Individualized ambient environment monitoring

Abstract

Presented herein are techniques for intelligent monitoring of an ambient environment during a sensory device test using individualized / personalized monitoring parameters (e.g., individualized maximum background sound levels). For example, during the sensory device test, the ambient environment of the recipient is monitored and evaluated relative to one or more individualized monitoring parameters that are adjusted / set based on, for example, attributes of the test being performed, attributes of the sensory device recipient, and / or attributes of the sensory device.

Description

Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1INDIVIDUALIZED AMBIENT ENVIRONMENT MONITORINGBACKGROUNDField of the Invention[ooot] The present invention relates generally to individualized monitoring of an ambient environment of a recipient during a sensory device test.Related Art

[0002] Medical devices have provided a wide range of therapeutic benefits to recipients over recent decades. Medical devices can include internal or implantable components / devices, external or wearable components / devices, or combinations thereof (e.g., a device having an external component communicating with an implantable component). Medical devices, such as traditional hearing aids, partially or fully-implantable hearing prostheses (e.g., bone conduction devices, mechanical stimulators, cochlear implants, etc.), pacemakers, defibrillators, functional electrical stimulation devices, and other medical devices have been successful in performing lifesaving and / or lifestyle enhancement functions and / or recipient monitoring for a number of years.

[0003] The types of medical devices and the ranges of functions performed thereby have increased over the years. For example, many medical devices, sometimes referred to as “implantable medical devices,” now often include one or more instruments, apparatus, sensors, processors, controllers or other functional mechanical or electrical components that are permanently or temporarily implanted in a recipient. These functional devices are typically used to diagnose, prevent, monitor, treat, or manage a disease / injury or symptom thereof, or to investigate, replace or modify the anatomy or a physiological process. Many of these functional devices utilize power and / or data received from external devices that are part of, or operate in conjunction with, implantable components.SUMMARY

[0004] In one aspect, a method is provided. The method comprises: determining at least one threshold sound level for an environment based on a type of test being performed in the environment and information associated with a recipient of the test; while the test is being conducted, determining whether a sound level for the environment exceeds the at least one threshold sound level; and performing one or more actions based on determining whether the sound level for the environment exceeds the at least one threshold sound level.Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1

[0005] In another aspect, a system is provided. The system comprises: at least one microphone configured to capture sound signals from an ambient environment of the recipient during a hearing device test associated with a recipient of a hearing device; and at least one processor configured to : during the hearing device test, monitor the ambient environment using a plurality individualized per-frequency background sound limits; and initiate a corrective action when a sound level in the ambient environment exceeds at least one of the plurality of individualized per-frequency background sound limits.

[0006] In another aspect, another method is provided. The method comprises: during a sensory device test associated with a recipient of a sensory device, monitoring an ambient environment of the recipient based on a plurality of individualized background ambient limits; and initiating a corrective action when the at least one ambient level in the ambient environment exceeds at least one of the plurality of individualized per-frequency background sound limits.

[0007] In yet another aspect, one or more non-transitory computer readable storage media are provided that include instructions that, when executed by a processor, cause the processor to: monitor at least one noise level associated with an ambient sound environment during a hearing device test associated with a recipient of a hearing device; and initiate a corrective action when the at least one noise level exceeds at least one predetermined threshold level, wherein the at least one predetermined threshold level is set based a hearing capability of the recipient.BRIEF 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 a cochlear implant system with which aspects of the techniques presented herein can be implemented;[ooto] FIG. IB is a side view of a recipient wearing a sound processing unit of the cochlear implant system of FIG. 1A;[ooit] FIG. 1C is a schematic view of components of the cochlear implant system of FIG. 1 A;

[0012] FIG. ID is a block diagram of the cochlear implant system of FIG. 1A;

[0013] FIG. IE is a schematic diagram illustrating a computing device with which aspects of the techniques presented herein can be implemented;Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1

[0014] FIG. 2 is a flow diagram illustrating a method of determining a maximum level of background or ambient noise for a particular recipient and a particular test, according to some embodiments described herein;

[0015] FIG. 3 is a flow diagram illustrating a method of performing one or more actions based on determining whether results of a hearing device test for a recipient are valid for one or more frequency bands, according to embodiments described herein;

[0016] FIG. 4 is a diagram of an example audiogram for both ears of a recipient of a hearing device with an indication of background sound levels that render particular test results invalid, according to embodiments described herein;

[0017] FIG. 5 is a diagram of another audiogram for the recipient that indicates levels in which results of a different test are invalid, according to embodiments described herein;

[0018] FIG. 6 is a flow diagram of a method of performing one or more actions based on determining whether a noise level for an environment during a hearing device test exceeds at least one threshold noise level, according to embodiments described herein;

[0019] FIG. 7 is a diagram of a method of initiating a corrective action when at least one noise level exceeds at least one predetermined threshold level, according to embodiments described herein;

[0020] FIG. 8 is a perspective view of a tinnitus therapy device with which aspects of the techniques presented herein can be implemented; and

[0021] FIG. 9 is a schematic diagram illustrating a retinal prosthesis system with which aspects of the techniques presented herein can be implemented.DETAILED DESCRIPTION

[0022] Presented herein are techniques for intelligent monitoring of an ambient environment during a sensory device test using individualized / personalized monitoring parameters. For example, during the sensory device test, the ambient environment of the recipient is monitored and evaluated relative to one or more individualized background ambient limits (e.g., individualized per-frequency background sound levels) that are adjusted / set based on, for example, attributes of the test being performed, attributes of the sensory device recipient, and / or attributes of the sensory device. As used herein, the term “sensory device” refers to aAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 hearing device and / or medical device that is configured to worn by, or at least partially implanted in, a recipient, and that provides sensory inputs to the recipient.

[0023] There is an increasing need for “remote” or “self-guided” sensory device tests that can be performed outside of the clinical environment. Remote testing refers to tests that are guided / controlled by a clinician, but where the clinician is not physically present with the recipient (e.g., the recipient is at home and the test is administered via the Internet). Self-guided testing refers to tests administered by the recipient using, for example, a mobile device, computer, etc. Utilizing remote and / or self-guided testing is an effective way to ensure that recipients of sensory devices are experiencing optimal results while reducing clinical bottleneck.

[0024] It is to be appreciated that the techniques presented herein can be implemented with a number of different types of sensory device tests and / or with a number of different types of sensory devices. However, merely for ease of illustration, the techniques are primarily described with reference to the performance of hearing devices and hearing device tests. Hearing device tests can be used to, for example, evaluate the hearing of the recipient, adjust / set parameters of the hearing device, etc.

[0025] Remote or self-guided hearing device testing can take a number of different forms. For example, in certain arrangement, the testing is used to evaluate how well a hearing device is working for the recipient without having to visit a clinic to perform the test. When a remote test, such as an aided audiogram test, Digit Triplet Test (DTT) or another type of streamed performance test, is performed, audio is streamed to a processor of the hearing device and testing is performed using the streamed audio. That is, a recipient of the hearing device can listen for the streamed audio and perform one or more actions (e.g., inputting a word or number heard on a keypad, indicating that a tone has been heard, etc.) based on receiving the streamed audio. However, when the recipient has residual hearing either on an ear with a hearing device or on the opposite ear, ambient background sound (e.g., noise) can interfere with the test results (e.g., mask soft aided audiogram signals or interfere with speech understanding). If the background sound affects the test results, the test results are unreliable.

[0026] A standard solution would be to ensure that the test is administered in a sound treated room, but this defies the idea of remote / self-guided testing and puts a burden on the recipient and the clinic / clinician. Another solution would be to include a level meter in the sound processor of the hearing device that signals when the ambient sound level is too high. However,Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 the threshold acceptable level of the ambient or background sound can vary, for example, based on a type of test being performed, the amount of residual hearing the recipient has, attributes of the hearing device, etc. A recipient with two cochlear implants will have no residual hearing, while recipients of hearing aids (e.g., one or two hearing aids) will have residual hearing. As such, using a level meter to determine when the ambient sound level is too high can be overly cautious because some (or even most) recipients of hearing devices have limited (or no) residual hearing (e.g., in the case of only some cochlear implant recipients). For example, a recipient with no residual hearing can perform a test in a loud environment with no adverse effects, while a recipient with good low frequency residual hearing can require a relatively quiet environment to achieve reliable test results for some tests.

[0027] As such, embodiments described herein monitor the ambient sound (e.g., noise) level during a hearing device test using customized parameters / thresholds. For example, during a hearing device test, the background sound level in the ambient environment of the recipient is monitored and evaluated relative to one or more customized thresholds that are adjusted / set based on, for example, attributes of the hearing device test being performed, attributes of the hearing device recipient, and / or attributes of the hearing device. That is, embodiments described herein perform the monitoring in an intelligent way, specific for each test and each recipient, to ensure that the screening is not ‘too strict’ for a specific recipient while also determining when the test results are unreliable. In addition, if the recipient has a cochlear implant on one ear and a hearing aid on the other ear, the threshold levels for the test may be different depending on whether the hearing aid is on or off. Therefore, the parameters / thresholds for a patient may be customized based on whether the recipient’ s hearing aid is on or off.

[0028] As noted, there are a number of different types of sensory devices in / with which embodiments of the present invention can be implemented. Merely for ease of description, the techniques presented herein are primarily described with reference to a specific sensory device in the form of a cochlear implant system. However, it is to be appreciated that the techniques presented herein can also be partially or fully implemented by any of a number of different types of devices, including wearable devices (e.g., smartwatches), hearing devices, implantable medical devices, etc. As used herein, the term “hearing device” is to be broadly construed as any device that acts on an acoustical 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 ofAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 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 device systems, combinations or variations thereof, etc.), a device for use by a person with normal hearing (e.g., consumer devices that provide audio streaming, consumer headphones, earphones, and other listening devices), a hearing protection device, etc. In other examples, the techniques presented herein can be implemented by, or used in conjunction with, various implantable medical devices, such as visual devices (i.e., bionic eyes), sensors, pacemakers, drug delivery systems, defibrillators, functional electrical stimulation devices, catheters, seizure devices (e.g., devices for monitoring and / or treating epileptic events), sleep apnea devices, electroporation devices, etc.

[0029] FIGs. 1A-1D illustrate an example cochlear implant system 102 with which aspects of the techniques presented herein can be implemented. The cochlear implant system 102 comprises an external component 104 that is configured to be directly or indirectly attached to the body of the user, and an intemal / implantable component 112 that is configured to be implanted in or worn on the head of the user. In the examples of FIGs. 1A-1D, the implantable component 112 is sometimes referred to as a “cochlear implant.” FIG. 1A illustrates the cochlear implant 112 implanted in the head 154 of a user, while FIG. IB is a schematic drawing of the external component 104 worn on the head 154 of the user. FIG. 1C is another schematic view of the cochlear implant system 102, while FIG. ID illustrates further details of the cochlear implant system 102. For ease of description, FIGs. 1A-1D will generally be described together.

[0030] In the examples of FIGs. 1A-1D, the external component 104 comprises a sound processing unit 106, an external coil 108, and generally, a magnet fixed relative to the external coil 108. The cochlear implant 112 includes an implantable coil 114, an implant body 134, and an elongate stimulating assembly 116 configured to be implanted in the user’s cochlea. In one example, the sound processing unit 106 is an off-the-ear (OTE) sound processing unit, sometimes referred to herein as an OTE component, which is configured to send data and power to the implantable component 112. In general, an OTE sound processing unit is a component having a generally cylindrically shaped housing 111 and which is configured to be magnetically coupled to the user’s head 154 (e.g., includes an integrated external magnet 150 configured toAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 be magnetically coupled to an intemal / implantable magnet 152 in the implantable component 112). The OTE sound processing unit 106 also includes an integrated external (headpiece) coil 108 (the external coil 108) that is configured to be inductively coupled to the implantable coil 114.

[0031] It is to be appreciated that the OTE sound processing unit 106 is merely illustrative of the external devices that could operate with implantable component 112. For example, in alternative examples, the external component 104 can comprise a behind-the-ear (BTE) sound processing unit configured to be attached to, and worn adjacent to, the recipient’s ear. A BTE sound processing unit comprises a housing that is shaped to be worn on the outer ear of the user. In certain examples, the BTE is connected to a separate external coil assembly via a cable, where the external coil assembly is configured to be magnetically and inductively coupled to the implantable coil 114, while in other embodiments the BTE includes a coil disposed in or on the housing worn on the outer ear of the user. It is also to be appreciated that alternative external components could be located in the user’s ear canal, worn on the body, etc.

[0032] Although the cochlear implant system 102 includes the sound processing unit 106 and the cochlear implant 112, as described below, the cochlear implant 112 can operate independently from the sound processing unit 106, for at least a period, to stimulate the user. For example, the cochlear implant 112 can operate in a first general mode, sometimes referred to as an “external hearing mode,” in which the sound processing unit 106 captures sound signals which are then used as the basis for delivering stimulation signals to the user. The cochlear implant 112 can also operate in a second general mode, sometimes referred as an “invisible hearing” mode, in which the sound processing unit 106 is unable to provide sound signals to the cochlear implant 112 (e.g., the sound processing unit 106 is not present, the sound processing unit 106 is powered-off, the sound processing unit 106 is malfunctioning, etc.). As such, in the invisible hearing mode, the cochlear implant 112 captures sound signals itself via implantable sound sensors and then uses those sound signals as the basis for delivering stimulation signals to the user. Further details regarding operation of the cochlear implant 112 in the external hearing mode are provided below, followed by details regarding operation of the cochlear implant 112 in the invisible hearing mode. It is to be appreciated that reference to the external hearing mode and the invisible hearing mode is merely illustrative and that the cochlear implant 112 could also operate in alternative modes.

[0033] In FIGs. 1A and 1C, the cochlear implant system 102 is shown with an external device 110, configured to implement aspects of the techniques presented. The external device 110,Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 which is shown in greater detail in FIG. IE, 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 110 and the cochlear implant system 102 (e.g., sound processing unit 106 or the cochlear implant 112) wirelessly communicate via a bi-directional communication link 126. The bi-directional communication link 126 can comprise, for example, a short-range communication, such as Bluetooth link, Bluetooth Low Energy (BLE) link, a proprietary link, etc.

[0034] Returning to the example ofFIGs. 1A-1D, the sound processing unit 106 of the external component 104 also comprises one or more input devices configured to capture and / or receive input signals (e.g., sound or data signals) at the sound processing unit 106. The one or more input devices include, for example, one or more sound input devices 118 (e.g., one or more external microphones, audio input ports, telecoils, etc.), one or more auxiliary input devices 128 (e.g., audio ports, such as a Direct Audio Input (DAI), data ports, such as a Universal Serial Bus (USB) port, cable port, etc.), and a short-range wireless transmitter / receiver (wireless transceiver) 120 (e.g., for communication with the external device 110), each located in, on or near the sound processing unit 106. However, it is to be appreciated that one or more input devices can include additional types of input devices and / or less input devices (e.g., the short- range wireless transceiver 120 and / or one or more auxiliary input devices 128 could be omitted).

[0035] The sound processing unit 106 also comprises the external coil 108, a charging coil, a closely-coupled radio frequency transmitter / receiver (RF transceiver) 122, at least one rechargeable battery 132, and an external sound processing module 124. The external sound processing module 124 can be configured to perform a number of operations that are represented in FIG. ID by a sound processor 133. The sound processor 133 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 sound processing operations. That is, the sound processor 133 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.

[0036] Returning to the example of FIGs. 1A-1D, the implantable component 112 comprises an implant body (main module) 134, a lead region 136, and the stimulating assembly 116, all configured to be implanted under the skin (tissue) 115 of the user. The implant body 134 generally comprises a hermetically-sealed housing 138 that includes, in certain examples, atAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 least one power source 125 (e.g., one or more batteries, one or more capacitors, etc.), in which the RF interface circuitry 140 and a stimulator unit 142 are disposed. The implant body 134 also includes the intemal / implantable coil 114 that is generally external to the housing 138, but which is connected to the RF interface circuitry 140 via a hermetic feedthrough (not shown in FIG. ID).

[0037] As noted, the stimulating assembly 116 is configured to be at least partially implanted in the user’s cochlea. The stimulating assembly 116 includes a plurality of longitudinally spaced intra-cochlear electrical stimulating contacts (electrodes) 144 that collectively form a contact array (electrode array) 146 for delivery of electrical stimulation (current) to the recipient’s cochlea. The stimulating assembly 116 extends through an opening in the recipient’s cochlea (e.g., cochleostomy, the round window, etc.) and has a proximal end connected to stimulator unit 142 via lead region 136 and a hermetic feedthrough (not shown in FIG. ID). Lead region 136 includes a plurality of conductors (wires) that electrically couple the electrodes 144 to the stimulator unit 142. The implantable component 112 also includes an electrode outside of the cochlea, sometimes referred to as the extra-cochlear electrode (ECE) 139.

[0038] As noted, the cochlear implant system 102 includes the external coil 108 and the implantable coil 114. The external magnet 150 is fixed relative to the external coil 108 and the intemal / implantable magnet 152 is fixed relative to the implantable coil 114. The external magnet 150 and the intemal / implantable magnet 152 fixed relative to the external coil 108 and the intemal / implantable coil 114, respectively, facilitate the operational alignment of the external coil 108 with the implantable coil 114. This operational alignment of the coils enables the external component 104 to transmit data and power to the implantable component 112 via a closely-coupled wireless link 148 formed between the external coil 108 with the implantable coil 114. In certain examples, the closely-coupled wireless link 148 is an 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 implantable component and, as such, FIG. ID illustrates only one example arrangement.

[0039] As noted above, the sound processing unit 106 includes the external sound processing module 124. The external sound processing module 124 is configured to process the received input audio signals (received at one or more of the input devices, such as sound input devices 118 and / or auxiliary input devices 128) and convert the received input audio signals into output control signals for use in stimulating a first ear of a recipient or user (i.e., the external soundAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 processing module 124 is configured to perform sound processing on input signals received at the sound processing unit 106). Stated differently, the one or more processors (e.g., processing element(s) implementing firmware, software, etc.) in the external sound processing module 124 are configured to execute sound processing logic in memory to convert the received input audio signals into output control signals (stimulation signals) that represent electrical stimulation for delivery to the recipient.

[0040] As noted, FIG. ID illustrates an embodiment in which the external sound processing module 124 in the sound processing unit 106 generates the output control signals. In an alternative embodiment, the sound processing unit 106 can send less processed information (e.g., audio data) to the implantable component 112, and the sound processing operations (e.g., conversion of input sounds to output control signals 156) can be performed by a processor within the implantable component 112.

[0041] In FIG. ID, according to an example embodiment, output control signals (stimulation signals) are provided to the RF transceiver 122, which transcutaneously transfers the output control signals (e.g., in an encoded manner) to the implantable component 112 via the external coil 108 and the implantable coil 114. That is, the output control signals (stimulation signals) are received at the RF interface circuitry 140 via the implantable coil 114 and provided to the stimulator unit 142. The stimulator unit 142 is configured to utilize the output control signals to generate electrical stimulation signals (e.g., current signals) for delivery to the user’s cochlea via one or more of the stimulating contacts 144. In this way, cochlear implant system 102 electrically stimulates the user’s auditory nerve cells, bypassing absent or defective hair cells that normally transduce acoustic vibrations into neural activity, in a manner that causes the recipient to perceive one or more components of the input audio signals (the received sound signals).

[0042] As detailed above, in the external hearing mode, the cochlear implant 112 receives processed sound signals from the sound processing unit 106. However, in the invisible hearing mode, the cochlear implant 112 is configured to capture and process sound signals for use in electrically stimulating the user’s auditory nerve cells. In particular, as shown in FIG. ID, an example embodiment of the cochlear implant 112 can include a plurality of implantable sound sensors 165(1), 165(2) that collectively form a sensor array 160, and an implantable sound processing module 158. Similar to the external sound processing module 124, the implantable sound processing module 158 can comprise, for example, one or more processors and a memory device (memory) that includes sound processing logic. The memory device canAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 comprise any one or more of: Non-Volatile Memory (NVM), Ferroelectric Random Access Memory (FRAM), read only memory (ROM), random access memory (RAM), magnetic disk storage media devices, optical storage media devices, flash memory devices, electrical, optical, or other physical / tangible memory storage devices. The one or more processors are, for example, microprocessors or microcontrollers that execute instructions for the sound processing logic stored in memory device.

[0043] In the invisible hearing mode, the implantable sound sensors 165(1), 165(2) of the sensor array 160 are configured to detect / capture input sound signals 166 (e.g., acoustic sound signals, vibrations, etc.), which are provided to the implantable sound processing module 158. The implantable sound processing module 158 is configured to convert received input sound signals 166 (received at one or more of the implantable sound sensors 165(1), 165(2)) into output control signals 156 for use in stimulating the first ear of a recipient or user (i.e., the implantable sound processing module 158 is configured to perform sound processing operations). Stated differently, the one or more processors (e.g., processing element(s) implementing firmware, software, etc.) in the implantable sound processing module 158 are configured to execute sound processing logic in memory to convert the received input sound signals 166 into output control signals 156 that are provided to the stimulator unit 142. The stimulator unit 142 is configured to utilize the output control signals 156 to generate electrical stimulation signals (e.g., current signals) for delivery to the user’s cochlea, thereby bypassing the absent or defective hair cells that normally transduce acoustic vibrations into neural activity.

[0044] It is to be appreciated that the above description of the so-called external hearing mode and the so-called invisible hearing mode are merely illustrative and that the cochlear implant system 102 could operate differently in different embodiments. For example, in one alternative implementation of the external hearing mode, the cochlear implant 112 could use signals captured by the sound input devices 118 and the implantable sound sensors 165(1), 165(2) of sensor array 160 in generating stimulation signals for delivery to the user.

[0045] FIG. IE is a block diagram illustrating one example arrangement for an external computing device 110 configured to perform one or more operations in accordance with certain embodiments presented herein. As shown in FIG. IE, in its most basic configuration, the external computing device 110 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 canAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 communicate with and control the performance of other components of the external computing device 110. 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.

[0046] In certain embodiments, the memory 184 comprises logic that, when executed, enables the processing unit 183 to perform aspects of the techniques presented. In particular, the memory 184 can include a background sound analysis module 131 and a hearing device test module 135. Each of the background sound analysis module 131 and the hearing device test 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 background sound analysis module 13 land the hearing device test 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. ID illustrates the background sound analysis module 131 and the hearing device test module 135 as being implemented / performed at the external device 110, it is to be appreciated that these elements (e.g., functional operations) could also or alternatively be implemented / performed by the external component 104 and / or cochlear implant 112.

[0047] In the illustrated example of FIG. IE, the external computing device 110 further includes a network adapter 186, one or more input devices 187, and one or more output devices 188. The external computing device 110 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 110Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 that provides network access (e.g., access to at least one network 189). The network adapter186 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 devices187 are devices over which the external computing device 110 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 110 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.

[0048] It is to be appreciated that the arrangement for the external computing device 110 shown in FIG. IE 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 110 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.

[0049] As noted, certain embodiments described herein provide for intelligently monitoring background sound (e.g., noise) present in the ambient environment of a recipient during a hearing device test using individualized / personalized monitoring parameters (e.g., individualized maximum background sound levels). That is, in accordance with embodiments presented herein, the background sound monitoring is specifically customized / tailored based one or more attributes of the hearing device test being performed, one or more attributes of the recipient that is the subject of the hearing device test, and / or one or more attributes of the hearing device associated with the recipient. The monitoring can be used to, for example, determine whether the background sound is too loud based on the test being performed and information (e.g., the residual hearing) associated with the recipient of the hearing device testAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 and, accordingly, initiate one or more remedial or corrective actions (e.g., automatically pause the test, automatically re-perform part of the test, etc.).

[0050] Reference is now made to FIG. 2, which is a flow diagram illustrating a method 200 of determining a maximum level of background / ambient sound (e.g., noise) for a particular recipient and a particular hearing device test. For ease of description, FIG. 2 is described with reference to cochlear implant system 102 from FIGs. 1A-1E.

[0051] In particular, as illustrated in FIG. 2, at 202, the external device 110 (e.g., background sound analysis module 131) determines a type of hearing device test to be performed. This determination can be made in any of a number of different manners using, for example, data from hearing device test module 135, data received from a remote source, based on an input from a user, etc. As noted, the hearing device tests can also take a number of different forms. In one example, hearing device test may be any form of psychophysical hearing related test. In another example, one test that can be performed is an aided audiogram test where the recipient is provided with a series of pure tones streamed from a smartphone to create an aided audiogram. The aided audiogram test is used to confirm that soft sounds are audible to the recipient and to monitor performance and identify hearing acuity issues.

[0052] Another type of streaming test that can be performed is a DTT test. The DTT is a speech-in-noise hearing test used to assess speech understanding in noise by asking individuals to repeat sequences of three digits presented with background sound. The recipient of the test can enter the three digits that were heard into an external device, such as a smartphone. The streamed noise in the background increases or decreases until the recipient has a 50% chance of getting the numbers correct. The final noise level measures how much noise the recipient can tolerate before starting to lose speech perception. Another type of test that can be performed is a word test, which is used to assess a recipient’s ability to identify words. Word recognition tests evaluate a recipient's ability to identify one-syllable words. A recipient can enter the word that was heard into an external device, such as a smartphone. An algorithm can correct for any spelling errors.

[0053] Other types of tests can be performed remotely by a recipient of a hearing device. Different tests can have different thresholds for an amount of background sound that can be tolerated while still producing accurate results. For example, an aided audiogram test can tolerate less background sound then a speech in noise test. In addition, different tests may have different requirements for the number of frequency bands to look at. For example, if an aidedAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 audiogram test is being performed and there is high frequency noise during a low frequency test tone, this could be less interfering than when higher frequency is being tested. The fdter can change depending on the test or even depending on what part of the test is being performed. Requirements associated with each test (e.g., a level of acceptable background sound when performing the test and / or additional information) can be stored in a database, represented by block 204 in FIG. 2. The database 204 can be part of memory 184 and / or could be located at a remote location (e.g., cloud server).

[0054] At 206, background sound analysis module 131 obtains the stored requirements associated with the type hearing device test (selected hearing device test 202) from database 204. Also at 206, the background sound analysis module 131 uses the type of the test and the stored requirements for the selected hearing device test 202 to determine per-frequency background sound limits (represented in FIG. 2 by arrow 207) associated with the given test.

[0055] The per-frequency background sound limits for a given test can be determined in a number of different manners. For example, the Speech Transmission Index (STI) can be used to predict the effect of noise on speech intelligibility for hearing impaired people based on the energy content per-frequency band. Based on the model and / or the identified requirements for the type of test, different noise limits can be determined for different frequency bands. For example, a first noise level can be acceptable when performing a particular test using sounds in a first frequency band, but the same noise level may not be acceptable when performing the particular test using sounds in a second frequency band. In this example, results produced when performing the particular test in the second frequency band can be unreliable.

[0056] Returning to FIG. 2, at 212, the external device 110 (e.g., background sound analysis module 131) access a recipient hearing record 208 associated with the recipient and to obtain / determine audiogram data 210 for both ears for the recipient of the hearing device test. An audiogram is a chart that records the softest sounds heard at different frequencies at each ear. The audiogram indicates how well a recipient can hear at different frequencies. For example, a recipient with low frequency residual hearing can be able to hear sounds in lower frequency bands and may not be able to hear sounds in higher frequency bands. Other recipients may be able to hear sounds in higher frequency bands, but not in lower frequency bands. Each recipient can have a different audiogram indicating their hearing level in different frequency bands. In addition, each recipient can have a different audiogram for each ear since hearing loss can affect each of their ears differently. In some cases, a recipient of a hearing aid may have different audiograms depending upon whether the hearing aid is turned on or off.Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1

[0057] At 212, the background sound analysis module 131 also obtains the per-frequency background sound limits 207 for the selected hearing device test 202. As such, at this point, the background sound analysis module 131 has the recipient’ s audiogram data 210 and the per- frequency background sound limits 207 for the given test. This information is then used to determine “individualized per-frequency background sound limits” 214 for use in monitoring the ambient environment of the recipient during performance of the hearing device test. As used herein, reference to “individualized per-frequency background sound limits” refers to background sound limits / thresholds that are individually selected / set for each of a plurality of sound frequency bands, based on the attributes of the selected hearing device test 202 to be performed and the attributes of the recipient that is to be the subject of the selected hearing device test 202. In other words, in accordance with embodiments presented herein, different frequency bands can have different background sound thresholds that, when exceeded, can trigger a remedial / corrective action.

[0058] Optionally, the individualized per-frequency background sound limits 214 can also be based, in part, on one or more attributes of the hearing device itself. The use of one or more attributes of the hearing device itself could be determined from a record or database of information associated with the hearing device, similar to how the recipient’s audiogram data 210 is obtained.

[0059] In one example, the background sound analysis module 131 applies an audiological model to determine the individualized per-frequency background sound limits 214 for the selected hearing device test 202. For example, using the per-frequency background sound limits 207 for the given test and the recipient’s audiogram data 210 for both ears, the upper limit of a noise level per-frequency band can be determined for the particular test being received by the particular recipient. The individualized per-frequency background sound limits 214 can be output and / or subsequently used to monitor the test.

[0060] As noted above, the individualized per-frequency background sound limits 214 can vary between different sound frequency bands and can vary between recipients and / or between different hearing device tests. For example, a particular recipient can have different individualized per-frequency background sound limits for different tests. As indicated above, a threshold test can be more sensitive than a speech-in-noise test and the individualized per- frequency background sound limits can be lower for the threshold test than for a speech-in- noise test. In addition, the individualized per-frequency background sound limits for a particular test can differ per recipient (e.g., due to differing levels of residual hearing inAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 recipients, different levels of hearing per threshold in recipients, etc.). The individualized per- frequency background sound limits can be used when performing a hearing device test to determine whether environmental or ambient noise exceeds the maximum noise levels per- frequency while the hearing device test is being conducted.

[0061] Reference is now made to FIG. 3, which is a flow diagram illustrating a method 300 for using the individualized per-frequency background sound limits to monitor a hearing device test, in accordance with embodiments presented herein. For ease of description, FIG. 3 is described with reference to cochlear implant system 102 from FIGs. 1A-1E.

[0062] The method 300 begins at 302 where the hearing device test is administered to the recipient (e.g., using hearing device test module 135) while recording the background sound in the ambient environment using one or more microphones. The background sound can be recorded using, for example, a one or more microphones of the cochlear implant system 100, one or more microphones of the external device 110, and / or one or more microphones microphone located within the ambient environment of the recipient during the hearing device test (e.g., using an internet of things (IOT) network, Wi-Fi® connections, Bluetooth® or BLE connections, etc.). At 304, the background sound is analyzed on a per-frequency band basis relative to the individualized per-frequency background sound limits 214 and, at 306, a determination is made whether the background sound level in any frequency band exceeds the determined maximum sound level (as indicated by the individualized per-frequency background sound limits 214). For example, the sound levels per-frequency band of the background sound are compared to the individualized per-frequency background sound limits 214. At 308, if none of the sound levels exceeded the maximum noise levels for any frequency band while the test was being conducted, then the results of the test are accepted.

[0063] However, if it is determined at 306 that one or more of the sound levels per-frequency band exceeded a corresponding maximum noise level as indicated by the individualized per- frequency background sound limits 214 while the test was being conducted, then one or more corrective or remedial actions can be taken. One action can include, for example, warning the recipient that the background sound level is too high and providing a notification suggesting that the recipient move to a quieter environment. Another action can include pausing the test. For example, the test can be paused if the noise is transient, and the test can resume when the noise level has dropped below the threshold. Another action can include displaying the test data to an audiologist with a warning that one or more noise levels have been exceeded and the test results can be unreliable. In addition, a report may be sent to the audiologist indicating theAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 noise levels that were measured in each frequency band. This action can be performed if, for example, there is a consistent noise throughout the test that exceeds the maximum noise level. In this case, the audiologist can determine to accept the test results, not accept the test results, or accept the test results in some of the frequency bands and determine that the test results are unreliable in other frequency bands.

[0064] Another action that can be taken includes redoing a portion of the test. For example, if the noise level is exceeded in a frequency band for a portion of the test (e.g., for one word, one tone, one number triplet, etc.), the results of that portion of the test can be discarded and a new portion of the test can be provided in the same frequency band. In this case, the portion of the test can be re-conducted if the environmental noise is temporarily elevated.

[0065] In some embodiments, a score can be calculated that indicates an impact of the noise level on the test results. For example, a constant humming during the test can interfere with the test results more than a door slamming during the test. In some embodiments, if the score indicates that the interference is minimal, the test results can be accepted even if the noise level exceeds the maximum level in one or more frequency bands. In other embodiments, the score can be displayed to an audiologist, and the audiologist can determine whether the test results are valid based, in part, on the score. In some embodiments, more than one of the actions can be taken or a different action can be taken. In some embodiments, the action or actions that are taken can be based on a number of factors, such as a length of time that the noise level is exceeded (e.g., a door slamming versus a television on in the background), a volume of the noise level, information associated with the recipient, or other factors.

[0066] As noted, in certain embodiments presented herein, the hearing device or an external device associated with the hearing device (e.g., mobile phone) could be connected to other devices in the ambient environment (e.g., via IOT, Wi-Fi®, Bluetooth®), etc. As such, another corrective or remedial action that can be taken in accordance with embodiments presented herein (when one or more of the sound levels per-frequency band exceeded a corresponding maximum noise level as indicated by the individualized per-frequency background sound limits 214 while the test was being conducted) could be to adjust the operation of a connected device in the environment. For example, a corrective or remedial action could include turning on / off a noisy connected device, adjusting the settings (e.g., volume) of a connected device, etc.

[0067] Reference is now made to FIG. 4, which is a diagram of an audiogram 400 for both ears of a recipient of a hearing device with an indication of background sound levels that renderAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 particular test results invalid. In particular, plot 402 is an audiogram associated with a left ear of the recipient of the hearing device and plot 404 is an audiogram associated with of a right ear of the recipient of the hearing device.

[0068] As illustrated in FIG. 4, the recipient experiences a higher level of hearing in lower frequencies (and is in the “normal hearing” range for the right ear in the 250 Hz range) and experiences higher level of hearing loss in higher frequencies. In this example, it has been determined that any background sound levels that are audible render the test results invalid. In another words, in this example, noise levels can never be audible and should always be below the audiometric thresholds for the recipient. This requirement can be made, for example, for an aided audiogram test.

[0069] Area 406 illustrates the allowable level of background sound for the recipient based on the recipient’s hearing capability. As illustrated, as the frequency increases, the level of acceptable background sound increases. In other words, since the recipient experiences severe hearing loss in sounds above 4000 Hz, the recipient is unable to hear quieter sounds in these frequence ranges. For example, as illustrated by plot 402, the recipient is unable to hear sounds quieter than 80 dB at 8000 Hz in the left ear and, as illustrated by plot 404, the recipient is unable to hear sounds quieter than 75 dB at 8000 Hz in the right ear. Therefore, any background sound that is quieter than 75 dB at 8000 Hz will not affect test results because the recipient is unable to hear the background sound at this frequency. Similarly, the recipient is unable to hear sounds quieter than 20 dB at 800 Hz in the left ear and quieter than 25 dB in the right ear at 800 Hz. Therefore, background sound that is quieter than 20 dB at 800 Hz will not affect the test results.

[0070] Area 408 illustrates levels of background sound that render the test results invalid. In this example, any background sound that the recipient is able to hear will render the test results invalid. Therefore, as shown in audiogram 400, any background sound louder than, for example, 20 dB at 250 Hz will cause the test to fail. Similarly, any background sound louder than 80-85 dB at 4000 - 8000 Hz will cause the test to fail and render the test results invalid.

[0071] As illustrated by audiogram 400, the level of background sound at which the test will fail is dependent upon the recipient’s particular hearing. In addition, the background sound can be analyzed to identify the volume at different frequencies because the recipient’s hearing level can vary at different frequencies. As illustrated by audiogram 400, a test can be valid at different frequencies and invalid at other frequencies with the same level of background sound.Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1For example, a background sound level of 40 dB can render a test invalid at lower frequencies (e.g., between 250 and 1500 Hz) but may not invalidate test results at higher frequencies (e.g., between 3000 and 8000 Hz). This is because the recipient is able to hear quieter sounds at lower frequencies and experiences greater hearing loss at the higher frequencies.

[0072] Reference is now made to FIG. 5, which illustrates an audiogram 500 for the recipient, which indicates levels in which results of a different test are invalid. Audiogram 500 illustrates an example for a test (e.g., a word test) in which a signal-to-noise ratio of +15 dB produces acceptable test results.

[0073] In audiogram 500, plot 402 is an audiogram associated with the recipient’s left ear and plot 404 is an audiogram associated with the recipient’s right ear. Plots 402 and 404 are the same audiograms as plots 402 and 404 in FIG. 4, but the test being performed may be different. Line 508 illustrates the test level equivalent of 65 dB and line 506 illustrates a +15 dB signal- to-noise limit of 50 dB. In other words, if the test is streamed at the equivalent of 65 dB, any audible signal that is also above 50 dB (65 dB - 15 dB) can render the test results invalid. In this example, a 15 dB buffer is provided in which the recipient can be able to hear background sound, but the background sound does not affect the results of the test. The buffer may be provided for, for example, a DTT test.

[0074] In the example illustrated in FIG. 5, acceptable sounds are either below the audiogram plots (i.e., inaudible for the recipient) or below 50 dB (i.e., too soft compared to the speech of the test to have an effect). Area 510 illustrates background sound levels that are acceptable for different frequencies. As shown, the recipient is able to hear some of the background sound that is considered acceptable for this test. For example, at 500 Hz, background sound quieter than 50 dB is acceptable even though the recipient is able to hear noise louder than 20 dB at this frequency. Because the test is streamed at 65 dB, any background sound below 50 dB will not affect the recipient’s ability to hear the streamed words, even though the recipient can be able to hear the background sound. At higher frequencies (e.g., 8000 Hz), background sound up to 75 dB is acceptable because the recipient is unable to hear sounds quieter than 75 dB at this frequency.

[0075] Area 512 illustrates background sound levels that render the test results invalid. The area of invalid background sound levels is lower than in audiogram 400 because this test allows for some background sound to be heard by the recipient. However, if the background sound isAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 audible to the recipient and within 15 dB of the test level equivalent (i.e., louder than 50 dB), the test results are invalid.

[0076] In some embodiments, the signal-to-noise ratio buffer may not be a straight horizontal noise. For example, a model can be implemented to indicate how much speech understanding is likely affected by the noise (e.g., based on the type of noise) at different frequencies. In this example, a slope of the signal-to-noise line can vary based on frequency. For example, at some frequencies, the safety margin of acceptable noise can be, for example, 15 dB and at other frequencies, the safety margin can be, for example, 10 dB or 20 dB. Using a model can provide a more accurate indication of acceptable levels of background sound at different frequency ranges.

[0077] In some cases, a spread of masking may be experienced in which a noise at a specific frequency can mask sounds in nearby frequencies even though there is no noise at that frequency. In particular, an ‘upward spread of masking’ may be experienced in which the masking effect extends mostly to higher frequencies. This is caused by basilar membrane mechanics resulting in non-ideal filters in the ear. Using a model may account for any upward spread of making, even though it may be a second order effect.

[0078] As illustrated in FIGs. 4 and 5, information or requirements associated with the test being administered and information associated with the hearing capabilities of the recipient of the test can be used to intelligently define acceptable levels of background sound that will not render results of the test invalid. By determining the background sound thresholds based on the recipient and the type of test being conducted, more precise and reliable results can be achieved without placing overly broad background sound level restrictions on recipients who are less affected by the background sound (i.e., recipients with little or no residual hearing).

[0079] Reference is now made to FIG. 6, which is a flowchart of a method 600 of performing one or more actions based on determining whether a sound level for an environment during a hearing device test exceeds at least one threshold sound level.

[0080] At 602, at least one threshold sound level for an environment is determined based on a type of test being performed in the environment and information associated with a recipient of the test. For example, a threshold sound level for different frequency ranges can be determined based on requirements of the test and an audiogram associated with the recipient.

[0081] At 604, while the test is being conducted, it is determined whether a sound level for the environment exceeds the at least one threshold sound level. In some embodiments, aAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 microphone of a hearing device associated with the test can detect the noise in the environment and the noise can be analyzed. For example, a sound level for a plurality of different frequency ranges can be determined. The sound level in the different frequency ranges can be compared to the threshold sound level for the different frequency ranges to determine whether the sound level is above the threshold sound level for any of the frequency ranges.

[0082] At 606, one or more actions are performed based on determining whether the sound level for the environment exceeds the at least one threshold sound level. For example, if the sound level does not exceed the at least one threshold level, the results of the test are considered acceptable. If the sound level exceeds the at least one threshold level, a recipient can be instructed to move to a quieter environment, the test can be paused and resumed when the sound level decreases, an audiologist or clinician can be notified that the test results can be unreliable, a portion of the test can be re-conducted, a score that indicates an impact the noise has on the test results can be calculated, a combination of the actions can be taken, or a different action can be taken.

[0083] Reference is now made to FIG. 7, which is flowchart of a method 700 of initiating a corrective action when at least one sound level exceeds at least one predetermined threshold level.

[0084] At 702, during a hearing device test associated with a recipient of a hearing device, at least one sound level associated with an ambient sound environment is monitored. For example, a microphone of the hearing device can monitor the sound level of the ambient sound environment, and the sound level can be analyzed to identify the sound levels in different frequency ranges.

[0085] At 704, a corrective action is initiated when the at least one sound level exceeds at least one predetermined threshold level. The at least one predetermined threshold level is set based on a hearing capability of the recipient. In some embodiments, the at least one predetermined threshold level includes a threshold level for each of a plurality of frequency ranges. The at least one threshold level can be set based on an audiogram associated with the recipient. The corrective action can include instructing the recipient to move to a quieter environment, pausing the test and resuming the test when the sound level decreases, notifying an audiologist or clinician that the test results can be unreliable, re-conducting a portion of the test, calculating a score that indicates an impact the noise has on the test results, performing a combination of the actions, or performing a different action.Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1

[0086] 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. 8 and 9. The techniques of the present disclosure can be applied to other devices, such as neurostimulators, cardiac pacemakers, cardiac defibrillators, sleep apnea management stimulators, seizure therapy stimulators, tinnitus management stimulators, and vestibular stimulation devices, 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.

[0087] 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).

[0088] 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 chain 836, 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,Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 where the vibration is perceived as sounds to provide relief of tinnitus symptoms experienced by the recipient.

[0089] One or more tests can be performed in relation to the tinnitus therapy device 800. In accordance with embodiments presented herein, while the one or more tests are being performed, the ambient environment of the recipient can be monitored using individualized per-frequency background sound limits determined based on, for example, one or more attributes of the recipient of the tinnitus therapy device 800, one or more attributes of the test being performed, and / or one or more attributes of the tinnitus therapy device 800.

[0090] FIG. 9 illustrates a retinal prosthesis system 901 that comprises an external device 910 (which can correspond to the wearable device 100) configured to communicate with an implantable retinal prosthesis 900 via signals 951. The retinal prosthesis 900 comprises an implanted processing module 925, and a retinal prosthesis sensor-stimulator 990 is positioned proximate the retina of a recipient. The external device 910 and the processing module 925 can communicate via coils 908, 914.

[0091] In an example, sensory inputs (e.g., photons entering the eye) are absorbed by a microelectronic array of the sensor-stimulator 990 that is hybridized to a glass piece 992 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 990 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.

[0092] The processing module 925 includes an image processor 923 that is in signal communication with the sensor-stimulator 990 via, for example, a lead 988 that extends through surgical incision 989 formed in the eye wall. In other examples, processing module 925 is in wireless communication with the sensor-stimulator 990. The image processor 923 processes the input into the sensor-stimulator 990 and provides control signals back to the sensor-stimulator 990 so the device can provide an output to the optic nerve. That said, in an alternate example, the processing is executed by a component proximate to, or integrated with, the sensor-stimulator 990. 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.Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1

[0093] The processing module 925 can be implanted in the recipient and function by communicating with the external device 910, such as a BTE unit, a pair of eyeglasses, etc . The external device 910 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 990 captures light / images, in which sensor-stimulator 990 is implanted in the recipient.

[0094] One or more tests can be performed in relation to the retinal prosthesis system 901. In accordance with embodiments presented herein, while the one or more tests are being performed, the ambient environment of the recipient can be monitored using individualized background ambient limits determined based on, for example, one or more attributes of the recipient of the retinal prosthesis system 901 , one or more attributes of the test being performed, and / or one or more attributes of the retinal prosthesis system 901. In these examples, the individualized background ambient limits are not referenced to sound, but instead could be referenced to other ambient values, such light or other visual signals in the ambient environment, temperature, etc.

[0095] In general, and as noted above, the techniques presented herein can implemented with a number of different types of sensory devices and a number of different types of sensory device tests. In various embodiments, various aspects of the ambient environment could be monitored using individualized background ambient limits. For example, aspects presented herein can monitor ambient sound, (e.g., noise) levels, temperature levels of the surrounding air, light signals, the level of radiated and conducted signals (e.g., atmospherics, interference from other sources, and circuit noise, etc.), etc. In each case, the threshold monitoring levels can be individualized for the recipient of the sensory test and, in addition, the threshold monitoring levels are separated into various ‘bands’ so that environment can be monitored in an intelligent manner.

[0096] 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.Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1

[0097] 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.

[0098] 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.

[0099] 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.[ootoo] 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.[ooiot] 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.

[0102] 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. 3065.0867i Client Ref. No. CID04064WOPC1CLAIMSWhat is claimed is:

1. A method comprising : determining at least one threshold sound level for an environment based on a type of test being performed in the environment and information associated with a recipient of the test; while the test is being conducted, determining whether a sound level for the environment exceeds the at least one threshold sound level; and performing one or more actions based on determining whether the sound level for the environment exceeds the at least one threshold sound level.

2. The method of claim 1, wherein the test is a hearing assessment associated with a hearing device.

3. The method of claim 2, wherein the test is an aided audiogram test.

4. The method of claim 2, wherein the test is a Digit Triplet Test (DTT).

5. The method of claim 2, wherein the test is a speech in noise test.

6. The method of claim 1, wherein the test is a psychophysical hearing related test.

7. The method of claim 1, wherein the information associated with a recipient of the test includes an audiogram.

8. The method of claim 1, 2, 3, 4, 5, 6, or 7, wherein performing the one or more actions includes: instructing the recipient to move to a quieter environment based on determining that the sound level for the environment exceeds the at least one threshold sound level.

9. The method of claim 1, 2, 3, 4, 5, 6, or 7, wherein performing the one or more actions includes: pausing the test based on determining that the sound level for the environment exceeds the at least one threshold sound level; andAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 resuming the test when the sound level for the environment is below the at least one threshold sound level.

10. The method of claim 1, 2, 3, 4, 5, 6, or 7, wherein performing the one or more actions includes: instructing a user that results associated with the test may be unreliable when based on determining that the sound level for the environment exceeds the at least one threshold sound level.

11. The method of claim 1, 2, 3, 4, 5, 6, or 7, wherein performing the one or more actions includes: re-conducting a portion of the test based on determining that the sound level for the environment exceeds the at least one threshold sound level.

12. The method of claim 1, 2, 3, 4, 5, 6, or 7, wherein performing the one or more actions includes: calculating a score indicating an impact of the sound level on results of the test.

13. The method of claim 1, 2, 3, 4, 5, 6, or 7, wherein determining the at least one threshold sound level for the environment includes: determining a plurality of sound level thresholds, wherein the plurality of sound level thresholds are each associated with a different sound frequency band.

14. The method of claim 1, 2, 3, 4, 5, 6, or 7, wherein the recipient is a recipient of a hearing device and wherein the method further comprises: determining the sound level using sound data captured via a microphone of the hearing device.

15. A system, comprising: at least one microphone configured to capture ambient sound signals from an ambient environment of a recipient during a hearing device test associated with a recipient of a hearing device; and at least one processor configured to:Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 during the hearing device test, monitor the ambient environment using a plurality of individualized per-frequency background sound limits; and initiate a corrective action when a sound level in the ambient environment exceeds at least one of the plurality of individualized per-frequency background sound limits.

16. The system of claim 15, wherein the plurality of individualized per-frequency background sound limits are set based on a hearing ability of the recipient.

17. The system of claim 16, wherein the plurality of individualized per-frequency background sound limits are set based on one or more audiograms associated with the recipient.

18. The system of claim 15, wherein the plurality of individualized per-frequency background sound limits are set based on one or more attributes of the hearing device test.

19. The system of claim 15, wherein the plurality of individualized per-frequency background sound limits are set based on one or more attributes of the hearing device.

20. The system of claim 15, 16, 17, 18, or 19, wherein the hearing device test is an aided audiogram test.

21. The system of claim 15, 16, 17, 18, or 19, wherein the hearing device test is a Digit Triplet Test (DTT).

22. The system of claim 15, 16, 17, 18, or 19, wherein the hearing device test is a speech in noise test.

23. The system of claim 15, 16, 17, 18, or 19, wherein initiating the corrective action includes: generating a notification to the recipient to move to a quieter environment; determining when the recipient is in the quieter environment; and re-performing a portion of the hearing device test when the recipient is in the quieter environment.Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC124. The system of claim 15, 16, 17, 18, or 19, wherein initiating the corrective action includes: pausing the hearing device test based on determining that the sound level in the ambient environment exceeds at least one of the plurality of individualized per-frequency background sound limits; and resuming the hearing device test when the sound level for the ambient environment is below the plurality of individualized per-frequency background sound limits.

25. The system of claim 15, 16, 17, 18, or 19, wherein initiating the corrective action includes: instructing a user that results associated with the hearing device test are unreliable.

26. The system of claim 15, 16, 17, 18, or 19, wherein initiating the corrective action includes: automatically re-performing a portion of the hearing device test.

27. The system of claim 15, 16, 17, 18, or 19, further comprising: calculating a score indicating an impact of the sound level of the ambient environment on the hearing device test.

28. The system of claim 15, 16, 17, 18, or 19, further comprising: a speaker for generating sound signals during the hearing device test.

29. A method comprising: during a sensory device test associated with a recipient of a sensory device, monitoring an ambient environment of the recipient based on a plurality of individualized per-frequency background ambient limits; and initiating a corrective action when at least one ambient level in the ambient environment exceeds at least one of the plurality of individualized per-frequency background ambient limits.Atty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC130. The method of claim 29, wherein the plurality of individualized per-frequency background ambient limits are a plurality of individualized per-frequency background sound limits.

31. The method of claim 30, wherein the plurality of individualized per-frequency background sound limits are set based a hearing capability of the recipient.

32. The method of claim 31, wherein the plurality of individualized per-frequency background sound limits are set using at least one audiogram associated with the recipient.

33. The method of claim 30, wherein the sensory device test is a hearing device test, and wherein the plurality of individualized per-frequency background sound limits are set based one or more attributes of the hearing device test.

34. The method of claim 30, wherein the sensory device is a hearing device, and wherein the plurality of individualized per-frequency background sound limits are set based one or more attributes of the hearing device.

35. The method of claim 29, 30, 31, 32, 33, or 34, wherein the plurality of individualized per-frequency background ambient limits are set based one or more attributes of the recipient.

36. The method of claim 29, 30, 31, 32, 33, or 34, wherein the plurality of individualized per-frequency background ambient limits are set based one or more attributes of the sensory device test.

37. The method of claim 29, 30, 31, 32, 33, or 34, wherein the plurality of individualized per-frequency background ambient limits are set based one or more attributes of the sensory device.

38. One or more non-transitory computer readable storage media comprising instructions that, when executed by a processor, cause the processor to: monitor at least one noise level associated with an ambient sound environment during a hearing device test associated with a recipient of a hearing device; andAtty. Docket No. 3065.0867i Client Ref. No. CID04064WOPC1 initiate a corrective action when the at least one noise level exceeds at least one predetermined threshold level, wherein the at least one predetermined threshold level is set based a hearing capability of the recipient.

39. The one or more non-transitory computer readable storage media of claim 38, wherein the at least one predetermined threshold level is set based on an audiogram associated with the recipient.

40. The one or more non-transitory computer readable storage media of claim 38 or 39, wherein the at least one noise level includes a plurality of noise levels, each being associated with one of a plurality of frequency ranges and wherein the at least one predetermined threshold level includes a plurality of threshold levels, each being associated with one of the plurality of frequency ranges.

41. The one or more non-transitory computer readable storage media of claim 38 or 39, wherein the at least one predetermined threshold level is further set based on a type of the hearing device test.

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