task. Thus, when the actual duration is used to calculate the recovery time period, the possible power down periods of the wireless device during the performance of the communication task are not added to the recovery time period.
The constants may range from 0.5 to 2, preferably from 0.6 to 1.8, more preferably from 0.7 to 1.5, most preferably from 0.8 to 1.4. For example, the constant may be equal to 1.125.
The recovery time period applied after the end of the communication task performed by the wireless communication unit may be calculated from the charge or current drawn from the power supply during the performance of the communication task.
When calculating the recovery time period, the scheduler may take into account the power state, i.e. the discharge state of the battery. For example, the constant may increase as a function of the discharge state of the battery.
The communication request may contain a priority of the communication task.
The communication request may include a start time for performing the requested communication task.
The communication request may include a duration for performing the requested communication task.
The scheduler may determine that the requested start time is unavailable and may communicate to the requesting task that another start time must be requested.
The scheduler may determine that an already scheduled task cannot be executed at a scheduled start time, e.g. due to a request with a higher priority, and may communicate to the already scheduled task that a new start time must be requested.
The scheduler may be configured to: the communication task having the lower priority is allowed to perform communication before the communication task having the higher priority as long as the communication task having the lower priority will end its communication at the time of the appropriate recovery time period of the power supply to elapse before the communication task having the higher priority is started.
The scheduler may also schedule other tasks than the wireless communication tasks, and thus the scheduler may be configured to receive task requests from other tasks than the wireless communication tasks and may schedule each task according to task priority and the state of the power supply.
The scheduler may also take into account the power consumption of other tasks besides wireless communication when scheduling. Examples of other tasks include power consumption algorithms, storage in flash memory, etc. The recovery time period for such other tasks may be calculated in the same manner as explained above in relation to the recovery time period for the wireless communication task. The constants may be different for different types of tasks, e.g. due to different power consumption.
The scheduler may be configured to power down one or more parts of the hearing aid circuitry to avoid excessive power consumption due to simultaneous operation of the power consuming circuitry.
For example, the scheduler may be configured to turn off the wireless communication unit during sleep, e.g., during writing to and/or reading from flash memory, during execution of a power consumption algorithm, etc.
Preferably, the scheduler is configured to schedule the next start time for each requested task, even if repeated execution of a given task, multiple start times that can be easily determined, or have been determined, e.g. streaming audio, i.e. the scheduler is configured not to schedule multiple start times for a given task. In this way the number of scheduled tasks is kept low, thereby making the scheduler simple and dynamic as no re-scheduling in response to new requests is required.
In the case where a communication task ends or terminates earlier than scheduled, the scheduler may be configured to recalculate the recovery time period based on the actual duration and/or actual power consumption of the suspected communication task. After the recalculated recovery time period has elapsed, and until the scheduled start time of the next scheduled task, there may be sufficient time to execute another task, and as described above, the scheduler may be configured to: the execution of another task is allowed even if the task has a lower priority than the next scheduled task, as long as the task will end at the time of the associated recovery time period to elapse before the next scheduled task starts.
The signal processing in the new hearing aid may be performed by dedicated hardware or may be performed in one or more signal processors or in a combination of dedicated hardware and one or more signal processors.
A protocol is a system of numerical rules for exchanging data within or between devices, for example, in a network. The protocol defines the syntax, semantics and synchronization of the communication. The protocol can be implemented in hardware, software, or both.
The communication task comprises an action requesting a communication to be performed, e.g. transmitting a data packet to the hearing aid. The communication request may be performed by another device or processor in the hearing aid that needs to cooperate with the communication unit of the hearing aid.
As used herein, the terms "processor," "signal processor," "controller," "system," and the like are used to refer to a CPU-related entity, either hardware, a combination of hardware and software, or software in execution.
For example, a "processor," a signal processor, "controller," "system," and the like can be, but are not limited to being, a process running on a processor, an object, an executable, a thread of execution, and/or a program.
By way of example, the terms "processor," "signal processor," "controller," "system," and the like designate an application running in the processor and a hardware processor. One or more "processors," signal processors, "" controllers, "" systems, "or the like, or any combination thereof, may be involved in the processes and/or concepts being performed, and one or more" processors, "signal processors," "controllers," "systems," or the like, or any combination thereof, may be implemented in one hardware processor, may be implemented in combination with another hardware circuit, and/or may be distributed between two or more hardware processors, and may also be implemented in combination with other hardware circuits.
Further, a processor (or similar term) may be any element or any combination of elements capable of performing signal processing. For example, the signal processor may be an ASIC processor, an FPGA processor, a general purpose processor, a microprocessor, a circuit element, or an integrated circuit.
Drawings
In the following, the new method and the hearing aid will be explained in more detail with reference to the drawings, in which
Fig. 1 schematically illustrates a hearing aid according to the appended claims communicating in a wireless network.
Fig. 2 is a schematic view of a new hearing aid according to the appended claims.
Fig. 3 illustrates time slots and frames.
FIG. 4 illustrates various task requests, an
Fig. 5 shows a reservation list and a priority task list.
Detailed Description
In the following, various examples of the new method and hearing aid are illustrated. However, the new method and hearing aid according to the appended claims may be embodied in different forms and should not be construed as limited to the examples set forth herein.
It should be noted that the figures are schematic and simplified for clarity, and that they show only the details necessary for understanding the new method and the hearing aid, while other details are left out.
Like reference symbols in the various drawings indicate like elements. Therefore, like elements will not be described in detail in the description of each drawing.
Fig. 1 schematically illustrates binaural hearing aids 10L, 10R, i.e. a left ear hearing aid 10L and a right ear hearing aid 10R, each having a wireless communication unit for connection to a wireless network interconnecting the two hearing aids and interconnecting the hearing aids 10L, 10R and a plurality of other devices in the wireless network. In the example illustrated in fig. 1, a doorbell, a mobile phone, a cordless phone, a television, and an accessory device are also connected to the wireless network.
The ID identifies each device. The ID is unique in the network.
The hearing aid network illustrated in fig. 1 operates in the Industrial Scientific Medical (ISM) band at 2.4 GHz. It comprises 80 channels of 1MHz bandwidth. A frequency hopping time division multiplexing scheme is used. During acquisition, the frequency hopping scheme includes reducing the number of frequency channels for faster acquisition, e.g., less than 16 frequency channels, preferably 8 frequency channels. The members of the reduced channel set represent acquisition channels. Preferably, the acquisition channels are distributed evenly among all the frequency bands utilized by the network.
Fig. 2 shows a schematic view of the new hearing aid 10.
The hearing aid 10 has ZnO2A battery 12 connected for powering the hearing aid circuitry 14.
The hearing aid circuit 14 includes an input transducer 16 in the form of a microphone 16. When the hearing aid 10 is in operation, the microphone 16 outputs an analog audio signal 18 based on the acoustic sound signal reaching the microphone 16.
The analog-to-digital converter 20 converts the analog audio signal 18 into a corresponding digital audio signal 22 for digital signal processing in the hearing aid circuitry 14. In particular, the hearing loss processor 24A is configured to compensate for the hearing loss of the user of the hearing aid 10. Preferably, the hearing loss processor 24A includes a dynamic range processor, as is known in the art, for compensating for the loss of accessory frequencies of the dynamic range of the user, as is commonly referred to in the art as supplemental. Thus, the hearing loss processor 24A outputs a digital hearing loss compensated audio signal 26. The hearing aid may be configured to restore loudness such that the loudness of the hearing loss compensation signal as perceived by a user wearing the hearing aid 10 substantially matches the loudness of the acoustic sound signal reaching the microphone 16, as already perceived by a normally audible listener.
The digital-to-analog converter 28 converts the digital hearing loss compensated audio signal 26 into a corresponding analog hearing loss compensated audio signal 30.
An output transducer in the form of a receiver 32 converts the analog hearing loss compensated audio signal 30 into a corresponding acoustic signal for transmission to the eardrum of the user, thereby causing the user to hear the sound arriving at the microphone; while the individual hearing loss of the user is compensated.
The hearing loss processor 24A forms part of a processor a which executes a part 36A of the operating system 36A, 36B of the hearing aid and a memory 38A.
The hearing aid circuit 14 further comprises a wireless communication unit B with a radio device 34 configured to wirelessly communicate with other devices in a hearing aid network as shown in fig. 1 for a binaural hearing aid system. The wireless communication unit B includes a processor that executes a portion 36B of the hearing aid's operating system 36A, 36B and memory 38B, as well as a processor 24B that performs various communication protocols and other tasks.
The operation of the hearing aid 10 is controlled by the operating system 36A, 36B. The operating systems 36A, 36B are configured to manage hearing aid hardware and software resources, including, for example, the hearing loss processor 24A and possibly other processors and associated signal processing algorithms, the wireless communication unit B, memory resources 38A, 38B, the power supply 12, etc., and the operating systems 36A, 36B allocate hearing aid resources to tasks to be performed.
The operating system 36A, 36B schedules tasks to efficiently use hearing aid resources and also includes computational software for cost allocation including power consumption, processor time, memory location, wireless transmission and other resources.
Although the application code of the task is normally executed directly by the appropriate parts of the hearing aid circuitry, for various tasks such as wireless communication and memory allocation, the operating system acts as an intermediary between the task and the hearing aid circuitry hardware and will frequently cause the system to invoke or interrupt the respective operating system function.
Specifically, the operating system 36B controls the radio device 34 to perform wireless communication with other devices according to the respective communication protocols and the priorities of the respective communication tasks.
The scheduler 40 schedules each task based on task priority and the discharge state of the capacitor 42 to power the radio 34 and charging by the battery 12 through the resistor 44 in response to the task request.
The circuit with the resistor 44 and the capacitor 42 may be omitted, i.e. the resistor 44 may be replaced by a short circuit and the capacitor 42 may be replaced by an open circuit, and in this case the scheduler 40 schedules each task based on task priority and discharge status of the battery 12 in response to task requests.
In the illustrative example of the combination of the battery 12 and the capacitor 42, to provide a recovery time period of power between the end of the current or most recent communication task and the start of the next communication task, the scheduler 40 calculates the time of the earliest possible start-up for executing the next communication task based on the estimated power consumption of the current or most recent communication task.
The recovery time period applied after the communication task performed by the radio 34 ends may be calculated as the estimated or actual duration of the communication task performed by the radio 34 multiplied by a constant.
The estimated duration may consist of a time period increased by pre-processing, transmitting, receiving and post-processing of the communication task.
The actual duration may consist of a period of time increased by the period of time during which the radio 34 is actually powered while performing the communication task. Thus, when the actual duration is used to calculate the recovery time period, the possible power down period of the radio 34 during the performance of the communication task is not added to the recovery time period.
In the exemplary hearing aid 10, the constant may be equal to 1.125.
In another example, the recovery time period applied after the end of a communication task performed by the radio 34 may be calculated from the charge or current drawn from the power supply during the performance of the communication task.
Furthermore, the scheduler 40 may take into account the power state, i.e. the discharge state of the battery 12 and/or the capacitor 42, when calculating the recovery time period. For example, the above-mentioned constant may increase as a function of the discharge of the battery 12.
The scheduler 40 may determine that the requested start time is not available and may communicate to the requesting task that another start time must be requested.
The scheduler 40 may determine that an already scheduled task cannot be executed at a scheduled start time, e.g. due to the entry of a request with a higher priority, and may communicate to the already scheduled task that a new start time has to be requested.
The scheduler 40 may be configured to: communication tasks having a lower priority are allowed to perform communication before communication tasks having a higher priority, as long as the communication tasks having a lower priority will end their communication at the time of the associated recovery time period to elapse before the communication tasks having a higher priority are started. This may be useful, for example, if a task is terminated or ended in a time shorter than the request duration. This may reserve space for another task to be executed before the next scheduled task is started.
The scheduler 40 may also take into account the power consumption of other tasks in addition to wireless communication when scheduling. Examples of other tasks include power consumption algorithms, storage in flash memory, etc. The recovery time period for such other tasks may be calculated in the same manner as explained above in relation to the recovery time period for the wireless communication task. The constants may be different for different types of tasks, e.g. due to different power consumption.
The scheduler 40 may be configured to power down one or more portions of the hearing aid circuitry to avoid excessive power consumption due to simultaneous operation of power consuming circuitry, such as the radio 34, flash memory, signal processors executing signal processing algorithms, etc.
For example, the scheduler 40 may be configured to turn off the radio 34 during sleep, e.g., during writes to and/or reads from flash memory, during execution of power consumption algorithms, etc.
Preferably, the scheduler 40 is configured to schedule only the next start time for each task, even if repeated execution of a given task, multiple start times that can be easily determined, or have been determined, e.g., streaming audio, i.e., the scheduler 40 is configured not to schedule the start time order of a given task. In this way the number of scheduled tasks remains low, thereby allowing the scheduler 40 to remain simple and dynamic as no rescheduling in response to new requests is required.
In the case where a communication task ends or terminates earlier than scheduled, the scheduler 40 may be configured to recalculate the recovery time period based on the actual duration and/or actual power consumption of the suspected communication task. After the recalculated recovery time period has elapsed, and until the scheduled start time of the next scheduled task, there may be sufficient time to execute another task, and the scheduler 40 may be configured to: the execution of another task is allowed even if the other task has a lower priority than the next scheduled task, as long as the lower priority task will end at the time of the lower priority task's associated resume time period to elapse before the next scheduled task starts.
An exemplary protocol is shown in fig. 3, where the time division has a length of 1250 mus (minimal Bluetooth)TMTwice the length of a slot). The slot numbers are 0 to 255.
256 slots, i.e., slot 0 to slot 255, constitute one frame. The frames are also numbered.
Among the factors that influence the slot length selection are the lower delay time required by the system, and the desired low overhead with respect to preamble and phase-locked loop (PLL) locking.
Preferably, the length of the time slot is a multiple of 625 μ S, so as to be able to be at BLUETOOTH (i.e., not be blocked)TMThe protocol according to the invention is implemented in the enabling device.
Each time slot (except time slot 128) is used for transmission by one dedicated device so that data collisions within the network are prevented. Any slave device may transmit data in time slot 128 so that a collision may occur in this time slot. The host device transmits timing information in slot 0. The slot and frame counters of the slave device are synchronized with the counters of the master device of the network.
A device may use one or more time slots for data transmission. The time slots may be assigned during manufacture of a given device, or the time slots may be dynamically assigned during acquisition. Preferably, the allocation table is stored in the host device.
The operation of the scheduler 40 is as shown in fig. 4 and 5.
FIG. 4 illustrates a communication request made by two communication tasks, task 1 and task 2. Task 1 may be a communication task related to audio streaming from a television to a hearing aid, e.g. performed according to a hearing aid network communication protocol, and task 2 may be a communication task related to communication between a smartphone and a hearing aid performed according to a bluetooth low energy protocol. Each communication request contains the start time, duration and priority of the communication task to be performed. The duration includes pre-processing, transmission, reception, and post-processing of the communication task. In fig. 4, the open area indicates pretreatment and post-treatment.
In the example illustrated, communication task 1 has formed two communication requests to enable the audio data to be retransmitted if the first transmission (request 1) was unsuccessful. The second request has been made high priority so that the probability of performing the second communication service at the requested time is high. In the example of fig. 4, the communication task 1 has a priority of 2, the communication task 2 has a priority of 3, and the communication task 3 has a priority of 1. The highest priority has the lowest priority number.
If a communication request has been received, the scheduler 40 calculates the end time of each communication request as the sum of the request duration d and the recovery time period during which power restoration is permitted. In the illustrated example, the recovery time period is equal to 9/8 times the duration.
Thus, the end time1＝t1+d1+9/8*d1And end time2＝t2+d2+9/8*d2And end time3＝t3+d3+9/8*d3。
Some communication tasks may not be active. For example, a remote control may not be used at some times. The active and inactive tasks are marked as indicated in the request list shown in fig. 5. The parameters of the inactive task may be the now unused parameters of the most recent communication request.
As shown in fig. 5, the scheduler 40 now schedules communication tasks according to the request list and forms an illustrative priority list formed by listing the active communication requests in priority order. Then, the scheduler identifies the task having a request whose end time is earlier than the start time of the communication task having the highest priority (communication request 3 in the illustrated example). In the illustrated example, both communication request 1 and communication request 2 have a ratio t in such a way that a corresponding task can be executed before the task with communication request 3 is started3An early end time. In this case, the communication task having the highest priority, i.e., the task having communication request 1, is executed.
In the case where the task with communication request 1 is successfully executed, since the audio data has now been successfully communicated, the scheduler 40 deletes the communication request 3, i.e., the second reservation of the communication request 1. Due to the end time1Greater than t2And the message is sent to the requesting task that must make a new communication request, the scheduler 40 also determines that communication task 2 cannot be executed at the requested time;
at communication task 1 at t1Ending immediately thereafter, e.g. in case no header is detected due to noise, a new ending time is calculated based on a correspondingly shorter update calculation of the recovery time and at the start time t of the communication request 22Later than the new end time of the communication task 1, the end time t2At the start time t of a higher priority communication request 33Previously, communication task 2 was performed. If the time t is over2Has already been later than t3Communication task 2 will be rescheduled, i.e. scheduler 40 will transmit the message to the requesting task that must make a new communication request.
At communication task 1 at t1Then the end is immediately made; however, later than in the previous example, so that the new end time is later than t2Then communication task 2 is rescheduled again and the communication task of communication request 3 is performed.
Claims (19)
1. A hearing aid comprising a power supply connected to supply power to hearing aid circuitry, the hearing aid having:
an input transducer configured to output an audio signal based on a signal applied to the input transducer and representative of sound;
a hearing loss processor configured to compensate for a hearing loss of a user of the hearing aid and to output a hearing loss compensated audio signal;
an output transducer configured to output an auditory output signal based on the hearing loss compensated audio signal, the auditory output signal receivable by a human auditory system to cause a user to hear sound; and
a wireless communication unit configured to communicate with another device; and
an operating system configured to control the wireless communication unit to perform communication with other devices according to respective communication protocols and communication task priorities, wherein the operating system includes:
a scheduler configured to receive communication requests from communication tasks and schedule each of the communication tasks based on task priority and a state of the power supply, wherein the scheduler is configured to calculate an earliest possible start time for executing a next communication task based on an estimated power consumption of a current or latest communication task in order to provide a recovery time period for the power supply.
2. The hearing aid according to claim 1, wherein the hearing aid circuit comprises a voltage multiplier for providing a current to the wireless communication unit.
3. The hearing aid according to claim 1, wherein the hearing aid circuitry comprises a capacitor for providing a current to the wireless communication unit.
4. The hearing aid according to claim 2, wherein the hearing aid circuitry comprises a capacitor for providing a current to the wireless communication unit.
5. A hearing aid according to claim 3, wherein the hearing aid circuit comprises a resistor connected between the power supply and the capacitor.
6. The hearing aid of claim 4, wherein the hearing aid circuit comprises a resistor connected between the power supply and the capacitor.
7. The hearing aid according to claim 1, wherein the recovery time period is the duration of the current or most recent communication task multiplied by a constant.
8. The hearing aid according to claim 1, wherein said recovery time period is a function of the current drawn from said power supply during the performance of said current or most recent communication task.
9. The hearing aid of claim 1, wherein the power source comprises a battery, and wherein the recovery time period is a function of a state of the battery.
10. The hearing aid according to any of claims 1-6, wherein at least one of said communication requests contains a priority of said communication task.
11. The hearing aid according to any one of claims 1-6, wherein at least one of said communication requests comprises a start time for performing the requested communication task.
12. The hearing aid according to any of the preceding claims 1-6, wherein at least one of said communication requests comprises a duration of performing the requested communication task.
13. The hearing aid according to any one of claims 1-6, wherein the scheduler is configured to: the communication task having the lower priority is allowed to perform communication before the communication task having the higher priority as long as the communication task having the lower priority will end its communication at the time of the recovery time period of the power supply to elapse before the communication task having the higher priority is started.
14. The hearing aid according to any of claims 1-6, wherein the scheduler is configured to switch off the communication unit during sleep time periods.
15. The hearing aid according to claim 12, wherein the scheduler is configured to determine that the requested activation time is not available and to communicate to the requesting task that another activation time has to be requested.
16. The hearing aid according to any one of claims 1-6, wherein said scheduler is configured to determine that an already scheduled task cannot be executed at said scheduled start time and to communicate to said already scheduled task that a new start time has to be requested.
17. The hearing aid according to any one of claims 1-6, wherein the scheduler is configured to take into account the power consumption of other tasks than wireless communication when scheduling.
18. The hearing aid according to any one of claims 1-6, wherein at least a part of the operating system is comprised in the hearing loss processor.
19. A method of scheduling wireless communication for a hearing aid, the hearing aid comprising a power supply connected to supply power to hearing aid circuitry, the hearing aid having:
an input transducer configured to output an audio signal based on a signal applied to the input transducer and representative of sound;
a hearing loss processor configured to compensate for a hearing loss of a user of the hearing aid and to output a corresponding hearing loss compensated audio signal;
an output transducer configured to output an auditory output signal based on the hearing loss compensated audio signal, the auditory output signal receivable by a human auditory system to cause a user to hear sound;
a wireless communication unit configured to communicate with another device; and
an operating system configured to control the wireless communication unit to communicate with other devices according to a plurality of communication tasks having respective communication protocols and priorities, the method comprising:
receiving a communication request from the communication task,
scheduling an order according to which communication tasks with the communication requests are transmitted by the wireless communication unit based on task priorities and a state of the power supply, wherein the scheduling comprises calculating an earliest possible start time for executing a next communication task based on an estimated power consumption of a current or latest communication task, so as to provide a recovery time period of the power supply.
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| DKPA201400103 | 2014-02-24 | ||
| DKPA201400103 | 2014-02-24 |
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| CN108024186B (en) * | 2016-11-02 | 2020-07-10 | 宏碁股份有限公司 | Hearing aid and recovery time dynamic adjustment method for wide dynamic range compression of hearing aid |
| CN110650422A (en) * | 2018-06-26 | 2020-01-03 | 深圳市智汇声科技有限公司 | Hearing assistance method and system, and host and slave thereof |
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| EP2378793B1 (en) * | 2010-04-14 | 2013-01-23 | GN Resound A/S | Hearing instrument configured for wireless communication in bursts and a method of supplying power to such |
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| CN1394308A (en) * | 2000-09-22 | 2003-01-29 | 索尼株式会社 | Arithmetic processing system and control method, task management system and method |
| JP2003202935A (en) * | 2002-01-08 | 2003-07-18 | Mitsubishi Electric Corp | Power management system and power management method |
| CN1838077A (en) * | 2005-03-25 | 2006-09-27 | 株式会社东芝 | Schedulability determination method and real-time system |
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