Charging control

Abstract

Presented herein are techniques to control charging signals for a rechargeable battery in a first medical device in response to interference detected at a second medical device.

Description

Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1CHARGING CONTROLBACKGROUNDField of the Invention[ooot] The present invention relates generally to techniques for controlling a charging profile for an implantable medical device.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: establishing a communication link between a first charging device configured to charge a first implantable medical device implanted in a recipient and a second charging device configured to charge a second implantable device implanted in the recipient; detecting, at the second implantable device, interference caused by the first charging device charging the first implantable medical device; in response to detecting the interference, sending by the second charging device, viaAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 the communication link, an indication of the interference; and in response to receiving the indication, the first charging device modifying a charging profile according to which the first charging device charges the first implantable medical device.

[0005] In another aspect, a bilateral implantable medical device system is provided. The bilateral implantable medical device system comprises: a first external component configured to send first charging signals to a first implantable device; and a second external component configured to send second charging signals to a second implantable device, wherein the second external component is configured to alert the first external component of interference detected by the second implantable device, and, in response, the first external component is configured to adjust a parameter of the first charging signals.

[0006] In another example, a medical system is provided. The medical system comprises: a first battery charger configured to wirelessly charge a first implantable device and having a plurality of charging modes; a second battery charger configured to wirelessly charge a second implantable device; and a wireless communication link between the first battery charger and the second battery charger, wherein the wireless communication link is configured to notify the first battery charger to switch between a first one of the plurality of charging modes and a second one of the plurality of charging modes.

[0007] In another example, a battery charging control system is provided. The battery charging control system comprises: a first device having a rechargeable battery and a charging device configured to supply first charging signals to the first device to charge the rechargeable battery; and a second device, proximate the first device, and including components that wireless communicate with one another over a first wireless link, wherein the second device is configured to notify the charging device to change the first charging signals to second charging signals when the second device detects interference of the first wireless link as a result of the first charging signals.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 view of a cochlear implant system in which embodiments presented herein can be implemented;Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1[ooto] FIG. IB is a side view of a recipient wearing the cochlear implant system of FIG. 1A;[ooit] FIG. 1C is a schematic view of the components of the cochlear implant system of FIG. 1A;

[0012] FIGs. ID and IE are block diagrams of cochlear implants forming part of the cochlear implant system of FIG. 1A;

[0013] FIG. 2A is schematic diagram of a bilateral cochlear implant system in which battery charging control can be implemented;

[0014] FIG. 2B is a schematic diagram of another bilateral cochlear implant system in which battery charging control can be implemented;

[0015] FIG. 3 is a functional block diagram of selected components of the bilateral systems of FIG. 2A or FIG. 2B;

[0016] FIG. 4 is a timing diagram showing a first charging profile and a second charging profile according to which a charging device charges a battery of an implantable device;

[0017] FIG. 5 is another timing diagram showing a first charging profile and a second charging profile according to which a charging device charges a battery of an implantable device;

[0018] FIG. 6 is yet another timing diagram showing a first charging profile and a second charging profile according to which a charging device charges a battery of an implantable device;

[0019] FIG 7 is a flowchart illustrating a process for controlling a charging profile of a charging device;

[0020] FIG. 8 is a schematic diagram illustrating a vestibular stimulator system 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 controlling the charging of a power source, such as a rechargeable battery, of a first implantable medical device based on information / data received from a second implantable medical device. More specifically, in accordance with embodimentsAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 presented herein, both of a first implantable medical device and a second implantable medical device are implanted in a recipient, and a first charging device is configured to charge the first implantable medical device, while a second charging device configured to charge a second implantable device implanted in the recipient. At least one of the second charging device or the second implantable device detects interference caused by the first charging device charging the first implantable medical device. In response to detecting the interference, the second charging device sends an indication of the interference to the first charging device. In response to receiving the indication, the first charging device modifies a charging profile according to which the first charging device charges the first implantable medical device (e.g., the first charging device adjusts / changes one or more parameters of charging signals provided to the first implantable medical device. In one embodiment, the charging profile includes a fastcharging mode and the modification to the charging provide can comprise switching to a different charging mode (e.g., a charging mode that results in relatively slower charging).

[0023] There are a number of different types of devices in / with which embodiments of the present invention can be implemented. However, for ease of illustration, the techniques presented herein are primarily described with reference to hearing device systems comprises of at least two devices that operate to convert sound signals into one or more acoustic, mechanical, and / or electrical stimulation signals for delivery to a user / recipient. The one or more hearing devices that can form part of a hearing device system include, for example, one or more personal sound amplification products (PSAPs), hearing aids, cochlear implants, middle ear stimulators, bone conduction devices, brain stem implants, electro-acoustic cochlear implants or electro-acoustic devices, and other devices providing acoustic, mechanical, and / or electrical stimulation to a recipient.

[0024] One specific type of hearing device system, referred to herein as a “binaural hearing device system” or more simply as a “binaural system,” includes two hearing devices, where one of the two hearing devices is positioned at each ear of the recipient. More specifically, in a binaural system each of the two hearing devices provides stimulation to one of the two ears of the recipient (i.e., either the right or the left ear of the recipient). The binaural system can include any combination of one or more personal sound amplification products (PSAPs), hearing aids, middle ear auditory prostheses, bone conduction devices, direct acoustic stimulators, electro-acoustic prostheses, auditory brain stimulators, cochlear implants, combinations or variations thereof, etc., The techniques presented herein can be implemented with any of a number of other types of systems, including balance prostheses (e.g., vestibularAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 implants), retinal or other visual prostheses, cardiac devices (e.g., implantable pacemakers, defibrillators, etc.), seizure devices, sleep apnea devices, electroporation devices, spinal cord stimulators, deep brain stimulators, motor cortex stimulators, sacral nerve stimulators, pudendal nerve stimulators, vagus / vagal nerve stimulators, trigeminal nerve stimulators, diaphragm (phrenic) pacers, pain relief stimulators, other neural, neuromuscular, or functional stimulators, etc. In further embodiments, the presented herein can also be implemented by, or used in conjunction with, systems comprising remote microphone devices, consumer electronic devices, etc.

[0025] In certain examples, aspects of the techniques will be generally described with reference to a specific system, namely a bilateral cochlear implant system. As used herein, a “bilateral cochlear implant system” is a specific type of binaural system that includes first and second cochlear implants located at first and second ears, respectively, of a recipient. In such systems, each of the two cochlear implant system delivers stimulation (current) pulses to one of the two ears of the recipient (i.e., either the right or the left ear of the recipient). In a bilateral cochlear implant system, one or more of the two cochlear implants can also deliver acoustic stimulation to the ears of the recipient (e.g., an electro-acoustic cochlear implant) and / or the two cochlear implants may not need to be identical with respect to, for example, the number of electrodes used to electrically stimulate the cochlea, the type of stimulation delivered, etc.

[0026] FIGs. 1A-1E are diagrams illustrating one example bilateral cochlear implant system 100 configured to implement the techniques presented herein. More specifically, FIGs. 1A-1E illustrate an example bilateral system 100 comprising left and right cochlear implants, referred to as cochlear implant 102L and cochlear implant 102R. FIGs. 1A and IB are schematic drawings of a recipient wearing the left cochlear implant 102L at a left ear 14 IL and the right cochlear implant 102R at a right ear 141R, while FIG. 1C is a schematic view of each of the left and right cochlear implants. FIGs. ID and IE are block diagrams illustrating further details of the left cochlear implant 102L and the right cochlear implant 102R, respectively.

[0027] Referring specifically to FIG. 1C, cochlear implant 102L includes an external component 104L that is configured to be directly or indirectly attached to the body of the recipient and an implantable component 112L configured to be implanted in the recipient. The external component 104L comprises a sound processing unit 106L, while the implantable component 112L includes an internal coil 114L, a stimulator unit 142L and an elongate stimulating assembly (electrode array) 116L implanted in the recipient’s left cochlea (not shown in FIG. 1C).Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1

[0028] The cochlear implant 102R is substantially similar to cochlear implant 102L. In particular, cochlear implant 102R includes an external component 104R comprising a sound processing unit 106R, and an implantable component 112R comprising internal coil 114R, stimulator unit 142R, and elongate stimulating assembly 116R.

[0029] FIG. ID is a block diagram illustrating further details of cochlear implant 102L, while FIG. IE is a block diagram illustrating further details of cochlear implant 102R. As noted, cochlear implant 102R is substantially similar to cochlear implant 102L and includes like elements as that described below with reference to cochlear implant 102L. For ease of description, further details of cochlear implant 102R have been omitted from the description.

[0030] As noted, the external component 104L of cochlear implant 102L includes a sound processing unit 106L. The sound processing unit 106L comprises one or more input devices 113L that are configured to receive input signals (e.g., sound or data signals). In the example of FIG. ID, the one or more input devices 113L include one or more sound input devices 118L (e.g., microphones, audio input ports, telecoils, etc.), one or more auxiliary input devices 119L (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 wireless transmitter / receiver (transceiver) 120E. However, it is to be appreciated that one or more input devices 113E can include additional types of input devices and / or less input devices (e.g., one or more auxiliary input devices 119E could be omitted).

[0031] The sound processing unit 106E also comprises one type of a closely-coupled transmitter / receiver (transceiver) 122E, referred to as radio-frequency (RF) transceiver 122E, a power source 123E, and a processing module 124E. The processing module 124E comprises one or more processors 125E and a memory 126E that includes sound processing logic 127E and battery charging control logic 128E.

[0032] In the examples of FIGs. 1A-1E, the sound processing unit 106L and the sound processing unit 106R are off-the-ear (OTE) sound processing units (i.e., components having a generally cylindrical shape and which is configured to be magnetically coupled to the recipient’s head), etc. However, it is to be appreciated that embodiments of the present invention can be implemented by sound processing units having other arrangements, such as by a behind-the-ear (BTE) sound processing unit configured to be attached to and worn adjacent to the recipient’s ear, including a mini or micro-BTE unit, an in-the-canal unit that is configured to be located in the recipient’s ear canal, a body-worn sound processing unit, etc.Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1

[0033] Although the cochlear implant 102L includes the sound processing unit 106L and the implantable component 112L, as described below, the implantable component 112L can operate independently from the sound processing unit 106L, for at least a period, to stimulate the user. For example, the implantable component 112L can operate in a first general mode, sometimes referred to as an “external hearing mode,” in which the sound processing unit 106L captures sound signals which are then used as the basis for delivering stimulation signals to the user. The implantable component 112L can also operate in a second general mode, sometimes referred as an “invisible hearing” mode, in which the sound processing unit 106L is unable to provide sound signals to the implantable component 112L (e.g., the sound processing unit 106L is not present, the sound processing unit 106L is powered-off, the sound processing unit 106L is malfunctioning, etc.). As such, in the invisible hearing mode, the implantable component 112L 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 implantable component 112L in the external hearing mode are provided below, followed by details regarding operation of the implantable component 112L 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 implantable component 112L could also operate in alternative modes.

[0034] The implantable component 112L comprises an implant body (main module) 134L, a lead region 136L, and the intra-cochlear stimulating assembly 116L, all configured to be implanted under the skin / tissue (tissue) 115 of the recipient. The implant body 134L generally comprises a hermetically-sealed housing 138L in which RF interface circuitry 140L, at least one rechargeable battery 143L, an implantable sound processor 158L, and a stimulator unit 142L are disposed. One or more implantable sound sensors 160L can be disposed, in, one, or electrically connected to the implant body 134L. The implant body 134L also includes the intemal / implantable coil 114L that is generally external to the housing 138L, but which is connected to the transceiver 140L via a hermetic feedthrough (not shown in FIG. ID).

[0035] As noted, stimulating assembly 116L is configured to be at least partially implanted in the recipient’s cochlea. Stimulating assembly 116L includes a plurality of longitudinally spaced intra-cochlear electrical stimulating contacts (electrodes) 144L that collectively form a contact or electrode array 146L for delivery of electrical stimulation (current) to the recipient’s cochlea.Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1

[0036] Stimulating assembly 116L 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 142L via lead region 136L and a hermetic feedthrough (not shown in FIG. ID). Lead region 136L includes a plurality of conductors (wires) that electrically couple the electrodes 144L to the stimulator unit 142L.

[0037] As noted, the cochlear implant 102L includes the external coil 108L and the implantable coil 114L. The coils 108L and 114L are typically wire antenna coils each comprised of multiple turns of electrically insulated single-strand or multi-strand platinum or gold wire. Generally, a magnet is fixed relative to each of the external coil 108L and the implantable coil 114L. The magnets fixed relative to the external coil 108L and the implantable coil 114L facilitate the operational alignment of the external coil 108L with the implantable coil 114L. This operational alignment of the coils enables the external component 104L to transmit data, as well as possibly power, to the implantable component 112L via a closely-coupled wireless link formed between the external coil 108L with the implantable coil 114L. In certain examples, the closely-coupled wireless link is a radio frequency (RF) link. However, various other types of energy transfer, such as infrared (IR), electromagnetic, capacitive, and inductive transfer, can be used to transfer the power and / or data from an external component to an implantable component and, as such, FIG. ID illustrates only one example arrangement.

[0038] As noted above, sound processing unit 106L includes the processing module 124L. In an external hearing mode, the processing module 124L is configured to convert received input signals (received at one or more of the input devices 113L) into output signals 145L for use in stimulating a first ear of a recipient (i.e., the processing module 124L is configured to perform sound processing on input signals received at the sound processing unit 106L). Stated differently, in the external sound processing mode, the one or more processors 125L are configured to execute sound processing logic stored, for example, in in memory 126L to convert the received input signals into output signals 145L that represent electrical stimulation for delivery to the recipient.

[0039] In the embodiment of FIG. ID, the output signals 145L are provided to the RF transceiver 114, which transcutaneously transfers the output signals 145L (e.g., in an encoded manner) to the implantable component 112L via external coil 108L and implantable coil 114L. That is, the output signals 145L are received at the RF interface circuitry 140L via implantable coil 114L and provided to the stimulator unit 142L. The stimulator unit 142L is configured to utilize the output signals 145L to generate electrical stimulation signals (e.g., current signals)Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 for delivery to the recipient’s cochlea via one or more stimulating contacts 144L. In this way, cochlear implant 102L electrically stimulates the recipient’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 received sound signals.

[0040] As detailed above, in the external hearing mode, the implantable component 112L receives processed sound signals from the sound processing unit 106L. However, in the invisible hearing mode, the implantable component 112L 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 implantable component 112L can include a plurality one or more implantable sound sensors 160L, and an implantable sound processing module 158L. The implantable sound processing module 158L can comprise, for example, one or more processors and a memory device (memory) that includes sound processing logic. The memory device can 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.

[0041] In the invisible hearing mode, one or more implantable sound sensors 160L are configured to detect / capture input sound signals (e.g., acoustic sound signals, vibrations, etc.), which are provided to the implantable sound processing module 158L. The implantable sound processing module 158L is configured to convert received input sound signals into output control signals for use in stimulating the first ear of a recipient or user (i.e., the implantable sound processing module 158L 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 158L are configured to execute sound processing logic in memory to convert the received input sound signals into output control signals that are provided to the stimulator unit 142L. The stimulator unit 142L is configured to utilize the output control signals 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.Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1

[0042] 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 102L could operate differently in different embodiments. For example, in one alternative implementation of the external hearing mode, the one or more implantable sound sensors 160L could use signals captured by the sound input devices 118L and the one or more implantable sound sensors 160 in generating stimulation signals for delivery to the user. In an alternative embodiment, the sound processing unit 106L can send less processed information (e.g., audio data) to the implantable component 112L, and the sound processing operations (e.g., conversion of input sounds to output control signals) can be performed by a processor within the implantable component 112L.

[0043] In certain embodiments, the external component 104L could be temporarily or permanently replaced by a dedicated charging device that is configured to only or primarily provide power / charging signals (power) to the implantable component 112L. As used herein, the term “charging device” or “charger” is to be construed as any device that is configured to transfer power to an implantable component, regardless of the other capabilities of the device. For example, as used herein, a “charging device” or “charger” could be a sound processing unit that transfers both processed data and power to an implantable component, or dedicated device that transfers only or primarily power to an implantable component, etc.

[0044] As noted, cochlear implant 102R is substantially similar to cochlear implant 102L and comprises external component 104R and implantable component 112R. Again, for ease of description, a detailed discussion of cochlear implant 102R is not provided herein.

[0045] It is to be appreciated that the arrangements of cochlear implants 102L and 102R, as shown in FIGs. 1A-1E, are merely illustrative and that the cochlear implants 102L and 102R could have different arrangements. For example, in certain embodiments, the implantable components 112L and 112R could each include a wireless transceiver that is similar to the wireless transceivers 120L and 120R. In the same or other embodiments, the implantable components 112L and 112R could each include processing modules that are similar to the processing modules 124L and 124R. The implantable components 112L and 112R could also include processing modules that are not necessarily the same as the processing modules 124L and 124R, for example, in terms of functional capabilities.

[0046] The cochlear implants 102L and 102R are configured to establish a binaural wireless communication link / channel 162 (binaural wireless link) that enables the cochlear implants 102L and 102R (e.g., the sound processing units 104L / 104R and / or the implantableAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 components 112L / 112R, if equipped with wireless transceivers) to wirelessly communicate with one another. The binaural wireless link 162 can be, for example, a magnetic induction (MI) link, a standardized wireless channel, such as a Bluetooth®, Bluetooth® Low Energy (BLE) or other channel interface making use of any number of standard wireless streaming protocols, a proprietary protocol for wireless exchange of data, etc. Bluetooth® is a registered trademark owned by the Bluetooth® SIG. The binaural wireless link 162 is enabled by the wireless transceivers 120L and 120R.

[0047] As noted, implantable components 112L / 112R each include at least one rechargeable implanted battery 143L / 143Rthat needs re-charging. In general, the more quickly an implanted battery can be recharged, the better the recipient experience will likely be. Thus, there is a desire to enable fast charging of a given implanted battery. However, it has been discovered that certain battery charging operations (e.g., fast charging operations) performed at a first device, such as cochlear implant 112L, can cause interference at a second device, such as cochlear implant 112R. As such, presented herein are techniques to modify or control charging operations (charging profile) at a first device, in response to the detection of interference at a second device.

[0048] For example, in the context of FIGs. 1A-1E, charging operations can be implemented to charge / re-charge implantable battery 143L. During these charging operations, cochlear implant 102R (e.g., external component 104R and / or implantable component 112R) detects interference at cochlear implant 102R. In response, using binaural wireless communication link / channel 162, external component 104R sends external component 104L a notification regarding the detected interference. In response, external component 104L (e.g., battery charging control logic 128L) modifies the charging operations to mitigate the interference detected at cochlear implant 102R.

[0049] Further details of the battery charging control operations presented herein are provided below with reference to bilateral cochlear implant systems. As noted elsewhere herein, reference to bilateral cochlear implant systems is merely illustrative and that techniques presented herein can be implemented in any of a number of different systems having two devices.

[0050] More specifically, FIG. 2A is schematic diagram of a bilateral cochlear implant system 200 illustrating further details of the battery charging control operations presented herein. As shown, the bilateral cochlear implant system 200 includes a right-side, or ipsi-lateral, or firstAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 implantable device 230a including a microphone 240a, a left-side, or contra-lateral, or second implantable device 230b including a microphone 240b. A first external device or first charging device 250a serves to charge an internal battery 220a (e.g., power source 125 in FIG. ID) of first implantable device 230a, and a second external device or second charging device 250b serves to charge an internal battery 220b of second implantable device 230b. Charging, according to a predetermined charging profile, can be accomplished via a first closely coupled link 235a and a second closely coupled link 235b established, respectively, between the first implantable device 230a and the first charging device 250a, and the second implantable device 230b and the second charging device 250b.

[0051] That is, an alternating current waveform or pulsed waveform can be generated, e.g., by first charging device 250a and is supplied to a coil internal to first charging device 250a. That coil is paired with a coil in first implantable device 230a, which receives the waveform via closely coupled link 235a and transforms the waveform into a direct current signal that is used to charge battery 220a. Notably, not only can battery charging waveforms (power) be supplied via closely couple link 235a, 235b, but data signals can also be exchanged between the charging devices 250a, 250b and first implantable device 230a and second implantable device 230b.

[0052] As shown in FIG. 2A, the first charging device 250a and the second charging device 250b can be “off-the-ear” or “OTE” devices. However, as shown in the bilateral cochlear implant system 201 of FIG. 2B, at least one of the charging devices could be a “behind-the- ear” or “BTE” device 255. Whether an OTE or BTE device is used, a magnet can be used to align relevant parts of the devices 250a, 250b, 255 (i.e., coils) to the relevant parts of the implantable devices 230a, 230b (i.e., coils).

[0053] As noted, from a usability perspective, the more quickly an implanted battery in either of first implantable device 230a or the second implantable device 230b can be recharged, the better the user experience will likely be. In this regard, and in accordance with an embodiment, and with reference, for example, to FIG. 2A, the first charging device 250a and the second charging device 250b are configured to communicate with one another over a wireless link 280 to share relevant information to optimize the manner in which battery charging is achieved. As described elsewhere herein, the information provided via wireless link 280 can relate to interference detected at first implantable device 230a, second implantable device 230b, first charging device 250a, or second charging device 250b.Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1

[0054] FIG. 3 is a functional block diagram of selected components of a bilateral system 300, generally representing operations that can be performed at systems 200 or 201 of FIG. 2A and FIG. 2B. As shown, system 300 comprises a first charging device 350a and a second charging device 350b. Each of the first charging device 350a and the second charging device 350b includes an instance of battery charging control logic 390, the functionality of which is described further below. A first implantable device 330a is in communication with first charging device 350a via closely coupled link 335a. First implantable device 330a includes a battery 320a. Likewise, a second charging device 350b is in communication with second implantable device 330b via closely coupled link 335b. Second implantable component includes a battery 320b. The closely coupled links 335a, 335b (providing power and perhaps data) can be magnetic induction (MI) links that operate at a frequency in the range of about 5 to 50 MHz.

[0055] First charging device 350a and second charging device 350b are in communication with each other via wireless link 380, which can also be a magnetic induction link that operates in a frequency range of 2-15 MHz. However, any form of wireless link can be implemented to enable communication between first charging device 350a and second charging device 350b.

[0056] In operation, a user can be notified, e.g., via predetermined sound signals (e.g., beeps) or a mobile device application, that at least one of the batteries 320a, 320b needs re-charging. As such, the user can attach (e.g., magnetically secure) one or both of first charging device 350a and second charging device 350b to respective first implantable device 230a and second implantable device 230b. In the scenario in which both charging devices are attached, wireless link 380 is established between first charging device 350a and second charging device 350b, enabling instances of battery charging control logic 390 to communicate with each other and exchange information with one another. It is also possible that first implantable device 330a can communicate with second implantable device 330b, and / or with second charging device 350b. Likewise, second implantable device 330b can communicate with first charging device 350a.

[0057] In one embodiment, battery charging control logic 390 detects, via, e.g., voltage detection, the charge level of its own charging device and, via communication over closely couple links 335a, 335b, the charge level of the respective battery 320a or battery 320b that it is charging. In this regard, battery charging control logic 390 can be configured to exchange, via wireless link 380, battery charge level information. With that information, battery charging control logic 390 can, in response, notify the user, via predetermined sound signals (e.g., beeps)Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 or via a mobile device (not shown), that it is desirable to swap the charging devices given the relative charge levels. For example, battery 320a can have a high charge level and first charging device 350a can also have a high charge level. Meanwhile, battery 320b can have a low charge level and second charging device 350b can have a low charge level. As such, it can be desirable to swap first charging device 350a with second charging device 350b to better match a more highly charged charging device with a lower charged implanted battery to improve overall charging performance.

[0058] Similarly, battery charging control logic 390 can be able to learn, via communication over closely couple links 335a, 335b, the temperature rise occurring with respect to a given implantable device 230, 230b (which can have incorporated therein a temperature sensor (not shown)). Such temperature information can also be exchanged, via wireless link 380, to help improve overall user experience. That is, in the event battery charging is increasing the temperature of either of the implantable devices beyond a predetermined threshold, then it can be desirable to stop charging battery 320a or 320b until the temperature of the implantable device has decreased to a predetermined value. This can ensure that the implantable devices are not causing the recipient unnecessary discomfort.

[0059] In addition, battery charging control logic 390 can be operable to be responsive to learning that a contralateral implantable device 230a or 230b, or a closely coupled link 335a, 335b thereof, is experiencing interference as a result of a manner in which the battery 320a, 320b of an ipsi-lateral implantable device (the other of 230a, 230b) is being charged. More specifically, as an example, first charging device 350a can be configured, under the control of battery charging control logic 390, to charge battery 320a of first implantable device 230a according to a selected charging profile. That charging profile can include any number of charging approaches including charging speed (e.g., slow charging mode or fast charging mode), use of a specific charging frequency, use of a specific charging signal (pulse) duration, use of a specific charging signal amplitude, etc. Under some circumstances and given selected charging profiles, the charging of battery 320a by first charging device 350a can cause interference with, e.g., the closely coupled link 335b between second charging device 350b and second implantable device 330b. The charging of battery 320a by first charging device 350a can also cause interference to wireless link 380. In accordance with an embodiment, in response to detecting interference in the operations of second implantable device 330b (and / or operations of wireless link 380), second charging device 350b, or communication therebetween via closely couple link 335b, battery charging control logic 390 of second charging device 350bAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1(i.e., the contralateral / interfered with device) is configured to notify the ipsi-lateral device (here, first charging device 350a) of the presence of that interference.

[0060] Interference detection can be performed by either an implantable device (e.g., second implantable device 330b) or a charging device (e.g., second charging device 350b or an external sound processor). In one implementation, battery charging control logic 390 monitors bit error rate or packet error rate to detect whether interference is impacting, e.g., closely coupled link 335b.

[0061] For an RF link, the charging device and / or sound processor can slowly charge the implantable device and send audio or stimulation commands to the implantable device. The implantable device reads the message it receives and computes a cyclic redundancy check (CRC). If the CRC does not match, then battery charging control logic 390, or other logic, informs the charging device or sound processor through a back link. If the charging device or sound processor does not receive a back link or if it receives information from the implantable device that the previous packet it received was corrupted, then it increments its Packet Error rate accordingly. Having a packet error rate above a certain threshold indicates that there is interference stronger than the system can tolerate.

[0062] For a magnetic induction (MI) Link, the same process can be applied, but in this case bit error rate can be monitored by the charging device or sound processor or implantable device. For a 2.4Ghz link, the same process can be used, and packet error rate rather than bit error rate is monitored.

[0063] In sum, a charging device or a sound processor sends data through one channel (e.g., an RF Link, MI Link or 2.4GHz) and can receive feedback from the implantable device. For example, the implantable device receives data and then attempts to decode that data. If the decoding process fails, the implantable device either does not send feedback (no acknowledgment) or sends specific information to the external device (sound processor or charging device). The external device (or possibly the implantable device as well) keeps track of packet / bit error rate and compares the detected values with a threshold. When that threshold is exceeded, then battery charging control logic is configured to notify its contralateral device (e.g., first charging device 350a) that interference is detected.

[0064] In response to being notified of interference being detected, battery charging control logic 390 of first charging device 350a is configured to modify the charging profile according to which the first charging device 350a charges the battery 320a of first implantable deviceAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1330a to eliminate the interference detected on the contralateral side. FIGs. 4-6 illustrate different ways in which an interference -generating charging profde can be changed or modified to a non-interfering charging profile.

[0065] Figure 4 shows a first series of power pulses 410 in a given time frame 450 with a first power level 420 (or amplitude) and a second series of power pulses 430 with a second power level 440 in another time frame 450 of equal length. It is noted that charging can also be achieved using a continuous wave (e.g., an infinitely long pulse) where the amplitude of the wave determines a speed of charging. The first series of power pulses 410 can be associated with a first, or fast, charging profile that is generated by first charging device 350a under the control of battery charging control logic 390. The second series of power pulses 430 can be associated with a second, or slow, charging profile that is generated by first charging device 350a under the control of battery charging control logic 390. Generally speaking, and as noted previously, the more quickly a battery of an implantable device is charged the better the user experience is likely to be. Accordingly, when a user initially attaches a charging device to an implantable device, battery charging control logic 390 can select a fastest charging profile with which to charge the battery associated with the implanted device. However, in this case, the higher power level 420 of the first series of power pulses 410 can cause interference at a contralateral device, such as second implantable device 330b and / or its closely coupled link 335b. Upon detecting this interference, battery charging control logic 390 is configured to notify first charging device 350a, via wireless link 380, that it (the contralateral side) is experiencing interference.

[0066] In response to receiving a notification that the contralateral side is experiencing interference, battery charging control logic 390 is configured to modify the charging profile with which it is presently charging the ipsi-lateral battery. In this case, battery charging control logic 390 can change the charging profile such that the amplitude of the power pulses (or, e.g., continuous wave) being delivered by first charging device 350a is reduced to second power level 440. In this way, the battery 320a can still be charged on the ipsi-lateral side, but in a manner that no longer causes interference to the contralateral side.

[0067] FIG. 5 shows a first series of power pulses 510 in a given time frame 550 with a first duty cycle 520 and a second series of power pulses 530 with a second duty cycle 540 in another time frame 550 of equal length. That is, the second duty cycle is shorter that the first duty cycle 520. The first series of power pulses 510 can be associated with a first, or fast, charging profile that is generated by first charging device 350a under the control of battery charging controlAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 logic 390. The second series of power pulses 530 can be associated with a second, or slow, charging profde that is generated by first charging device 350a under the control of battery charging control logic 390. Generally speaking, and as noted previously, the more quickly a battery of an implantable device is charged the better the user experience is likely to be. Accordingly, when a user initially attaches a charging device to an implantable device, battery charging control logic 390 can select a fastest charging profile with which to charge the battery associated with the implanted device. However, in this case, the higher first duty cycle 520 of the first series of power pulses 510 can cause interference at a contralateral device, such as second implantable device 330b and / or its closely coupled link 335b. Upon detecting this interference, battery charging control logic 390 is configured to notify first charging device 350a, via wireless link 380, that it (i.e., the contralateral side) is experiencing interference.

[0068] In response to receiving a notification that the contralateral side is experiencing interference, battery charging control logic 390 is configured to modify the charging profile with which it is presently charging the ipsi-lateral battery. In this case, battery charging control logic 390 can change the charging profile such that the duty cycle of the power pulses being delivered by first charging device 350a is reduced to second duty cycle 540. In this way, the battery 320a can still be charged on the ipsi-lateral side, but in a manner that no longer causes interference to the contralateral side.

[0069] FIG. 6 shows a first series of power pulses 610 in a given time frame 650 with a first pulse rate 620 and a second series of power pulses 630 with a second pulse rate 640 in another time frame 650 of equal length. That is, the second pulse rate 640 is lower than the first pulse rate 620 (two pulses versus three pulses in the save time period or time frame). The first series of power pulses 610 can be associated with a first, or fast, charging profile that is generated by first charging device 350a under the control of battery charging control logic 390. The second series of power pulses 630 can be associated with a second, or slow, charging profile that is generated by first charging device 350a under the control of battery charging control logic 390. Generally speaking, and as noted previously, the more quickly a battery of an implantable device is charged the better the user experience is likely to be. Accordingly, when a user initially attaches a charging device to an implantable device, battery charging control logic 390 can select a fastest charging profile with which to charge the battery associated with the implanted device. However, in this case, the higher pulse rate of first pulse rate 620 can cause interference at a contralateral device, such as second implantable device 330b and / or its closely coupled link 335b. Upon detecting this interference, battery charging control logic 390 isAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 configured to notify first charging device 350a, via wireless link 380, that it (the contralateral side) is experiencing interference. In a continuous wave charging scenario, modifying a carrier frequency of the charging signal (i.e., the frequency of the sinusoid which is transmitted during the power pulses) is another way to reduce interference at a contralateral device. For example, the charging profile could switch from 6.78MHz to 5MHz and vice versa.

[0070] In response to receiving a notification that the contralateral side is experiencing interference, battery charging control logic 390 is configured to modify the charging profile with which it is presently charging the ipsi-lateral battery. In this case, battery charging control logic 390 can change the charging profile such that the frequency of the power pulses being delivered by first charging device 350a is reduced to the second pulse rate 640 (or frequency, as the case can be). In this way, the battery 320a can still be charged on the ipsi-lateral side, but in a manner that no longer causes interference to the contralateral side.

[0071] Y et another approach to modify a charging profile is to modify the Q-factor in response to a notification of interference. For example, Q-factor can be modified by configuring resistors in series or parallel with the transmitter coil 114L, 114R. Such changes can control the amplitude and frequency spectrum of the transmitted power.

[0072] It is to be appreciated that the techniques presented herein can be implemented using any of a number of different charging techniques. For example, the series of power pulses depicted in FIGs. 4-6 can be over a dedicated charging link or a split link in which power and data share the same link, but in a time division multiplexed fashion.

[0073] FIG. 7 is a flowchart illustrating a process for controlling a charging profile of a charging device to mitigate interference caused by that charging device to a contralateral device. At 710 an operation includes establishing a communication link between a first charging device configured to charge a first implantable medical device implanted in a recipient and a second charging device configured to charge a second implantable device implanted in the recipient. At 712, an operation includes detecting, at the second implantable device, interference caused by the first charging device charging the first implantable medical device. At 714, an operation includes in response to detecting the interference, sending by the second charging device, via the communication link, an indication of the interference. And, at 716, an operation includes in response to receiving the indication, the first charging device modifying a charging profile according to which the first charging device charges the first implantable medical device.Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1

[0074] 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.

[0075] FIG. 8 illustrates an example vestibular stimulator system 802, with which embodiments presented herein can be implemented. As shown, the vestibular stimulator system 802 comprises an implantable component (vestibular stimulator) 812 and an external device / component 804 (e.g., external processing device, battery charger, remote control, etc.). The external device 804 comprises a transceiver unit 860. As such, the external device 804 is configured to transfer data (and potentially power) to the vestibular stimulator 812.

[0076] The vestibular stimulator 812 comprises an implant body (main module) 834, a lead region 836, and a stimulating assembly 816, all configured to be implanted under the skin / tissue (tissue) 815 of the recipient. The implant body 834 generally comprises a hermetically-sealed housing 838 in which RF interface circuitry, one or more rechargeable batteries, one or more processors, and a stimulator unit are disposed. The implant body 834 also includes an intemal / implantable coil 814 that is generally external to the housing 838, but which is connected to the transceiver via a hermetic feedthrough (not shown).

[0077] The stimulating assembly 816 comprises a plurality of electrodes 844(l)-(3) disposed in a carrier member (e.g., a flexible silicone body). In this specific example, the stimulating assembly 816 comprises three (3) stimulation electrodes, referred to as stimulation electrodes 844(1), 844(2), and 844(3). The stimulation electrodes 844(1), 844(2), and 844(3) function as an electrical interface for delivery of electrical stimulation signals to the recipient’s vestibular system.

[0078] The stimulating assembly 816 is configured such that a surgeon can implant the stimulating assembly adjacent the recipient’s otolith organs via, for example, the recipient’s oval window. It is to be appreciated that this specific embodiment with three stimulation electrodes is merely illustrative and that the techniques presented herein can be used withAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 stimulating assemblies having different numbers of stimulation electrodes, stimulating assemblies having different lengths, etc.

[0079] In operation, the vestibular stimulator 812, the external device 804, and / or another external device can be configured to implement the techniques presented herein. That is, the vestibular stimulator 812, possibly in combination with the external device 804 and / or another external device, can include an evoked biological response analysis system, as described elsewhere herein.

[0080] 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.

[0081] 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.

[0082] 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.

[0083] 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. TheAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 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.

[0084] 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.

[0085] 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.

[0086] 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.

[0087] 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.

[0088] 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 disclosedAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 steps can be excluded without departing from the present disclosure. Further, the disclosed processes can be repeated.

[0089] 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.

[0090] 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. 3065.0857i Client Ref. No. CID03846WOPC1CLAIMSWhat is claimed is:

1. A method comprising : establishing a communication link between a first charging device configured to charge a first implantable medical device implanted in a recipient and a second charging device configured to charge a second implantable device implanted in the recipient; detecting, at the second implantable device, interference caused by the first charging device charging the first implantable medical device; in response to detecting the interference, sending by the second charging device, via the communication link, an indication of the interference; and in response to receiving the indication, the first charging device modifying a charging profile according to which the first charging device charges the first implantable medical device.

2. The method of claim 1, wherein the interference comprises interference of communication over a communication link other than the communication link between the first charging device and the second charging device.

3. The method of claim 1 or 2, further comprising the second implantable device notifying the second charging device of the interference.

4. The method of claim 1 or 2, wherein modifying the charging profile comprises reducing an amplitude of a charging waveform transmitted by the first charging device.

5. The method of claim 1 or 2, wherein modifying the charging profile comprises modifying a duty cycle of a charging waveform transmitted by the first charging device.

6. The method of claim 1 or 2, wherein modifying the charging profile comprises modifying a pulse rate or frequency of a charging waveform transmitted by the first charging device.

7. The method of claim 1 or 2, wherein modifying the charging profile comprises modifying a Q-factor of a link between the second charging device and the second implantable device.Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC18. The method of claim 1 or 2, wherein charging of the first implantable medical device by the first charging device is performed over one of a separated link and a split link.

9. The method of claim 1 or 2, wherein the first implantable medical device and the second implantable device are at least one of cochlear implant or an acoustic implant.

10. A bilateral implantable medical device system, comprising: a first external component configured to send first charging signals to a first implantable device; and a second external component configured to send second charging signals to a second implantable device, wherein the second external component is configured to alert the first external component of interference detected by the second implantable device, and, in response, the first external component is configured to adjust a parameter of the first charging signals.

11. The bilateral implantable medical device system of claim 10, wherein the first external component is configured to adjust a speed of the first charging signals.

12. The bilateral implantable medical device system of claim 10, wherein the first external component is configured to adjust a duty cycle of the first charging signals.

13. The bilateral implantable medical device system of claim 10, 11, or 12, wherein the first external component and the second external component maintain a wireless communication link between themselves.

14. The bilateral implantable medical device system of claim 10, 11, or 12, wherein the interference is of a radio frequency link communication channel between the second implantable device and the second external component or between the first external component and the second external component.

15. The bilateral implantable medical device system of claim 10, 11, or 12, wherein the first external component is configured to lower an amplitude of a first charging signal.Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC116. The bilateral implantable medical device system of claim 10, 11, or 12, wherein the first external component is configured to modify a duty cycle of a first charging signal.

17. A medical system, comprising: a first battery charger configured to wirelessly charge a first implantable device and having a plurality of charging modes; a second battery charger configured to wirelessly charge a second implantable device; and a wireless communication link between the first battery charger and the second battery charger, wherein the wireless communication link is configured to notify the first battery charger to switch between a first one of the plurality of charging modes and a second one of the plurality of charging modes.

18. The medical system of claim 17, wherein the second battery charger is configured to notify the first battery charger to switch between the first one of the plurality of charging modes and the second one of the plurality of charging modes in response to interference detected by the second implantable device as a result of the first battery charger operating in accordance with the first one of the plurality of charging modes.

19. The medical system of claim 18, wherein the first one of the plurality of charging modes is a fast-charging mode.

20. The medical system of claim 18, wherein the second one of the plurality of charging modes is characterized by a lower amplitude charging waveform compared to the first one of the plurality of charging modes.

21. The medical system of claim 17, wherein the first battery charger and the second battery charger are interchangeable.

22. A battery charging control system, comprising: a first device having a rechargeable battery and a charging device configured to supply first charging signals to the first device to charge the rechargeable battery; andAtty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC1 a second device, proximate the first device, and including components that wireless communicate with one another over a first wireless link, wherein the second device is configured to notify the charging device to change the first charging signals to second charging signals when the second device detects interference of the first wireless link as a result of the first charging signals.

23. The battery charging control system of claim 22, wherein the second charging signals cause a slower charging of the rechargeable battery compared to the first charging signals.

24. The battery charging control system of claim 22, wherein the second device comprises an external component and an implantable component and the first wireless link enables communication between the external component and the implantable component.

25. The battery charging control system of claim 22, wherein the second device comprises at least one of a cochlear implant and an acoustic implant.

26. The battery charging control system of claim 22, wherein the second charging signals have a lower amplitude than the first charging signals.

27. The battery charging control system of claim 22, wherein the second charging signals have a lower duty cycle than the first charging signals.

28. The battery charging control system of claim 22, wherein the second charging signals have a lower pulse rate or frequency than the first charging signals.

29. The battery charging control system of claim 22, 23, 24, 25, 26, 27, or 28, wherein the second device detects interference of the first wireless link based on a bit error rate or a packet error rate.

30. The battery charging control system of claim 22, 23, 24, 25, 26, 27, or 28, wherein the second device is configured to notify the charging device via a second wireless link different from the first wireless link.Atty. Docket No. 3065.0857i Client Ref. No. CID03846WOPC131. One or more non-transitory computer readable storage media comprising instructions that, when executed by one or more processors, are configured to: establish a communication link between a first charging device configured to charge a first implantable medical device implanted in a recipient and a second charging device configured to charge a second implantable device implanted in the recipient; receive, at the first charging device, an indication that the second implantable device has detected interference caused by the first charging device charging the first implantable medical device; in response to receiving the indication, modify a charging profile according to which the first charging device charges the first implantable medical device.

32. The one or more non-transitory computer readable storage media of claim 31, wherein the interference comprises interference of communication over a communication link other than the communication link between the first charging device and the second charging device.

33. The one or more non-transitory computer readable storage media of claim 31 or 32, wherein the instructions to modify the charging profile comprise instructions that, when executed by the one or more processors, are configured to: reduce an amplitude of a charging waveform transmitted by the first charging device.

34. The one or more non-transitory computer readable storage media of claim 31 or 32, wherein the instructions to modify the charging profile comprise instructions that, when executed by the one or more processors, are configured to: modify a duty cycle of a charging waveform transmitted by the first charging device.

35. The one or more non-transitory computer readable storage media of claim 31 or 32, wherein the instructions to modify the charging profile comprise instructions that, when executed by the one or more processors, are configured to: modify a pulse rate or frequency of a charging waveform transmitted by the first charging device.

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