Hearing prosthesis battery autonomy configuration

Abstract

What is presented herein is a technique for determining an estimated battery autonomy (e.g., estimated run time) of a medical device having at least one actuator / transducer configured to mechanically stimulate a recipient. The medical device is specifically configured for the recipient and, as such, operates according to a plurality of recipient-specific settings. The configuration of the medical device for the recipient (e.g., the plurality of recipient-specific settings) as well as the frequency and sound level current consumption characteristics of the medical device are used to determine the estimated battery autonomy of the medical device. An environmental profile of the recipient can also be used along with the configuration of the medical device for the recipient as well as the frequency and sound level current consumption characteristics of the medical device to determine the estimated battery autonomy.

Description

background Technical Field

[0002] This invention generally relates to techniques for configuring the battery autonomy of a hearing prosthesis based on the recipient's hearing prescription. Background Technology

[0004] Over the past few decades, medical devices have provided a wide range of therapeutic benefits to recipients. Medical devices can include internal or implantable components / devices, external or wearable components / devices, or combinations thereof (e.g., devices having an external component that communicates with the implantable component). Medical devices, such as conventional 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 for many years in performing life-saving and / or lifestyle improvement functions and / or recipient monitoring.

[0005] Over the years, the types of medical devices and the range of functions they perform have increased. For example, many medical devices, sometimes referred to as “implantable medical devices,” now typically include one or more instruments, devices, sensors, processors, controllers, or other functional mechanical or electrical components permanently or temporarily implanted in a recipient. These functional devices are typically used to diagnose, prevent, monitor, treat, or manage diseases / injuries or their symptoms, or to study, replace, or modify anatomical structures or physiological processes. Many of these functional devices utilize power and / or data received from an external device that is part of or operates in conjunction with the implantable component. Summary of the Invention

[0006] In one aspect, a method is provided. The method includes: obtaining a hearing prescription associated with a recipient of a mechanically stimulated auditory prosthesis, wherein the mechanically stimulated auditory prosthesis is configured to be powered by at least one battery; and determining an estimated battery autonomy of the mechanically stimulated auditory prosthesis based on the hearing prescription and the frequency sound level current consumption of the mechanically stimulated auditory prosthesis.

[0007] In another aspect, one or more non-transitory computer-readable storage media are provided. The one or more non-transitory computer-readable storage media include instructions operable, when executed by at least one processor, to: obtain a first set of operating settings for a battery-powered medical device having at least one actuator, wherein the first set of operating settings is determined based on characteristics of a recipient of the medical device; obtain data indicating frequency-dependent current consumption of at least one actuator; and predict an estimated operating time of the medical device when operating according to the first set of operating settings based on the data indicating frequency-dependent current consumption of the at least one actuator.

[0008] In another aspect, a computing device is provided. The computing device includes: at least one interface for communicating with a battery-powered hearing prosthesis, wherein the hearing prosthesis is configured to capture sound signals and convert them into mechanical stimulation signals for delivery to a recipient; a memory; and one or more processors configured to: obtain a hearing prescription associated with a recipient of the hearing prosthesis; obtain data indicating the current consumption of the hearing prosthesis, wherein the hearing prosthesis has a current consumption dependent on the properties of the sound signals captured and converted into mechanical stimulation signals for delivery to the recipient; obtain an acoustic environment profile associated with the recipient of the hearing prosthesis; and determine an estimated battery autonomy of the hearing prosthesis based on the hearing prescription associated with the recipient, the data indicating the current consumption of the hearing prosthesis, and the acoustic environment profile associated with the recipient.

[0009] In another aspect, a method is provided. The method includes: determining a first set of operating settings for a battery-powered hearing prosthesis including at least one actuator, wherein the first set of operating settings is determined based on characteristics of a recipient of the hearing prosthesis; obtaining data indicating frequency-dependent current consumption of at least the hearing prosthesis; obtaining an acoustic environment profile associated with the recipient of the hearing prosthesis; and determining an estimated battery autonomy of the hearing prosthesis based on the first set of operating settings, the data indicating frequency-dependent current consumption of the hearing prosthesis, and the acoustic environment profile associated with the recipient. Attached Figure Description

[0010] Embodiments of the present invention are described herein in conjunction with the accompanying drawings, wherein:

[0011] Figure 1A This is a top view of a fully implantable middle ear auditory prosthesis, some of the embodiments proposed herein can be implemented using the fully implantable middle ear auditory prosthesis;

[0012] Figure 1B It shows Figure 1AA schematic diagram of a fully implantable middle ear hearing prosthesis;

[0013] Figure 1C yes Figure 1A A schematic diagram of a fully implantable middle ear hearing prosthesis;

[0014] Figure 2A This is a perspective view of a percutaneous bone conduction device, some of the embodiments presented herein can be implemented using the percutaneous bone conduction device;

[0015] Figure 2B yes Figure 2A Functional block diagram of a transcutaneous bone conduction device;

[0016] Figure 3A The following is a three-dimensional diagram according to certain embodiments presented herein, showing the current consumed by an exemplary bone conduction device as a function of both the frequency and level of the input sound signal;

[0017] Figure 3B The following is a three-dimensional diagram according to certain embodiments presented herein, illustrating the relationship between the frequency and level of the input sound signal. Figure 3A The output level of an exemplary bone conduction device;

[0018] Figure 4 This is a detailed flowchart of an exemplary method according to certain embodiments presented herein;

[0019] Figure 5 This is a diagram illustrating further details of the battery autonomy estimation process according to certain embodiments presented herein;

[0020] Figure 6 This is a block diagram of a computing device according to certain embodiments presented herein;

[0021] Figure 7 This is a schematic diagram of an active percutaneous bone conduction device, some of the embodiments presented herein can be implemented using the active percutaneous bone conduction device;

[0022] Figure 8 This is a schematic diagram of a passive percutaneous bone conduction device, some of the embodiments proposed herein can be implemented using the passive percutaneous bone conduction device;

[0023] Figure 9 This is a flowchart of a method according to certain embodiments presented herein; and

[0024] Figure 10 This is a flowchart of another method according to some embodiments presented herein. Detailed Implementation

[0025] This paper presents a technique for determining the estimated battery autonomy (e.g., estimated runtime) of a medical device having at least one actuator / transducer configured to mechanically stimulate a recipient. The medical device is specifically configured for the recipient and therefore operates according to multiple recipient-specific settings. The configuration of the medical device for the recipient (e.g., multiple recipient-specific settings) and the current consumption characteristics of the medical device are used to determine the estimated battery autonomy of the medical device. The recipient's environmental profile may also be used, along with the configuration of the medical device for the recipient and the current consumption characteristics of the medical device, to determine the estimated battery autonomy.

[0026] For ease of description only, this document primarily refers to exemplary middle ear auditory prostheses (middle ear implants) and exemplary percutaneous bone conduction devices to describe the techniques proposed herein. However, it should be understood that the techniques proposed herein can also be implemented with a variety of other devices / systems, including other medical devices / systems. For example, the techniques proposed herein can be implemented with other auditory prostheses, including other bone conduction devices, hearing aids, other middle ear auditory prostheses, direct acoustic stimulators, electroacoustic prostheses, cochlear implants, auditory brain stimulators, etc. The techniques proposed herein can also be used with tinnitus treatment devices, vestibular devices (e.g., vestibular implants), 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, and electroporation devices. wait Use them together.

[0027] Figure 1A This is a top view of a fully implantable middle ear hearing prosthesis 100 according to certain embodiments presented herein. Figure 1B It shows Figure 1A A schematic diagram of the middle ear hearing prosthesis 100 implanted in recipient 101, and Figure 1C This is a schematic block diagram of a middle ear hearing prosthesis 100. For ease of description, it will be described together. Figure 1A-1C .

[0028] A fully implantable medical device, such as a middle ear hearing prosthesis 100, is one in which all components of the device are configured to be implanted into the tissue 113 of the recipient 101 (e.g., muscle tissue, epithelial tissue, nerve tissue, connective tissue, fat, bone tissue). wait The device below. Because all components are implantable, a fully implantable medical device can operate without external devices, at least for a limited time. However, external devices, such as Figure 1CThe external device 150 shown can work with a fully implantable medical device. The external device can be configured, for example, to provide power and / or data to the implantable medical device, receive data from the implantable medical device, etc.

[0029] Figure 1A-1C The middle ear hearing prosthesis 100 includes a sound input module / unit 102, an implant body 104, an actuator 106, and a coil 108, all implanted in the body of a recipient 101. The sound input unit 102 includes a basic rigid housing 110 in which at least two implantable sensors 112, 114 are disposed / positioned. Implantable sensor 112 is configured / designed to pick up (capture) external acoustic sounds, while implantable sensor 114 is configured / designed to pick up (capture) vibrations, such as those caused by body noise. That is, implantable sensor 112 is a “sound” sensor / converter primarily configured to detect / receive external acoustic sounds, such as an implantable microphone, while implantable sensor 114 is a “vibration” sensor primarily configured to detect / receive internal body noise and vibrations (e.g., vibrations caused by the movement of an implantable actuator). Sound sensor 112 and vibration sensor 114 are sometimes collectively referred to herein as “implantable hearing sensors” 144. As used herein, actuator 106, sound sensor 112 and vibration sensor 114 are sometimes collectively referred to as “transducers” (i.e., actuator 106, sound sensor 112 and vibration sensor 114 are each devices that convert changes in physical quantities (energy) into electrical signals or vice versa).

[0030] The housing 110 is hermetically sealed and includes a diaphragm 116 adjacent to the sound sensor 112. The diaphragm 116 may be integral with the housing 110 and / or may be a separate element attached (e.g., welded) to the housing 110. The sound input unit 102 is configured to be implanted within the recipient 101. Figure 1B In one example shown, the sound input unit 102 is configured to be implanted within the skin / tissue of the recipient's outer ear 103. In this location, a diaphragm 116 is located beneath the skin of the recipient near the ear canal 105. In operation, sound signals incident on the skin adjacent to the diaphragm 116 (i.e., on top of the diaphragm) cause the skin adjacent to the diaphragm 116, and thus the diaphragm 116 itself, to displace (vibrate) in response to the sound signal. The displacement of the diaphragm 116 is detected by a sound sensor 112. In this way, the sound sensor 112, although implanted within the recipient's body, is able to detect external acoustic signals (external acoustic sounds).

[0031] exist Figure 1A-1CIn this example, the sound sensor 112 and the vibration sensor 114 may each be electrically connected to the implant body 104 (e.g., in a separate shell connected to the main implant body 104). In operation, the sound sensor 112 and the vibration sensor 114 detect input (sound / vibration) signals (e.g., external acoustic sounds and / or body noise) and convert the detected input signals into electrical signals (e.g., via lead 120) provided to the processing unit 118. The processing unit 118 is configured to generate a stimulation control signal 119 based at least on the external acoustic sounds and / or vibrations detected by the sound sensor 112 and / or the vibration sensor 114, respectively. Figure 1C ).

[0032] exist Figure 1B In the example, processing unit 118 includes at least one processor 122 and a memory device (memory) 124. Memory 124 may include any one or more of the following: non-volatile memory (NVM), ferroelectric random access memory (FRAM), read-only memory (ROM), random access memory (RAM), disk storage media device, optical storage media device, flash memory device, electrical, optical, or other physical / tangible memory storage device. At least one processor 122 is, for example, a microprocessor or microcontroller that executes instructions for logic stored in memory device 124. Processing unit 118 may be implemented, for example, on one or more printed circuit boards (PCBs).

[0033] exist Figure 1C In this context, memory 124 includes sound processing logic 126 and battery monitoring logic 125. Sound processing logic 126, when executed by at least one processor 122, causes at least one processor 122 to perform the sound processing operations described herein (e.g., converting external acoustic sounds and / or body noise detected by sound sensor 112 and / or vibration sensor 114 into stimulus control signals 119). As further described below, battery monitoring logic 125, when executed by at least one processor 122, causes at least one processor 122 to monitor the discharge of battery 130 based on estimated battery autonomy, and in some examples, initiates one or more operations based on battery monitoring.

[0034] It should be understood that Figure 1C The arrangement of the processing unit 118 is merely illustrative, and the techniques presented herein can be implemented with many different processing arrangements. For example, the sound processing unit 118 can be implemented using a processing unit formed by any one or a combination of the following: one or more processors (e.g., one or more digital signal processors (DSPs), one or more uC cores) arranged to perform operations such as those described herein. wait firmware, software wait .

[0035] As shown in the figure, the implant body 104 includes an airtight housing 128 in which the processing unit 118 is disposed. A rechargeable power source (e.g., a rechargeable battery) 130 and communication and charging circuitry 132 are also disposed in the housing 128. The communication and charging circuitry 132 includes, for example, a tightly coupled transmitter / receiver (transceiver) sometimes referred to as a radio frequency (RF) transceiver, and circuitry for recharging at least one rechargeable battery 130.

[0036] Electrically connected to the communication and charging circuit 132 is an implantable coil 108 disposed outside the housing 128. The implantable coil 108 is typically a wire antenna coil composed of multi-turn electrically insulated single or multi-strand platinum or gold wire. The electrical insulation of the implantable coil 108 is provided by a flexible molding material (e.g., a silicone molding material) 109. Figure 1A This is provided. Generally, the implantable coil 108 and the communication and charging circuitry 132 enable the receiving of power and data from an external device (e.g., external device 150) and potentially the transmission of data to the external device. However, it should be understood that various types of energy transmission, such as infrared (IR), electromagnetic, capacitive, and inductive transmission, can be used to transmit power and / or data from an external device, and therefore, Figure 1B Only one exemplary arrangement is shown.

[0037] As described above, the communication and charging circuitry 132 and the implantable coil 108 enable the middle ear hearing prosthesis 100 to receive data / power from and / or transmit data to an external device. That is, modulated signals transmitted bidirectionally via the inductive link (RF coil 108 and external device) are used to support battery charging, device programming, status queries, and remote user control. In some examples, the external device may include an over-the-ear (OTE) unit. In other examples, the external device may include a behind-the-ear (BTE) unit or a miniature BTE unit configured to be worn adjacent to the recipient's outer ear. Alternative external devices may include, for example, devices worn in the recipient's ear canal, body-worn processors, fitting systems, computing devices, pillow chargers, consumer electronics devices (e.g., mobile phone communications), etc.

[0038] The use of communication and charging circuitry 132 and implantable coil 108 for communication with external devices has been described with reference to the following. Figure 1C However, in some embodiments, the implant body 104 may also include a short-range wireless interface 133 for communicating with external devices. The short-range wireless interface 133 may be, for example, a Bluetooth® interface, a Bluetooth® Low Energy (BLE) interface, or other interfaces utilizing any number of standard or proprietary protocols. Bluetooth® is a registered trademark owned by the Bluetooth® SIG.

[0039] As described above, processing unit 118 generates stimulation control signal 119. Stimulation control signal 119 (e.g., via lead 134) is provided to actuator 106 for delivering a mechanical stimulation signal to receiver 101. Figure 1C In the diagram, the mechanical stimulation signal (vibration signal or vibration) delivered to the receiver is indicated by arrow 121. Since actuator 106 delivers the mechanical stimulation signal to receiver 101, actuator 106 is sometimes referred to herein as a "mechanical stimulation device." Therefore, the middle ear auditory prosthesis 100 is sometimes referred to herein as a type of "mechanically stimulated auditory prosthesis." As described above, in Figure 1A-1C In the example, the mechanical stimulation device (actuator 106) was implanted in the recipient 101.

[0040] exist Figure 1C In the example, actuator 106 delivers vibration (mechanical stimulation signal) 121 to the recipient via the ossicular chain (ossicles) 136 (i.e., the bones of the middle ear, which include the malleus, incus, and stapes). That is, actuator 106 is physically connected to ossicle 136 via a connecting member 107 that moves (vibrates) in response to the vibration of actuator 106. Actuator 106 may be, for example, an electromagnetic or piezoelectric actuator with power consumption depending on the frequency.

[0041] Because the ossicle 136 is connected to the oval window (not shown) of the cochlea 138, the vibration imparted to the ossicle 136 by the actuator 106 will cause the oval window to hinge (vibrate) in response to that vibration. Similar to normal hearing, this vibration of the oval window establishes a fluid motion wave of the perilymph within the cochlea 138, which in turn activates the hair cells inside the cochlea 138. The activation of the hair cells enables the generation of appropriate nerve impulses, which are transmitted to the brain (also not shown) via the spiral ganglion cells (not shown) and the auditory nerve (not shown), where they are perceived as sound.

[0042] It should be understood that Figure 1B The arrangement of the actuator 106 mechanically coupled to the ossicle 136 shown is merely illustrative, and the techniques presented herein can be used with various mechanical stimulation devices. For example, in alternative embodiments, the actuator 106 may be directly coupled to the oval window, another opening in the cochlea 138 (e.g., a cochlear fenestration or circular window), an opening in the recipient's semicircular canals, or the recipient's skull. wait .

[0043] Figure 2A This is a perspective view of a percutaneous bone conduction device 200 that can be used with certain embodiments presented herein, and Figure 2B This is a schematic block diagram of a percutaneous bone conduction device 200. For ease of explanation, it will be described together. Figure 2A and2B .

[0044] Transcutaneous bone conduction device 200 Figure 2A The bone conduction device 200 is shown positioned behind the recipient's outer ear 203. It includes a housing 248 in which multiple functional components are located, and one or more sound input devices 244 are configured to receive input signals, such as acoustic sound signals (sound signals). Figure 2A and 2B In the example, one or more audio input devices 244 include two microphones positioned on the housing 248. However, the audio input device 244 may also or alternatively include, for example, a pickup coil, an audio port, a Universal Serial Bus (USB) port, or a wireless input (e.g., wireless streaming audio). wait It should also be recognized that one or more voice input devices 244 may be located, for example, within housing 248, on a cable extending from bone conduction device 200. wait .

[0045] like Figure 2B As shown, the bone conduction device 200 also includes an actuator 206, a processing unit 218, at least one battery 230 (e.g., at least one rechargeable battery or at least one disposable battery), a short-range wireless interface 233, and a user interface module 237.

[0046] The short-range wireless interface 233 can be, for example, a Bluetooth® interface, a Bluetooth® Low Energy (BLE) interface, or other interfaces utilizing any number of standard proprietary protocols. The user interface module 237 allows the receiver or other users to interact with the bone conduction device 200. For example, the user interface module 212 can allow the receiver to adjust volume, change voice processing strategies, and turn the device on / off. wait The user interface module 212 may also or alternatively include an indicator for status indication, such as a light-emitting diode (LED).

[0047] Processing unit 218 includes at least one processor 222 and a memory device (memory) 224. Memory 224 may include any one or more of the following: non-volatile memory (NVM), ferroelectric random access memory (FRAM), read-only memory (ROM), random access memory (RAM), disk storage media device, optical storage media device, flash memory device, electrical, optical, or other physical / tangible memory storage device. At least one processor 222 is, for example, a microprocessor or microcontroller that executes instructions for logic stored in memory 224. Processing unit 218 may be implemented, for example, on one or more printed circuit boards (PCBs).

[0048] Memory 224 includes sound processing logic 226 and battery monitoring logic 225. Sound processing logic 226, when executed by at least one processor 222, causes at least one processor 222 to perform the sound processing operations described herein (e.g., converting external acoustic sounds detected by sound input device 244 into stimulus control signals). As further described below, battery monitoring logic 225, when executed by at least one processor 222, causes at least one processor 222 to monitor the discharge of battery 230 based on estimated battery autonomy, and in some examples, initiates one or more operations based on battery monitoring.

[0049] It should be understood that Figure 2B The arrangement of the processing unit 218 is merely illustrative, and the techniques presented herein can be implemented with many different processing arrangements. For example, the sound processing unit 218 can be implemented using a processing unit formed by any one or a combination of the following: one or more processors (e.g., one or more digital signal processors (DSPs), one or more uC cores) arranged to perform operations such as those described herein. wait firmware, software wait Additionally, the processing unit 218 may include a charging circuit for charging / recharging the power supply 130 and a circuit for driving the actuator 206.

[0050] In operation, processing unit 118 generates a stimulation control signal based on the input signal detected / captured by sound input device 244. The stimulation control signal is provided to actuator 206 for delivering mechanical stimulation signal 221 to recipient 201 via anchoring system (fixation system) 252 configured to be implanted in the recipient's body. Figure 2A and 2B In one example, the anchoring system 252 includes a percutaneous abutment 254 fixed to the recipient’s skull 215 via a bone anchor (e.g., a bone screw) 256. The percutaneous abutment 254 extends from the skull 215 through tissue 213.

[0051] As shown in the figure, the bone conduction device 200 includes a coupling device 245 configured to attach to a percutaneous abutment 254. The coupling device 245 attaching to the percutaneous abutment 254 forms a mechanical connection between the actuator 206 and the skull, which facilitates the efficient transmission of a mechanical stimulation signal 221 to the skull 215. When applied to the skull 215, the mechanical stimulation signal 221 causes movement of fluid within the recipient's cochlea 238, which in turn induces auditory sensation (i.e., enables the recipient to receive the sound signal received at the sound input device 244). Because the actuator 206 delivers the mechanical stimulation signal to the recipient 201, the actuator 206 is sometimes referred to herein as a "mechanical stimulation device," and the bone conduction device 200 is sometimes referred to herein as a type of "mechanical stimulation auditory prosthesis." The actuator 206 may be, for example, an electromagnetic or piezoelectric actuator with power consumption depending on the frequency.

[0052] As described above, the middle ear hearing prosthesis 100 and the percutaneous bone conduction device 200 include at least one battery 130 and 230, which respectively provide operating power to other components of the respective devices. However, each battery 130 and battery 230 can only provide a limited amount of power to the other components of the respective devices. Subsequently, the respective battery 130 or battery 230 will need to be replaced (e.g., in the case of a disposable battery) or recharged (e.g., in the case of an integrated rechargeable battery). Integrated (built-in) rechargeable batteries are used with implantable components (e.g., the middle ear hearing prosthesis 100), while integrated rechargeable batteries are increasingly used in external devices, such as the percutaneous bone conduction device 200.

[0053] The total amount of energy a battery can store at any given time (usually measured in milliampere-hours (mAh) or milliwatt-hours (mWh)) is referred to herein as the battery's "capacity". The use of mWh to indicate energy capacity takes into account both current and battery voltage. When using mWh, batteries with different chemistry compositions can be compared equally, such as zinc-air (up to 1.45 V) and lithium-ion (up to 4.2 V).

[0054] The capacity of the battery within a device typically defines the time the device can operate before needing to recharge or replace the battery; this is sometimes referred to herein as the device's "runtime" or "battery autonomy." Therefore, a larger battery capacity generally results in longer battery autonomy (i.e., a larger capacity battery can typically power the device for a longer period). However, increasing battery capacity requires increasing battery size, which in turn increases device size. Therefore, a trade-off must be struck between battery capacity and battery size (and the corresponding device size). Furthermore, there is a general desire to keep devices as small as possible, thus imposing physical constraints on battery size and ultimately, battery capacity.

[0055] For certain medical devices, such as cochlear implants and other electrical stimulation prostheses, current consumption is relatively constant and independent of the properties of the input sound signal. Therefore, for electrical stimulation prostheses, the current draw / consumption of a particular prosthesis can be measured during a fitting / test session, and thus the battery autonomy of the electrical stimulation auditory prosthesis can be calculated. That is, the runtime of the electrical stimulation auditory prosthesis, or more precisely, how long the battery may last before needing to be recharged, can be calculated using only current measurements.

[0056] However, for medical devices / prosthetics with mechanical stimulation mechanisms (e.g., middle ear hearing prosthesis 100, transcutaneous bone conduction device 200, hearing aids) wait (Sometimes referred to herein as a "mechanical stimulation prosthesis"), the current consumption / outflow of the device (e.g., actuator) is highly dependent on the properties of the acoustic signal received and processed by the mechanical stimulation prosthesis to stimulate the recipient. Current consumption can depend on both the level (signal level or amplitude) and the frequency of the acoustic signal. Therefore, it is not possible to accurately estimate / predict the battery autonomy of a mechanical stimulation prosthesis using conventional techniques.

[0057] This paper presents a technique for estimating / predicting the battery autonomy of a particular mechanically stimulated auditory prosthesis when used by a specific recipient. Specifically, as further described below, the technique uses the recipient's "hearing prescription" or "operational procedure / diagram" and, in some embodiments, is based on supplementary recipient data, such as the recipient's environmental profile, to estimate the battery autonomy of the mechanically stimulated auditory prosthesis.

[0058] For ease of description, reference is generally made to bone conduction device 200 having rechargeable battery 230. Figure 2A and 2B Further details of the technology presented herein are described. It should be understood that reference to the bone conduction device 200 and its components is for illustrative purposes only, and the technology presented herein can be used with other types of implantable medical devices, such as the middle ear auditory prosthesis 100, percutaneous bone conduction devices, direct acoustic stimulators, and hearing aids. wait Use them together.

[0059] As described above, the current consumption of a mechanically stimulated auditory prosthesis, such as bone conduction device 200, can depend on both the frequency and level of the input sound signal received (and processed) by the mechanically stimulated auditory prosthesis. Figure 3A The diagram generally illustrates the correlation between this current consumption and the sound frequency and sound level.

[0060] More specifically, Figure 3AIt is a three-dimensional graph / chart showing the current consumed by the exemplary bone conduction device 200 as a function of both the frequency and level of the input sound signal received, processed, and converted into a mechanical stimulation signal by the bone conduction device 200. That is, Figure 3A This includes a first axis 360 and a second axis 362. The first axis shows the frequency of the input audio signal in Hertz (Hz), and the second axis shows the input signal level in Decibels (dBV). Additionally, Figure 3A Including a third axis 364, which illustrates the current consumption in milliamperes (mA) of an exemplary bone conduction device 200 as a function of frequency and signal level. As shown in the figure, in Figure 3A In the example, lower frequency sounds will consume / use more current than higher frequencies (except for the frequency band near the actuator's resonance), and higher sound levels will consume more current than lower sound levels.

[0061] Figure 3B This is a 3D graph / plot showing the frequency and level of the input sound signal as a function of both. Figure 3A The output level of the exemplary bone conduction device 200. That is, Figure 3B This includes a first axis 360 and a second axis 362. The first axis shows the frequency of the input audio signal in Hertz (Hz), and the second axis shows the input signal level in Decibels (dBV). Additionally, Figure 3B Including the third axis 366, which illustrates the output level of an exemplary bone conduction device 200 as a function of frequency and signal level, in decibels (dB, re: 1µN) relative to 1 micronewton. As shown in the figure, in Figure 3B In the example, lower frequency sounds will consume / use more current than higher frequencies (except for the frequency band near the actuator's resonance), and higher sound levels will consume more current than lower sound levels.

[0062] Figure 3A The reduction in current consumption around 800 Hz is shown. This reduction is due to the resonant frequency of the actuator 206 within the bone conduction device 200, at which the actuator 206 is most efficient. Similarly, although current consumption is very low around 800 Hz, Figure 3B The output level is shown to be strongest at the same frequency (800 Hz), which is again attributed to the resonant frequency of the actuator 206 below.

[0063] Figure 3A and 3BIn general, it is shown that in order to predict / estimate the battery autonomy of the bone conduction device 200 (or another mechanically stimulated auditory prosthesis), the operation of the device itself needs to be characterized as a function of both sound level and sound frequency (e.g., current consumption is determined as a function of sound level and sound frequency). The current consumption of the bone conduction device 200 (or another mechanically stimulated auditory prosthesis) as a function of both sound level and sound frequency is sometimes referred to herein as the “frequency sound level current consumption” of the bone conduction device 200.

[0064] Unlike electrically stimulated auditory prostheses, mechanical stimulation of the frequency sound level current consumption of an auditory prosthesis alone is insufficient to determine the estimated battery autonomy of the prosthesis when used by a particular recipient. Instead, as described below, the estimated battery autonomy is also based on the prosthesis's operating settings for a given recipient.

[0065] More specifically, different recipients of the bone conduction device 200 may have different types and / or levels of hearing loss (e.g., two recipients may have different levels of hearing loss in the lower frequency range). wait Therefore, the effectiveness of mechanically stimulated auditory prostheses and other auditory prostheses often depends on how well a particular prosthesis is configured for, or "fits" to, a particular recipient. For example, the "fitting" of an auditory prosthesis to a particular recipient (sometimes referred to as "programming" or "mapping") produces a set of recipient-specific operating settings (collectively and often referred to as the recipient's "hearing prescription" or "operational procedure / diagram") that defines the specific operating characteristics of the auditory prosthesis to convert sound signals into mechanical stimulation for delivery to the recipient. In the case of mechanically stimulated auditory prostheses, the fit determines, among other parameters, the frequency-dependent gain settings of the prosthesis (e.g., the gain used to drive the actuator at each of many frequency bands / regions). That is, since a recipient's hearing loss may be different at all frequencies, different gains can be used to drive the actuator at different frequency bands / regions (e.g., to amplify the sound signal). Other settings that may affect current consumption may include, for example, the applied sound compression (e.g., how much sound is compressed in the sound processing unit), LED settings, wireless streaming capabilities, wireless interface power amplification, or other settings that may affect the current consumption of the device. For example, in high-frequency sound compression, loud sounds are suppressed while low sounds are amplified. Generally, greater sound compression results in lower current consumption. Therefore, the applied compression level can be increased to reduce current consumption.

[0066] Because different recipients may have different types and / or levels of hearing loss, different recipients of the bone conduction device 200 may have different hearing prescriptions (e.g., device operation settings based on the recipient's hearing loss). Therefore, the hearing prescription for the recipient of the bone conduction device 200 (or other mechanically stimulating auditory prostheses) is sometimes referred to herein as a "recipient-specific hearing prescription".

[0067] According to certain embodiments presented herein, a recipient-specific hearing prescription associated with a recipient 201 of the bone conduction device 200 and the frequency sound level current consumption of the bone conduction device 200 can be used to estimate / predict the battery autonomy of the rechargeable battery 230. However, in some embodiments, the estimation / prediction of battery autonomy may also be based on data / information indicating / characterizing a typical “sound environment profile” or “environment profile” of the recipient. As used herein, a recipient’s sound environment profile is information indicating the type of sound environment(s)(s) the recipient is exposed to, and in some embodiments, is one or more quantitative measures indicating the recipient’s exposure to different sound environments (e.g., the time spent, rate, etc., in each environment). wait (Data). The audio environment profile may include, for example, the receiver's age, hobbies, living conditions, family details, and occupation. wait .

[0068] Accurately estimating / predicting the battery autonomy of a mechanostimulation auditory prosthesis, such as bone conduction device 200, is important to ensure that the battery autonomy is sufficient to operate the device substantially for a full day. That is, it is generally expected that a new disposable battery will provide the recipient with at least a full day of operation (i.e., a new disposable battery should power the bone conduction device for at least approximately 14-16 hours without requiring battery replacement). Similarly, it is generally assumed that the recipient is capable of charging his / her rechargeable battery overnight, and therefore, the goal is to provide the recipient with approximately a full day of operation on a single battery charge (i.e., a fully charged battery should power the bone conduction device for at least approximately 14-16 hours without requiring recharging).

[0069] For some recipients, the estimated battery autonomy determined according to the techniques presented herein may be insufficient to operate the device for a day. In such embodiments, the hearing prescription associated with the recipient (i.e., one or more settings of the bone conduction device 200) can be adjusted / changed to reduce the device's current consumption and correspondingly increase battery autonomy to ensure that the recipient does not lose hearing before the end of the day. For example, if battery autonomy is too short, the frequency-dependent gain setting, sound compression, etc., of the bone conduction device 200 can be adjusted. waitIn some such embodiments, the gain applied in certain frequency bands / regions that consume additional current (e.g., low frequencies) but are less important for speech recognition can be reduced. This reduction can be applied to all sound environments or a subset thereof.

[0070] Conversely, for some recipients, the estimated battery autonomy may be significantly greater than the battery autonomy required to operate the bone conduction device 200 for one day. In such embodiments, one or more settings of the bone conduction device 200 can be adjusted / altered to reduce the battery capacity (e.g., changing the termination voltage of the battery 230). Generally, higher-capacity batteries have shorter cycle lives than lower-capacity batteries. By reducing the battery capacity, the cycle life of the integrated rechargeable battery 230 can be increased.

[0071] Figure 4 This is a detailed flowchart illustrating various aspects of the method 468 of the technique proposed in this paper. Again, for ease of explanation, reference will be made to... Figure 2A and 2B Bone conduction device 200 Description method 468.

[0072] Method 468 begins at 470, where a computing device (e.g., a computer, mobile device, cooperative system, etc.) obtains the frequency sound level current consumption of the bone conduction device 200. That is, the computing device obtains data indicating the current consumed by the bone conduction device 200 when processing sound signals of different levels and frequencies. In some embodiments, the data indicating the current consumed by the bone conduction device 200 can be obtained from the bone conduction device itself (e.g., the device internally measures the current) or from another device. For example, the measuring device can be configured to determine the output force of the bone conduction device 200, and this data can be used to determine the current consumed by the bone conduction device 200 when processing sound signals of different levels and frequencies.

[0073] At 472, the computing device obtains data representing the hearing loss of a specific recipient 201, referred herein as recipient-specific hearing loss (hearing loss relative to frequency). Recipient-specific hearing loss may be determined by the computing device (e.g., during a cooperative session), obtained from the recipient's clinical records (e.g., determined by prior measurements), etc. In some embodiments, recipient-specific hearing loss may be represented by audiograms of one or both ears of recipient 201. An audiogram is a graph showing the audible thresholds of standardized frequencies as measured by an audiometer (e.g., a graphical representation of the relationship between sound frequency and minimum audible sound intensity).

[0074] At 474, recipient-specific hearing loss is used to generate / determine a recipient-specific hearing prescription associated with the recipient of the bone conduction device 200. As mentioned above, a recipient-specific hearing prescription refers to a set of operational settings of the bone conduction device 200 configured based on the recipient's hearing loss. Also as mentioned above, the hearing prescription may include, for example, frequency-dependent gain settings of the bone conduction device 200 for generating mechanical stimulation signals to be delivered to the recipient.

[0075] At 476, the computing device generates an estimate / prediction of the battery autonomy of the rechargeable battery 230 based at least on a recipient-specific hearing prescription and the frequency sound level current consumption of the bone conduction device 200. That is, when the bone conduction device 200 is operated according to a recipient-specific hearing prescription, an estimate of the operating time of the bone conduction device 200 is generated using the recipient-specific hearing prescription and the frequency sound level current consumption. See below for reference. Figure 5 Further details are provided regarding the generation of estimates of battery autonomy.

[0076] return Figure 4 At point 478, it is determined whether the estimated battery autonomy is suitable / appropriate for the recipient. Generally, determining whether the estimated battery autonomy is suitable for the recipient can take many different forms and can determine, for example, whether the battery autonomy is too short and / or too long. Determining that the battery autonomy is too short means that the battery autonomy may not be sufficient to power the bone conduction device 200 for one day (e.g., at least 16 hours). Determining that the battery autonomy is too long means that the battery autonomy is significantly greater than the battery autonomy required to power the bone conduction device 200 for one day.

[0077] In some examples, the operation at 478 may include estimating battery autonomy against one or more threshold time levels. For example, the operation at 478 may include comparing the estimated battery autonomy against a minimum battery autonomy threshold (e.g., 16 hours), and / or comparing the estimated battery autonomy against a maximum battery autonomy threshold (e.g., 24 hours). Estimating battery autonomy is appropriate if the estimated battery autonomy is below the maximum battery autonomy threshold but above the minimum battery autonomy threshold.

[0078] More generally, determining at point 478 may include determining whether the estimated battery autonomy is greater than at least a first time threshold. In other embodiments, determining at point 478 may include determining whether the estimated battery autonomy is greater than at least a first time threshold and less than at least a second time threshold.

[0079] exist Figure 4In the example, if it is determined at 478 that the estimated battery autonomy is suitable for the recipient, method 468 proceeds to 480, where the bone conduction device 200 is programmed / configured using a recipient-specific hearing prescription. That is, at 480, a recipient-specific hearing prescription is instantiated in the bone conduction device 200 for subsequent use by the recipient. However, if it is determined at 478 that the estimated battery autonomy is unsuitable for the recipient, method 468 proceeds to 482. At 482, the computing device generates an adjusted recipient-specific hearing prescription based on the result of determining whether the estimated battery autonomy is suitable and, in some embodiments, based on one or more inputs from a user (e.g., a hearing expert).

[0080] The generation of an adjusted recipient-specific hearing prescription may depend on whether the estimated battery autonomy (at 478) is determined to be too short or too long. For example, if the estimated battery autonomy is determined to be too short, the recipient-specific hearing prescription can be adjusted by reducing the current consumption / power consumption of the bone conduction device 200. In some such embodiments, the frequency-dependent gain setting for driving the actuator 206 to generate the mechanical stimulation signal can be adjusted in certain frequency regions. In the same or other embodiments, certain features of the bone conduction device 200 can be disabled, and the applied sound compression can be adjusted. wait If the estimated battery autonomy is determined to be too long, the capacity of the rechargeable battery 230 can be reduced (e.g., by changing the battery's termination voltage). It should be noted that a receiver with initial low current requirements may accept a reduced charging termination voltage, but this reduction may need to be removed or adjusted in the future if the device's current requirements change.

[0081] After generating the adjusted recipient-specific hearing prescription, method 468 returns to 476, where an updated estimate of battery autonomy (updated estimated battery autonomy) is generated using the adjusted recipient-specific hearing prescription and the frequency sound level current consumption of the bone conduction device 200. This updated estimated battery autonomy is analyzed at 478 in a manner similar to that described above to determine whether the updated estimated battery autonomy is suitable for the recipient.

[0082] Next, if the updated estimate of battery autonomy is appropriate, the method terminates at 480, where the bone conduction device 200 is programmed / configured using an adjusted recipient-specific hearing prescription. Otherwise, method 468 returns to 482 to generate another adjusted recipient-specific hearing prescription. Operations 482, 476, and 478 are repeated until it is determined that the updated estimate of battery autonomy is appropriate, and accordingly, at 480, the bone conduction device 200 is programmed using the corresponding adjusted recipient-specific hearing prescription. In some examples, 482, 476, and 478 may need to be iterated several times before acceptable battery autonomy is achieved.

[0083] It should be understood that method 468 is merely illustrative, and the various operations can be performed in different combinations and / or sequences. For example, in some embodiments, a battery autonomy estimate can be generated using a recipient-specific hearing prescription (e.g., combining 476 with 474 and 482). In such embodiments, the estimated battery autonomy, or data associated therewith, can be displayed in real time to a user (e.g., a hearing expert) via a display screen of a computing device. For example, when the computing device (e.g., in response to user input) adjusts the recipient-specific hearing prescription, the user can again see the updated estimated battery autonomy on the screen in real time. For example, the user can change the frequency-dependent gain setting of the bone conduction device 200, and the computing device can determine and display the resulting updated estimated battery autonomy in real time. In this way, the need to cycle through 476, 478, and 482 can be eliminated.

[0084] As mentioned above, Figure 5 This is a schematic diagram illustrating further details regarding the generation / determination of estimated battery autonomy according to certain embodiments presented herein. Specifically, Figure 5 The diagram illustrates different input data that can be used to generate estimates of battery autonomy. The generation / determination of estimates of battery autonomy is discussed in... Figure 5 The general shape is represented by box 585, and the estimated battery autonomy obtained is... Figure 5 The middle part is roughly represented by box 586.

[0085] like Figure 5 As shown, estimated battery autonomy can be generated based on multiple different input data from multiple different sources. Specifically, as mentioned above, estimated battery autonomy is generated at least based on the recipient-specific hearing prescription and the frequency sound level current consumption of the bone conduction device 200. Figure 5 In the diagram, the recipient-specific hearing prescription is represented by box 587, while the frequency sound level current consumption of the bone conduction device 200 is represented by box 588.

[0086] Frequency sound level current consumption 588 (current characterization) can be determined, for example, during the design and development of the bone conduction device, or during device manufacturing. Current consumption can be measured in many different ways, including at different frequencies, at different signal levels, and using sound files representing different acoustic environments.

[0087] like Figure 5 As shown, in some embodiments, the estimated battery autonomy can also be generated based on the receiver's "acoustic environment profile." Figure 5In the diagram, the receiver's acoustic environment profile is represented by box 589. As mentioned above, the receiver's acoustic environment profile is used to estimate the types of acoustic environments the receiver is exposed to daily, and in some embodiments, it estimates the receiver's daily exposure to these acoustic environments (e.g., the frequency at which the receiver may be exposed to a particular acoustic environment, and the amount of time the receiver may spend in a particular acoustic environment each day). wait Personal data / information of the recipient. The audio environment profile may include, for example, the recipient's age, gender, hobbies, ethnicity, living situation, family details, and occupation. wait .

[0088] For example, a profile of a school-aged child's auditory environment could indicate how many 7 hours she typically spends at school each day (e.g., listening to lectures, talking with classmates). wait One example is watching streaming video for one hour daily, participating in physical activity for one hour daily, and the remaining data being taken in a home environment with siblings. In contrast, an older adult's sound environment profile might indicate spending 1-2 hours watching television, 1-2 hours talking, and being relatively quiet for the rest of the day. Generally, various pieces of information about the recipient's daily routine can be used to generate a sound environment profile. Furthermore, more extensive information about the recipient's daily routine will produce a more accurate sound environment profile and ultimately a more accurate estimate of battery autonomy.

[0089] In some embodiments, estimated battery autonomy may also be generated based on battery data 591. Battery data 591 may include, for example, battery capacity and cycle life (e.g., the number of complete charge / discharge cycles a battery can support before its capacity drops below a certain threshold of its initial capacity and becomes insufficient to achieve its intended purpose). wait For new devices, battery capacity or cycle life can be obtained from the battery manufacturer. However, if the battery has been used for some time (e.g., in the case of refitting), it may be necessary to estimate or calculate the battery capacity or cycle life in some way. For example, if the recipient has low current requirements during the first fit, the battery capacity may have been intentionally reduced by lowering the charge termination voltage to obtain more charging cycles. When the recipient returns for refitting (possibly via remote fitting), it may be necessary to increase that charge termination voltage again. Battery capacity or cycle life can each be estimated or calculated in a variety of different ways. For example, some embodiments may determine the "battery days" (e.g., the number of days the battery has been used) of the bone conduction device and analyze that date based on manufacturer data to determine the current battery capacity or cycle life. The number of charge / discharge cycles may also be tracked, and remaining capacity, lifespan, and battery health can be calculated directly. wait .

[0090] In some embodiments, estimated battery autonomy can also be generated based on recorded data obtained from other receivers. Figure 5 In this context, recorded data obtained from other recipients is represented by box 590 and referred to as "previous recipient data." More specifically, certain medical devices, such as bone conduction device 200, can be configured to collect (record) data while a recipient is using the medical device. The resulting recorded data may include, for example, data related to the recipient's acoustic environment and measures indicating the recipient's daily exposure to various acoustic environments. This recorded data can be combined with data about the recipient (e.g., hearing prescriptions, age, hobbies, occupation, etc.) to form previous recipient data 590. Previous recipient data 590 can be depersonalized (e.g., recipient identification data is erased) and stored in a database of previous recipient data, which can be used to match other recipients with similar hearing prescriptions and / or similar acoustic environment profiles.

[0091] A database of prior recipient data, comprised of data from numerous recipients, is created over time and ultimately analyzed during the battery autonomy estimation process. In these embodiments, analyzing prior recipient data 590 from other recipients with similar hearing prescriptions and / or similar acoustic environment profiles allows for better prediction of which acoustic environments a recipient is exposed to daily, which correspondingly improves the accuracy of the estimated battery autonomy 596. The more recipients with similar profiles, the better the prediction of the estimated battery autonomy 596. This type of data can be important, for example, when a new recipient is first fitted with the bone conduction device 200.

[0092] Finally, in some embodiments, the estimated battery autonomy can also be generated based on recorded data obtained from a particular recipient's use of the bone conduction device 200 (i.e., data recorded by the recipient themselves). Figure 5 In this context, the recorded data obtained from the recipient's use of the bone conduction device 200 is represented by box 592 and referred to as "recorded recipient data." That is, when the recipient is permitted to use the bone conduction device 200, the bone conduction device 200 can record data (e.g., statistical data) indicating what sound environments, sound levels, etc., a particular recipient is exposed to daily (e.g., data related to the recipient's sound environments and exposure to various sound environments since the previous interaction session). This data may include the type of sound environment, the time spent in each environment, the sound level, the frequency, and characteristics. wait The recording of receiver data can be implemented as part of battery monitoring logic 225.

[0093] For example, the recorded receiver data 592 can be used when a receiver returns to the hearing specialist after one or more previous / previously co-co ...

[0094] exist Figure 5 In the example, if one, two, three, etc., different types of input data are available (e.g., 588, 589, 590, 591, and / or 592), the different input data can be added to the battery autonomy estimate with different weights. For example, the sound environment profile 589 can be weighted in one way, while previous receiver data 590 (e.g., data recorded from other receivers) can be weighted in another way. Recorded receiver data 592 can be weighted with a relatively higher importance than previous receiver data 590.

[0095] Generally, the accuracy of battery autonomy estimation / prediction for mechanostimulatory auditory prostheses such as bone conduction device 200 will depend on the actual acoustic environment experienced by the recipient. Therefore, it may be impossible to accurately predict how long the battery will last on any given day, especially if the recipient is exposed to unexpected acoustic environments or acoustic conditions that differ from the typical acoustic environment profile. Typically, the battery will last for shorter periods on some days and longer periods on others. Therefore, mechanostimulatory auditory prostheses according to embodiments presented herein, such as bone conduction device 200, may include additional battery support features, such as advanced low-battery warning systems or dedicated programs for different situations. For example, the device may be prepared in conjunction with a special low-current program that can be used when the recipient knows he / she will need to operate the device for an extended period (e.g., while traveling, staying up all night to watch the Olympics on the other side of the world, etc.).

[0096] In some such embodiments, an advanced low-battery warning system, which may be implemented as part of battery monitoring logic 225, knows the initial estimated battery autonomy and is configured to monitor the discharge of battery 230 (e.g., dynamically determine / estimate remaining battery autonomy throughout the day). That is, bone conduction device 200 may include functionality that knows the estimated battery autonomy and is configured to monitor the discharge of battery 230. Thus, bone conduction device 200 can warn the recipient (or parent or caregiver) when, for example, the remaining battery autonomy falls below a threshold level, or when the battery is discharging too quickly.

[0097] Although described as part of the bone conduction device 200, battery support functionality can also be built into an external device (e.g., a smartphone application) that operates with the bone conduction device 200. In such embodiments, the external device can receive data from the bone conduction device 200 for monitoring the battery 230. In any case, the bone conduction device 200 and / or the external device can enable the recipient or other user to take one or more actions to increase the autonomy of the remaining battery (e.g., temporarily adjusting the gain setting at a specific frequency).

[0098] As described above, in some embodiments, the estimated battery autonomy can be determined at a computing device (e.g., a desktop computer, laptop computer, tablet computer, mobile phone, cooperating system, etc.). Figure 6 An exemplary computing device 670, which can be used to determine the estimated battery autonomy of a recipient according to certain embodiments presented herein, is shown. As shown, the computing device 670 includes a plurality of interfaces / ports 678(1)-678(N), a memory device (memory) 680, at least one processor 684, and a user interface 686.

[0099] Interfaces 678(1)-678(N) may include, for example, network ports (e.g., Ethernet ports), wireless network interfaces, universal serial bus (USB) ports, IEEE 1394 interfaces, PS / 2 ports, etc. wait Any combination of. Figure 6 In the example, interface 678(1) is connected to bone conduction device 200. Interface 678(1) can be directly connected to bone conduction device 200 and can be configured to communicate with bone conduction device 200 via wired or wireless connection (e.g., telemetry, Bluetooth, etc.).

[0100] User interface 686 includes one or more output devices, such as a liquid crystal display (LCD) and speakers, for presenting visual or auditory information to clinicians, audiologists, or other users. User interface 686 may also include one or more input devices, such as a keypad, keyboard, mouse, or touchscreen. wait .

[0101] Memory 680 includes cooperating logic 681 and battery autonomy logic 683. Memory 680 may include any one or more of the following: non-volatile memory (NVM), ferroelectric random access memory (FRAM), read-only memory (ROM), random access memory (RAM), disk storage media device, optical storage media device, flash memory device, electrical, optical, or other physical / tangible memory storage device. At least one processor 122 is, for example, a microprocessor or microcontroller that executes instructions for logic stored in memory device 124. Processing unit 118 may be implemented, for example, on one or more printed circuit boards (PCBs).

[0102] At least one processor 684 is, for example, a microprocessor or microcontroller that executes instructions for cooperating with logic 681 and battery autonomy logic 683. Therefore, generally, memory 680 may include one or more tangible (non-transitory) computer-readable storage media (e.g., memory devices) encoded with software including computer-executable instructions, and when the software is executed (by processor 684), it is operable to perform the techniques described herein.

[0103] As mentioned above, Figure 1A-1C Figures 2A-2B illustrate two suitable configurations of medical devices in which the techniques described herein can be implemented. It should be understood that these two arrangements are illustrative, and the techniques described herein can be implemented in a variety of other medical device configurations and / or other contexts. For example, embodiments of the techniques proposed herein can be used with other auditory prostheses, including other bone conduction devices, other middle ear prostheses, hearing aids, direct acoustic stimulators, electroacoustic prostheses, cochlear implants, auditory brain stimulators, etc. The techniques proposed herein can also be used with tinnitus treatment devices, vestibular devices (e.g., vestibular implants), 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, and electroporation devices. wait Use them together.

[0104] For example, Figure 7 This is a schematic diagram illustrating an exemplary percutaneous bone conduction device 700, some embodiments of which are implemented using the exemplary percutaneous bone conduction device. The percutaneous bone conduction system 700 includes an external device / component 750 and an implantable component 712. The percutaneous bone conduction device 700 is an active percutaneous bone conduction device, meaning that a mechanical stimulation device (e.g., an actuator 706) is located within the implantable component 712. Specifically, the actuator 706 is located within the housing 728 of the implantable component 712.

[0105] External device 750 includes one or more sound input devices 744 that convert sound into electrical signals. Specifically, a percutaneous bone conduction device 700 provides these electrical signals to an actuator 706, or to a sound processor (not shown) that processes the electrical signals, and then provides those processed signals to an implantable component 712 via a magnetic induction link through the recipient's skin. In this regard, a transmitter coil 742 of external device 750 sends these signals to an implantable receiver coil 756 located in implantable component 712. Components (not shown) in housing 728 (e.g., a signal generator or implantable sound processor) then generate an electrical signal to be delivered to actuator 706 via electrical lead assembly 760. Actuator 706 converts the electrical signal into vibrations.

[0106] Actuator 706 is mechanically coupled to housing 728. Housing 728 is substantially rigidly attached to bone fixation device 746. In this regard, housing 728 includes through-hole 762, the outline of which is conformed to the outer contour of bone fixation device 746. Housing screws 764 are used to secure housing 728 to bone fixation device 746. In this way, actuator 706 is able to deliver mechanical stimulation signals to the skull 715 of the recipient.

[0107] Figure 8 An exemplary embodiment of a percutaneous bone conduction device 800 is illustrated, which can be implemented using the percutaneous bone conduction device presented herein. In this example, the percutaneous bone conduction device 800 includes an external device / component 850 and an implantable component 812 implanted beneath the recipient's tissue (e.g., skin, fat, muscle). Figure 8 The percutaneous bone conduction device 800 is a passive percutaneous bone conduction device, meaning that the actuator 806 is located in the external device 850 (i.e., not implanted in the recipient).

[0108] More specifically, the actuator 806 is located within the housing 841 of the external component and is coupled to the plate 846. The plate 846 may be in the form of a permanent magnet and / or in another form that generates and / or responds to a magnetic field, or otherwise allows the establishment of a magnetic attraction between the external device 850 and the implantable component 812 sufficient to keep the external device 850 in contact with the recipient's skin.

[0109] In an exemplary embodiment, the vibration actuator 806 is a device that converts electrical signals into vibrations. In operation, one or more sound input elements 844 convert sound signals into electrical signals. Specifically, a transcutaneous bone conduction device 800 provides these electrical signals to the actuator 806, or to a sound processor (not shown) that processes the electrical signals, and then provides these processed signals to the actuator 806. The actuator 806 converts the electrical signals (processed or unprocessed) into vibrations. Because the actuator 806 is mechanically coupled to the plate 846, vibrations are transmitted from the actuator 806 to the plate 846. The implantable plate assembly 852 is part of the implantable component 812 and is made of a ferromagnetic material, which in some embodiments may be in the form of a permanent magnet that generates and / or responds to a magnetic field, or otherwise allows for the establishment of a magnetic attraction between the external device 850 and the implantable component 812 sufficient to keep the external device 850 in contact with the recipient's skin. Therefore, the vibrations generated by the actuator 706 are transmitted from plate 846 through the skin to plate 855 of the implantable plate assembly 852. This can be achieved through mechanical conduction through the skin due to vibrations caused by direct contact between the external device 850 and the skin and / or by the magnetic field between the two plates. These vibrations are transmitted without the need for a solid object to penetrate the skin, such as an abutment as detailed above with respect to percutaneous bone conduction devices.

[0110] As can be seen, in this embodiment, the implantable plate assembly 852 is substantially rigidly attached to the bone fixation device 847. In this regard, the implantable plate assembly 852 includes a through-hole 854 profiled to conform to the outer profile of the bone fixation device 847. Therefore, the through-hole 854 forms a bone fixation device interface segment profiled to conform to an exposed section of the bone fixation device 847. In an exemplary embodiment, the size and dimensions of the segment are set such that there is at least a sliding fit or an interference fit relative to the segment. Plate screws 856 are used to secure the implantable plate assembly 852 to the bone fixation device 847. Figure 8 As can be seen, the head of the plate screw 856 is larger than the hole through the implanted plate assembly 852, and therefore the plate screw 856 securely holds the implanted plate assembly 852 to the bone fixation device 847.

[0111] The embodiments described above have been generally referred to as auditory prostheses that directly and mechanically stimulate the recipient using vibrations (e.g., the physical path between the actuator and the recipient's body). However, as mentioned above, the techniques can also be implemented in hearing aids or other auditory prostheses that indirectly and mechanically stimulate the recipient using acoustic stimulation signals. Specifically, some hearing aids include actuators in the form of "receivers" that emit acoustic signals that stimulate the recipient via the tympanic cavity, ossicular chain, etc. In such embodiments, the actuator (receiver) has a current consumption that depends on the frequency (and possibly the sound level). Therefore, as used herein, the term "mechanically stimulated auditory prosthesis" includes acoustic hearing aids, and the term "actuator" includes the receiver of such acoustic hearing aids.

[0112] Figure 9 This is a flowchart of method 990 according to some embodiments presented herein. Method 990 begins at 992, where a computing device obtains a hearing prescription associated with a recipient of a mechanically stimulated auditory prosthesis, wherein the mechanically stimulated auditory prosthesis is configured to be powered by at least one battery. At 994, the computing device determines an estimated battery autonomy of the mechanically stimulated auditory prosthesis based on the hearing prescription and the frequency sound level current consumption of the mechanically stimulated auditory prosthesis.

[0113] Figure 10 This is a flowchart of method 1090 according to certain embodiments presented herein. Method 1090 begins at 1092, where a computing device determines a first set of operating settings for a battery-powered auditory prosthesis including at least one actuator. The first set of operating settings is determined based on characteristics of the recipient of the auditory prosthesis. At 1094, the computing device obtains data indicating frequency-dependent current consumption of at least the auditory prosthesis. At 1096, the computing device obtains an acoustic environment profile associated with the recipient of the auditory prosthesis. At 1098, the computing device determines an estimated battery autonomy of the auditory prosthesis based on the first set of operating settings, the data indicating frequency-dependent current consumption of the auditory prosthesis, and the acoustic environment profile associated with the recipient.

[0114] It should be understood that the embodiments presented herein are not mutually exclusive, and various embodiments can be combined with one embodiment in any of a variety of different ways.

[0115] The invention described and claimed herein is not limited in scope to the specific preferred embodiments disclosed herein, as these embodiments are intended to be illustrative rather than limiting of several aspects of the invention. Any equivalent embodiments are intended to be within the scope of the invention. In fact, various modifications to the invention will become apparent to those skilled in the art from the foregoing description, in addition to those shown and described herein. Such modifications are also intended to fall within the scope of the appended claims.

Claims

1. A method for estimating battery autonomy, comprising: Obtaining a hearing prescription associated with a recipient of a mechanically stimulated auditory prosthesis, wherein the mechanically stimulated auditory prosthesis is configured to be powered by at least one battery; and The estimated battery autonomy of the mechanically stimulated auditory prosthesis is determined based on the hearing prescription and the frequency sound level current consumption of the mechanically stimulated auditory prosthesis, wherein the frequency sound level current consumption is defined as the current consumption of the mechanically stimulated auditory prosthesis as a function of both sound level and sound frequency.

2. The method according to claim 1, further comprising: The mechanical stimulation auditory prosthesis is configured based on the estimated battery autonomy.

3. The method according to claim 1, further comprising: Obtain data indicating the recipient's hearing loss; as well as A hearing prescription for the recipient is generated based on data indicating the recipient's hearing loss.

4. The method according to claim 3, wherein, Obtaining data indicating the recipient's hearing loss includes: Obtain an audiogram of the hearing loss in at least the first ear of the recipient.

5. The method according to claim 1, further comprising: Determine whether the estimated battery autonomy is suitable for the recipient.

6. The method according to claim 5, wherein, Determining whether the estimated battery autonomy is suitable for the recipient includes: Determine whether the estimated battery autonomy is greater than a first time threshold.

7. The method according to claim 6, wherein, Determining whether the estimated battery autonomy is suitable for the recipient also includes: Determine whether the estimated battery autonomy is less than a second time threshold.

8. The method according to claim 5, wherein, Determining that the estimated battery autonomy is unsuitable for the recipient, and wherein the method includes: Based on the estimated battery autonomy, an adjusted hearing prescription is determined for the recipient.

9. The method according to claim 8, further comprising: Based on the adjusted hearing prescription associated with the recipient and the frequency sound level current consumption of the mechanical stimulation auditory prosthesis, the adjusted estimated battery autonomy of the mechanical stimulation auditory prosthesis is determined.

10. The method according to claim 8, wherein, Determining the adjusted hearing prescription associated with the recipient includes: Adjust one or more frequency-dependent gain settings of the mechanical stimulation auditory prosthesis.

11. The method according to claim 1, further comprising: Determine the receiver's acoustic environment profile; as well as The estimated battery autonomy is determined based on the hearing prescription, the frequency sound level current consumption of the mechanical stimulation auditory prosthesis, and the recipient's acoustic environment profile.

12. The method of claim 11, further comprising: Obtain prior recipient data associated with other recipients of other mechanically stimulated auditory prostheses; as well as The estimated battery autonomy is determined based on the hearing prescription, the frequency sound level current consumption of the mechanical stimulation auditory prosthesis, the recipient's acoustic environment profile, and the previous recipient data.

13. The method of claim 12, further comprising: Record recipient data associated with the recipient's use of the mechanical stimulation auditory prosthesis during a given time period; A detailed profile of the receiver's acoustic environment is determined based on the recorded receiver data; as well as The adjusted estimated battery autonomy is determined based on the hearing prescription, the frequency sound level current consumption of the mechanical stimulation auditory prosthesis, and the refined sound environment profile.

14. The method of claim 13, further comprising: The mechanical stimulation auditory prosthesis is programmed based on the adjusted estimated battery autonomy.

15. One or more non-transitory computer-readable storage media, comprising instructions operable, when executed by at least one processor, to: A first set of operating settings is obtained for a battery-powered medical device having at least one actuator, wherein... The first set of operation settings is determined based on the characteristics of the recipient of the medical device; Obtain data indicating frequency-dependent current consumption of at least one of the actuators; as well as The estimated operating time of the medical device when operating according to the first set of operating settings is predicted based on data indicating the frequency-dependent current consumption of the at least one actuator.

16. The one or more non-transitory computer-readable storage media of claim 15, further comprising instructions operable to perform the following operations: Obtain data indicating the current consumption of the at least one actuator, depending on the sound level; and Based on data indicating frequency-dependent current consumption of the at least one actuator and data indicating sound level-dependent current consumption of the at least one actuator, the estimated operating time of the medical device when operating according to the first set of operation settings is predicted.

17. One or more non-transitory computer-readable storage media according to claim 15, wherein, The medical device is an auditory prosthesis, and wherein the one or more non-transitory computer-readable storage media further include instructions operable to perform the following operations: Obtain data indicating the recipient's hearing loss; and The first set of operating settings is determined based on data indicating the recipient's hearing loss.

18. The one or more non-transitory computer-readable storage media of claim 15, further comprising instructions operable to perform the following operations: Determine whether the estimated runtime is suitable for the recipient.

19. One or more non-transitory computer-readable storage media according to claim 18, wherein, Instructions operable to determine whether the estimated runtime is suitable for the recipient include instructions operable to perform the following operations: Determine whether the running time is greater than a first time threshold.

20. One or more non-transitory computer-readable storage media according to claim 19, wherein, Instructions operable to determine whether the estimated runtime is suitable for the recipient include instructions operable to perform the following operations: Determine whether the running time is less than the second time threshold.

21. One or more non-transitory computer-readable storage media according to claim 18, wherein, Determining that the estimated runtime is suitable for the recipient, and wherein the one or more non-transitory computer-readable storage media further include instructions operable to perform the following operations: Configure the medical device based on the estimated runtime.

22. The one or more non-transitory computer-readable storage media according to claim 18, wherein, Determining that the estimated runtime is unsuitable for the recipient, and wherein the one or more non-transitory computer-readable storage media further include instructions operable to perform the following operations: Based on the estimated runtime, a second set of operational settings for the medical device is determined; and Based on data indicating frequency-dependent current consumption of the at least one actuator, the adjusted estimated operating time of the medical device when operating according to the second set of operating settings is predicted.

23. One or more non-transitory computer-readable storage media according to claim 22, wherein, The instructions operable to determine a second set of operational settings for the medical device include instructions operable to perform the following operations: Adjust one or more frequency-dependent gain settings of the medical device between the first set of operating settings and the second set of operating settings.

24. The one or more non-transitory computer-readable storage media of claim 15, further comprising instructions operable to perform the following operations: Obtain the environmental profile of the recipient; and Based on frequency-dependent current consumption data indicating the at least one actuator and the environmental profile of the recipient, the estimated operating time of the medical device when operating according to the first set of operating settings is predicted.

25. One or more non-transitory computer-readable storage media according to claim 24, wherein, The recipient's environmental profile refers to the recipient's acoustic environment profile.

26. The one or more non-transitory computer-readable storage media of claim 24, further comprising instructions operable to perform the following operations: Obtain prior recipient data associated with other recipients of other medical devices; and Based on frequency-dependent current consumption data indicating the at least one actuator, the recipient's environmental profile, and previous recipient data, the estimated runtime of the medical device when operating according to the first set of operating settings is predicted.

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