EP4080904A1 - Procédé de fonctionnement d'un appareil auditif - Google Patents

Procédé de fonctionnement d'un appareil auditif Download PDF

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Publication number
EP4080904A1
EP4080904A1 EP22164425.5A EP22164425A EP4080904A1 EP 4080904 A1 EP4080904 A1 EP 4080904A1 EP 22164425 A EP22164425 A EP 22164425A EP 4080904 A1 EP4080904 A1 EP 4080904A1
Authority
EP
European Patent Office
Prior art keywords
movement
hearing
audio signal
signal
hearing system
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Pending
Application number
EP22164425.5A
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German (de)
English (en)
Inventor
Rosa-Linde FISCHER
Ronny Hannemann
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Sivantos Pte Ltd
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Sivantos Pte Ltd
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Filing date
Publication date
Application filed by Sivantos Pte Ltd filed Critical Sivantos Pte Ltd
Publication of EP4080904A1 publication Critical patent/EP4080904A1/fr
Pending legal-status Critical Current

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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R1/00—Details of transducers, loudspeakers or microphones
    • H04R1/10—Earpieces; Attachments therefor ; Earphones; Monophonic headphones
    • H04R1/1091—Details not provided for in groups H04R1/1008 - H04R1/1083
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/552—Binaural
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/41—Detection or adaptation of hearing aid parameters or programs to listening situation, e.g. pub, forest
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/43—Signal processing in hearing aids to enhance the speech intelligibility
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power

Definitions

  • the invention relates to a method for operating a hearing system, which has a hearing device with at least one microphone and with an earphone and with a motion sensor.
  • the invention also relates to a hearing system, in particular a hearing aid device, for carrying out the method.
  • Hearing aid devices are portable hearing aids that are used to care for people who are hard of hearing or hard of hearing.
  • different designs of hearing aid devices such as behind-the-ear hearing aids (BTE) and hearing aids with an external receiver (RIC: receiver in the canal) and in-the-ear hearing aids (ITE), for
  • BTE behind-the-ear hearing aids
  • RIC receiver in the canal
  • ITE in-the-ear hearing aids
  • concha hearing aids or canal hearing aids ITE: In-The-Ear
  • CIC Completely-In-Channel
  • IIC Invisible-In-The-Channel
  • the hearing aids listed by way of example are worn on the outer ear or in the auditory canal of a hearing aid device user.
  • Bone conduction hearing aids, implantable or vibrotactile hearing aids are also available on the market. The damaged hearing is stimulated either mechanically or electrically.
  • such hearing aids have an input converter, an amplifier and an output converter as essential components.
  • the input transducer is typically an acousto-electric transducer such as a microphone and/or an electromagnetic receiver such as an induction coil or (radio frequency, RF) antenna.
  • the output transducer is usually in the form of an electro-acoustic transducer, such as a miniature speaker (earphone), or an electromechanical transducer, such as a bone conduction earphone. realized.
  • the amplifier is usually integrated into a signal processing device. The energy is usually supplied by a battery or a chargeable accumulator.
  • a so-called binaural hearing aid device two such hearing aids are worn by a user, with a communication link existing between the hearing aids.
  • data possibly also large amounts of data, are exchanged wirelessly between the hearing device on the right and left ear.
  • the exchanged data and information enable the hearing aids to be adapted particularly effectively to a particular acoustic environment. In particular, this enables a particularly authentic spatial sound for the user and improves speech understanding, even in noisy environments.
  • ANS autonomic nervous system
  • hearing loss dementia
  • Parkinson's disease a diseases or comorbidities
  • ANS autonomic nervous system
  • several such diseases often occur, so that, for example, people with Parkinson's also regularly have a hearing disorder or hearing loss.
  • hearing impairment or hearing loss is associated with a reduced ability to perceive self-movement. In combination with other diseases, this can lead to a reduced feeling of "safety”, and thus to a vicious circle of decreasing physical activity, further loss of self-confidence and an increased level of self-confidence fall risk.
  • rehabilitation measures after falls and accompanying injuries are usually time-consuming, expensive and often difficult to implement if the affected persons also suffer from hearing loss and age-related or disease-related cognitive decline.
  • sonification means in particular the use of non-speech audio signals in order to convey information or perceive data. Auditory perception has advantages in temporal, spatial, amplitude and frequency resolution, which opens possibilities as an alternative or complement to visualization techniques.
  • rhythmic auditory cueing is possible, which is defined as the application of repetitive isosynchronous beats with the aim of synchronizing the motor execution of a movement with this rhythm.
  • this is implemented in training sessions, which are carried out on a treadmill, for example.
  • real-time "sonification" of movement parameters, which are converted into acoustic feedback is also possible in special training sessions, for example to make information about the length and strength of a movement audible.
  • the invention is based on the object of specifying a particularly suitable method for operating a hearing system.
  • a simple and reliable support of one's own movement should be made possible, which can preferably be used in everyday life.
  • the invention is also based on the object of specifying a particularly suitable hearing system for carrying out the method.
  • the method according to the invention is intended for operating a hearing system, in particular a hearing aid device, and is suitable and designed for this.
  • the hearing system has a hearing aid.
  • the hearing device is used in particular to care for a hearing-impaired user (hearing system user).
  • the hearing aid is designed to pick up sound signals from the environment and output them to a user of the hearing aid.
  • the hearing device has at least one acousto-electrical input converter, in particular a microphone, and at least one electro-acoustic output converter, for example a receiver.
  • the input converter picks up sound signals (noises, tones, speech, etc.) from the environment and converts them into an electrical input signal (acoustic data).
  • An electrical output signal is generated from the electrical input signal by modifying the input signal in signal processing.
  • Signal processing is part of the hearing aid, for example.
  • the signal processing has, for example, an (output) amplifier for (selective) amplification of the input signal or for setting a signal level of the output signal.
  • the output transducer generates an acoustic sound signal from the output signal.
  • the input converter and the output converter and possibly also the signal processing are housed in particular in a housing of the hearing aid.
  • the housing is designed in such a way that it can be worn by the user on the head and near the ear, eg in the ear, on the ear or behind the ear.
  • the hearing aid is preferably designed as a BTE hearing aid, ITO hearing aid or RIC hearing aid.
  • the hearing device can be designed binaurally, and for this purpose have two individual devices, which each have at least one input transducer and at least one output transducer and are thus designed to pick up sound signals from the environment and output them to a user of the hearing device.
  • the method described below can be carried out in one of the individual devices or in both individual devices or jointly by the two individual devices.
  • a wireless interface is provided for data exchange between the two individual devices.
  • the wireless interface is, for example, a Bluetooth interface or a WLAN interface or an MI interface (MI-Link, MI: Magnetic Induction).
  • the Bluetooth interface is, for example, a regular or a low-energy (so-called low-energy) Bluetooth interface.
  • a monaural hearing device with only one individual device is also suitable.
  • the explanations regarding a monaural hearing device can be transferred to a binaural hearing device and vice versa.
  • the hearing device also has a motion sensor for detecting movements of the hearing system user.
  • the movement sensor is provided and set up to detect three-dimensional (body) movements or movement events, in particular translatory and/or rotary movements.
  • the movement sensor is designed here, for example, as an accelerometer and/or as a gyroscope, ie as a gyroscopic (position) sensor.
  • the movement sensor can also be a pulse, blood pressure or light sensor.
  • a combination of accelerometer and/or gyroscope and/or heart rate sensor and/or blood pressure sensor and/or light sensor is also possible.
  • the movement sensor is preferably integrated in the hearing aid, in particular in its housing.
  • a motion sensor is preferably integrated in each of the individual devices.
  • the hearing device is worn on the head and in the vicinity of the ear of the hearing system user, so that head movements of the hearing system user in particular can be detected by means of the movement sensor.
  • head movements of the hearing system user in particular can be detected by means of the movement sensor.
  • walking or gait movements ie body movements due to walking or running, can also be detected at least indirectly via the movement sensor of the hearing device.
  • a “movement” is to be understood here and below as a particular translational and/or rotational body movement of the hearing system user, ie a movement action or a (temporal) sequence of movement actions (movement sequence).
  • the term “movement pattern” refers in particular to a characterization of the respective (body) movement using characteristic (movement) variables (movement parameters), which are determined, for example, using recorded data.
  • the movement pattern of a walking movement can be characterized by a step frequency, a step length and step synchronicity.
  • a "movement pattern” is to be understood here in particular as a (chronological) signal sequence characterizing the respective (body) movement or a signal pattern or signal curve of the recorded data or of the characteristic variables derived therefrom.
  • an actual movement of the hearing system user is recorded as movement sensor data from the movement sensor and as movement noise data from the input transducer during operation of the hearing system.
  • An "actual movement" of the hearing system user is to be understood here in particular as a movement of the hearing system user's own body.
  • Motion sensor data is to be understood here as meaning, in particular, direction-dependent accelerations and/or rotations, which are detected by means of the motion sensor.
  • “Movement noise data” is to be understood here in particular as acoustic signals in the signal (acoustic signal, acoustic data) detected by the input transducer, which can be directly or indirectly traced back to the body or personal movement of the hearing system user (movement noise).
  • the analysis or acquisition of the movement noise or movement noise data from the input transducer data/signals (acoustic data) can be carried out using a movement noise classifier, for example.
  • a classifier can, for example, be an artificial intelligence or a neural network, in particular a deep neural network (DNN), which is correspondingly trained with different movement noises.
  • DNN deep neural network
  • the movement sensor data and/or movement noise data are thus a measure of the body movements performed by the hearing system user.
  • An actual movement pattern for the actual movement is determined on the basis of the movement sensor data and/or the movement noise data.
  • the actual movement or the movement sensor data and/or the movement noise data is analyzed during the execution of the actual movement, that is to say the actual actual movement is characterized on the basis of the recorded signal curves/signal patterns.
  • a target movement pattern is determined for the movement of the hearing system user recognized by the hearing system. For example, a desired step frequency and/or step length or the like is determined for a walking movement with a certain walking speed. If the hearing system user suffers from an ANS disease, the target movement pattern can be, for example can also be an externally specified or stored movement pattern. Alternatively, the target movement pattern can also be a stored movement pattern of a previous movement by the hearing system user himself, which serves, for example, as an individual starting value (baseline).
  • baseline individual starting value
  • the actual movement pattern is compared with the target movement pattern and, depending on the comparison, an audio signal with a perceptible signal level is generated by means of the output converter, which audio signal supports the hearing system user in carrying out the movement.
  • deviations between the variables or movement parameters characterizing the movement are determined on the basis of the actual and target movement patterns, and depending on this, a perceptible, acoustic, audio signal is output to the hearing system user in order to adjust the (actual) movement of the hearing system user to a desired Adjust (target) movement.
  • the signal level of the audio signal is to be understood here in particular as the volume of the acoustic audio signal.
  • the movement patterns or deviations in the movement patterns act as triggers for the audio signal.
  • the audio signal acts as an acoustic movement feedback or as an acoustic movement feedback, which helps the hearing system user to perceive his own movement and to adapt it to a desired movement.
  • a particularly suitable method for operating a hearing system is thereby implemented.
  • the hearing system is thus used to monitor and control the movement of the hearing system user.
  • the movement sensor in the hearing device which is worn to compensate for hearing impairment, is thus used according to the invention to monitor and support the movement pattern of the hearing device wearer.
  • a core idea of the invention is therefore, in particular, to detect the movements of the hearing system user (e.g. gait, rotation, etc.) using the hearing aid, and to analyze the detected movements and compare them with a predetermined or desired movement, and the hearing system user an acoustic Present a signal to adjust or verify his movement. Based In the movement analysis, for example, the current walking (gait) or the general movement is identified and compared with an ideal (target) movement pattern.
  • the provision of audible or perceptible audio signals during a movement can help the hearing instrument user to learn new movements or to optimize certain movements, i.e. to perform a movement with an appropriate force or duration, which the hearing instrument user can identify through acoustic aspects of the audio signal (volume, pitch, etc.). , rhythm, et cetera) is displayed.
  • the procedure improves the self-perceived movement of the hearing system user and extends it to use in everyday life.
  • Auditory feedback may be more accurate than visual feedback for a hearing aid user, particularly but not exclusively for hearing aid users with a hearing loss or hearing impairment.
  • This embodiment thus also offers advantages beyond applications for hearing-impaired users, particularly in the field of physical rehabilitation through applied sonification.
  • sonification stimulates subcortical learning and is therefore superior to verbal and visual cues in general and particularly in age- or disease-related cognitive impairments.
  • the method according to the invention contributes to safety, to reducing the risk of falling, to fewer injuries and to lower costs in the healthcare system.
  • the hearing system user gets better physical condition, which is expressed in optimal gait symmetry, safe walking speed, etc. This allows the hearing aid user to retrain, for example, stride length and/or arm-leg synchronization, and even learn new complex movements that help them lead high-quality independent lives.
  • the method according to the invention offers advantages with regard to the multi-sensory integration of somatosensory and acoustic feedback on movement patterns in general and gait patterns in particular.
  • Multisensory integration is a basis for learning in the brain, and thus a basis for relearning how to walk safely and for compensating for the loss of self-perceived movement in hearing impairment due to the reduced acoustic feedback in hearing impairment.
  • the present invention makes it possible to offer additional benefits of hearing systems beyond hearing. Therefore, people may be willing to use hearing aids even if they only have a mild hearing impairment because they receive additional (health-related) benefits.
  • learning or relearning movements is not limited to specific training sessions, but can also take place in everyday life. This increases the training frequency and training duration compared to normal training hours, so that the hearing system user learns better.
  • the hearing system acts essentially in the manner of a pacemaker or metronome, ie as an extended feedback or feedback system, which causes a particularly rhythmic acoustic feedback or a sonification of kinematic movement pattern parameters.
  • a pacemaker or metronome ie as an extended feedback or feedback system, which causes a particularly rhythmic acoustic feedback or a sonification of kinematic movement pattern parameters.
  • This enables the hearing system user to adjust or synchronize their current (non-optimal) movement pattern with the acoustically reproduced (ideal, optimal) movement pattern. This reduces the risk of falling, for example, and improves the execution of the desired movement by the hearing system user.
  • the hearing system preferably continuously compares the current actual movement pattern and the target movement pattern, with the acoustic audio signal being set as optimally as possible in every situation. It is conceivable here, for example, for the audio signal to be generated only as a function of the situation. In other words, a respective situation is classified, for example, and depending on this the acoustic feedback is generated by means of the audio signal or not.
  • the method according to the invention is used, for example, for the specific amplification of gait or movement noises, e.g. B. footstep sound when walking, cycling, swimming in water or other complex movements.
  • gait or movement noises e.g. B. footstep sound when walking, cycling, swimming in water or other complex movements.
  • the processes of multisensory integration in the brain are supported by somatosensory feedback from the respective sensor cells in the feet and the acoustic feedback of movement noises (e.g. footsteps, arm or swimming noises).
  • the method according to the invention is used for training purposes in order to relearn or improve movements or motor skills (learning application).
  • the "shape" of the audio signal is changed by means of the hearing system in order to bring about changes in the body movement of the hearing system user.
  • a change in body movement is to be understood here, for example, as a change in the temporal movement sequence (timings), or a (movement) force, or other details of the movement action.
  • a desired application is preferably specified at the start of the method.
  • the target movement pattern is suitably determined or selected as a function of the respective application.
  • the respectively optimal movement pattern is determined as the target movement pattern for the respective application. For example, given a given gait, the desired walking speed, walking rhythm and walking distance are determined.
  • the audio signal generated can vary depending on the selected application.
  • the selection of the application or the specification of the target movement can take place, for example, during an adjustment or fine adjustment of the hearing device.
  • the target movement or the application is specified via a user interface of an additional device coupled to the hearing device using signal technology.
  • the additional device is preferably a mobile operating and display device, for example a mobile phone, in particular a mobile phone with a computer function or a smartphone or a tablet computer.
  • the additional device suitably has stored application software (operating software).
  • the application software application software
  • This embodiment is based on the consideration that modern operating and display devices, such as in particular smartphones or tablet computers, are widespread in today's society and are generally available and accessible to a user at any time. In particular, the user of the hearing system It is very likely that they have such an operating and display device in their household.
  • the application software is preferably also suitable and set up for setting operating parameters of the hearing aid, such as a volume.
  • the user does not need an additional, separate operating system to monitor and adjust the hearing system, but it is possible to use the existing smartphone to specify the target movement and to evaluate the movement data by (subsequently) downloading and/or installing the application software . In this way, user-side costs are advantageously reduced.
  • the surfaces of smartphones or tablet computers which are typically designed as touchscreens (display, display), also allow a particularly simple and intuitive operation of the application software of the additional device formed thereby.
  • a smartphone or tablet computer can be retrofitted in a particularly cost-effective manner for monitoring one's own movement.
  • the operating and display device includes an internal controller, the core of which is formed at least by a microcontroller with a processor and a data memory, in which the functionality for carrying out the method is implemented in the form of application software in terms of programming, so that the method or the monitoring of the Own movement - if necessary in interaction with the user - is carried out automatically when executing the application software in the microcontroller.
  • the actual movement pattern is preferably determined using both the movement sensor data and the movement noise data.
  • the movement noise data from the input transducer or the microphone are used here, for example for determining the movement quality, for example a periodicity.
  • different footstep sounds from step to step can indicate a balance disorder.
  • the deviation from a periodic (target) footstep noise can thus be used as a measure for adjusting the audio signal.
  • the duration of the individual swimming strokes, and thus the corresponding movement noise duration can vary. The duration of the stroke thus provides information that can be taken into account when generating the audio signal.
  • the audio signal generated according to the method has a perceptible signal level, which means that the audio signal has a signal level which the hearing system user can perceive in the acoustic signal generated by the output transducer.
  • the acoustically generated signal is, for example, an amplified signal from the input converter for supplying a hearing-impaired hearing system user.
  • the signal level of the audio signal can be adjusted by the hearing system user, for example via a remote control or an additional device. It is conceivable here, for example, that the signal level of the audio signal can be set separately by the hearing system user.
  • the rhythmic audio signal for example, is provided by the input transducer signal.
  • the audio signal can be generated binaurally, monaurally or alternatingly monaurally, for example.
  • a time frame or a schedule for carrying out the method can be specified, that is to say that the method is started at a specific point in time and ended at a further specific point in time. It is possible here, for example, for a hearing system user to be able to specify the intervals at which, or how often, a check and control or support of the patient's own movement should take place. It is also conceivable, for example, for a desired schedule to be stored in the hearing system, ie for example a period of time per hour, day, week, etc.
  • the audio signal is generated for a predetermined period of time when the deviation between the actual movement pattern and the desired movement pattern reaches or exceeds a predetermined threshold value. This means that the audio signal is generated when the movement patterns indicate that there is a risk to the health or safety of the hearing aid user.
  • the hearing system user it is possible for the hearing system user to set, influence or change the volume of the audio signal manually, for example via an additional device. It is also possible, for example, for the hearing system user to start, pause and end the method manually.
  • a probability of a future deviation of the actual movement pattern from the target movement pattern of the hearing system user is determined on the basis of the recorded movement sensor data and/or movement noise data.
  • a method is used, for example, as described in the applicant's international application of December 16, 2020 with the file number, which was still unpublished at the time of filing PCT/EP2020/086518 is described.
  • Their disclosure content, in particular their claims (with associated explanations) are hereby expressly included in the present application. Particular reference is made to claims 1 and 2 with the associated statements specifically on specification pages 8 to 14.
  • the deviation of the actual movement pattern from the target movement pattern can be realized, for example, in the form of a fall or falling event, so that in particular a fall probability as in FIG PCT/EP2020/086518 is determined.
  • other deviations can also be predicted, with the audio signals generated according to the method intervening in a supportive manner in order to reduce or prevent such a predicted deviation.
  • the target movement pattern is adjusted based on the probability.
  • the current setpoint movement pattern is adapted in such a way that the probability of a deviation or a fall or fall is reduced or minimized as far as possible.
  • the target movement pattern is updated in order to take account of the current actual movement pattern and thus to avoid larger, undesired, future deviations. If, for example, the risk of falling is to be minimized by optimizing the gait/walking behavior, the necessary walking speed, step synchronicity and other patterns are determined and used as a trigger for the audio signal. For example, a rhythm of the audio signal is changed in order to reduce the risk of the hearing system user falling or to maximize the safety of the hearing system user.
  • a threshold value comparison of the probability to be used as a triggering criterion for the movement monitoring/adjustment.
  • the audio signal is only generated if the probability reaches or exceeds a stored threshold value, i.e. if there is a sufficiently high risk of falling.
  • a signal property, in particular the signal level, of the audio signal is set based on the probability determined.
  • the signal level of the audio signal is changed as a measure to reduce the risk of falling or falling.
  • the audio signal is used as a sonification of the target movement pattern.
  • the desired movement pattern is muted, for example a rhythmic audio signal generated as a beat or trigger sound for a walking motion or swimming motion.
  • the target movement pattern or the audio signal can also be a measure or sonification for a desired breathing movement, in particular the audio signal can thus also be used to support mediation exercises.
  • the sonification of the target movement pattern ensures that the hearing system user is supported in executing a desired target movement.
  • the movement noises detected by the input transducer are used as the audio signal.
  • the movement noises ie the noises or sound signals (movement noise data) caused by one's own movement
  • the input converter specifically amplified to generate the audio signal.
  • footsteps are amplified more than other signals from the input transducer, so that the hearing system user can reliably perceive the footsteps. This improves the hearing system user's self-perceived movement.
  • the input converter signal (acoustic data) is analyzed and specifically processed with regard to the movement noise data.
  • the processing can lead to increased audibility, adjustments to the frequency form, the sound character, the duration or other things.
  • An additional or further aspect of the invention provides that the signal level of the audio signal is adjusted proportionally to a deviation between the target movement pattern and the actual movement pattern.
  • the volume of the audio signal is adjusted as a function of the comparison.
  • the signal level is reduced when the actual and target movement patterns match, and increased when the actual and target movement patterns deviate from one another.
  • the volume of the perceived audio signal acts as additional acoustic feedback for the deviation from the desired execution of the movement.
  • an environmental situation is determined using the acoustic data of the input transducer, with a signal property or signal characteristic, in particular the signal level, of the audio signal being set using the determined environmental situation.
  • the optimum output amplification for the audio signal is thus set on the basis of the specific environmental situation.
  • a decision about the appropriateness of the generation of the audio signal can also be made on the basis of the specific environmental situation. For example, the volume of the audio signal is increased in noisy environments, such as when walking along a busy street. It is also possible for the generation of the audio signal to be paused or interrupted if, for example, a speech situation or a conversation by the hearing system user is detected.
  • An environmental situation is to be understood here in particular as an acoustic environmental situation or a hearing situation.
  • the environmental situation is identified and described, for example, by means of a situation detection and/or at least one level measurement and/or at least one algorithm of the hearing device or the signal processing.
  • the environmental situation is classified according to specific criteria, and a specific setting of the hearing device parameters and/or hearing device power is assigned to each of these classes.
  • the signal level or the volume of the audio signal is preferably always audible for the hearing system user.
  • the hearing aid analyzes the ambient level (internal level meter), takes into account, for example, the hearing loss of the hearing aid wearer (audiogram information or derived from the hearing aid fitting) and ensures audibility, in particular by automatically adjusting the output amplification of the audio signal.
  • Relative changes in the audibility of the audio signal can be used to display different "qualities" of movement sequences.
  • the relative level of a footstep sound can indicate different step sizes or left-right asymmetries.
  • the optimum for the user would be achieved if all audio signals were displayed at the same level.
  • the frequency shape or pitch of the audio signal may indicate the length of a stroke. The goal of the hearing instrument user would be to get the right pitch that indicates optimal stroke length.
  • the actual and/or the target movement pattern are stored in a memory. This makes it possible, for example, to record and monitor progress or changes in movement patterns. This data can, for example, be made available to medical experts and/or the hearing system user, for example through visualization on an external additional device. In addition or as an alternative, it is possible, for example, to use the stored movement patterns to derive changes in the risk of falling or falling and to assess the movement quality of the assisted movement.
  • the hearing system according to the invention is designed in particular as a hearing aid device and has a hearing aid.
  • the hearing device has at least one input converter for receiving an acoustic environment signal and an output converter for outputting an acoustic signal, as well as a movement sensor for detecting a body movement of a hearing system user.
  • the hearing system also has a controller, ie a control unit.
  • the controller is integrated into the hearing device, for example, and is part of a signal processing system, for example.
  • the controller it is also conceivable for the controller to be part of an additional device, in particular a smartphone, which is or can be coupled to the hearing aid in terms of signaling.
  • the controller is generally set up—in terms of program and/or circuitry—to carry out the method according to the invention described above.
  • the controller is thus specifically set up to analyze or characterize a user movement or a movement event and to generate a signal supporting the movement.
  • the controller is formed, at least in its core, by a microcontroller with a processor and a data memory, in which the functionality for carrying out the method according to the invention is implemented programmatically in the form of operating software (firmware), so that the method - optionally in interaction with a hearing system user - is carried out automatically when the operating software is executed in the microcontroller.
  • the controller can also be formed by a non-programmable electronic component, such as an application-specific integrated circuit (ASIC), in which the functionality for carrying out the method according to the invention is implemented with circuitry means.
  • ASIC application-specific integrated circuit
  • the 1 shows the basic structure of a hearing system 2 according to the invention.
  • the hearing system 2 is designed as a hearing aid device with a binaural hearing device 4 with two hearing aid devices or individual devices 6a, 6b coupled with signals.
  • the individual devices 6a, 6b are in this case configured as behind-the-ear hearing aid devices (BTE).
  • BTE behind-the-ear hearing aid devices
  • the individual devices 6a, 6b are coupled or can be coupled to one another in terms of signal technology by means of a wireless communication link 8.
  • the communication connection 8 is, for example, an inductive coupling between the individual devices 6a and 6b; alternatively, the communication connection 8 is designed, for example, as a radio connection, in particular as a Bluetooth or RFID connection, between the individual devices 6a and 6b.
  • the structure of the individual devices 6a, 6b is explained below using the example of the individual device 6a.
  • the individual devices 6a includes, as in the 1 shown schematically, a device housing 10, in which one or more microphones, also referred to as acousto-electric input converter 12 are installed. A sound or the acoustic signals in an environment of the hearing system 2 is recorded with the input converters 12 and converted into electrical acoustic data 14 .
  • the acoustic data 14 are processed by a controller 15 of a signal processing device 16 which is also arranged in the device housing 10 .
  • the signal processing device 16 uses the acoustic data 14 to generate an output signal 18 which is routed to a loudspeaker or earpiece 20 .
  • the earphone 20 is designed as an electro-acoustic output converter 20, which converts the electrical output signal 18 into an acoustic signal and outputs it.
  • the acoustic signal is transmitted to the eardrum of a hearing system user, optionally via a sound tube (not shown in detail) or an external receiver with an otoplastic seated in the auditory canal.
  • an electromechanical output converter as the receiver 20, such as in the case of a bone conduction receiver.
  • the individual device 6a and in particular the signal processing device 16 are supplied with energy by means of a battery 22 accommodated in the device housing 10.
  • the signal processing device 16 is coupled to a movement sensor 24 of the individual device 6a.
  • the motion sensor 24 detects acceleration and/or rotational movements of the individual device 6a and sends them to the Operation as motion sensor data 26 to the signal processing device 16.
  • the motion sensor 24 is designed, for example, as a 3D acceleration sensor. Additionally or alternatively, the movement sensor 24 is designed, for example, as a position sensor, in particular as a gyroscopic sensor.
  • the signal processing device 16 is also routed in terms of signals to a first transceiver 28 and to a second transceiver 30 of the individual device 6a.
  • the transceiver 28 is used to send and receive wireless signals via the communication link 8
  • the transceiver 30 is used to send and receive wireless signals via a communication link 32 to an auxiliary device 34 external to the hearing aid ( 2 ).
  • auxiliary device 34 external to the hearing aid ( 2 ).
  • the additional device 34 is designed as a separate, mobile, operating and display device, which is coupled or can be coupled in terms of signals to the hearing aid 4 by means of the communication link 32 .
  • the additional device 34 also referred to below as a smartphone, has a touch-sensitive display unit (display) 36, which is also referred to below as a touchscreen.
  • the smartphone 34 is expediently brought into the transmission range of the communication connection 32 .
  • the signaling coupling between the smartphone 34 and the transceivers 30 of the individual devices 6a and 6b takes place here via a corresponding integrated transceiver (not specified), for example a radio or radio antenna, of the smartphone 34.
  • the smartphone 34 has an integrated controller, which is essentially formed by a microcontroller with an implemented application software 38 for programmatic evaluation of signals and data transmitted by means of the communication connection 32 .
  • the application software 38 is preferably a mobile app or a smartphone app that is stored in a data memory of the controller.
  • the controller provides during operation, the application software 38 is displayed on the display unit 36 embodied as a touchscreen, with the application software 38 being operable by a hearing system user by means of the touch-sensitive surface of the display unit 36 .
  • an actual movement of the hearing system user is recorded as movement sensor data 26 from the movement sensor 24 and as movement noise data 44 from the input transducer 12.
  • the analysis or detection of the movement noise or movement noise data 44 from the acoustic data 14 can take place here, for example, by means of a movement noise classifier 46 of the controller 15 .
  • the classifier 46 is part of the input converter 12, but the classifier 46 can also be designed separately from the input converter 12.
  • An actual movement pattern 48 for the actual movement or personal movement of the hearing system user is determined on the basis of the movement sensor data 26 and the movement noise data 44 .
  • the analysis of the movement sensor data 26 and the movement noise data 44 or the determination of the actual movement pattern 48 derived therefrom is carried out, for example, by means of a classifier or a (first) evaluation unit 50 of the controller 15.
  • a (second) evaluation unit 52 of controller 15 determines a target movement pattern 54 .
  • the evaluation unit 52 compares the actual movement pattern 48 with the desired movement pattern 54, with a control signal 56 for a tone generator 58 being generated on the basis of the comparison.
  • the tone generator 58 generates an electrical signal 60 which is amplified by means of an amplifier 62 and sent as an amplified signal 64 to the output converter 20 which converts the signal 64 into an audio signal 66 which can be heard.
  • the audio signal 66 or the signals 60 and 64 can in this case be a sonification of the target movement pattern 54 .
  • the particularly rhythmic audio signal 66 supports a walking movement of the hearing system user, for example as a beat or trigger noise.
  • the signal level or the volume of the audio signal 66 is preferably always audible for the hearing system user.
  • the controller 15 uses a level meter or an environment classifier 68 to analyze the environment level, which results from the acoustic data 14 of the input transducer 12 .
  • a hearing loss or a hearing impairment of the hearing system user is taken into account and a signal level signal 70 is generated.
  • the signal level signal 70 sets a signal level of the audio signal 66 . in the in 3
  • the signal level of the signal 60 is adjusted for this purpose, so that the signal level of the audio signal 66 is subsequently varied.
  • the signal level signal 70 can also be used to adjust the amplifier or the signal 64 .
  • the actual and/or the target movement pattern 48, 54 are stored in a memory 72 of the controller 15. This makes it possible, for example, to detect and monitor progress or changes in the movement patterns 48, 54. This data can be made available, for example, to medical experts and/or the hearing system user, for example through visualization on the display unit 36 of the additional device 34.
  • An application 74 is preferably transmitted to the hearing device 4 by means of the additional device 34 or by means of the application software 38 .
  • the evaluation unit 52 and the tone generator 58 are controlled, for example, and the target movement pattern 54 and/or the audio signal 66 is changed as a result.
  • the controller 15 uses the recorded movement sensor data 26 and/or movement noise data 44 to determine a probability that the hearing system user will fall or fall in the future.
  • the probability can be determined, for example, in the evaluation unit 50 .
  • Target movement pattern 56 is preferably adapted as a function of the probability determined.
  • the target movement pattern 56 or the audio signal 66 is adapted in such a way that the probability of a fall or fall is reduced or minimized as much as possible.
  • a rhythm of the audio signal 66 is changed in order to reduce the risk of the hearing system user falling.
  • the signal level of the signal 60 or the audio signal 66 is adjusted based on the determined probability.
  • the individual devices 6a, 6b of the binaural hearing aid 4 output the audio signal 66 synchronously with one another, for example.
  • the same audio signal 66 it is conceivable here for the same audio signal 66 to be output at different volumes (depending on the hearing system user's hearing loss and/or depending on the deviation from the actual/target movement) at the same time.
  • the same audio signal 66 is also possible, for example, for the same audio signal 66 to be generated at different times, for example the single device worn on the left ear generates the audio signal 66 when stepping forward with the left foot, while the single device worn on the right ear generates the audio signal 66 analogously a step forward with the right foot.
  • the individual devices 6a, 6b may generate different audio signals 66 or differently manipulated audio signals 66 for the right and left ear, particularly if the balance is impaired or if movement is restricted on one side (eg limping with one leg).
  • the movement noises detected by the input converter 12 are to be used as the audio signal 66 .
  • the tone generator 58 can influence a signal property of the movement noise data 44, such as a signal level, a rhythm or a frequency response of the movement noise data 44.
  • the tone generator 58 can also be omitted and the amplifier 62 can be used directly.
  • the signal level of the audio signal 66 is set, for example, as a function of the deviation of the actual movement pattern 48 from the target movement pattern 54 .

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  • Engineering & Computer Science (AREA)
  • Physics & Mathematics (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Neurosurgery (AREA)
  • Otolaryngology (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
EP22164425.5A 2021-04-22 2022-03-25 Procédé de fonctionnement d'un appareil auditif Pending EP4080904A1 (fr)

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US11847379B1 (en) * 2022-09-23 2023-12-19 Blackbird Neuroscience Inc. Audio processing method and system for environmental enrichment therapy

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EP3585072A1 (fr) * 2018-06-18 2019-12-25 Sivantos Pte. Ltd. Procédé de fonctionnement d'un système de dispositif auditif et système de dispositif auditif
WO2020206155A1 (fr) * 2019-04-03 2020-10-08 Starkey Laboratories, Inc. Système de surveillance et son procédé d'utilisation

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EP3097702A1 (fr) 2014-01-24 2016-11-30 Bragi GmbH Système écouteur multifonction pour activités sportives
DE102014109007A1 (de) 2014-06-26 2015-12-31 Nikolaj Hviid Multifunktionskopfhörersystem für sportliche Aktivitäten
US20180233018A1 (en) 2017-02-13 2018-08-16 Starkey Laboratories, Inc. Fall prediction system including a beacon and method of using same
WO2020097353A1 (fr) 2018-11-07 2020-05-14 Starkey Laboratories, Inc. Systèmes de thérapie physique et d'entraînement vestibulaire avec rétroaction visuelle
US11806530B2 (en) 2020-04-21 2023-11-07 Cochlear Limited Balance compensation

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US20150010177A1 (en) * 2013-07-02 2015-01-08 Samsung Electronics Co., Ltd. Hearing aid and method for controlling hearing aid
EP3585072A1 (fr) * 2018-06-18 2019-12-25 Sivantos Pte. Ltd. Procédé de fonctionnement d'un système de dispositif auditif et système de dispositif auditif
WO2020206155A1 (fr) * 2019-04-03 2020-10-08 Starkey Laboratories, Inc. Système de surveillance et son procédé d'utilisation

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US20220345834A1 (en) 2022-10-27
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US11962976B2 (en) 2024-04-16

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