Execution and initialisation of processes for a device

Systems and methods for detecting when a device is placed into an operational position are disclosed. Upon determination that the device is in the operational position, one or more processes can be executed. Execution or initialization of the processes upon detection of the operational position provides for the determination of optimal settings than would otherwise be determined if the processes automatically executed before detection of the operational position. Further aspects of the present disclosure relate to determining when the device is no longer in an operational position upon which time the execution of the processes are terminated. The settings in place upon termination can be saved and reapplied the next time the device is in the operational position.

BACKGROUND

Hearing loss, which can be due to many different causes, is generally of two types: conductive and sensorineural. In many people who are profoundly deaf, the reason for their deafness is sensorineural hearing loss. Those suffering from some forms of sensorineural hearing loss are unable to derive suitable benefit from auditory prostheses that generate mechanical motion of the cochlea fluid. Such individuals can benefit from implantable auditory prostheses that stimulate nerve cells of the recipient's auditory system in other ways (e.g., electrical, optical, and the like). Cochlear implants are often proposed when the sensorineural hearing loss is due to the absence or destruction of the cochlea hair cells, which transduce acoustic signals into nerve impulses. Auditory brainstem implants might also be proposed when a recipient experiences sensorineural hearing loss if the auditory nerve, which sends signals from the cochlear to the brain, is severed or not functional.

Conductive hearing loss occurs when the normal mechanical pathways that provide sound to hair cells in the cochlea are impeded, for example, by damage to the ossicular chain or the ear canal. Individuals suffering from conductive hearing loss can retain some form of residual hearing because some or all of the hair cells in the cochlea function normally.

Individuals suffering from conductive hearing loss often receive a conventional hearing aid. Such hearing aids rely on principles of air conduction to transmit acoustic signals to the cochlea. In particular, a hearing aid typically uses an arrangement positioned in the recipient's ear canal or on the outer ear to amplify a sound received by the outer ear of the recipient. This amplified sound reaches the cochlea causing motion of the perilymph and stimulation of the auditory nerve.

In contrast to conventional hearing aids, which rely primarily on the principles of air conduction, certain types of hearing prostheses commonly referred to as bone conduction devices, convert a received sound into vibrations. The vibrations are transferred through the skull to the cochlea causing motion of the perilymph and stimulation of the auditory nerve, which results in the perception of the received sound. Bone conduction devices are suitable to treat a variety of types of hearing loss and can be suitable for individuals who cannot derive sufficient benefit from conventional hearing aids.

SUMMARY

Aspects of the present disclosure relate to systems and methods for detecting when a medical device is placed into an operational position on a recipient. Upon determination that the device is in the operational position, one or more processes can be executed. Execution of the processes upon detection of the operational position provides for the determination of optimal settings than would otherwise be determined if the processes automatically executed upon device initialization. Further aspects of the present disclosure relate to determining when the device is no longer in an operational position upon which time the execution of the processes are terminated. The settings in place upon termination can be saved and reapplied the next time the device is in the operational position.

Further aspects of the present disclosure relate to a feedback algorithm that reduces the likelihood of generating audible artefacts. In examples, the feedback algorithm executes with an initial phase that employs a faster adaptation speed. During the initial phase, the amplitude of the device may be incrementally increased. Upon completion of the initial phase, the feedback algorithm may be adjusted to employ an operational adaptation speed.

DETAILED DESCRIPTION

Various types of devices, such as medical devices that operate on and/or within a recipient or such as consumer electronic devices that generate or assist in generation of audible output, utilize processes that execute after the devices are turned on and that could execute before the devices are put into the location or one of the locations the devices are intended to operate in (e.g., an operational position), but that operate more effectively and/or efficiently when executed after the devices or one or more components of the devices are put into an operational position. Non-limiting examples of such processes including beam forming and feedback algorithms. The operation of such processes is effectible by a position of the devices or one or more components of the devices.

For instance, many recipients of auditory prostheses can experience discomfort during initialization of the auditory prosthesis. The discomfort can be the result of audible artifacts that are generated during the establishment of a stable feedback loop for the auditory prosthesis. Feedback is a major concern when increasing gain in any system with a microphone or similar sensor in the vicinity of the output transducer. Problematic feedback occurs when the gain (i.e., amplitude) of the device is larger than the attenuation in the feedback loop outside the device, i.e., a negative remaining gain margin, which is often the state of an auditory prosthesis during initialization of the device.

One common method to reduce feedback is to identify when feedback occurs and cancel out the feedback signal with an adaptive filter in a feedback algorithm. Some pre-filtering or other start point criteria are often used to adapt faster with less audible artefacts. In existing systems, a feedback algorithm is executed as soon as an auditory prosthesis is initialized and before it is placed in an operational position. For example, auditory prostheses are generally initialized while still in a recipient's hand and then subsequently placed in an operational position, e.g., on the recipient's head, within the recipient's ear, etc. However, because the establishment of the feedback loop is performed while an auditory prosthesis (in its entirety) or a component of the auditory prosthesis, e.g., a sound processor, is in the recipient's hand, the established feedback loop is not optimally set for operational performance. This results in a sub-optimal result and/or a sub-optimal experience, e.g., audible artefacts.

For instance, when a feedback algorithm is first initialized, the adaptation speed of the feedback algorithm can be set to an aggressive, e.g., quicker, speed. The aggressive adaptation speed can result in the generation of audible artifacts, e.g., chirps or tones, that can cause discomfort or embarrassment to a recipient.

Aspects of the present disclosure relate to detecting when a component of an auditory prosthesis, e.g., an external device for an implantable prosthesis, a hearing aid, etc., is placed in an operational position for the recipient. Upon detection of the placement, a feedback algorithm having a faster initial adaptation speed is executed for a limited time. In this way the auditory prosthesis adapts to address, e.g., changes within the recipient, where a portion of the feedback path exists in some embodiments, since the auditory prosthesis was fitted to the recipient and/or was last in an operational position. A result is determination of optimal operational settings. In embodiments, in order to reduce the likelihood of audible artefacts, the initial feedback algorithm is performed during a ramp up of volume (e.g., gain or amplitude) which allows the feedback algorithm to adapt before high gain introduces a feedback problem.

Additional embodiments relate to initialization settings based on a feedback measurement setting, for example using a pre-filter or allowing the adaptive feedback algorithm to start from a previously determined feedback setting, for example using frequency based upon air delay, filter dynamics, step size, etc. In doing so, the difference between the initialization settings and any changes to the feedback path since the initial fitting of the auditory prosthesis will be reduced, thereby allowing for the use of a slower adaptation speed during an initialisation stage. A slower adaptation speed reduces the likelihood of instability and/or audible artefacts, thereby enhancing the recipient's experience. For instance, settings can be smoothed and/or averaged over time. In alternative embodiments, samples of the filter settings are saved during this first initialization time and an averaged filter is then used as starting point for the adaptive filter during a subsequent initialization.

Various devices that can employ and benefit from the systems and methods disclosed herein will now be described. While specific devices are described herein, one of skill in the art will appreciate that other types of devices can employ the aspects disclosed herein without departing from the scope of this disclosure. For instance, the type of processes executed upon placement of an auditory prosthesis in an operational position can vary depending on the type of the auditory prosthesis. Some types of auditory prostheses, such as certain cochlear implants, do not have problems with feedback, but do utilize beam forming algorithms. Like feedback algorithms, beam forming algorithms are best initialized while the device executing such is set in an operational position. Other auditory prostheses (e.g., traditional hearing aids, bone conduction devices, direct acoustic stimulators, middle ear devices, electro-acoustic implants, etc.), do have problems with feedback and some utilize beam forming algorithms. Such devices ideally initialize feedback and beamforming algorithms while the auditory prostheses, or a component of the auditory prosthesis, is set in an operational position, as described herein.

FIG. 1depicts a partial cross-sectional schematic view of an active transcutaneous bone conduction device100worn on a recipient. The active transcutaneous bone conduction device100includes an external device140and an implantable component150. The bone conduction device100ofFIG. 1is an active transcutaneous bone conduction device in that the vibrating actuator152is located in the implantable component150. Specifically, a vibratory element in the form of vibrating actuator152is located in an encapsulant154of the implantable component150. In the various examples described herein, implanted encapsulants154can be biocompatible ceramic, plastic, or other materials. In an example, much like the vibrating actuator152described below with respect to transcutaneous bone conduction devices, the vibrating actuator152is a device that converts electrical signals into vibration.

External component140includes a sound input element126that converts sound into electrical signals. Specifically, the transcutaneous bone conduction device100provides these electrical signals to a sound processor (not shown) that processes the electrical signals, and then provides those processed signals to the implantable component150through the skin132, fat128, and muscle134of the recipient via a magnetic inductance link. In this regard, a transmitter coil142of the external component140transmits these signals to implanted receiver coil156located in an encapsulant158of the implantable component150. Successful communications between transmitter coil142and receiver coil156can be indicative of the external component140being in an operational position (and in some embodiments, trigger, e.g., a ‘coil-on’ alert). If the coils are too far apart, too misaligned, shifted, etc., such successful communications are not possible. The margin for error in terms of placement of the transmitter coil142of the external component140in relation to the implanted receiver coil156depends on the characteristics of a given device.

The vibrating actuator152converts the electrical signals into vibrations. In another example, signals associated with external sounds can be sent to an implanted sound processor disposed in the encapsulant158, which then generates electrical signals to be delivered to vibrating actuator152via electrical lead assembly160. The vibrating actuator152is mechanically coupled to the encapsulant154. Encapsulant154and vibrating actuator152collectively form a vibrating element. The encapsulant154is substantially rigidly attached to bone fixture146B, which is secured to bone136. A silicone layer154A can be disposed between the encapsulant154and the bone136. In this regard, encapsulant154includes through hole162that is contoured to the outer contours of the bone fixture146B. Screw164is used to secure encapsulant154to bone fixture146B. As a result of the screw164and the bone fixture146B, the vibrating actuator152maintains a relatively stable position in relation to the recipient's head. As result of this relatively stable position, portions of the feedback path within the recipient are relatively consistent between cycles of operation of the active transcutaneous bone conduction device100. Less stable locational relationships between an actuator and a recipient might be found for other types of auditory prostheses, such as hearing aids and passive transcutaneous bone conduction devices, which could negatively impact beam forming and/or feedback algorithms.

FIG. 2is a schematic diagram of a percutaneous bone conduction device200. Sound207is received by sound input element252. In some arrangements, sound input element252is a microphone configured to receive sound207, and to convert sound207into electrical signal254. Alternatively, sound207is received by sound input element252as an electrical signal. As shown inFIG. 2, electrical signal254is output by sound input element252to electronics module256. Electronics module256is configured to convert electrical signal254into adjusted electrical signal258. As described below in more detail, electronics module256can include a sound processor, control electronics, transducer drive components, and a variety of other elements.

As shown inFIG. 2, transducer260receives adjusted electrical signal258and generates a mechanical output force in the form of vibrations that is delivered to the skull of the recipient via anchor system262, which is coupled to bone conduction device200. Delivery of this output force causes motion or vibration of the recipient's skull, thereby activating the hair cells in the recipient's cochlea (not shown) via cochlea fluid motion. A power module270provides electrical power to one or more components of bone conduction device200. For ease of illustration, power module270has been shown connected only to user interface module268and electronics module256. However, it should be appreciated that power module270can be used to supply power to any electrically powered circuits/components of bone conduction device200.

User interface module268, which is included in bone conduction device200, allows the recipient to interact with bone conduction device200. For example, user interface module268can allow the recipient to adjust the volume, alter the speech processing strategies, power on/off the device, etc. In the example ofFIG. 2, user interface module268communicates with electronics module256via signal line264.

Bone conduction device200can further include external interface module266that can be used to connect electronics module256to an external device, such as a fitting system. Using external interface module266, the external device, can obtain information from the bone conduction device200(e.g., the current parameters, data, alarms, etc.), and/or modify the parameters of the bone conduction device200used in processing received sounds and/or performing other functions.

In the example ofFIG. 2, sound input element252, electronics module256, transducer260, power module270, user interface module268, and external interface module266have been shown as integrated in a single housing, referred to as an auditory prosthesis housing or an external portion housing250. However, it should be appreciated that in certain examples, one or more of the illustrated components can be housed in separate or different housings. Similarly, it should also be appreciated that in such examples, direct connections between the various modules and devices are not necessary and that the components can communicate, for example, via wireless connections. Additionally, the bone conduction device200can include a sensor276that can be used to detect when the device200is in an operational position on the recipient. For example, the sensor276can detect the presence of a corresponding emitter (RFID, Bluetooth, Wi-Fi, etc.) located on the anchor system262. Alternatively, the sensor276can detect a condition of the transducer module260(e.g., the load on the transducer module) indicative of that component being engaged with the anchor system262. Such detection can then be communicated to the electronics module256that the device is in an operational position. The sensor276can also be a proximity or position sensor, or may be a button, switch, or other mechanical element that can detect a connection between the transducer module260and the anchor system262.

Typically, the external portion housing250is attached to the anchor system262in a relatively rigid manner via a so called snap coupling. When in operation, the external portion housing250is snapped to the anchor system262. As a result of this attachment, the external portion housing250(and the actuator or vibrator contained therein) maintains a relatively stable position in relation to the recipient's head, e.g., the external portion housing250is prevented from shifting during operation and from one cycle of operation to the next. As result of this relatively stable position, portions of the feedback path are relatively consistent between cycles of operation of the percutaneous bone conduction device200. Less stable locational relationships might be found for other types of auditory prostheses, such as hearing aids and passive transcutaneous bone conduction devices. Note however that in some such embodiments, the external portion housing250is able to rotate about an axis of the anchor system262. That is to stay that at the start of each cycle of operation, the external portion housing250might be rotated more or less (in relation to a hypothetical zero degrees of rotation) than in the previous cycle of operation, which can have in impact or beam forming algorithms, particularly the initialization of the beam forming algorithm.

FIG. 3depicts an example of a passive transcutaneous bone conduction device300that includes an external portion304and an implantable portion306. The device300ofFIG. 3is a passive transcutaneous bone conduction device in that a vibrating actuator308is located in the external portion304. In such devices, there are typically no active electrical or mechanical components in the implanted portion306.

Vibrating actuator308is located in housing310of the external component, and is coupled to a pressure or transmission plate312. The pressure plate312can be in the form of a permanent magnet and/or in another form that generates and/or is reactive to a magnetic field, or otherwise permits the establishment of magnetic attraction between the external portion304and the implantable portion306sufficient to hold the external portion304against the skin of the recipient. Magnetic attraction can be further enhanced by utilization of a magnetic implantable plate316that is secured to the bone336. Single magnets are depicted inFIG. 3. In alternative examples, multiple magnets in both the external portion304and implantable portion306can be utilized. In a further alternative example the pressure plate312can include an additional plastic or biocompatible encapsulant (not shown) that encapsulates the pressure plate312and contacts the skin332of the recipient. The device300may include a sensor or other component330, such as those described above, so as to detect when the device300is in an operational position. These sensors or components330can, e.g., detect RFID, Bluetooth, or WiFi emitted from an implantable portion306. Alternatively, the sensor330can detect a magnetic field indicative of the device300being in an operational position. In another example, the sensor330can be a button or mechanical switch or structure that is depressed when the device300is in contact with the skin332. The sensor330may also be disposed within the device300, discrete from the plate, and detect a load condition on the vibrating actuator308that is indicative of the pressure plate312being in contact with the skin332. In the illustrated embodiment ofFIG. 3, the sensor330is disposed on the pressure plate312, but in other embodiments, the sensor330is disposed elsewhere, such as elsewhere within the device300.

In an example, the vibrating actuator308is a device that converts electrical signals into vibration. In operation, sound input element326converts sound into electrical signals. Specifically, the transcutaneous bone conduction device300provides these electrical signals to vibrating actuator308, via a sound processor (not shown) that processes the electrical signals, and then provides those processed signals to vibrating actuator308. The vibrating actuator308converts the electrical signals into vibrations. Because vibrating actuator308is mechanically coupled to pressure plate312, the vibrations are transferred from the vibrating actuator308to pressure plate312. Implantable plate assembly314is part of the implantable portion306, and can be made of a ferromagnetic material that can be in the form of a permanent magnet. The implantable portion306generates and/or is reactive to a magnetic field, or otherwise permits the establishment of a magnetic attraction between the external portion304and the implantable portion306sufficient to hold the external portion304against the skin332of the recipient. Accordingly, vibrations produced by the vibrating actuator308of the external portion304are transferred from pressure plate312to implantable plate316of implantable plate assembly314. This can be accomplished as a result of mechanical conduction of the vibrations through the skin332, resulting from the external portion304being in direct contact with the skin332and/or from the magnetic field between the two plates312,316. These vibrations are typically transferred without a component penetrating the skin332, fat328, or muscular334layers on the head.

As can be seen, the implantable plate assembly314is substantially rigidly attached to bone fixture318in this example. Implantable plate assembly314includes through hole320that is contoured to the outer contours of the bone fixture318, in this case, a bone fixture318that is secured to the bone336of the skull. This through hole320thus forms a bone fixture interface section that is contoured to the exposed section of the bone fixture318. In an example, the sections are sized and dimensioned such that at least a slip fit or an interference fit exists with respect to the sections. Plate screw322is used to secure implantable plate assembly314to bone fixture318. As can be seen inFIG. 3, the head of the plate screw322is larger than the hole through the implantable plate assembly314, and thus the plate screw322positively retains the implantable plate assembly314to the bone fixture318. In certain examples, a silicon layer324is located between the implantable plate316and bone336of the skull.

But while implantable components of the passive transcutaneous bone conduction device300are relatively rigidly fixed to the skull of the recipient, the external components can rotate during and between cycles of operation of the passive transcutaneous bone conduction device300. The external components can also shift as they are typically not, e.g., snapped in to place during operation. This rotation and/or shifting can impact operation of, e.g., beam forming algorithms and feedback algorithms.

FIG. 4is a perspective view of a direct acoustic stimulator400B, comprising an external component442which is directly or indirectly attached to the body of the recipient, and internal component444B which is implanted in the recipient. The recipient has an outer ear401, a middle ear405and an inner ear407. Components of outer ear401, middle ear405and inner ear407are described below. In a fully functional ear, outer ear401comprises an auricle410and an ear canal402. An acoustic pressure or sound wave is collected by auricle410and channeled into and through ear canal402. Disposed across the distal end of ear canal402is a tympanic membrane404which vibrates in response to the sound wave. This vibration is coupled to oval window or fenestra ovalis (not shown) through three bones of middle ear405, collectively referred to as the ossicles. Bones of middle ear405serve to filter and amplify the sound wave, causing the oval window to articulate, or vibrate in response to vibration of tympanic membrane404. This vibration sets up waves of fluid motion of the perilymph within cochlea441. Such fluid motion, in turn, activates tiny hair cells (not shown) inside of cochlea441. Activation of the hair cells causes appropriate nerve impulses to be generated and transferred through the spiral ganglion cells (not shown) and auditory nerve414to the brain (also not shown) where they are perceived as sound.

External component442typically comprises one or more sound input elements, such as microphones431, sound processing unit424, a power source (not shown), and an external transmitter unit (also not shown). The internal component444B comprises internal receiver unit432, stimulator unit420, and stimulation arrangement450B. Stimulation arrangement450B is implanted in middle ear405and includes actuator440, stapes prosthesis454and coupling element453connecting the actuator440to the stapes prosthesis454. In this example, stimulation arrangement450B is implanted and/or configured such that a portion of stapes prosthesis454abuts round window421. It should be appreciated that stimulation arrangement450B can alternatively be implanted such that stapes prosthesis454abuts an opening in horizontal semicircular canal426, in posterior semicircular canal427or in superior semicircular canal428.

A sound signal is received by one or more microphones424, processed by sound processing unit426, and transmitted as encoded data signals to internal receiver432. Based on these received signals, stimulator unit420generates drive signals that cause actuation of actuator440. This actuation is transferred to stapes prosthesis454such that a wave of fluid motion is generated in the perilymph in scala tympani. Such fluid motion, in turn, activates the hair cells of the organ of Corti. Activation of the hair cells causes appropriate nerve impulses to be generated and transferred through the spiral ganglion cells (not shown) and auditory nerve414to the brain (also not shown) where they are perceived as sound.

FIG. 4provides an illustrative example of a direct acoustic stimulator system, more specifically, a direct acoustic cochlear stimulator. A middle ear mechanical stimulation device (or middle ear device) can be configured in a similar manner, with the exception that instead of the actuator440being coupled to the inner ear of the recipient, the actuator is coupled to a bone of the middle ear405. For example, the actuator can stimulate the middle ear by direct mechanical coupling via a coupling element (e.g., similar to coupling element453).

Referring toFIG. 5, cochlear implant system500includes an implantable component544typically having an internal receiver/transceiver unit532, a stimulator unit520, and an elongate lead518. The internal receiver/transceiver unit532permits the cochlear implant system510to receive and/or transmit signals to an external device. The external device can be a button sound processor worn on the head that includes a receiver/transceiver coil and sound processing components. Alternatively, the external device can be just a receiver/transceiver coil in communication with a BTE device that includes the sound processing components and microphone. The implantable component544includes an internal coil536, and preferably, a magnet (not shown) fixed relative to the internal coil536. The magnet is embedded in a pliable silicone or other biocompatible encapsulant, along with the internal coil536. Signals sent generally correspond to external sound513. Internal receiver unit532and stimulator unit520are hermetically sealed within a biocompatible housing, sometimes collectively referred to as a stimulator/receiver unit. The magnets facilitate the operational alignment of the external and internal coils, enabling internal coil536to receive power and stimulation data from external coil530. The external coil530is contained within an external portion550. Elongate lead518has a proximal end connected to stimulator unit520, and a distal end implanted in cochlea540. Elongate lead518extends from stimulator unit520to cochlea540through mastoid bone519. An intra-cochlear region546extends from the lead518and into the cochlea540.

In certain examples, external coil530transmits electrical signals (e.g., power and stimulation data) to internal coil536via a radio frequency (RF) link, as noted above. Internal coil536is typically a wire antenna coil comprised of multiple turns of electrically insulated single-strand or multi-strand platinum or gold wire. The electrical insulation of internal coil536is provided by a flexible silicone molding. Various types of energy transfer, such as infrared (IR), electromagnetic, capacitive and inductive transfer, can be used to transfer the power and/or data from external device to cochlear implant. Communication of the signals between the external coil530and the internal induction coil536can be indicative of the external device530being in an operational position. Certain cochlear implant systems500can also include a speaker542that extends into an ear canal of a recipient so as to deliver audible sounds at certain predetermined frequencies. Such devices, referred to as electro-acoustic implants, can also benefit from the technologies described herein to reduce feedback.

FIG. 6is a schematic diagram of a totally implantable cochlear implant600. In a totally implantable cochlear implant600, all components are configured to be implanted under skin/tissue602of a recipient. Because all components of cochlear implant system600are implantable, cochlear implant system600operates, for at least a finite period of time, without the need of an external device. An external device604can be used to charge the internal battery, to supplement the performance of the implanted microphone/system, or for when the internal battery no longer functions. External device604can be a dedicated charger or a conventional cochlear implant sound processor. Either way, the external device604preferably incorporates a microphone.

As noted, cochlear implant system600includes a main implantable component606having a hermetically sealed, biocompatible housing608. The technologies described herein that detect an operational position can be incorporated into either or both of the external device604and the main implantable component606. Disposed in main implantable component606is a microphone610configured to sense a sound signal612. Microphone610can include one or more components to pre-process the microphone output. As an alternative, the microphone and other aspects of the system can be included in an upgrade or tethered module as opposed to in a unitary body as shown inFIG. 6. For example, a remote microphone610atethered to the main implantable component606can be utilized.

An electrical signal614representing sound signal612detected by microphone610,610ais provided from the microphone610,610ato sound processing unit616. Sound processing unit616implements one or more speech processing and/or coding strategies to convert the pre-processed microphone output into data signals618for use by stimulator unit620. Stimulator unit620utilizes data signals618to generate electrical stimulation signals622for delivery to the cochlea of the recipient. In the example ofFIG. 6, cochlear implant system600comprises stimulating lead assembly624for delivering stimulation signal622to the cochlea.

Cochlear implant system600also includes a rechargeable power source626. Power source626can comprise, for example, one or more rechargeable batteries. As described below, power is received from an external device, such as external device604, and is stored in power source626. The power can then be distributed to the other components of cochlear implant system600as needed for operation.

Main implantable component606further comprises a control module628. Control module628includes various components for controlling the operation of cochlear implant600, or for controlling specific components of cochlear implant system600. For example, controller628can control the delivery of power from power source626to other components of cochlear implant system600. For ease of illustration, main implantable component606and power source626are shown separate. However, power source626can alternatively be integrated into a hermetically sealed housing606or part of a separate module coupled to component606. Magnetic sensors (not shown) are operatively connected to the control module628and are described further herein (e.g., sensor330).

As noted above, cochlear implant system600further comprises a receiver or transceiver unit630that permits cochlear implant system600to receive and/or transmit signals632to the external device604. For ease of illustration, cochlear implant system600is shown having a transceiver unit630in main implantable component606. In alternative arrangements, cochlear implant system600includes a receiver or transceiver unit which is implanted elsewhere in the recipient outside of main implantable component606.

Transceiver unit630is configured to transcutaneously receive power and/or data632from external device604. Power634can also be transferred to and from the transceiver unit630to charge the power source626. Signals636(power, data, or otherwise) can also be sent to/from the transceiver630, the sound processing unit616, and other components of the device as required or desired. As used herein, transceiver unit630refers to any collection of one or more implanted components which form part of a transcutaneous energy transfer system. Further, transceiver unit630includes any number of component(s) which receive and/or transmit data or power, such as, for example a coil for a magnetic inductive arrangement, an antenna for an alternative RF system, capacitive plates, or any other suitable arrangement. Various types of energy transfer, such as infrared (IR), electromagnetic, capacitive and inductive transfer, can be used to transfer the power and/or data632from external device604to the main implantable component606.

As noted, transceiver unit630receives power and/or data632from external device604. In the illustrative arrangement ofFIG. 6, external device604comprises a power source (not shown) disposed in an off the ear processor, which is held in place on the recipient's head using any of the foregoing techniques described, e.g., via a magnet (not show) disposed in the external device604and another magnet (not shown) disposed in the main implantable component606. In such embodiments, the external device604is able to rotate and shift to some degree during operation and in between cycles of operation of the cochlear implant system600and/or external component604, which can have an impact on a beam forming algorithm in operation on cochlear implant system600. Further, the presence of the external device604can be detected using any of the suitable techniques described herein. Nevertheless, the external device shown inFIG. 6is merely illustrative, and other external devices can be alternatively used.

While specific types of auditory prostheses have been described herein, one of skill in the art will appreciate that the systems and methods disclosed herein can be performed using other types of auditory prostheses. For example, the aspects described herein can be performed using a hearing aid, middle ear implant, or other device. Other types of devices can also benefit from the aspects disclosed herein such as, for example, headphones, mobile phones, wireless earpieces, etc. Operational positioning can vary depending on the type of device. For example, hearing aids and passive transcutaneous auditory implant lacks a snap coupling or other type of fastener that limits its processor to a range of positions. Thus, the operational positioning of the sound processor for such a device is not so limited in its range of positioning. As such, there can be greater changes to the effective feedback path of such devices than there will be with other in which the sound processor does snap into position, e.g., a percutaneous auditory prosthesis.

Having described various devices that can employ the aspects disclosed herein, the disclosure will now describe various methods for executing processes in an efficient manner.FIG. 7is an exemplary method700for executing a process upon detecting that a device is in an operational position. The method700can be implemented using hardware, software, or a combination of hardware and software. In embodiments, the method700can be performed by an auditory prosthesis, such as, for example, a bone conduction device, a middle ear device, a hearing aid, etc. The method700may also be performed using a general computing device connected to and/or in communication with any of the foregoing. Flow begins at operation702where a device is initialized. In one example, initializing a device includes powering on the device. As described above, some processes executed by the device produce better results when the device is in an operational position than they would if the processes were executed before the device is in an operational position. However, in some aspects, while such processes might not complete before the device is in place, parameters can be set upon initialization of the device at operation702.

After initializing the device, flow continues to operation704where a monitoring of the device position is performed. As previously described, aspects disclosed herein relate to performing actions when a device is in an operational position. In examples, an operational position refers to the positioning of a device in a manner that the device is intended to operate in. As an example, an operational position may be a physical location such as the placement of an external sound processor for an implantable auditory prosthesis within proximity of an implanted component, placement of a hearing aid in a recipient's ear canal, placement of a headset on an outer ear, etc. In examples, the determination may be made using various components of a device such as, but not limited to, an external and/or implanted coil, and external and/or implanted magnet, an accelerometer, a gyroscope, a magnetic field sensor, a proximity sensor, a button, a switch, or any other type of component capable of generating information that can be used to determine a physical location of a device. Alternatively, an operational position may refer to placing the device in an operational state such as, for example, establishing a data connection between different operational components of a device. For example, an auditory prosthesis may be considered to be in an operational position upon the establishment of a data link between an external sound processor and an implanted component of the auditory prosthesis, e.g., via external and implanted coils. Flow continues to decision operation706where a determination is made as to whether the device is in an operational position. If the device is not in an operational position, flow branches NO and returns to operation704where the method continues to monitor the device's position.

If the device is in an operational position, flow branches YES to operation708. At operation708a process is executed. In examples, the process executed at operation708is a process that produces improved results, makes better determinations, or provides better outcomes when executed during the correct operational placement of a device. One example of such a process is initialization of a feedback algorithm. Initialization of a feedback algorithm can result in audible artifacts, particularly in systems that include a microphone or other type of input device in the vicinity of an output transducer. When feedback occurs at an auditory prosthesis, the recipient of the auditor prosthesis can experience discomfort. Feedback algorithms combat feedback by cancelling out a feedback signal using an adaptive filter. The settings applied to the adaptive filter have an effect on the feedback reduction. The proper settings can vary depending on the positioning of the device. Because of this, execution of a feedback algorithm provides better results when the execution begins when the device is in an operational positon, which is not necessarily the same instance as when the device is initialized. One of skill in the art will appreciate that various different types of feedback algorithms can be practiced with the various aspects disclosed herein without departing from the spirit or scope of this disclosure. One of skill in the art will appreciate that other types of processes also benefit from beginning execution when a device is in an operational position. For example, a beam forming algorithm may also benefit from executing at the time that a device is placed into an operational position. For instance, beam forming algorithms typically focus on sounds coming from a direction in front of the recipient. If a device is still held in the recipient's hand or otherwise not facing in a proper direction during initialization of the beam forming algorithm, the device might configure itself to reduce as noise speech coming from the direction in front of the recipient. In some embodiments, before the beam forming algorithm is initialized, the microphones of the device are configured to operate in omni directional mode. Changes in gain settings are also better performed when the device is an operational position. In further aspects, the different processes can be executed sequentially or in parallel upon detection that the device is in place. In one example, beam forming can be executed prior to execution of the feedback algorithm. Because directionality can affect the feedback path, if the beam forming is performed before feedback reduction, additional benefits can be gained from the feedback algorithm. While the disclosure describes various different processes executing at operation708, one of skill in the art will appreciate that other types of processes can be executed at operation708without departing from the scope of this disclosure.

Flow continues to decision operation710where a determination is made as to whether the device is still in an operational position. As discussed with respect to operation704, the determination can be based upon the physical location of the device and/or an operating state of a device.

As indicated herein, the device may rotate, shift or move otherwise to some degree and still remain in an/the operational position. Typically, and depending on device type, relatively stability of the feedback path, etc., an auditory prosthesis provides 0-6 dB of additional available gain during a fitting of the prostheses to a recipient. Further, some feedback algorithms with phase shifting provide 10-12 dB of additional gain without artefacts and up to 20 dB of additional gain with some artefacts. This means that in some embodiments, there is between 4-12 dB in feedback algorithm margin. So long as the movement of the device does not consume that margin, the device affectively remains in an/the operational position. Moreover, in some embodiments, the operation of the device might be interrupted temporarily. For instance, a recipient might lean against a wall or interrupt a feedback path between a speaker and a microphone of the device. Such actions could have a negative impact on operation of the device, e.g., consume the margin referred to herein. So long as the interruption is brief, e.g., less than 1 second or within range of some other time, the device remains in the operational position despite the interruption. If the margin is consumed or consumed for a significant period of time, the device in some embodiments treats that as the device no longer being in the operational position even if, for instance, successful communications between external and internal components of the device remain.

If the device is still in an operational position, flow branches YES and returns to operation708where the one or more processes continue execution. If the device is no longer in an operational position, flow branches NO to operation712. At operation712, one or more processes executed at operation708are terminated. In one example, terminating processes provides for an increase in battery life for the device. Energy usage can be minimized by halting the execution of processes that are unnecessary based upon a device's position and/or state. Additionally, halting of the one or more processes prevents the device from transitioning into a sub-optimal or inoperable state. For example, the continuation of certain feedback reduction and/or beam forming algorithms (e.g., ongoing dynamic adjustments) can result in sub-optimal settings being applied to the device due to the fact that the device is no longer in an operational position. For example, feedback and beam forming settings applied when an auditory prosthesis is in the hand of a recipient will not produce optimal results.

Flow then continues to optional operation714. At optional operation714, the state or settings of the device at the time the device is removed from the operational position are saved. Saving the state or settings can include saving any parameters or settings generated using one or more processes executed at operation708. Saving the state or settings allows for the initialization of the device to the functional state or settings when the device was last in an operational position. This can lead to an enhanced experience for the recipient when the device is again placed into operation, e.g., less aggressive settings during initialization of the feedback algorithm.

FIG. 8is an exemplary method800for executing a feedback algorithm upon detecting that a sound processor of an auditory prosthesis is in an operational position. The method800can be implemented using hardware, software, or a combination of hardware and software. In embodiments, the method800can be performed by an auditory prosthesis, such as, for example, a bone conduction device, a middle ear device, a hearing aid, etc. The method800may also be performed using a general computing device connected to and/or in communication with the foregoing devices. Flow begins at operation802where a pre-filter may be set for a feedback algorithm. In examples, the pre-filter may be settings that were determined during a previous fitting process for the device. In further examples, the pre-filter may be settings that were in place the last time that the device was in an operational position. In further embodiments, other parameters may be set at operation802. For example, parameters related to step-size for gain increase, frequency parameters depending upon air delay, filter dynamics, etc. may be set at operation802. Setting a pre-filter at operation802allows the feedback algorithm to employ slower adaptation than is possible at a later stage (e.g., at operation808). Slower adaptation reduces the risk of instability and reduces the chance that audible artifacts occur, thereby enhancing the recipient's experience.

Flow continues to operation804where monitoring of the position of the sound processor is performed. The monitoring is performed to determine whether the sound processor is in an operational position. In one example, the sound processor may be in an operational position when the sound processor is in a substantially fixed location that is expected while the device remains in operation. In one example, the sound processor may be in a substantially fixed location based upon a locational relationship of the sound processor with respect to another component of the auditory prosthesis, with respect to the recipient, or with respect to both. In other aspects, an operational position may be defined by a substantially fixed feedback path that is expected while the device is in an operational position. In still other aspects, the operational position may be defined by feedback settings. For example, the sound processor may be in an operational position when it is determined that the current feedback settings are settings that tend to be consistent from one instance of operation to the next. In one example, the sound processor can be determined to be in an operational position based upon a coil-on event. That is, if the external and internal coils of the sound processor are within proximity to one another and/or upon the establishment of a data link between the coils, then it can be determined that the sound processor is in an operational position. In an alternate embodiment, the determination of the operational position can be based upon the proximity of internal and external magnets of the auditory prosthesis. When the internal and external magnets are in a close proximity, then the sound processor can be determined to be in an operational position.

Flow continues to decision operation806where a determination is made as to whether the sound processor is in an operational position based upon the monitoring performed at operation804. If it is determined that the device is not in an operational position, flow branches NO and returns to operation804where continued monitoring of the sound processor's position is performed. If the sound processor is determined to be in an operational position, flow branches YES to operation808. At operation808, an initial phase of a feedback algorithm is executed. In examples, the initial phase of the feedback algorithm can have a first adaptation speed. The first adaptation speed can be more aggressive, e.g., faster, than an operational adaptation speed. In examples, it is beneficial to apply a more aggressive adaptation speed during the initial phase to quickly identify and set optimal settings for the sound processor. However, faster adaptation speeds increase the likelihood of audible artifacts. As will be discussed in further detail with respect toFIG. 9, certain mechanisms can be employed to reduce the likelihood of such artifacts during the initial phase. Further, the relative stability of the feedback path, which depends in part on device type, can be used to configure/select the first and/or second adaptation speeds and adjust or set other settings or characteristics during an initialization and/or operational phase of a feedback or other algorithm. For instance, the first adaptation speed can be relatively slower for devices with a relatively stable feedback path.

After the initial phase has completed, flow continues to operation810where an operational phase of the feedback algorithm is executed. In one example, the initial phase can be completed after a set amount of time. Alternatively, the initial phase can be completed upon reaching a certain state or collection of settings. For example, the initial phase can be completed upon reaching a stable feedback loop, that is, upon reaching a consistent state or collection of settings for the feedback algorithm. During the operational phase, the adaptation speed of the feedback algorithm may be reduced, that is, a less aggressive adaptation speed can be applied. It is possible to reduce the adaptation speed because a stable feedback loop can be in place during the operational phase partly through the use of a properly configured and timed initial phase. The slower adaption speed reduces the likelihood of audible artifacts during the operation of the sound processor.

After entering the operational phase, flow continues to decision operation812. At decision operation812, a determination is made as to whether the sound processor is still in the operational position. The determination can be made according to the various examples described with respect to operations804and806. If the sound processor is still in an operational position, flow branches YES and returns to operation810where the operational phase of the feedback algorithm continues to execute. However, if the sound processor is no longer in an operational position, then flow branches NO to operation814. At operation814, the execution of the feedback algorithm is terminated. Because the sound processor is no longer in an operational position, any adjustments made by the feedback algorithm may result in sub-optimal performance. In other words, any adjustments made after the sound processor is no longer in an operational position can be invalid.

After terminating execution of the feedback algorithm, flow continues to optional operation816. At optional operation816, parameters and or settings in place at the time the sound processor was in operational position can be saved. Saving the parameters and or settings allows for the initialization of the sound processor to the saved parameters and or settings. For example, the settings saved at operation814can be applied during the initialization operation802the next time the sound processor is activated. This allows for the sound processor to more efficiently and/or less aggressively reach a stable feedback loop, which, in turn, reduces the likelihood of audible artifacts.

FIG. 9is an exemplary method900for performing phased feedback reduction. The method900can be implemented using hardware, software, or a combination of hardware and software. In embodiments, the method900can be performed by an auditory prosthesis, such as, for example, a middle ear device, a bone conduction device, a hearing aid, etc. The method900can also be performed using a general computing device. In examples, the method900can be performed during operations508and510of the method500. Flow begins at operation902where a reduced amplification level setting is applied. Reduction of the amplification setting can reduce the likelihood of audible artifacts occurring during initialization of a feedback algorithm. In examples, in addition to setting a reduced amplification setting, an amplification step can be set at operation902. The amplification step defines how quickly the amplitude of the auditory prosthesis can be altered. For example, an amplification step of 5 dB can be set. Under such circumstances, the amplification of the auditory prosthesis can be adjusted in 5 dB increments. Other step sizes can be set without departing from the spirit of this disclosure.

Flow continues to operation904where a feedback algorithm is executed with a first adaptation speed. In examples, the operation902can be performed at the initialization of the feedback algorithm. Because the algorithm is just initialized, the feedback loop is more likely to be unstable. Because of this, a faster adaptation speed can be employed to quickly stabilize the feedback loop. The first adaptation speed can be faster, e.g., more aggressive. Because a reduced amplification level was set at operation902, the likelihood of audible artifacts is reduced during execution of the aggressive adaptation speed. Flow continues to operation906where the amplification level is adjusted by an amplification step size. In this manner, the amplification level of the auditory prosthesis can be incrementally brought to an operational amplification setting while continuing to perform aggressive feedback reduction. The incremental increase reduces the likelihood of generating an audible artifact. The amplification step size can be determined by a prior setting, for example, by a level determined during operation902. Alternatively, the amplification step size can be dynamically determined based upon the status of the feedback loop.

Flow continues to decision operation908where a determination is made as to whether the initial phase of the feedback algorithm has completed. In one example, the initial phase can be completed after a set amount of time. Alternatively, the initial phase can be completed upon reaching a certain state or collection of settings. For example, the initial phase can be completed upon reaching a stable feedback loop, that is, upon reaching a consistent state or consistent settings for the feedback algorithm. If the feedback algorithm is still in the initial phase, flow branches NO and returns to operation906where the amplification is adjusted again by a step size and the feedback algorithm continues to operate at a faster adaptation speed. If the initial phase has completed, flow branches YES to operation910.

At operation910, the adaptation speed of the feedback algorithm is reduced, e.g., a less aggressive adaptation speed is applied. The slower adaption speed reduces the likelihood of audible artifacts during the operation of the sound processor. Flow then continues to operation912where the feedback algorithm continues to operate at the reduced adaptation speed.

FIG. 10is an embodiment of a system1000in which the various systems and methods disclosed herein can operate. The most basic components of the system1000may be included as part of an auditory prosthesis. In alternate embodiments, a client device in communication with the auditory prosthesis, can be employed to set and/or perform the feedback algorithms and other processes disclosed herein. In such embodiments, a client device, such as client device1002, can communicate with one or more auditory prostheses, such as auditory prosthesis1004, via a network806. In embodiments, a client device can be a remote control, a laptop, a personal computer, a smart phone, a PDA, a netbook, a tablet computer, a server or any other type of computing device, such as the computing device inFIG. 10. In embodiments, the client device1002and the auditory prosthesis1004may communicate via communication channel1006. Communication channel1006can be any type of network capable of facilitating communications between the client device1002and the auditory prosthesis1004. Examples of a communication channel can be an RF connection, a Bluetooth connection, a WiFi connection, or any other type of connection capable of transmitting instructions between client device1002and auditory prosthesis1004.

In embodiments, the various systems and methods disclosed herein can be performed by an auditory prosthesis, e.g., auditory prosthesis1004, a client device, e.g., client device1002, or by both the auditory prosthesis and client device. For example, in embodiments the client device may perform a method to identify a control expression and instruct the auditory prosthesis to apply an audio setting adjustment. In such embodiments, client device1002can transmit instructions to the auditory prosthesis to apply an audio setting instruction via communication connection1006.

Communication channel1006, in certain embodiments, is capable of real-time or otherwise suitably fast transmission of, e.g., instructions from client device1002to auditory prosthesis1004. In such embodiments, instructions from the client device1002based on its processing of a control expression and related conversation is received in good time by the auditory prosthesis1004. If, for instance, such instructions are not transmitted suitably fast, an audio setting adjustment to auditory prosthesis1004might not be made in time benefit the recipient (e.g., in time for the repeat of a conversation fragment the recipient requested with the control expression).

The embodiments described herein can be employed using software, hardware, or a combination of software and hardware to implement and perform the systems and methods disclosed herein. Although specific devices have been recited throughout the disclosure as performing specific functions, one of skill in the art will appreciate that these devices are provided for illustrative purposes, and other devices can be employed to perform the functionality disclosed herein without departing from the scope of the disclosure.

This disclosure described some embodiments of the present technology with reference to the accompanying drawings, in which only some of the possible embodiments were shown. Other aspects can, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments were provided so that this disclosure was thorough and complete and fully conveyed the scope of the possible embodiments to those skilled in the art.

Although specific embodiments were described herein, the scope of the technology is not limited to those specific embodiments. One skilled in the art will recognize other embodiments or improvements that are within the scope of the present technology. Therefore, the specific structure, acts, or media are disclosed only as illustrative embodiments. The scope of the technology is defined by the following claims and any equivalents therein.