User directed frequency mapping

Abstract

Presented herein are techniques for determining a frequency allocation table for a medical device based on an input from a recipient of the medical device. A first type of signal is delivered to the recipient of the medical device. Contemporaneously with delivering the first type of signal, a second type of stimulation signal is delivered to the recipient. At least one input is received, at a computing device, from the recipient. The at least one input adjusts at least one relational parameter between the first type of stimulation signal and the second type of stimulation signal. One or more parameters of the medical device are set / determined based on the at least one input from the recipient.

Description

Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1USER DIRECTED FREQUENCY MAPPING BACKGROUNDField of the Invention[ooot] The present invention relates generally to mapping frequencies to stimulation electrodes based on a user input.Related Art

[0002] Medical devices are devices that are intended to be used for medical purposes. They can vary in both their intended use and indications for use. Examples range from simple, low-risk medical supplies to complex, potentially high-risk devices that are implanted and / or sustain life, such as deep brain stimulators and brain-computer interfaces. Other categories of medical device include diagnostic equipment.

[0003] Hearing devices act on an actual or potential auditory perception of an individual, including to improve perception of sound signals, to reduce perception of sound signals, etc. In particular, a hearing device can deliver sound signals to a user in any form, including in the form of acoustical stimulation, mechanical stimulation, electrical stimulation, etc., and / or can operate to suppress all or some sound signals. As such, a hearing device can be a device for use by a hearing-impaired person (e.g., hearing aids, middle ear auditory prostheses, bone conduction devices, direct acoustic stimulators, electro-acoustic hearing prostheses, auditory brainstem stimulators, bimodal hearing prostheses, bilateral hearing prostheses, dedicated tinnitus therapy devices, tinnitus therapy devices, etc.) or a device for use by a person with normal hearing (e.g., a consumer device that provides audio streaming, a consumer headphone, an earphone, etc.), a hearing protection device (e.g., a noise cancellation headset, a loudness reduction apparatus, etc.), etc.SUMMARY

[0004] In one aspect, a method is provided. The method comprises: delivering an acoustic signal to a recipient of a medical device; contemporaneously with delivering of the acoustic signal, delivering an electrical stimulation signal to the recipient; receiving, at a computing device, at least one input from the recipient, wherein the at least one input adjusts at least one relational parameter between the acoustic signal and the electrical stimulation signal; and determining, with at least one processor, a frequency allocation table for the medical device based on the at least one input from the recipient.Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1

[0005] In another aspect, a system is provided. The system includes: a medical device comprising a stimulator unit and a plurality of electrodes implanted at an inner ear of a recipient; an output device configured to vibrate fluid in the inner ear; one or more processors configured to: control the stimulator unit to deliver an electrical stimulation signal via a first one of the plurality of electrodes located at a first tonotopic region of the inner ear; and control the output device to contemporaneously deliver a second stimulation signal, wherein the second stimulation signal is configured to induce perception of a tone that is estimated to correspond to the first tonotopic region; and a computing device configured to receive at least one input from the recipient, wherein the at least one input indicates a frequency relationship between the electrical stimulation signal and the second stimulation signal; and wherein the one or more processors are further configured to program the medical device with stimulation frequencies based on the frequency relationship between the electrical stimulation signal and the second stimulation signal.

[0006] In another aspect, a method is provided. The method includes: contemporaneously delivering a first type of stimulation and a second type of stimulation to a recipient of a medical device; following the delivering, receiving subjective feedback from the recipient indicating a relationship between the first type of stimulation and the second type of stimulation; and programing the medical device with stimulation parameters based on the subjective feedback.

[0007] In another aspect, one or more non-transitory computer readable storage media including instructions are provided that, when executed by a processor of a medical device, cause the processor to: cause a first type of stimulation signal to be delivered to a recipient of the medical device; contemporaneously with delivery of the first type of stimulation signal, cause a second type of stimulation signal to be delivered to the recipient; obtain at least one input from the recipient, wherein the at least one input characterizes a relationship between the first type of stimulation signal and the second type of stimulation signal; and determine one or more stimulation parameters for the medical device using the at least one input.Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1BRIEF DESCRIPTION OF THE DRAWINGS

[0008] Embodiments of the present invention are described herein in conjunction with the accompanying drawings, in which:

[0009] FIG. 1A is a schematic diagram illustrating an electro-acoustic hearing device with which aspects of the techniques presented herein can be implemented;[ooto] FIG. IB is a block diagram of the electro-acoustic hearing device of FIG. 1A;[ooit] FIG. 1C is a schematic diagram illustrating a computing device with which aspects of the techniques presented herein can be implemented;

[0012] FIG. 2 is a flow chart illustrating a method of determining frequency mappings for electrodes using input from a recipient of a hearing device, according to an example embodiment;

[0013] FIG. 3 is a diagram illustrating an exemplary user interface of an application used to receive a user input to match positions of electrodes to frequency ranges, according to an example embodiment;

[0014] FIG. 4 is a flow chart of a method of determining a frequency allocation table for a hearing device based on at least one input from a recipient of the hearing device, according to an example embodiment;

[0015] FIG. 5 is a flow chart of a method of programming a medical device with stimulation frequencies based on subjective feedback from a recipient of the medical device, according to an example embodiment;

[0016] FIG. 6 is a schematic diagram illustrating a vestibular stimulator system with which aspects of the techniques presented herein can be implemented;

[0017] FIG. 7 is a schematic diagram illustrating a retinal prosthesis system with which aspects of the techniques presented herein can be implemented;

[0018] FIG. 8 is a schematic diagram illustrating a tinnitus therapy device with which aspects of the techniques presented herein can be implemented; and

[0019] FIG. 9 is a perspective view of an upper airway stimulation device with which aspects of the techniques presented herein can be implemented.Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1DETAILED DESCRIPTION

[0020] Presented herein are techniques for determining stimulation parameters, such as a frequency allocation table, for a stimulating device (e.g., hearing device, medical device, etc.) based on an input from the recipient of the stimulating device. In particular, a first type of stimulation signal (e.g., an acoustic signal) is delivered to the recipient and, contemporaneously with delivery of the first type of stimulation signal, a second type of stimulation signal (e.g., an electrical stimulation signal) is delivered to the recipient. At least one input is received (e.g., at a computing device), from the recipient, where the at least one input adjusts at least one relational parameter between the first type of stimulation signal and the second type of stimulation signal. The input is used, potentially in combination with other inputs received from the recipient, to set / determine one or more stimulation parameters for the stimulating device. In one form, the one or more stimulation parameters include a frequency allocation table for the stimulating device.

[0021] There are a number of different types of device in / with which the techniques presented herein can be implemented. For example, it is to be appreciated that the techniques presented herein can also be partially or fully implemented by consumer electronic devices (e.g., consumer hearing devices, consumer computing devices such as mobile phones and tablets, audio equipment such as home theatre and car audio systems, etc.), computing systems (e.g., servers in data centers, Intemet-of-Things (loT) devices), various types of software systems, such as databases, machine learning and artificial intelligence systems, other medical devices, such as diagnostic equipment or life sustaining equipment, etc. The techniques presented herein could be used in or with sensory protheses, including hearing aids and cochlear implants, and various medical devices, such as pacemakers, drug delivery systems, implantable defibrillators, functional electrical stimulation devices, sleep disorder devices (e.g., sleep apnea devices), seizure devices (e.g., devices for monitoring and / or treating epileptic events), balance or movement disorder devices (e.g., vestibular stimulation devices), tinnitus management devices, visual implants (e.g., bionic eyes), and other neuromodulation devices (e.g., braincomputer interfaces).

[0022] Merely for ease of description, the techniques presented herein are primarily described with reference to a specific device, namely an electro-acoustic hearing device (e.g., a hearing device that can deliver both acoustic and electrical stimulation to a recipient). As described further below, in certain examples, the techniques presented herein obtain data from a recipient of an electro-acoustic hearing device for determining / generating a frequency allocation tableAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1associated with the electro-acoustic hearing device. For example, certain electro-acoustic hearing devices include both an acoustic receiver and one or more electrodes disposed at (e.g., in, on, or near) a recipient’s inner ear. Such electro-acoustic hearing devices are useful in cases where a recipient has some residual hearing in certain frequency / tonotopic regions of the inner ear (e.g., which can be stimulated acoustically to evoke a hearing percept), but needs electrical stimulate to evoke hearing percepts in other frequency / tonotopic regions of the inner ear.

[0023] More specifically, individuals suffer from different types of hearing loss (e.g., conductive and / or sensorineural) and / or different degrees / severity of hearing loss. However, it is now common for many recipients to retain some residual natural hearing ability (residual hearing) after receiving a hearing device. For example, progressive improvements in the design of intra-cochlear electrode arrays (stimulating assemblies), surgical implantation techniques, tooling, etc. have enabled atraumatic surgeries which preserve at least some of the recipient’s fine inner ear structures (e.g., cochlea hair cells) and the natural cochlea function, particularly in the lower frequency regions of the cochlea.

[0024] Due, at least in part, to the ability to preserve residual hearing, the number of recipients who are candidates for different types of hearing devices, such as electro-acoustic hearing prostheses, cochlear implants, tinnitus stimulators, etc. has continued to expand. As such, it is becoming increasingly common for recipients to rely on both electrical stimulation (i.e., current signals) and acoustic stimulation (i.e., natural or amplified acoustic sounds) at the same ear. Typically, due to the limits of residual hearing, the acoustic stimulation is used to present sound signal components corresponding to the lower frequencies of sound signals, while the electrical stimulation is used to present sound signal components corresponding to the higher frequencies of sound signals.

[0025] Recipients with residual hearing typically benefit from having acoustic stimulation in addition to electrical stimulation, because the acoustic stimulation adds a more “natural” sound to their hearing perception compared to electrical stimulation signals only in that ear. In particular, temporal coding of auditory signals is particularly important for low frequencies and is best achieved with acoustic stimulation. As such, combined electric-acoustic stimulation benefits specifically from this low-frequency acoustic coding. For example, the addition of the acoustic stimulation can provide improved pitch and music perception and / or appreciation, as the acoustic signals can contain a more salient lower frequency (e.g., fundamental pitch, F0) representation than is possible with electrical stimulation. Other benefits of residual hearingAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1can include, for example, improved sound localization, binaural release from unmasking, the ability to distinguish acoustic signals in a noisy environment, etc.

[0026] The cochlea is tonotopically mapped, meaning that certain regions / areas of the cochlea respond to different frequencies of sound. In general, the areas that respond to lower frequencies are located towards the apical / distal end of the cochlea, while the areas that respond to higher frequencies are located towards the basal / proximal end of the cochlea. Typically, a recipient’s residual hearing remains in the lower frequency areas (i.e., the more apical areas of the cochlea) and these are the areas that can be stimulated using acoustic stimulation. In contrast, the higher frequency areas (i.e., the more basal areas of the cochlea) typically do not include residual hearing and these are the areas that are stimulated using electrical stimulation.

[0027] To deliver both acoustic and electrical stimulation to a recipient, the recipient can be fitted with an electro-acoustic hearing device. FIG. 1A is schematic diagram of such a medical device in the form of an exemplary electro-acoustic hearing device 100 configured to implement embodiments of the present invention, while FIG. IB is a block diagram of the electro-acoustic hearing device. For ease of illustration, FIGs. 1A and IB will be described together.

[0028] The electro-acoustic hearing device 100 includes an external component 102 and an intemal / implantable component 104. The external component 102 is directly or indirectly attached to the body (e.g., skin / tissue 101) of the recipient and comprises a sound processing unit 110, an external coil 106, and, generally, a magnet (not shown in FIG. 1A) fixed relative to the external coil 106. The external coil 106 is connected to the sound processing unit 110 via a cable 134. The sound processing unit 110 comprises one or more sound input devices 108 (e.g., microphones, audio input ports, cable ports, telecoils, a wireless transceiver, etc.), a sound processor 112, an external transceiver unit (transceiver) 114, and power source 116. In the example of FIGs. 1A and IB, the sound processing unit 110 is a behind-the-ear (BTE) sound processing unit. However, in other embodiments, the sound processing unit 110 could be a body-worn sound processing unit, a button sound processing unit, an in-the-ear (ITE) unit, etc.

[0029] Connected to the sound processing unit 110 (e.g., wirelessly, via a cable 134, etc.) is a hearing aid component 141. The hearing aid component 141 includes a receiver 142 (FIG. IB) that can be, for example, positioned in or near the recipient’s outer ear. The receiver 142Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1is an acoustic transducer that is configured to deliver acoustic signals (acoustic stimulation) to the recipient via the recipient’s ear canal and middle ear.

[0030] FIGs. 1A and IB illustrate the use of a receiver 142 to deliver acoustic stimulation to the recipient. However, as noted above, it is to be appreciated that the acoustic stimulation can be delivered in a number of other manners. For example, other embodiments can include an external or implanted vibrator that is configured to deliver acoustic stimulation to the recipient. In still other embodiments, the hearing aid component 141 could be omitted and the recipient’s cochlea is acoustically stimulated using unaided acoustic signals provided to the recipient’s cochlea via the natural hearing path (i.e., via the functioning outer ear and middle ear). Acoustic stimulation can also be delivered using an in-the-ear hearing aid, controlled by the sound processor 112.

[0031] As shown in FIG. IB, the implantable component 104 comprises an implant body (main module) 122, a lead region 124, and an elongate intra-cochlear stimulating assembly 126. The implant body 122 generally comprises a hermetically-sealed housing 128 in which an internal transceiver 130 and a stimulator unit 132 are disposed. The implant body 122 also includes an intemal / implantable coil 136 that is generally external to the housing 128, but which is connected to the transceiver 130 via a hermetic feedthrough (not shown in FIG. IB). Implantable coil 136 is 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 implantable coil 136 is provided by a flexible molding (e.g., silicone molding), which is not shown in FIG. IB. Generally, a magnet is fixed relative to the implantable coil 136.

[0032] Elongate stimulating assembly 126 is configured to be at least partially implanted in the recipient’s cochlea 120 and includes a plurality of longitudinally spaced intra-cochlear electrical stimulating contacts (electrodes) 138 that collectively form a contact array 140 for delivery of electrical stimulation (current signals) to the recipient’s cochlea. In certain arrangements, the contact array 140 can include other types of stimulating contacts, such as optical stimulating contacts, in addition to the electrodes 138.

[0033] Stimulating assembly 126 extends through an opening 121 in the cochlea (e.g., cochleostomy, the round window, etc.) and has a proximal end connected to stimulator unit 132 via lead region 124 and a hermetic feedthrough (not shown in FIG. IB). Lead region 124 includes a plurality of conductors (wires) that electrically couple the electrodes 138 to the stimulator unit 132.Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1

[0034] Returning to external component 102, the sound input device(s) 108 are configured to detect / receive sound signals and to generate electrical output signals therefrom. The sound processor 112 is configured to execute sound processing that converts the output signals received from the sound input device(s) into coded data signals that represent acoustical and / or electrical stimulation for delivery to the recipient. That is, as noted, the electro-acoustic hearing device 100 operates to evoke perception by the recipient of sound signals received by the sound input device(s) 108 through the delivery of one or both of electrical stimulation signals and acoustic stimulation signals to the recipient. As such, depending on the current operational settings (sometimes referred to as an operational “map”), the sound processor 112 is configured to convert the output signals received from the sound input device(s) into a first set of output signals representative of electrical stimulation and / or into a second set of output signals representative of acoustic stimulation. The output signals representative of electrical stimulation are represented in FIG. IB by arrow 115, while the output signals representative of acoustic stimulation are represented in FIG. IB by arrow 117.

[0035] The output signals 115 are provided to the transceiver 114. The transceiver 114 is configured to transcutaneously transfer the output signals 115, in an encoded manner, to the implantable component 104 via external coil 106. More specifically, the magnets fixed relative to the external coil 106 and the implantable coil 136 facilitate the operational alignment of the external coil 106 with the implantable coil 136. This operational alignment of the coils enables the external coil 106 to transmit the output signals 115, as well as power signals received from power source 116, to the implantable coil 136. In certain examples, external coil 106 transmits the encoded output signals 115 to implantable coil 136 via a radio frequency (RF) link. However, various other types of energy transfer, such as infrared (IR), electromagnetic, capacitive and inductive transfer, can be used to transfer the power and / or data from an external component to an electro-acoustic hearing device and, as such, FIG. IB illustrates only one example arrangement.

[0036] In general, the encoded output signals 115 are received at the transceiver 130 and provided to the stimulator unit 132. The stimulator unit 132 is configured to utilize the output signals 115 to generate electrical stimulation (e.g., current signals) for delivery to the recipient’s cochlea via one or more stimulating contacts 138. In this way, electro-acoustic hearing device 100 electrically stimulates the recipient’s auditory nerve cells, bypassing absent or defective hair cells that normally transduce acoustic vibrations into neural activity, in aAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1manner that causes the recipient to perceive one or more components of the received sound signals.

[0037] Also shown in FIG. IB, the sound processing unit 110 also comprises a signal adjustment module 131 and a user input module 135. Each of the sound processor 112, signal adjustment module 131, and the user input module 135 can be formed by one or more processors (e.g., one or more Digital Signal Processors (DSPs), one or more uC cores, etc.), firmware, software, etc. arranged to perform operations described herein. That is, the sound processor 112, signal adjustment module 131, and the user input module 135 can each be implemented as firmware elements, partially or fully implemented with digital logic gates in one or more application-specific integrated circuits (ASICs), partially or fully in software, etc. Although FIG. IB illustrates the sound processor 112, signal adjustment module 131, and the user input module 135 as being implemented / performed at the sound processing unit 110, it is to be appreciated that these elements (e.g., functional operations) could also or alternatively be implemented / performed as part of the implantable component 104, as part of the external device 111, etc.

[0038] FIGs. 1 A and IB illustrate an arrangement in which the electro-acoustic hearing device 100 includes an external component 102. However, it is to be appreciated that embodiments of the present invention can be implemented in auditory prostheses having alternative arrangements. For example, embodiments of the present invention can be implemented in a totally implantable auditory prosthesis. A totally implantable auditory prosthesis is an auditory prosthesis in which all components are configured to be implanted under skin / tissue of a recipient. Because all components are implantable, a totally implantable auditory prosthesis is configured to operate, for at least a finite period of time, without the need of an external device. However, an external device can be used to, for example, charge an internal power source (battery) of a totally implantable auditory prosthesis.

[0039] It is also to be appreciated that aspects of techniques presented herein could be implemented in a device comprising an in-the-ear (ITE) component operating as a hearing aid and an implant operating as a cochlear implant (e.g., mostly implantable cochlear implant). In such examples, two processors are operating and either or both could be adjusted / set based on the techniques presented herein. In particular, there is a processor in the implantable component for use in delivering electrical stimulation and a processor in the ITE component for a for use in delivering acoustic stimulation. A microphone can be provided in the ITE component which sends microphone signals as input to the acoustic stimulation processor (inAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1the ITE component), and as input signals to the electrical stimulation processor (in the implant) via sending a wireless data to the implant.

[0040] In FIGs. 1A and IB, the cochlear implant system is shown with an external device 111, configured to implement aspects of the techniques presented. The external device 111, which is shown in greater detail in FIG. 1C, is a computing device, such as a personal computer (e.g., laptop, desktop, tablet), a mobile phone (e.g., smartphone), a remote control unit, etc. The external device 111 and the electro-acoustic hearing device (e.g., sound processing unit 110 or the implantable component 104) wirelessly communicate via a bi-directional communication link 127. The bi-directional communication link 127 can comprise, for example, a short-range communication, such as Bluetooth link, Bluetooth Low Energy (BLE) link, a proprietary link, etc.

[0041] FIG. 1C is a block diagram illustrating one example arrangement for an external computing device 111 configured to perform one or more operations in accordance with certain embodiments presented herein. As shown in FIG. 1C, in its most basic configuration, the external computing device 111 includes at least one processing unit 183 and a memory 184. The processing unit 183 includes one or more hardware or software processors (e.g., Central Processing Units) that can obtain and execute instructions. The processing unit 183 can communicate with and control the performance of other components of the external computing device 111. The memory 184 is one or more software or hardware-based computer-readable storage media operable to store information accessible by the processing unit 183. The memory 184 can store, among other things, instructions executable by the processing unit 183 to implement applications or cause performance of operations described herein, as well as other data. The memory 184 can be volatile memory (e.g., RAM), non-volatile memory (e.g., ROM), or combinations thereof. The memory 184 can include transitory memory or non-transitory memory. The memory 184 can also include one or more removable or non-removable storage devices. In examples, the memory 184 can include RAM, ROM) EEPROM (Electronically-Erasable Programmable Read-Only Memory), flash memory, optical disc storage, magnetic storage, solid state storage, or any other memory media usable to store information for later access. By way of example, and not limitation, the memory 184 can include wired media, such as a wired network or direct-wired connection, and wireless media, such as acoustic, RF, infrared, other wireless media, or combinations thereof. In certain embodiments, the memory 184 comprises logic 195 that, when executed, enables the processing unit 183 to perform aspects of the techniques presented.Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1

[0042] In the illustrated example of FIG. 1C, the external computing device 111 further includes a network adapter 186, one or more input devices 187, and one or more output devices 188. The external computing device 111 can include other components, such as a system bus, component interfaces, a graphics system, a power source (e.g., a battery), among other components. The network adapter 186 is a component of the external computing device 111 that provides network access (e.g., access to at least one network 189). The network adapter 186 can provide wired or wireless network access and can support one or more of a variety of communication technologies and protocols, such as Ethernet, cellular, Bluetooth, near-field communication, and RF, among others. The network adapter 186 can include one or more antennas and associated components configured for wireless communication according to one or more wireless communication technologies and protocols. The one or more input devices 187 are devices over which the external computing device 111 receives input from a user. The one or more input devices 187 can include physically-actuatable user-interface elements (e.g., buttons, switches, or dials), a keypad, keyboard, mouse, touchscreen, and voice input devices, among other input devices that can accept user input. The one or more output devices 188 are devices by which the external computing device 111 is able to provide output to a user. The output devices 188 can include a display 190 (e.g., a liquid crystal display (LCD)) and one or more speakers 191, among other output devices for presentation of visual or audible information to the recipient, a clinician, an audiologist, or other user.

[0043] It is to be appreciated that the arrangement for the external computing device 111 shown in FIG. 1C is merely illustrative and that aspects of the techniques presented herein can be implemented at a number of different types of systems / devices including any combination of hardware, software, and / or firmware configured to perform the functions described herein. For example, the external computing device 111 can be a personal computer (e.g., a desktop or laptop computer), a hand-held device (e.g., a tablet computer), a mobile device (e.g., a smartphone), a surgical system, and / or any other electronic device having the capabilities to perform the associated operations described elsewhere herein.

[0044] As noted, the electro-acoustic hearing device 100 delivers both acoustic stimulation and electrical stimulation to the inner ear. The inner ear is tonotopically mapped in that each region of the inner ear is acoustically responsive to acoustic signals in a respective, particular frequency range. In general, a more basal region (i.e., a region positioned more adjacent to an opening of the inner ear) is more responsive to higher frequency sounds, whereas a more apicalAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1region (i.e., a region positioned farther from the opening of the inner ear) is more responsive to lower frequency sounds.

[0045] In the electro-acoustic hearing device 100, the tonotopic nature of the inner ear is leveraged with a set frequency-to-electrode mapping in which particular electrodes are “associated with” or “mapped to” a specific acoustic frequency (e.g., to mimic natural hearing, it is desirable that, in response to an input pitch, nerve cells that best produce a pitch sensation similar to the input pitch are stimulated). That is, the electro-acoustic hearing device 100 is configured / set such that an electrode that is positioned at a corresponding tonotopic region responsive to a specific acoustic frequency (e.g., a region that would naturally be stimulated via acoustic hearing by that specific acoustic frequency) will deliver stimulation signals that have been generated from input signals at the specific acoustic frequency. Stated differently, specific frequency bands of input signals, such as sounds, are mapped (e.g., during a fitting of the electro-acoustic hearing device 100) to a set of one or more electrodes used to stimulate a selected (target) population of nerve cells to cause the recipient to perceive input of frequencies within the frequency bands. This process (e.g., assigning specific frequency bands of input signals to a set of one or more electrodes) is sometimes generally referred to herein as mapping “stimulation frequencies” or “frequencies” to electrodes or generation of a frequency allocation table (FAT), which in turn is used during operation of the prosthesis to generate / deliver stimulation to the recipient. The FAT can indicate a center frequency, as well as a range indicating other frequencies, such as a high limit frequency and / or a low limit frequency, relative to the center frequencies to be associated with the electrodes. Collectively, the frequency bands and associated electrodes form a stimulation channel that delivers stimulation signals at a wide range of frequencies to the recipient.

[0046] In certain conventional arrangements, the electro-acoustic fitting methodology provides a complete overlap of acoustic and electrical stimulation, even though user with some residual hearing may not be able to hear sounds at certain frequencies (e.g., higher frequencies) and only can acoustically hear sounds at other frequencies (e.g., lower frequencies). In other words, electrodes are allocated so as to cover the entire range at which stimulation signals could possibly be delivered (i.e., the entire tonotopic area that can be electrically stimulated), meaning a FAT is determined for the recipient so that electrodes are provided over an entire frequency spectrum, but the electrical stimulation provided at the frequency regions where the recipient can hear (e.g., lower frequencies) is minimal. However, despite this allocation, electrical stimulation signals are only delivered via the electrodes in areas where the recipientAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1has low or no residual hearing, while acoustic stimulation is used in the areas where the recipient has residual hearing. As the recipient’s residual hearing declines (which is a normal part of aging) the recipient’s map is adjusted to expand the area of electrical stimulation. In other words, the electrical stimulation to the electrodes in the areas where the recipient’s residual hearing has declined is increased to expand the electro-acoustic stimulation to these areas. To minimize the cognitive adjustment needed when a recipient’s map is adjusted, it would be useful if the frequency buckets assigned to electrical channels matched up with the acoustic frequency for that position on the cochlea.

[0047] Unfortunately, it can be difficult to provide desirable frequency-to-electrode mapping in a manner that effectively enables the recipient to perceive a hearing percept, such as by mimicking natural hearing. For instance, various factors, including anatomy-based factors (e.g., different cochlea have differently sized tonotopic regions), psychophysically-based factors (e.g., different recipients prefer to perceive different hearing frequencies), and / or electrophysiologically-based factors (e.g., different recipients have different levels of cochlea functionality), can affect a recipient’s perception of sound in response to a certain frequency-to-electrode mapping. Indeed, the frequency-to-electrode mapping for one recipient may not be suitable (e.g., may not enable a desirable hearing percept) for another recipient.

[0048] Techniques described herein provide for using responses / inputs from a recipient of a recipient device, such as electro-acoustic hearing device 100, with respect to electrical stimulation signals and acoustic stimulation signals in order to map stimulation frequencies to electrodes (e.g., to generate a FAT). According to certain embodiments, the electro-acoustic hearing device 100 provides stimulation via an electrode of the prosthesis while contemporaneously delivering a monotonic acoustic signal (acoustic tone). For example, the electrodes 138 of electro-acoustic hearing device 100 are mapped to stimulating / stimulation frequencies such that the electrodes activate according to the mapped stimulation frequency to electrically stimulate a recipient and enable the recipient to perceive a corresponding sound.

[0049] In one embodiment, the recipient can adjust one or more parameters (e.g., the pitch) of the acoustic tone (e.g., up or down) until the acoustic tone is perceived, by recipient, to be similar to the percept evoked by the electrical stimulation. That is, the recipient adjusts one or more parameters of acoustic tone until the acoustic tone and the electrical stimulation “sound” the same to the recipient. In another embodiment, the recipient can adjust the volume of the electrical stimulation signal (e.g., to ensure it is in a comfortable range) and / or the acoustic stimulation signal to determine a match of the decibel gain required on the acoustic signal toAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1match the loudness percept of the electrical signal. According to some embodiments, the recipient can use an application on a computing device (e.g., on a user device or smartphone) to cause the speech processor to provide the signals and adjust parameters associated with the signals.

[0050] As noted, according to certain techniques described herein, the recipient adjusts the pitch of the acoustic signal relative to an electrical stimulation delivered via one electrode. Once the pitch match is determined for that one electrode, the recipient can proceed to perform the same process for one or more other electrodes in cochlear positions in which the recipient has residual hearing. When a useful number of electrode measurements are recorded, the measurements are used to determine stimulation parameters, such as the frequency allocation table, for use in the electro-acoustic hearing device 100. In this way, the user’s input can be used to determine more accurate frequency mappings for the electrodes of the electro-acoustic hearing device 100.

[0051] As described above, the positions of the electrodes in the cochlea are recognized by a recipient’s brain as having a certain frequency. The electrodes are placed in the cochlea during a surgical procedure and the placement of each electrode is as close as possible to being ideal for a particular frequency range. However, due to a number of factors, the placement of each electrode might not be ideal for each electrode and for each recipient. Techniques described herein provide for mapping frequencies for electrodes based on receiving inputs from a user with residual hearing. According to some embodiments, an electrode of a hearing device is stimulated using a stimulation signal while an acoustic signal is simultaneously provided to the recipient’ s cochlea. A pitch of the acoustic signal is determined based on a position or assumed frequency range associated with the electrode. The user provides an input that indicates, for example, whether a pitch of the acoustic signal matches a perceived pitch of the stimulation signal. The recipient provides the input using an application on a user computing device, such as a smartphone. When the pitches of the signals do not match, the recipient modifies a relational parameter between the signals (e.g., changes a pitch of the acoustic signal) using the application and the signals are provided to the cochlea again.

[0052] The user continues to modify the pitch of the acoustic signal until the pitch of the acoustic signal matches a perceived pitch of the stimulation signal applied to the electrode. The data associated with the signals is used to map stimulation frequencies to the electrode. When the frequencies are mapped to electrodes in the cochlea in positions where the recipient has residual hearing, a frequency mapping is determined that can be expanded over time. InAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1this way, the electrodes are aligned with the correct frequency ranges prior to fitting a hearing device for a user. This reduces the relearning process for the recipient when the electrical stimulation is increased (e.g., as the recipient’s acoustic hearing decreases) and provides optimal stimulation hearing for the recipient.

[0053] For ease of description, the techniques presented herein are primarily described herein with reference to determining frequency allocation tables (FATs) for hearing devices. However, it is to be appreciated that reference to FATs is merely illustrative and that the techniques presented herein could be used to determine / set other stimulation parameters of a medical device.

[0054] Reference is now made to FIG. 2, which is a flow chart illustrating a method 200 of determining frequency mappings for electrodes using input from a recipient of a hearing device. In the example illustrated in FIG. 2, the hearing device is an electro-acoustic hearing device (e.g., electro-acoustic hearing device 100) that provides both acoustic signals and electrical stimulation signals to a recipient that has residual hearing in the ear where the hearing device is located.

[0055] At 202, a monotonic acoustic signal (e.g., a tone) is provided to the recipient while an electrical stimulation signal is contemporaneously (e.g., simultaneously) provided to an electrode of the hearing device. Similar to the acoustic signal, the electrical stimulation signal is configured to induce perception of a tone. In some embodiments, a pitch of the acoustic signal provided to the recipient is based on a position in the cochlea of the electrode receiving the stimulation signal. As discussed above, an electrode that is positioned at a corresponding tonotopic region in the cochlea is responsive to a specific acoustic frequency. The pitch of the monotonic acoustic signal is estimated to correspond to the acoustic frequency of the position of the electrode that is receiving the stimulation signal. In other words, the tone of the acoustic signal is determined to be similar to or the same as the tone percept induced by the stimulation signal at the electrode.

[0056] In one embodiment, the recipient uses an application on a computing device to initiate delivery of the acoustic signal and the electrical stimulation signal. For example, the recipient provides inputs on a display screen of the computing device to provide the signals. FIG. 3 illustrates an exemplary user interface 300 of an application used to match electrodes to stimulation frequency ranges. In this example, user interface 300 is used to determine the frequency range for electrode 05 in the cochlea. In some embodiments, the application isAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1programmed to perform testing for electrodes in regions where the recipient has residual hearing.

[0057] As illustrated in FIG. 3, user interface 300 includes a “Beep On / Off ’ option 302 that starts or stops the electrical stimulation signal to electrode 05 and a “Tone On / Off’ option 306 that turns on or off the acoustic signal / tone. In some embodiments, user interface 300 includes an option to turn on / off both the acoustic and stimulation signals simultaneously.

[0058] Returning to FIG. 2, at 204, it is determined whether the acoustic signal and the electrical stimulation signal are perceived to have the same pitch (i.e., sound the same to the recipient). In other words, the recipient provides feedback indicating whether the stimulation to the electrode provides a sound that is perceived as the same sound as the acoustic signal / tone that is provided to the cochlea. When the signals are perceived as sounding the same, a frequency range associated with the electrode can be determined. As described further below, the recipient can indicate that the signals sound the same by, for example, selecting the “Next Electrode” option 312 or the “Submit Results” option 314 on user interface 300 illustrated in FIG. 3.

[0059] If the signals do not sound the same, at 206, the recipient adjusts attributes / properties associated with one or both of the signals. In other words, the recipient adjusts at least one relational parameter between the acoustic signal and the electrical stimulation signal. In one embodiment, the recipient adjusts the pitch of the acoustic tone up or down until the acoustic tone sounds the same as the electrical stimulation for the electrode is perceived. For example, by selecting the up or down selection associated with the “Tone Pitch” option 310 on user interface 300 of FIG. 3, the recipient adjusts the pitch of the tone up or down to try to match the perceived pitch of the electrical stimulation signal for the electrode.

[0060] In some embodiments, the recipient adjusts the volume of the electrical stimulation signal (e.g., to ensure the volume is in a comfortable range) and the acoustic signal to determine a match of the decibel gain required on the acoustic signal to match the loudness percept of the electrical signal. The “Beep Volume” option 304 on user interface 300 allows the recipient to adjust the volume percept of the electrical stimulation signal up or down and the “Tone Volume” option 308 allows the user to adjust the volume of the acoustic signal up or down.

[0061] After the relational parameter between the acoustic signal and the electrical stimulation signal is adjusted, processing returns to 202 where the signals are simultaneously provided. For example, if the recipient adjusted a pitch of the acoustic signal, the acoustic signal with theAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1adjusted pitch is provided to the recipient while the electrical stimulation is simultaneously provided to the electrode (e.g., electrode 05). The process of adjusting properties of the signal or signals is repeated until the perceived pitch of the electrical stimulation is the same as the pitch of the acoustic signal.

[0062] At 204, if the signals sound the same, at 208, it is determined whether there are more electrodes to test. In other words, it is determined whether the recipient has provided feedback for all or a target number of electrodes in regions where the recipient has residual hearing. If there are more electrodes to test, the recipient selects the “Next Electrode” option 312 on user interface 300 and, at 210, a new electrode is identified. A new user interface 300 is provided to the recipient fortesting another electrode (e.g., electrode 06). The user performs the process described above (e.g., adjusting the tone of the acoustic signal) for the next electrode until the pitch of the acoustic signal matches the pitch percept of the electrical stimulation signal at the next electrode.

[0063] If there are no more electrodes to test, at 212, a frequency allocation table for the electrodes of the hearing device is determined. In some embodiments, if there are no more electrodes to test, the recipient is prevented from selecting the “Next Electrode” option 312 on user interface 300 (e.g., the “Next Electrode” option 312 is greyed and cannot be selected). If there are no more electrodes to test, the user selects the “Submit Results” option 314 on user interface 300 and the results are forwarded to a clinician to be used to inform the frequency allocation table for new maps for the hearing device. In some embodiments, the results can be submitted when a “useful” number of electrode measurements are recorded. For example, the frequency allocation table can be determined for the hearing device even if all of the electrodes in positions where the recipient has residual hearing have not been tested. In this case, enough electrodes are tested so that corresponding frequency ranges for the electrodes that have not been tested can be extrapolated. For example, if enough electrodes at fixed points have been evaluated, an algorithm can be used to determine the frequency ranges of the electrodes in positions that have not been tested.

[0064] When the frequency allocation table is determined, the frequency allocation table is instantiated in the hearing device. Subsequent electrical stimulation signals are delivered to the recipient of the hearing device in accordance with the frequency allocation table. Because the frequencies have been mapped for the electrodes based on the recipient’s input, when the recipient’s hearing deteriorates and the recipient’s electro-acoustic map is changed to increase the electrical stimulation for electrodes in areas where the recipient previously had residualAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1hearing, the relearning process is easier for the recipient. In other words, the positions of the electrodes are aligned to the optimal frequency ranges for the recipient prior to doing a fitting with a new map, which makes adjustment for the recipient easier than if the positions of the electrodes were not properly aligned.

[0065] Although the examples described in FIGs. 2 and 3 have illustrated determining a frequency allocation table for a hearing device, a similar process could be performed for other medical devices. For example, other parameters (e.g., wavelengths) of other types of signals (e.g., photons entering the eye) could be adjusted to match stimulation signals provided to other types of medical device. In addition, acoustic signals could be adjusted based on electrical stimulation signals for other types of medical devices, such tinnitus therapy devices.

[0066] Reference is now made to FIG. 4, which is a flow chart of a method 400 of determining a frequency allocation table for a hearing device based on at least one input from a recipient of the hearing device.

[0067] At 402, an acoustic signal is delivered to a recipient of a hearing device. At 404, contemporaneously with delivering the acoustic signal, an electrical stimulation signal is delivered to the recipient. For example, an electrical stimulation signal is delivered to an electrode of the hearing device at the same time as the acoustic signal / tone is delivered to the recipient. The hearing device is an electro-acoustic hearing device and the recipient has residual hearing in the earthat has the hearing device.

[0068] At 406, at least one input is received at a computing device from the recipient. The at least one input adjusts at least one relational parameter between the acoustic signal and the electrical stimulation signal. For example, the recipient provides an input on an application stored on the computing device to adjust a parameter or parameters associated with the acoustic signal and / or the electrical stimulation signal. The parameters can include, for example, the pitch of the acoustic signal, the volume of the acoustic signal, the volume of the electrical stimulation signal, etc. For example, the recipient can adjust the pitch of the acoustic signal up or down until the pitch of the acoustic signal matches a perceived pitch of the electrical stimulation signal.

[0069] At 408, a frequency allocation table is determined, using at least one processor, for the hearing device based on the at least one input. For example, properties associated with the acoustic signal are used to determine a frequency allocation table for the electrodes of the hearing device.Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1

[0070] Reference is now made to FIG. 5, which is a flow chart of a method 500 of programming a medical device with stimulation frequencies based on subjective feedback from a recipient of the medical device.

[0071] At 502, a first type of stimulation and a second type of stimulation are contemporaneously delivered to a recipient of the medical device. At 504, following the delivering, subjective feedback is received from the recipient indicating a frequency relationship between the first type of stimulation and the second type of stimulation. At 506, the medical device is programmed with stimulation frequencies based on the subjective feedback.

[0072] As previously described, the technology disclosed herein can be applied in any of a variety of circumstances and with a variety of different devices. Example devices that can benefit from technology disclosed herein are described in more detail in FIGs. 6-9 for a vestibular stimulator system, a retinal prosthesis system, a tinnitus therapy device, and an upper airway stimulation device, respectively. However, the techniques of the present disclosure can be applied to other devices, such as neurostimulators, cardiac pacemakers, cardiac defibrillators, seizure therapy stimulators, as well as other medical devices that deliver stimulation to tissue. Further, technology described herein can also be applied to consumer devices. These different systems and devices can benefit from the technology described herein.

[0073] FIG. 6 illustrates an example vestibular stimulator system 602, with which embodiments presented herein can be implemented. As shown, the vestibular stimulator system 602 comprises an implantable component (vestibular stimulator) 612 and an external device / component 604 (e.g., external processing device, battery charger, remote control, etc.). The external device 604 comprises a transceiver unit 660. As such, the external device 604 is configured to transfer data (and potentially power) to the vestibular stimulator 612.

[0074] The vestibular stimulator 612 comprises an implant body (main module) 634, a lead region 636, and a stimulating assembly 616, all configured to be implanted under the skin / tissue (tissue) 615 of the recipient. The implant body 634 generally comprises a hermetically-sealed housing 638 in which RF interface circuitry, one or more rechargeable batteries, one or more processors, and a stimulator unit are disposed. The implant body 634 also includes an intemal / implantable coil 614 that is generally external to the housing 638, but which is connected to the transceiver via a hermetic feedthrough (not shown).Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1

[0075] The stimulating assembly 616 comprises a plurality of electrodes 644(l)-(3) disposed in a carrier member (e.g., a flexible silicone body). In this specific example, the stimulating assembly 616 comprises three (3) stimulation electrodes, referred to as stimulation electrodes 644(1), 644(2), and 644(3). The stimulation electrodes 644(1), 644(2), and 644(3) function as an electrical interface for delivery of electrical stimulation signals to the recipient’s vestibular system.

[0076] The stimulating assembly 616 is configured such that a surgeon can implant the stimulating assembly adjacent the recipient’s otolith organs via, for example, the recipient’s oval window. It is to be appreciated that this specific embodiment with three stimulation electrodes is merely illustrative and that the techniques presented herein can be used with stimulating assemblies having different numbers of stimulation electrodes, stimulating assemblies having different lengths, etc.

[0077] It is to be appreciated that the vestibular stimulator 612 can be configured in accordance with the techniques presented herein. For example, the techniques described with can be used to allocate / map frequency ranges or stimulation areas to electrodes 644(l)-(3).

[0078] FIG. 7 illustrates a retinal prosthesis system 701 that comprises an external device 710 configured to communicate with an implantable retinal prosthesis 700 via signals 751. The retinal prosthesis 700 comprises an implanted processing module 725, and a retinal prosthesis sensor-stimulator 790 is positioned proximate the retina of a recipient. The external device 710 and the processing module 725 can communicate via coils 708, 714.

[0079] In an example, sensory inputs (e.g., photons entering the eye) are absorbed by a microelectronic array of the sensor-stimulator 790 that is hybridized to a glass piece 792 including, for example, an embedded array of microwires. The glass can have a curved surface that conforms to the inner radius of the retina. The sensor-stimulator 790 can include a microelectronic imaging device that can be made of thin silicon containing integrated circuitry that convert the incident photons to an electronic charge.

[0080] The processing module 725 includes an image processor 723 that is in signal communication with the sensor-stimulator 790 via, for example, a lead 788 that extends through surgical incision 789 formed in the eye wall. In other examples, processing module 725 is in wireless communication with the sensor-stimulator 790. The image processor 723 processes the input into the sensor-stimulator 790 and provides control signals back to the sensor-stimulator 790 so the device can provide an output to the optic nerve. That said, in anAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1alternate example, the processing is executed by a component proximate to, or integrated with, the sensor-stimulator 790. The electric charge resulting from the conversion of the incident photons is converted to a proportional amount of electronic current which is input to a nearby retinal cell layer. The cells fire and a signal is sent to the optic nerve, thus inducing a sight perception.

[0081] The processing module 725 can be implanted in the recipient and function by communicating with the external device 710, such as a BTE unit, a pair of eyeglasses, etc . The external device 710 can include an external light / image capture device (e.g., located in / on a behind-the-ear device or a pair of glasses, etc.), while, as noted above, in some examples, the sensor-stimulator 790 captures light / images, in which sensor-stimulator 790 is implanted in the recipient.

[0082] It is to be appreciated that the retinal prosthesis system 701 can be configured in accordance with the techniques presented herein. For example, the techniques described with can be used to allocate / map frequency ranges or stimulation areas to the sensor-stimulator 790.

[0083] FIG. 8 illustrates a tinnitus therapy device 800 (e.g., a tinnitus implant, a tinnitus management stimulator) including a sound input unit 802 (e.g., a microphone) configured to receive acoustic inputs. In some embodiments, the sound input unit 802 is implanted adjacent to an outer ear 803 to position a diaphragm 816 of the sound input unit 802 such that the diaphragm 816 is configured to be displaced (vibrate) in response to the acoustic inputs. The tinnitus therapy device 800 further includes an implant body 804 in which circuitry, such as a processor and / or a memory, is disposed. The implant body 804 is also coupled to a coil 808 to enable transfer of power / data between the tinnitus therapy device 800 and an external device. The implant body 804 is electrically coupled to the sound input unit 802 to receive the acoustic input. The tinnitus therapy device 800 is then configured to convert the acoustic input to tinnitus therapy control signals (e.g., based on a classification of the acoustic input).

[0084] The tinnitus therapy control signals are provided to an actuator 806 electrically coupled to the implant body 804 for delivery to the recipient. By way of example, a coupling member 840 couples the actuator 806 to an ossicular chain 836 (i.e., the malleus, the incus, and the stapes bones) positioned in a middle ear cavity between a tympanic membrane 813 and a cochlea 838 of the recipient, and the actuator 806 is configured to deliver the tinnitus therapy control signals. The actuator 806 is attached to a temporal bone 815 of the recipient via a fixation system 842 and is configured to impart motion to (e.g., vibrate) the ossicular chainAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1836, which is typically configured to amplify sound waves received via an ear canal 811. In operation, the actuator 806 is configured to impart motion based on the tinnitus therapy control signals, and such vibration creates waves of fluid motion of perilymph within the cochlea 838 to activate hair cells within the cochlea 838. Activation of the hair cells causes nerve impulses to be generated and transferred through spiral ganglion cells, an auditory nerve, and a brain, where the vibration is perceived as sounds to provide relief of tinnitus symptoms experienced by the recipient.

[0085] The tinnitus therapy device 800 can be configured in accordance with the techniques presented herein. For example, parameters can be determined for the therapy control signals provided to the actuator 806 based on user feedback associated with the acoustic input using the techniques presented herein.

[0086] FIG. 9 illustrates an upper airway stimulation device 900 (e.g., an upper airway implant, a sleep apnea management stimulator, a sleep disorder system) that includes an implant body 902, a sensor 904, and a stimulator 906. The upper airway stimulation device 900 is implantable in a recipient 908 to position the sensor 904 adjacent to lungs 910 of the recipient 908. Thus, the sensor 904 is able to receive input that indicates breathing performed by the recipient 908. The implant body 902 includes a housing in which circuitry, such as a processor and / or a memory, is disposed. The sensor 904 transmits electrical signals in response to receipt of the input, and the upper airway stimulation device 900 is configured to convert the electrical signals to stimulation signals, which are provided to the stimulator 906. The stimulator 906 is positioned adjacent to a hypoglossal nerve 912 of the recipient 908 and is configured to deliver the stimulation signals to the hypoglossal nerve 912, which fires nerve cells of a tongue of the recipient 908, thereby causing the tongue to contract and move (e.g., in an anterior direction) and increase a size of an opening of an airway of the recipient 908. Consequently, the upper airway stimulation device 900 generates stimulation signals based on the input to help the recipient 908 breathe more easily (e.g., while the recipient 908 is asleep to mitigate sleep apnea).

[0087] The upper airway stimulation device 900 can be configured in accordance with the techniques presented herein. For example, parameters can be determined for the electrical signals provided to the stimulator 906 based on user feedback associated with the input using the techniques presented herein.Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1

[0088] The above embodiments have been primarily described with reference to use of the techniques presented herein during implantation of a specific implantable component, namely a cochlear implant stimulating assembly. However, as described above with reference to FIGs.6, 7, 8, and 9, the techniques presented herein can be used to determine parameters associated with stimulation devices for implantation of a variety of implantable components, including sleep disorder devices (e.g., sleep apnea devices), balance or movement disorder devices (e.g., vestibular stimulation devices), tinnitus management devices, visual implants (e.g., bionic eyes), and other neuromodulation devices (e.g., brain-computer interfaces).

[0089] As should be appreciated, while particular uses of the technology have been illustrated and discussed above, the disclosed technology can be used with a variety of devices in accordance with many examples of the technology. The above discussion is not meant to suggest that the disclosed technology is only suitable for implementation within systems akin to that illustrated in the figures. In general, additional configurations can be used to practice the processes and systems herein and / or some aspects described can be excluded without departing from the processes and systems disclosed herein.

[0090] This disclosure described some aspects of the present technology with reference to the accompanying drawings, in which only some of the possible aspects were shown. Other aspects can, however, be embodied in many different forms and should not be construed as limited to the aspects set forth herein. Rather, these aspects were provided so that this disclosure was thorough and complete and fully conveyed the scope of the possible aspects to those skilled in the art.

[0091] As should be appreciated, the various aspects (e.g., portions, components, etc.) described with respect to the figures herein are not intended to limit the systems and processes to the particular aspects described. Accordingly, additional configurations can be used to practice the methods and systems herein and / or some aspects described can be excluded without departing from the methods and systems disclosed herein.

[0092] According to certain aspects, systems and non-transitory computer readable storage media are provided. The systems are configured with hardware configured to execute operations analogous to the methods of the present disclosure. The one or more non-transitory computer readable storage media comprise instructions that, when executed by one or more processors, cause the one or more processors to execute operations analogous to the methods of the present disclosure.Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1

[0093] Similarly, where steps of a process are disclosed, those steps are described for purposes of illustrating the present methods and systems and are not intended to limit the disclosure to a particular sequence of steps. For example, the steps can be performed in differing order, two or more steps can be performed concurrently, additional steps can be performed, and disclosed steps can be excluded without departing from the present disclosure. Further, the disclosed processes can be repeated.

[0094] Although specific aspects were described herein, the scope of the technology is not limited to those specific aspects. One skilled in the art will recognize other aspects or improvements that are within the scope of the present technology. Therefore, the specific structure, acts, or media are disclosed only as illustrative aspects. The scope of the technology is defined by the following claims and any equivalents therein.

[0095] It is also to be appreciated that the embodiments presented herein are not mutually exclusive and that the various embodiments can be combined with another in any of a number of different manners.

Claims

Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1CLAIMSWhat is claimed is:

1. A method comprising :delivering an acoustic signal to a recipient of a medical device; contemporaneously with delivering of the acoustic signal, delivering an electrical stimulation signal to the recipient;receiving, at a computing device, at least one input from the recipient, wherein the at least one input adjusts at least one relational parameter between the acoustic signal and the electrical stimulation signal; anddetermining, with at least one processor, a frequency allocation table for the medical device based on the at least one input from the recipient.

2. The method of claim 1, further comprising:instantiating the frequency allocation table in the medical device; anddelivering subsequent electrical stimulation signals to the recipient in accordance with the frequency allocation table.

3. The method of claim 1, wherein the medical device includes a plurality of electrodes implanted in an inner ear of the recipient, and wherein the method further comprises:delivering the electrical stimulation signal via a first one of the plurality of electrodes located at a first tonotopic location of the inner ear; anddelivering the acoustic signal as atone that is estimated to correspond to a frequency of the first tonotopic location.

4. The method of claim 3, further comprising:delivering a second electrical stimulation signal via a second one of the plurality of electrodes located at a second tonotopic location of the inner ear;contemporaneously with delivering of the second electrical stimulation signal, delivering a second acoustic signal as a tone that is estimated to correspond to a frequency of the second tonotopic location;receiving, at the computing device, at least one second input from the recipient, wherein the at least one second input adjusts at least one relational parameter between the second acoustic signal and the second electrical stimulation signal; andAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1determining, with at least one processor, the frequency allocation table for the medical device based on the at least one input from the recipient and the at least one second input from the recipient.

5. The method of claim 1, 2, 3, or 4, wherein receiving the at least one input comprises:receiving one or more inputs that adjusts a perceived pitch of the acoustic signal.

6. The method of claim 5, further comprising:delivering a subsequent acoustic signal to the recipient of the medical device, wherein a pitch of the subsequent acoustic signal is set based on the at least one input;contemporaneously with delivering of the subsequent acoustic signal, delivering the electrical stimulation signal to the recipient; andreceiving a subsequent input that adjust a perceived pitch of the acoustic signal.

7. The method of claim 5, wherein receiving one or more inputs that adjust a pitch of the acoustic signal comprises:receiving inputs until a perceived pitch of the acoustic signal matches a perceived pitch of the electrical stimulation signal.

8. The method of claim 1, 2, 3, or 4, wherein receiving the at least one input comprises:receiving at least one input that adjusts a perceived loudness of the acoustic signal.

9. The method of claim 1, 2, 3, or 4, wherein receiving the at least one input includes:receiving the at least one input at a display screen of the computing device.

10. The method of claim 1, 2, 3, or 4, wherein the medical device is a hearing device.

11. The method of claim 10, wherein the hearing device is an electro-acoustic hearing device.

12. The use of a device according to any of claims 1-9 in a cochlear implant, a sleep disorder device, a seizure device, a balance or movement disorder device, a tinnitus management device, or a visual device.Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC113. A system according to any of claims 1-9, wherein the system is a cochlear implant system, a sleep disorder system, a seizure system, a balance or movement disorder system, a tinnitus management system, or a visual system.

14. A system, comprising:a medical device comprising a stimulator unit and a plurality of electrodes implanted at an inner ear of a recipient;an output device configured to vibrate fluid in the inner ear;one or more processors configured to:control the stimulator unit to deliver an electrical stimulation signal via a first one of the plurality of electrodes located at a first tonotopic region of the inner ear; andcontrol the output device to contemporaneously deliver a second stimulation signal, wherein the second stimulation signal is configured to induce perception of a tone that is estimated to correspond to the first tonotopic region; anda computing device configured to receive at least one input from the recipient, wherein the at least one input indicates a frequency relationship between the electrical stimulation signal and the second stimulation signal,wherein the one or more processors are further configured to program the medical device with stimulation frequencies based on the frequency relationship between the electrical stimulation signal and the second stimulation signal.

15. The system of claim 14, wherein the second stimulation signal is an acoustic signal and wherein when receiving the at least one input from the recipient, the computing device is configured to receive one or more inputs that adjust a perceived pitch of the acoustic signal.

16. The system of claim 15, wherein the one or more processors are further configured to:control the output device to deliver a subsequent acoustic signal to the recipient of the medical device, wherein a pitch of the subsequent acoustic signal is set based on the at least one input; andAtty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1contemporaneously with delivering of the subsequent acoustic signal, control the stimulator unit to deliver the electrical stimulation signal;wherein the computing device is further configured to receive a subsequent input that adjusts a perceived pitch of the acoustic signal.

17. The system of claim 15, wherein, when receiving one or more inputs that adjust a perceived pitch of the acoustic signal, the computing device is further configured to receive inputs until the perceived pitch of the acoustic signal matches a perceived pitch of the electrical stimulation signal.

18. The system of claim 14, 15, 16, or 17, wherein when receiving the at least one input from the recipient, the computing device is configured to receive at least one input that adjusts a perceived loudness of the second stimulation signal.

19. The system of claim 14, 15, 16, or 17, wherein when receiving the at least one input from the recipient, the computing device is configured to receive the at least one input at a display screen of the computing device.

20. The system of claim 14, 15, 16, or 17, wherein the medical device is a hearing device.

21. The system of claim 20, wherein the hearing device is an electro-acoustic hearing device.

22. A method comprising:contemporaneously delivering a first type of stimulation and a second type of stimulation to a recipient of a medical device;following the delivering, receiving subjective feedback from the recipient indicating a relationship between the first type of stimulation and the second type of stimulation; and programing the medical device with stimulation parameters based on the subjective feedback.

23. The method of claim 22, the subjective feedback indicates a frequency relationship between the first type of stimulation and the second type stimulation.Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC124. The method of claim 23, wherein programing the medical device with stimulation parameters based on the subjective feedback comprises:programing the medical device with stimulation frequencies based on the subjective feedback.

25. The method of claim 22, 23, or 24, further comprising:using the subjective feedback to adjust a frequency parameter of the first type of stimulation; andcontemporaneously delivering the first type of stimulation with the adjusted frequency parameter and the second type of stimulation to the recipient.

26. The method of claim 22, 23, or 24, wherein the first type of stimulation or the second type of stimulation is an electrical stimulation signal.

27. The method of claim 22, 23, or 24, wherein the subjective feedback is associated with an adjustment of at least one relational parameter between the first type of stimulation and the second type of stimulation.

28. The method of claim 22, 23, or 24, wherein receiving the subjective feedback includes receiving the subjective feedback on a display screen of a computing device.

29. The use of a device according to any of claims 22-28 in an electro-acoustic hearing device, a cochlear implant, sleep disorder device, a seizure device, a balance or movement disorder device, a tinnitus management device, or a visual device.

30. A system according to any of claims 22-28, wherein the system is an electro-acoustic hearing device system, a cochlear implant system, a sleep disorder system, a seizure system, a balance or movement disorder system, a tinnitus management system, or a visual system.

31. One or more non-transitory computer readable storage media comprising instructions that, when executed by a processor of a medical device, cause the processor to:cause a first type of stimulation signal to be delivered to a recipient of the medical device;contemporaneously with delivery of the first type of stimulation signal, cause a second type of stimulation signal to be delivered to the recipient;Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1obtain at least one input from the recipient, wherein the at least one input characterizes a relationship between the first type of stimulation signal and the second type of stimulation signal; anddetermine one or more stimulation parameters for the medical device using the at least one input.

32. The one or more non-transitory computer readable storage media of claim 31, further comprising instructions that cause the processor to:instantiate the one or more stimulation parameters in the medical device; and delivering subsequent stimulation signals to the recipient in accordance with the one or more stimulation parameters.

33. The one or more non-transitory computer readable storage media of claim 31, wherein the one or more stimulation parameters comprise a frequency allocation table for the medical device.

34. The one or more non-transitory computer readable storage media of claim 31, wherein the at least one input adjusts a relational parameter between the first type of stimulation signal and the second type of stimulation signal stimulation signal.

35. The one or more non-transitory computer readable storage media of claim 34, wherein, when obtaining the at least one input from the recipient, the instructions cause the processor to obtain one or more inputs that adjusts a perceived pitch of at least one of the first type of stimulation signal or the second type of stimulation signal.

36. The one or more non-transitory computer readable storage media of claim 31, wherein first type of stimulation signal is an acoustic signal and the second type of stimulation signal is an electrical stimulation signal.

37. The one or more non-transitory computer readable storage media of claim 36, wherein the instructions cause the processor to:cause a subsequent acoustic signal to be delivered to the recipient of the medical device, wherein a pitch of the subsequent acoustic signal is set based on the at least one input;Atty. Docket No. 3065.0880i Client Ref. No. CID04100WOPC1contemporaneously with delivering of the subsequent acoustic signal, cause the electrical stimulation signal to be delivered to the recipient; andobtain a subsequent input that adjust a perceived pitch of the acoustic signal.

38. The one or more non-transitory computer readable storage media of claim 37, wherein, when obtaining the one or more inputs that adjust a pitch of the acoustic signal, the instructions cause the processor to obtain inputs until the perceived pitch of the acoustic signal matches a perceived pitch of the electrical stimulation signal.

39. The one or more non-transitory computer readable storage media of claim 31, 32, 33, 34, 35, 36, 37, or 38, wherein, when obtaining the at least one input from the recipient, the instructions cause the processor to obtain at least one input that adjusts a perceived loudness of at least one of the first type of stimulation signal or the second type of stimulation signal.

40. The one or more non-transitory computer readable storage media of claim 31, 32, 33, 34, 35, 36, 37, or 38, wherein the medical device is an electro-acoustic hearing system, a cochlear implant system, a sleep disorder system, a seizure system, a balance or movement disorder system, a tinnitus management system, or a visual system.

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