Transdermal power transfer

Abstract

A device includes an external component of a prosthesis configured to provide power to an implant device implanted in a human body, where the external component is configured such that a power output level to the implant device dynamically varies in a digital binary based on data that is based on a load of the implant device.

Description

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS

[0002] This application claims priority to U.S. Provisional Application No. 63 / 344,839, filed on May 23, 2022, and entitled “TRANSCUTANEOUS POWER TRANSFER,” with Helmut Christian EDER as the inventor, the entire contents of which are incorporated herein by reference in their entirety. Background Art

[0003] Medical devices have provided a wide range of therapeutic benefits to recipients over the last several decades. Medical devices may include internal or implantable components / devices, external or wearable components / devices, or combinations thereof (e.g., devices having external components that communicate with implantable components). 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 over the years in performing life-saving and / or lifestyle-improving functions and / or recipient monitoring.

[0004] Over the years, the types of medical devices and the range of functions performed by them 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 that are permanently or temporarily implanted in a recipient. These functional devices are typically used to diagnose, prevent, monitor, treat, or manage disease / injury or its 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

[0005] In an exemplary embodiment, there is a device that includes an external component of a prosthesis, which is configured to provide power to an implanted device implanted in a human body, wherein the external component is configured so that the power output level to the implanted device changes dynamically in a digital binary manner based on data, and the data is based on the load of the implanted device.

[0006] In an exemplary embodiment, there is a device comprising an external component of a prosthesis, the external component configured to provide power to an implanted device implanted in a human body, wherein the external component is configured such that a primary power variation scheme is based on varying the power output to the implanted device by varying the length of a time period of continuous maximum power output.

[0007] In an exemplary embodiment, there is a method comprising: automatically obtaining data based on data affected by a power load on a power-consuming implanted medical device implanted in a human body; automatically analyzing the obtained data; and transcutaneously providing power to the implanted medical device by increasing the power to the implant from a minimum amount to a maximum amount or decreasing the power to the implant from the maximum amount to the minimum amount based on a result of the analysis.

[0008] In an embodiment, a cochlear implant external component comprises: a housing; a radio frequency induction coil connected to or supported in the housing, the radio frequency induction coil configured to provide power to an implant device implanted in a human body; a battery; and a circuit configured to provide power from the battery to the radio frequency induction coil, wherein the circuit is configured so that the power output level to the implant device is dynamically changed in a digital binary manner based on data, the data being based on a load of the implant device. BRIEF DESCRIPTION OF THE DRAWINGS

[0009] Embodiments are described below with reference to the accompanying drawings, in which:

[0010] Figure 1 is a perspective view of an exemplary hearing prosthesis;

[0011] Figure 2 A functional block diagram of an exemplary cochlear implant is presented;

[0012] Figure 3A and Figure 3B and 3C An exemplary system for communication between devices is presented;

[0013] Figure 4 An exemplary retinal prosthesis is presented;

[0014] Figure 5 An exemplary vestibular implant is presented;

[0015] Figure 6 Exemplary data and power transmissions are presented;

[0016] Figure 7 An exemplary RF envelope is presented;

[0017] Figure 8 presents an exemplary RF envelope according to an exemplary embodiment;

[0018] Fig. 9 An exemplary usage scenario according to an exemplary embodiment is presented;

[0019] Fig. 9A Another RF envelope (top portion) is presented according to an exemplary embodiment;

[0020] Fig.10 Exemplary target voltage scenarios are presented; and

[0021] Fig.11 An exemplary algorithm according to an exemplary embodiment is presented. DETAILED DESCRIPTION

[0022] Only for ease of description, the technology proposed herein is described with reference to the background of illustrative medical devices (i.e., cochlear implants). However, it should be understood that the technology proposed herein can also be used together with a variety of other medical devices, which can benefit from the setting changes based on the position of the medical device while providing a wide range of therapeutic benefits to recipients, patients or other users. For example, the technology proposed herein can be used to determine the viability of various types of prostheses (e.g., vestibular implants and / or retinal implants) for specific humans. And about the latter, the technology proposed herein is also described with reference to the background of another illustrative medical device (i.e., retinal implants). The technology proposed herein is also applicable to vestibular devices (e.g., vestibular implants), visual devices (i.e., bionic eyes), sensors, pacemakers, drug delivery systems, defibrillators, functional electrical stimulation devices, catheters, epileptic seizure devices (e.g., devices for monitoring and / or treating epileptic events), sleep apnea devices, electroporation devices and other technologies.

[0023] Furthermore, while the teachings detailed herein relate to stimulating tissue within a person's inner ear to evoke auditory perceptions that the person would not otherwise be able to hear, it should be noted that any disclosure herein regarding cochlear implants generally and the nerves or tissues stimulated by their electrode arrays corresponds to disclosure regarding alternative embodiments of the ocular system generally and its nerves (including the optic nerve) in particular, as well as retinal implants / visual implants and / or vestibular implants and / or tissues stimulated by such devices, such disclosure being made for the sake of economy of text.

[0024] Figure 1is a perspective view of a cochlear implant, referred to as cochlear implant 100, implanted in a recipient, to which some of the embodiments and / or variations thereof detailed herein may be applicable. In particular, as will be detailed below, there are various aspects of the cochlear implant used with respect to vestibular implants, and therefore there is utility in describing the features of the cochlear implant for the purpose of understanding the vestibular implant. In some embodiments, cochlear implant 100 is part of a system 10, which may include external components, as will be detailed below. In addition, it should be noted that the teachings detailed herein are also applicable to other types of hearing prostheses, such as bone conduction devices (transcutaneous, active transcutaneous and / or passive transcutaneous), direct acoustic cochlear stimulators, middle ear implants, and conventional hearing aids, etc., by way of example only and not limitation. In fact, it should be noted that the teachings detailed herein are also applicable to so-called multi-modal devices. In exemplary embodiments, these multi-modal devices apply both electrical stimulation and acoustic stimulation to the recipient. In exemplary embodiments, these multi-modal devices evoke hearing perception via electrical hearing and bone conduction hearing.

[0025] In view of the above, it should be understood that at least some of the embodiments and / or variations thereof described herein are directed to body-worn sensory supplemental medical devices (e.g. Figure 1 Hearing prostheses that supplement hearing even in the absence of natural hearing, for example due to prior deterioration of natural hearing or lack of any natural hearing, for example since birth). It should be noted that at least some exemplary embodiments of some sensory supplementation medical devices relate to devices such as middle ear implants or active transcutaneous bone conduction devices that supplement hearing while retaining some natural hearing ability, as well as visual prostheses (which are applicable to both recipients with some natural visual ability and recipients without natural visual ability), all of which utilize transdermal power transfer. Therefore, the teachings detailed herein are applicable to any type of sensory supplementation medical device that can be used in a practical manner that utilizes transdermal power transfer. In this regard, the phrase sensory supplementation medical device refers to any device for providing sensation to a recipient, regardless of whether the applicable natural sensation is only partially impaired or completely impaired or actually never existed.

[0026] The recipient has an outer ear 101, a middle ear 105, and an inner ear 107. The components of the outer ear 101, the middle ear 105, and the inner ear 107 are described below, and then the cochlear implant 100 is described.

[0027] In a fully functional ear, the outer ear 101 includes the auricle 110 and the ear canal 102. Sound pressure or sound waves 103 are collected by the auricle 110, directed into and through the ear canal 102. The eardrum 104, which vibrates in response to the sound waves 103, is at the distal end of the ear canal 102. This vibration is coupled to the oval or elliptical window 112 through three bones of the middle ear 105, which are collectively referred to as the ossicles 106 and include the malleus 108, the incus 109, and the stapes 111. The bones 108, 109, and 111 of the middle ear 105 serve to filter and amplify the sound waves 103, causing the oval window 112 to pivot or vibrate in response to the vibration of the eardrum 104. This vibration causes the perilymph within the cochlea 140 to generate waves of fluid motion. This fluid motion, in turn, activates tiny hair cells (not shown) inside the cochlea 140. Activation of the hair cells causes appropriate nerve impulses to be generated and transmitted via spiral ganglion cells (not shown) and the auditory nerve 114 to the brain (also not shown) where they are perceived as sound.

[0028] As shown, cochlear implant 100 includes one or more components that are temporarily or permanently implanted in a recipient. Figure 1 1 shows a cochlear implant 100 having an external device 142, which (together with the cochlear implant 100) is part of a system 10, which is configured to provide power to the cochlear implant as described below, wherein the implanted cochlear implant includes a battery that is charged by power provided from the external device 142.

[0029] exist Figure 1 In the illustrative arrangement of , external device 142 may include a power source (not shown) disposed in behind-the-ear (BTE) unit 126. External device 142 also includes a component of a transcutaneous energy transfer link referred to as an external energy transfer assembly. The transcutaneous energy transfer link is used to transfer power and / or data to cochlear implant 100. Various types of energy transfer (e.g., infrared (IR), electromagnetic, capacitive, and inductive transfer) may be used to transfer power and / or data from external device 142 to cochlear implant 100. In Figure 1 In the illustrative embodiment of the invention, the external energy transfer assembly includes an external coil 130 that forms part of an inductive radio frequency (RF) communication link. The external coil 130 is typically a wire antenna coil consisting of multiple turns of electrically insulated single or multiple strands of platinum or gold wire. The external device 142 also includes a magnet (not shown) positioned within the turns of the external coil 130. It should be understood that Figure 1 The external devices shown in are merely illustrative and other external devices may be used with the embodiments.

[0030] The cochlear implant 100 includes an internal energy transmission assembly 132 that is positionable in a recess of the temporal bone adjacent to the recipient's auricle 110. As described in detail below, the internal energy transmission assembly 132 is a component of a transcutaneous energy transmission link and receives power and / or data from an external device 142. In the illustrative embodiment, the energy transmission link includes an inductive RF link, and the internal energy transmission assembly 132 includes a primary internal coil 136. The internal coil 136 is typically a wire antenna coil composed of multiple turns of electrically insulated single or multiple strands of platinum or gold wire.

[0031] The cochlear implant 100 also includes a main implantable component 120 and an elongated electrode assembly 118. In some embodiments, the internal energy transmission assembly 132 and the main implantable component 120 are hermetically sealed within a biocompatible housing. In some embodiments, the main implantable component 120 includes an implantable microphone assembly (not shown) and a sound processing unit (not shown) to convert sound signals received by the implantable microphone in the internal energy transmission assembly 132 into data signals. That is, in some alternative embodiments, the implantable microphone assembly may be located in a separate implantable component (e.g., having its own housing assembly, etc.), which is in signal communication with the main implantable component 120 (e.g., via leads between the separate implantable component and the main implantable component 120, etc.). In at least some embodiments, the teachings detailed herein and / or variations thereof may be used with any type of implantable microphone arrangement.

[0032] The main implantable component 120 also includes a stimulator unit (also not shown) that generates electrical stimulation signals based on the data signals. The electrical stimulation signals are delivered to the recipient via the elongated electrode assembly 118.

[0033] The elongated electrode assembly 118 has a proximal end connected to the main implantable member 120 and a distal end implanted in the cochlea 140. The electrode assembly 118 extends from the main implantable member 120 through the mastoid bone 119 to the cochlea 140. In some embodiments, the electrode assembly 118 can be implanted at least in the basal region 116, and sometimes more deeply. For example, the electrode assembly 118 can extend toward the top end of the cochlea 140, known as the cochlear apex 134. In some cases, the electrode assembly 118 can be inserted into the cochlea 140 via a cochleostomy 122. In other cases, the cochleostomy can be formed through the round window 121, the oval window 112, the promontory 123, or through the top turn 147 of the cochlea 140.

[0034] The electrode assembly 118 includes a longitudinally aligned and distally extending array 146 of electrodes 148 disposed along its length. As noted, the stimulator unit generates stimulation signals that are applied by the electrodes 148 to the cochlea 140, thereby stimulating the auditory nerve 114.

[0035] Figure 2 2 is a functional block diagram of a cochlear implant system 200 according to some examples of the technology described herein. Cochlear implant system 200 includes an implantable component 201 (e.g., Figure 1 implantable component 100) and external device 240 (e.g., Figure 1 external device 142).

[0036] External device 240 may be configured as a wearable external device such that external device 240 is worn by a recipient in close proximity to the implantable component, which may enable implantable component 201 to receive power and stimulation data from external device 240. Figure 1 As described in , magnets can be used to facilitate operative alignment of external device 240 with implantable component 201. In the case where external device 240 and implantable component 201 are in close proximity, transmission of power and data can be achieved through the use of near-field electromagnetic radiation, and components of external device 240 can be configured for use in conjunction with near-field electromagnetic radiation.

[0037] The implantable component 201 may include a transceiver unit 208, an electronics module 213 (which may be a stimulator component of a cochlear implant), and an electrode assembly 254 (which may include a Figure 1The transceiver unit 208 is configured to receive power and / or data transcutaneously from the external device 240. As used herein, the transceiver unit 208 refers to any collection of one or more components that form part of a transcutaneous energy transfer system. In addition, the transceiver unit 208 may include or be coupled to one or more components that receive and / or transmit data or power. For example, this example includes a coil of a magnetic inductive device coupled to the transceiver unit 208. Other arrangements are also possible, including antennas, capacitive plates, or any other practical arrangements for replacing RF systems. In an example, data modulates an RF carrier or a signal containing power. The transcutaneous communication link established by the transceiver unit 208 can utilize time interleaving of power and data on a single RF channel or band to transmit power and data to the implantable component 201. In some examples, the processor 244 is configured to cause the transceiver unit 246 to interleave power and data signals, such as described in U.S. Patent Publication No. 2009 / 0216296 to Meskens. In this way, the data signal is modulated with the power signal, and a single coil can be used to transmit power and data to implant component 201. Various types of energy transmission, such as infrared (IR), electromagnetic, capacitive, and inductive transmission, can be used to transmit power and / or data from external device 240 to implantable component 201. Other types of power transmission systems separate the power signal from the data signal. The teachings herein can be used in both types of arrangements.

[0038] Various aspects of implantable component 201 may require power to provide functionality, such as receiving signals, processing data, or delivering electrical stimulation. Power that directly powers the operation of various aspects of implantable component 201 may be described as operating power. There are two exemplary ways that implantable component 201 can receive operating power: a power source (e.g., a battery) inside implantable component 201 or a power source outside the implantable component. However, other methods or combinations of methods are possible. For example, an implantable component may have a battery but still receive operating power from an external component (e.g., to maintain internal battery life when the battery is fully charged).

[0039] The internal power source may be a power storage element (not depicted). The power storage element may be configured for long-term storage of power and may include, for example, one or more rechargeable batteries. Power may be received from an external source such as an external device 240 and stored in the power storage element for long-term use (e.g., charging the battery of the power storage element). The power storage element may then provide power to other components of the implantable component 201 as needed for operation over time without the need for an external power source. In this way, power from an external source may be considered charging power rather than operating power, because power from the external power source is used to charge the battery (which in turn provides operating power) rather than to directly power various aspects of the implantable component 201 that require power to operate. The power storage element may be a long-term power storage element configured to be the main power source for the implantable component 201.

[0040] In some embodiments, implantable component 201 receives operating power from external device 240, and implantable component 201 does not include an internal power source (e.g., a battery) / internal power storage device (but may include a capacitor). In other words, implantable component 201 is powered only by external device 240 or another external device that provides sufficient power to implantable component 201 to allow the implantable component to operate (e.g., receive data signals and take actions in response). The operating power may directly power the functions of the device rather than charging power storage elements of the device external to implantable component 201. In these examples, implantable component 201 may include ancillary components that can store charge (e.g., capacitors) or ancillary components that can store small amounts of power, such as a small battery (e.g., a motherboard CMOS battery) used to keep volatile memory powered or power a clock. However, such ancillary components themselves do not have sufficient power to allow the implantable component to provide the primary function of implantable component 201 (e.g., receive data signals and take actions in response thereto, such as providing stimulation), and therefore, even if the ancillary components are indispensable for the operation of implantable component 201, they cannot be said to provide operating power.

[0041] As shown, the electronics module 213 includes a stimulator unit 214 (e.g., which may correspond to Figure 1 The electronic module 213 may also include one or more other components for generating the electrical stimulation signal 215 or controlling the delivery of the electrical stimulation signal to the recipient. Figure 1 Description, leads (e.g., Figure 1 The elongated lead 118 of the stimulator unit 214 may be inserted into the cochlea of ​​the recipient. The lead may include an electrode assembly 254 configured to deliver the electrical stimulation signal 215 generated by the stimulator unit 214 to the cochlea.

[0042] exist Figure 2 In the exemplary system 200 depicted in FIG. 2 , the external device 240 includes a sound input unit 242, a sound processor 244, a transceiver unit 246, a coil 247, and a power supply 248. The sound input unit 242 is a unit configured to receive sound input. The sound input unit 242 may be configured as a microphone (e.g., arranged to output audio data representing the surrounding sound environment), an electrical input (e.g., a receiver for a frequency modulation (FM) listening system), and / or another component for receiving sound input. The sound input unit 242 may be or include a mixer for mixing multiple sound inputs together.

[0043] Processor 244 is a processor configured to control one or more aspects of system 200, including converting sound signals received from sound input unit 242 into data signals and causing transceiver unit 246 to transmit power and / or data signals. Transceiver unit 246 may be configured to send or receive power and / or data 251. For example, transceiver unit 246 may include circuit components that transmit power and data through coil 247 (e.g., inductively). Data signals from sound processor 244 may be transmitted to implantable component 201 using transceiver unit 246 for providing stimulation or other medical functions.

[0044] The transceiver unit 246 may include one or more antennas or coils, such as coil 247, for transmitting power or data signals. Coil 247 may be a wire antenna coil of electrically insulated single or multi-strand wire having a plurality of turns. The electrical insulation of coil 247 may be provided by a flexible silicone molding. Various types of energy transmission, such as infrared (IR), radio frequency (RF) electromagnetic, capacitive and inductive transmission, may be used to transmit power and / or data from external device 240 to implantable component 201.

[0045] Figure 3A An exemplary system 210 is depicted according to an exemplary embodiment, the exemplary system comprising: a hearing prosthesis 100, which in the exemplary embodiment corresponds to the cochlear implant 100 described in detail above; and a portable body-worn device (e.g., Figure 2 A) 2401 in the form of a mobile computer with a display 2421. The system includes a wireless link 230 between the portable handheld device 2401 and the hearing prosthesis 100. In an embodiment, the prosthesis 100 is an implant (functionally composed of a hearing prosthesis 100) implanted in the recipient 99. Figure 3A 100 is indicated by a dotted line in FIG. 100 ).

[0046] In an exemplary embodiment, the system 210 is configured such that the hearing prosthesis 100 and the portable handheld device 2401 have a symbiotic relationship. In an exemplary embodiment, the symbiotic relationship is the ability to display data related to one or more functions of the hearing prosthesis 100, and in at least some cases the ability to control the one or more functions. In an exemplary embodiment, this can be achieved by the ability of the handheld device 2401 to receive data from the hearing prosthesis 100 via a wireless link 230 (although in other exemplary embodiments, other types of links can be utilized, such as wired links, etc.). As will be described in more detail below, this can be achieved by communicating with a geographically remote device that communicates with the hearing prosthesis 100 and / or the portable handheld device 2401 via a link, such as an Internet connection or a cellular telephone connection, by way of example only and not limitation. In some such exemplary embodiments, the system 210 can also include a geographically remote device. Again, additional examples of this will be described in more detail below.

[0047] As noted above, in an exemplary embodiment, the portable handheld device 2401 includes a mobile computer and a display 2421. In an exemplary embodiment, the display 2421 is a touch screen display. In an exemplary embodiment, the portable handheld device 2401 also has the functionality of a portable cellular telephone. In this regard, by way of example only and not limitation, the device 2401 may be what is commonly known as a smart phone. That is, in an exemplary embodiment, the portable handheld device 2401 includes what is still commonly known as a smart phone.

[0048] It should be noted that in some other embodiments, the device 2401 need not be a computer device, etc. It can be a lower-tech recorder, or any device that can implement the teachings herein.

[0049] The phrase "mobile computer" includes devices configured to enable human-computer interaction, where the computer is expected to be moved away from a stationary position during normal use. Likewise, in an exemplary embodiment, the portable handheld device 2401 is what is commonly known as a smart phone. However, in other embodiments, less complex (or more complex) mobile computing devices may be utilized to implement the teachings detailed herein and / or variations thereof. In at least some embodiments, any device, system, and / or method that enables the teachings detailed herein and / or variations thereof to be practiced may be utilized. (As will be described in detail below, in some cases, the device 2401 is not a mobile computer, but rather a remote device (remote from the hearing prosthesis 100. Some of these embodiments will be described below).)

[0050] In an exemplary embodiment, the portable handheld device 2401 is configured to receive data from the hearing prosthesis and present one of a plurality of different interface displays on a display based on the received data. The exemplary embodiments will sometimes be described in terms of data received from the hearing prosthesis 100. However, it should be noted that any disclosure that also applies to data sent from the handheld device 2401 to the hearing prosthesis is also covered by such disclosure (and vice versa), unless otherwise specified or otherwise incompatible with the related art.

[0051] It should be noted that in some embodiments, system 210 is configured such that cochlear implant 100 and portable device 2401 have a relationship. By way of example only and not limitation, in an exemplary embodiment, the relationship is the ability of device 2401 to act as a remote microphone for prosthesis 100 via wireless link 230. Thus, device 2401 can be a remote microphone. That is, in an alternative embodiment, device 2401 is an independent recording / sound capture device.

[0052] It should be noted that in at least some exemplary embodiments, device 2401 corresponds to the Apple Watch commercially available in the United States as of January 10, 2021 TM Series 1 or Series 2. In an exemplary embodiment, device 2401 corresponds to a Samsung Galaxy Gear XT, commercially available in the United States as of January 10, 2021. TM Gear 2. The device is programmed and configured to communicate with the prosthesis and / or to implement the teachings detailed herein.

[0053] In an exemplary embodiment, the telecommunications infrastructure may communicate with the hearing prosthesis 100 and / or the device 2401. By way of example only and not limitation, a telecoil 2491 or some other communication system (Bluetooth, etc.) is used to communicate with the prosthesis and / or the remote device. Figure 2 B depicts an exemplary quasi-functional schematic diagram depicting communication between an external communication system 2491 (e.g., a telecoil) and the hearing prosthesis 100 and / or the handheld device 2401 via links 277 and 279, respectively (note that Figure 3B Depicted are two-way communications between the hearing prosthesis 100 and the external audio source 2491 and between the handheld device and the external audio source 2491 - in alternative embodiments, the communications are only one-way (e.g., from the external audio source 2491 to the respective device). However, it is noted that unless otherwise noted, Figure 3B The embodiments are applicable to any body-worn medical device / implantable device disclosed herein in some embodiments.

[0054] Figure 3CAn exemplary external component 1440 is depicted. The external component 1440 may correspond to the external component 142 of the system 10 (which may also represent other body-worn devices / devices used with implanted portions herein). As can be seen, the external component 1440 includes a behind-the-ear (BTE) device 1426 connected to an exemplary head member 1478 via a cable 1472, the head member including an external inductive coil 1458EX that corresponds to Figure 1 As shown, the external component 1440 includes a head member 1478, which includes a coil 1458EX and a magnet 1442. This magnet 1442 interacts with an implanted magnet (or implanted magnetic material) of the implantable component to maintain the head member 1478 on the skin of the recipient. In an exemplary embodiment, the external component 1440 is configured to transmit magnetic data and / or power to an implantable component including an inductive coil and / or receive magnetic data percutaneously through the coil 1458EX. The coil 1458X is electrically coupled to the BTE device 1426 via the cable 1472. The BTE device 1426 may include, for example, at least some of the components of the external devices / components described herein.

[0055] Figure 4 Exemplary embodiments of neural prostheses in general and retinal prostheses in particular and their use environments are presented, components of which may be used in whole or in part in some of the teachings herein. In some embodiments of retinal prostheses, a retinal prosthesis sensor-stimulator 10801 is positioned proximate to the retina 11001. In exemplary embodiments, photons entering the eye are absorbed by a microelectronic array of the sensor-stimulator 10801, which is hybridized with a glass piece 11201 containing, for example, an embedded microwire array. The glass may have a curved surface that conforms to the inner radius of the retina. The sensor-stimulator 108 may include a microelectronic imaging device, which may be made of thin silicon containing an integrated circuit system that converts incident photons into electronic charges.

[0056] The image processor 10201 is in signal communication with the sensor-stimulator 10801 via a cable 10401 that extends through a surgical incision 00601 in the eye wall (although in other embodiments, the image processor 10201 is in wireless communication with the sensor-stimulator 10801). The image processor 10201 processes the input of the sensor-stimulator 10801 and provides control signals back to the sensor-stimulator 10801 so that the device can provide a processed output to the optic nerve. That is, in alternative embodiments, the processing is performed by a component that is close to or integrated with the sensor-stimulator 10801. The charge generated by the conversion of the incident photons is converted into a proportional amount of electronic current, which is input to the nearby retinal cell layer. The cells are excited, and signals are sent to the optic nerve, thereby inducing visual perception.

[0057] The retinal prosthesis may include an external device disposed in a behind-the-ear (BTE) unit or in a pair of glasses, or any other type of component that may have practical value. The retinal prosthesis may include an external light / image capture device (e.g., located in / on a BTE device or a pair of glasses, etc.), and as noted above, in some embodiments, the sensor-stimulator 10801 captures light / images, which is implanted in the recipient.

[0058] To keep the disclosure compact, any disclosure herein of a microphone or sound capture device corresponds to a similar disclosure of a light / image capture device, such as a charge coupled device. It follows that any disclosure herein of a stimulator unit that generates an electrical stimulation signal or otherwise imparts energy to tissue to evoke hearing perception corresponds to a similar disclosure of a stimulator device for a retinal prosthesis. Any disclosure herein of a sound processor or processing of captured sound, etc., corresponds to a similar disclosure of a light processor / image processor having similar functions of a retinal prosthesis and processing captured images in a similar manner. In fact, any disclosure herein of a device for a hearing prosthesis corresponds to a disclosure of a device for a retinal prosthesis having similar functions of a retinal prosthesis. Any disclosure herein of assembling a hearing prosthesis corresponds to a disclosure of assembling a retinal prosthesis using similar actions. Any disclosure herein of a method of using or operating a hearing prosthesis or otherwise working with a hearing prosthesis corresponds to a disclosure of using or operating a retinal prosthesis or otherwise working with a retinal prosthesis in a similar manner.

[0059] Figure 5 An exemplary vestibular implant 500 is depicted. Figure 1The above-described cochlear implant is described in connection with various elements to describe some specific features. In this regard, some features of the cochlear implant are used in conjunction with the vestibular implant. For economy of text and figures, the same numbers are used to reference various elements of the vestibular implant that generally correspond to elements of the cochlear implant described above. Still, it should be noted that some features of the vestibular implant 500 will differ from the features of the cochlear implant described above. By way of example only and not limitation, there may be no microphone on the behind-the-ear device 126. Alternatively, sensors that have practical value in a vestibular implant may be included in the BTE device 126. By way of example only and not limitation, a motion sensor may be located in the BTE device 126. There may also be no sound processor in the BTE device. Instead, other types of processors, such as those that process data obtained from sensors, will be present in the BTE device 126. A power source such as a battery will also be included in the BTE device 126. With Figure 1 The transmitter / transceiver will be located in or otherwise in signal communication with the BTE device.

[0060] The implantable component includes a receiver stimulator in a manner associated with the cochlear implant described above. Here, the vestibular stimulator includes a main implantable component 120 and an elongated electrode assembly 1188 (where the elongated electrode assembly 1188 has some different features from the elongated electrode assembly 118 of the cochlear implant, some of which will be described later). In some embodiments, the internal energy transmission assembly 132 and the main implantable component 120 are hermetically sealed within a biocompatible housing. In some embodiments, the main implantable component 120 includes a processing unit (not shown) for converting data obtained by a sensor, which can be an onboard sensor implanted in the receiver, into a data signal.

[0061] The main implantable component 120 also includes a stimulator unit (also not shown) that generates electrical stimulation signals based on the data signals. The electrical stimulation signals are delivered to the recipient via the elongated electrode assembly 1188.

[0062] It should be briefly pointed out that although Figure 5 The embodiments shown in represent a partially implantable vestibular implant, but embodiments may include a fully implantable vestibular implant, for example where the motion sensor is located in the implantable portion in a manner similar to a cochlear implant.

[0063] The elongated electrode assembly 1188 has a proximal end connected to the main implantable component 120 and extends through a hole in the mastoid 119 in a manner similar to the elongated electrode assembly 118 of a cochlear implant and includes a distal end that extends into the inner ear. In some embodiments, the distal portion of the electrode assembly 1188 includes a plurality of leads 510 that branch from the body of the electrode assembly 118 to electrodes 520. The electrodes 520 can be placed at the base of the semicircular canals, such as Figure 5 In an exemplary embodiment, one or more of these electrodes are placed near the branches of the vestibular nerve that innervate the semicircular canals. In some embodiments, the electrodes are located outside the inner ear, while in other embodiments, the electrodes are inserted into the inner ear. It should also be noted that while this embodiment does not include an electrode array located in the cochlea, in other embodiments, one or more electrodes are located in the cochlea in a manner similar to a cochlear implant.

[0064] If a person has at least a partially functional nervous system in the vestibular system, a vestibular implant may have practical value for the person. Conversely, if the nervous system in the vestibular system is completely non-functional, there will be little practical value in implanting a vestibular implant in the human body. Embodiments include devices, systems, and methods that can determine whether the nervous system of a person in the vestibular system has sufficient function so that the person can benefit from a vestibular implant at least to some extent. This can have practical value for avoiding scenarios where a vestibular implant is implanted in a human body but the implant will have little practical value (because the nervous system is not functional enough). A corollary to this is that a retinal implant may have practical value for a person if the person has at least a partially functional nervous system of the visual system.

[0065] Therefore, the teachings herein relate to assessing whether people are suitable for vestibular implants before implantation.At least some of the teachings described in detail herein can make it possible to obtain data, and the data can provide the peripheral vestibular reaction (for example, the reaction from the vestibular nerve) indicating people when analyzed to exist and / or whether it is enough to make people become the mark of candidates for the practical results about vestibular implants.The data can be the data indicating vestibular nerve function (at least some functions).In addition, in some other embodiments, the teachings described in detail herein relate to assessing whether people are suitable for retinal implants before implantation.At least some of the teachings described in detail herein can make it possible to obtain data, and the data can provide the reaction indicating people to the electrical stimulation in the eye or the reaction to the electrical stimulation of the nerves of the optical system when analyzed to exist and / or whether it is enough to make people become the mark of candidates for the practical results about retinal implants.

[0066] It should also be noted that at least some exemplary embodiments relate to assessing whether a semicircular canal implant may be of practical value to a given person under test. That is, at least some exemplary embodiments include apparatus, systems, and methods for screening a person for a semicircular canal implant.

[0067] Some embodiments utilize unilateral or bilateral placement of galvanic vestibular stimulation (GVS) (monopolar and / or bipolar) to induce a sensation of motion in a person's head and / or body as a whole when the person is in a static position. In an exemplary embodiment, GVS is used for unilateral stimulation (but both "sides" may be stimulated in a continuous or spaced-apart manner, provided that there is sufficient time interval between stimulations). Embodiments include providing a weak current (AC or DC, depending on the embodiment) across the mastoid. The current is used to excite one or more of the otolith and semicircular canal afferent nerves. Embodiments may include continuous stimulation and / or pulsed stimulation and / or sine waves. Noise stimulation may also be used.

[0068] More specifically, in at least some exemplary embodiments, the above-described current is utilized to induce a sensation of head rolling about the naso-occipital axis, i.e., ear canal stimulation. In some exemplary embodiments, an evoked torsional eye movement response to the GVS is obtained and otherwise captured and evaluated. If sufficient movement is present, this may indicate a sufficiently functional neural system of the vestibular system, thereby indicating that the person may have a practical experience with the vestibular implant.

[0069] Some exemplary embodiments utilize GVS to stimulate synapses between vestibular hair cells and VIII nerve afferents. Thus, embodiments herein can provide information about "neural" rather than "sensory" function. A person with hair cell damage (e.g., due to ototoxic drug exposure) with preserved VIII nerve afferent function may have normal or even increased responses to vestibular electrical stimulation despite no response to heat and rotation testing.

[0070] Figure 1 , 4 The embodiments of and 5 (as well as exemplary embodiments used in active transcutaneous bone conduction devices and / or middle ear implants that use a transcutaneous power / data link to power an implanted actuator) require power to be transmitted through the recipient's skin to power the implanted device. The amount of power that needs to be transmitted can be large, and the power required can fluctuate rapidly and by large amounts (all of these phrases are of course relative - some specific examples are described below).

[0071] Figure 6 An electrical signal S is shown applied to a transmitter coil of an external device to transfer power to an implantable component at a duty cycle of approximately 65%. D A non-limiting example of. Figure 6 The duty cycle of a signal is usually considered to be the ratio of the on time to the total frame time or the on and off time. Figure 6 The total frame time is 1ms and the on-time is 0.65ms, which results in a duty cycle of 65%. Figure 6 shows how the electrical signal S D In the signal S, for example, five cycles per unit are used for encoding. More specifically, D During the on-time of the signal S, binary ones and zeros may be encoded as shown in the enlarged portion 180. D It need not be a square wave, as is typically shown. Instead, each signal burst may be modulated using known techniques such as on-off keying (OOK), frequency shift keying (FSK), phase shift keying (PSK), etc. to transmit power and / or data over the transdermal link.

[0072] Figure 7 It is presented that a prior art transdermal power transfer system varies power levels within a 1 millisecond frame for approximately 150 milliseconds. Figure 7 The figure shows the RF signal envelope (where the underlying signal is a sine wave). It can be seen that Figure 7 This prior art power regulation scheme ramps up the external power as the load on the implant increases. This is called an attack (power is increased from the baseline level of power supplied to the implant (in this example at Figure 7 The increase of the horizontal line depicted in Figure 7 This prior art power regulation scheme ramps down the external power as the load of the implant decreases. This is called decay. It should be noted that as can be seen, the ramp up and ramp down do not need to come from and / or go to the baseline power provided, respectively. In this example of a prior art transdermal power transfer system, the ramp up and / or ramp down is provided in fixed power level steps based on the implant load or the requirements of the implant.

[0073] In an exemplary embodiment of a prior art transdermal power delivery scheme, the attack time to ramp up to the "desired" power delivery may be 50 or 100 or 150 ms or more. In an exemplary embodiment, the decay time to ramp down to the baseline power may be one or two or three seconds.

[0074] The embodiments of the present invention are Figure 8 Based on the embodiment of Figure 7 (although embodiments may use some of its features, such as will be detailed below - in the embodiments, unless otherwise stated, Figure 7 (or for that matter Figure 1-6 Any structural features and / or method steps of the arrangement of the embodiment of the present invention may be used in conjunction with Figure 8 and the related embodiments before and after). Figure 8 Presented with Figure 7Different exemplary embodiments. In this respect, the invention of the present patent application corresponds to Figure 8 and the embodiments of the figures that follow. Any means-plus-function and / or step-plus-function claims related to power transmission schemes correspond to Figure 8 and subsequent figures. But again, some exemplary embodiments of the present invention may utilize some of the structure and / or functionality of the teachings detailed above, and for the purpose of text economy, its features will not be repeated below. And embodiments of implants according to the present invention may include one or more of the above-described structures and / or functions, and / or may implement one or more of the above-described method actions, and may include methods that include one or more of the above-described method actions. However, with respect to power transmission schemes, the power transmission schemes do not include the power transmission schemes detailed above. This is at most a related art that some aspects of the present invention may utilize. In many embodiments, there are Figure 7 The arrangement of the features is obviously different.

[0075] Figure 8 The RF envelope of the present invention is presented relative to time. In this embodiment, the power delivery is effectively ramped up and / or down immediately. This is in contrast to ramping up and down of the external power in fixed power level steps based on the implant load. Figure 7 The power regulation mechanism of implants is different. Figure 8 The transcutaneous power delivery scheme of refractory implant power delivery refers to a scheme with a duty cycle implant power mechanism that delivers maximum power or minimum power (in this exemplary embodiment - more on this below) depending on whether the load / demand of the implant has been met or is otherwise satisfied. In this arrangement, the external component meets the implant power demand by dynamically changing the percentage of time (e.g., duty cycle) of the maximum power RF frame relative to the minimum power RF frame. In this regard, the implant power demand is met by the external component. Figure 7 compared to, Figure 8 A high level conceptual difference in the principles of operation between existing power delivery schemes and embodiments of the present invention utilizing on-times and off-times for maximum duty cycle implant power regulation is provided. In embodiments, the device uses on-times and off-times only for time periods lasting at least any time period herein and / or for at least 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, or 90% or more of the time that an external device provides power to the implant during at least 1, 2, 3, 4, 5, 6, 7, 8, 9, 10 days or weeks or months.

[0076] In an exemplary embodiment of the transdermal power transmission scheme of the present invention, the change in the duty cycle in the binary manner detailed above adjusts the voltage of the implant to meet the set target voltage of the implant. In an exemplary embodiment, a system that continuously and / or periodically (in a time sufficient to implement the teachings detailed herein) implements the transdermal power transmission scheme according to the embodiments detailed herein evaluates the voltage of the implant to determine whether the implant voltage is above and / or below the target implant voltage. In an exemplary embodiment, the system is configured so that if it is determined that the implant voltage is below the target voltage of the implant, the system applies maximum power to be transmitted from the external component to the implant. Conversely, again, in an exemplary embodiment, if the voltage of the implant is above the target voltage, the system applies minimum power to be transmitted from the external component to the implant. As will be described in detail below, the maximum power and minimum power are merely exemplary embodiments.

[0077] In an exemplary embodiment, the arrangement just described herein provides a system that effectively ensures automatic compensation for any load variations of the implant.

[0078] Fig. 9 Four (4) figures are presented, which respectively show implant load relative to time, communication link data relative to time, and RF power envelope relative to time for exemplary scenarios utilizing exemplary embodiments of the teachings detailed herein. As seen with respect to the top figure, the implant load 910 varies with time, wherein the top figure depicts the milliwatts used by the implant over time. In short, in an exemplary embodiment, the target voltage of the implant is a voltage that has practical value for the operating efficiency of the implant, at least because it is related to the charging of the implant. By way of example only and not limitation, the target voltage can be a target voltage that has efficiency for the overall operation of the system, such as, for example, reducing the amount of heat generated from the implant, which represents a waste of energy transmitted thereto, and therefore represents a phenomenon of reducing the life of the battery of the external component relative to the situation in the absence of this heat generation. The target voltage can be selected for any reason or multiple reasons. Embodiments include maintaining the target voltage above a certain level to avoid resetting in certain circumstances (e.g., when a large transient occurs). In this exemplary embodiment, the target voltage is 5.5V. In some embodiments, the target voltage can be higher or lower than this voltage, depending on the design of the implant or other expected performance requirements. In an exemplary embodiment, this is a fixed value, while in other embodiments, the system may be one in which the target voltage may be adjusted automatically by the system and / or under the control of a healthcare professional, etc. Some additional features associated with the target voltage and / or selection and / or control of the target voltage are described below.

[0079] Still reference Fig. 9, it can be seen that there are a number of time intervals 912 where the implant load is constant. The time interval 912 spans a number of communication link updates 920 (here, by way of example, the interval 912 spans twenty (2) communication link updates, thus representing a 20 ms interval). By way of example only and not limitation, the implant load during the time interval 912 may be less than, equal to, or greater than 2, 2.25, 2.5, 2.75, 3, 3.25, 3.5, 3.75, 4, 4.25, 4.5, 4.75, 5, 5.25, 5.5, 5.75, 6, 6.25, 6.5, 6.75, 7, 7.25, 7.5, 7.75, 8, 8.25, 8. 5, 8.75, 9, 9.25, 9.5, 9.75, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30 mW, or any value or range of values ​​therebetween in increments of 0.01 mW (e.g., 2.28 mW, 7.88 mW, 3.03 to 5.55 mW, etc.). This may represent the load on the implant when the implant (in the case of a cochlear implant) is not evoked to hear the perception or otherwise when the recipient of the implant is in silence. This may correspond to the load required to keep the implant in a ready state to evoke hearing perception or otherwise provide the recipient with a stimulus indicative of a sound above the silence level. This may be the minimum value to keep the capacitor charge at a set level.

[0080] In an exemplary embodiment where a target voltage of the implant is utilized to control the power delivered to the implant, for example, when the voltage of the implant drops below the target voltage, the system controls the external component to deliver maximum power to the implant. When the implant voltage meets or exceeds the target voltage, the system controls the external component to deliver minimum power to the implant because the power delivered to the implant from the external component is sufficient to address the current load condition of the implant and / or because the load has decreased for any reason. This continues in an iterative manner, for example, during the use of the implant to evoke hearing perception or otherwise during the time period when the implant is activated.

[0081] Referring to the RF envelope 930, it can be seen that during the time interval 912, the duty cycle of the power transmission device of the external component reaches the maximum power transmission six (6) times, and for most of these times, the maximum power lasts for 1 ms. The fourth power transmission, or more accurately, the fourth time that the power transmission reaches the maximum value in the interval 912, lasts for two cycles. This may be because the power transmitted during this maximum power transmission time transmitted during the first cycle is insufficient to raise the voltage of the implant above the target voltage and / or to the target voltage (with the implant load remaining constant). That is, at the end and / or at a specified time during the first cycle, the system checks the voltage of the implant and determines that the voltage is below the target voltage, and therefore instructs the external component to remain at the maximum power transmission level for another cycle, and this continues until it is determined that the voltage of the implant meets and / or exceeds the target voltage (at which time the system instructs the external component to stop transmitting power at the maximum voltage), which may therefore correspond to transmitting power at the minimum voltage. The bottom graph showing implant voltage versus time presents the target voltage 950 and implant voltage 960 measured during the time interval 912 and additional time intervals. As can be seen, when it is determined that the implant voltage 960 is less than the target voltage 950, the external component is instructed to provide power to the implant at a maximum power level.

[0082] In certain embodiments, it should be noted that some of these may have very subtle and sometimes negligible influence on link in the short term and / or medium term, and the position of external components relative to implant components can be relative to lateral displacement and relative to both longitudinal displacement displacements.Here, this may be very subtle displacement, which may be the result of simple inertia caused by the movement of the recipient or even the recipient's pulse.The features that can change link / influence link and / or influence the load on implant will be discussed in more detail below.

[0083] Return to reference Fig. 9 , it can be seen that during interval 912, there are six low / minimum power transfer periods interleaved between the six maximum / high power transfer periods. These low / minimum power transfer periods are also of varying lengths. Again, this embodiment of the power transfer scheme shuts off the implant voltage, and if the implant voltage is at and / or above a certain level (the target voltage), the external component transfers power at a lower level. Therefore, it can be seen that there is a power transfer scheme that is binary in nature. When the implant needs power, or at least relative to time interval 912, when the implant needs power to maintain the target voltage, power is transferred from the external component at the maximum setting. When the requirement for voltage maintenance is met, maximum power transfer is terminated and only minimum power transfer occurs.

[0084] like Fig. 9As can be seen in FIG. 1 , interval 912 is immediately followed by a second interval, namely time interval 914. During time interval 914, the load on the implant increases. This may be a result of the sound environment becoming louder. By way of example only and not limitation, this may correspond to a sound that increases in volume rapidly in a linear manner. And note that while Fig. 9 The increase in implant load shown in is linear (and the decrease in implant load is also shown as being linear), but in other scenarios, the increase and / or decrease in load may be parabolic and / or exponential or may otherwise follow a curve. Regardless of why the implant load increases during time interval 914, it can be seen that for approximately 20 ms, which is the length of time interval 914, the load on the implant increases, and the increase occurs in a linear manner. Referring to the RF envelope 930, it can be seen that there are seven (7) time periods in which the external component reaches maximum power to transfer power to the implant, each of which is separated by a time period of low power transfer. In addition, it can be seen that these high power transfer periods vary in length. This may be due to any of the reasons detailed above and / or reasons that will be further expanded upon below. Referring to the implant voltage versus time graph, it can be seen that when the implant voltage 960 drops below the target voltage 950, a period of maximum power transfer begins, and the period of maximum power transfer is maintained until the implant meets and / or exceeds the target voltage, and then a period of low and / or minimum power transfer begins until the implant voltage drops below the target voltage.

[0085] And note that the sampling of the implant voltage occurs digitally. Here, the implant voltage is sampled once every millisecond. In other embodiments, the implant voltage can be sampled at least once every two or three or 4ms, or can be sampled faster than 1ms (or shorter than these time periods). The implant voltage can be sampled every cycle, or can be sampled every two or three or four cycles or more. And note that the number of times the implant voltage is sampled can vary according to a given scenario. For example, during normal operation, the implant voltage can be sampled every cycle, but after an extended silent period or after the implant voltage has maintained a stable period, the system can begin to sample the implant voltage every two or three or more cycles. In addition, in some embodiments, the implant voltage is always sampled every cycle. This can have practical value in terms of enabling the system to immediately meet the needs of the implant regarding the implant load, or more accurately, when combined with an arrangement in which an external component immediately applies the maximum power relative to the power transmitted to the implant, the system can be enabled to meet the immediate needs of the implant regarding the implant load.

[0086] Fig. 9Also shown is a time interval 916 where the increase in implant loading ceases and is constant, albeit more than twice as long as was the case during time interval 912. However, it can be seen that the RF envelope shows the length of time that the external component is transmitting power at the maximum power level during each of the maximum power level transmission time periods is longer than the length of time interval 914. This is the external component providing power to the implant to maintain the implant at or above the target voltage at a higher implant load. But there is more. Fig. 9 A dashed line 915 is shown above. This represents a change in the overall system relative to the immediately preceding situation. Here, in this exemplary scenario, this represents a recipient changing the volume cochlear implant system (or a system that automatically changes the volume), which causes an increase in the implant load beyond the load that can be directly attributed to the change in the environment that causes the linear increase in interval 914. Here, the increase in volume increases the required current level output by the electrodes of the cochlear implant. Alternatively, by way of example only, this may correspond to a change in the spectral composition of the sound environment, where different electrodes of the electrode array are more excited than in the previous situation, and the electrodes have a higher impedance relative to the electrodes used for stimulation at the previous frequency. In fact, in an alternative embodiment, the beginning of time interval 914 may represent the beginning of an increase in volume of the cochlear implant, the increase being linear, and then time position 915 may correspond to an increase in the loudness of the environment. In any case, as can be seen, the length of time that the external component applies maximum power is longer after time position 915 than before time position 915. As can be seen, during time interval 916, the length of time of maximum power is approximately as long as the length of time of maximum power during time interval 914 after time position 915. In this exemplary scenario, this may be because the cochlear implant is set to cause an increased volume at time position 915 and / or because the environment is louder during this time interval than in time interval 914. It can also be seen that during time interval 916, the length of the low power transmission period is the shortest compared to the previous two time intervals. When comparing the RF envelope plot with the Fig. 9The reason for this can be seen when comparing the implant voltage versus time graph shown in . As can be seen, the increased load demand of the implantable component causes the implant voltage to drop to a relatively low level (after increasing to a level above the target voltage), and the drop occurs at a relatively steep rate relative to what occurred before time interval 916. In fact, as can be seen, the rate of implant voltage increase from the beginning of each maximum power transfer period is lower during time interval 916 than during time intervals 912 and 914. It can also be seen that the rate of implant voltage decrease after each maximum power transfer period is completed (the rate during the minimum power transfer period) is greater during time interval 916 than during time intervals 912 and 914. This may be because the implant load is higher than during the previous time interval, and therefore, the drop is steeper and the voltage increase is more gradual (because more real-time power is consumed to evoke hearing perception, so less power is available to charge the capacitor, for example, thereby slowing the rate of increase of the implant voltage).

[0087] Again, all of these scenarios are exemplary and are presented to simply explain how the power transfer scheme according to the present embodiments may operate / function.

[0088] Fig. 9 Also shown is time interval 918. Time interval 918 may be a time interval where relative silence occurs at the beginning or where the environment otherwise associated with time interval 912 returns. Here, the cochlear implant may be set to the same volume as was the case at the beginning of time interval 916 (and therefore higher than was the case during time interval 912), but due to the relative silence, the implant is not stimulating, and therefore the load on the implant is the same as was the case during time interval 912. For example, if the environment during time interval 912 was an environment with a constant noise level but not silent, and therefore the implant was stimulating at that constant level, then the drop in implant load from time interval 916 to time interval 918 would not always return to the same level as was the case during time interval 912, because the volume of the cochlear implant would be set higher than was the case during time interval 912. In any case, in the scenario described for explaining the occurrence of implant load changes, at the beginning of time interval 918, there is silence, but then immediately there is an increased noise level, which therefore increases the load on the implant because the implant steadily increases the current applied by the electrodes during time interval 918 to transmit the increase in ambient loudness to the recipient (loudness increases linearly).

[0089] Time interval 922 is the time interval at which the load on the implant increases more rapidly. This may be due to changes in the environment or other reasons. But as can be seen, in the middle of time interval 922, changes that increase the implant load more rapidly occur. This change is fast enough so that in the remaining time interval, the external component delivers maximum power to the implant. At time interval 924, the implant load stabilizes at a very high level. Here, this can correspond to the implant delivering the maximum comfort level output from the electrode for the sound frequency to which it is exposed. For example, the surrounding environment may be very loud, so the maximum output set during the assembly of the implant occurs during time 924. As can be seen, the implant voltage is effectively kept below the target voltage throughout the entire period of time interval 924. The implant voltage is low, but does not reach the reset level, which can be, for example, 3V. Time 924 ends with a reduction in ambient sound, and therefore the electrode is no longer stimulated at the maximum comfort level. The implant voltage therefore rises rapidly to a voltage higher than the target level, and then the power transmission scheme converts the power output to a minimum power output, as can be seen. Therefore, this starts time interval 926, which is an interval that reduces the implant load on the implant. As can be seen, as the implant load decreases, the time intervals between the maximum power periods begin to be further apart, and the length of the maximum power periods begins to decrease to a significant extent. As can be seen, by way of comparison only, the implant voltage increases rapidly between given updates at a faster rate than during the time interval 916. Thus, the implant voltage increases above the target voltage for more than in the interval 916. And, because the load is relatively low, the time above the target voltage is also longer relative to the situation during the interval 916.

[0090] As an example, it is important to note that some of these may have a very subtle and sometimes negligible effect on the link in the short and / or medium term. In practice, the flap thickness (the distance between the implanted coil and the external coil) may change relatively immediately for a variety of physiological reasons, such as movement of the head at that location that causes the skin to tense and / or gather, and / or due to movement of the recipient where the inertia of the external coil (or even the implanted coil for that matter) changes the lateral and / or longitudinal displacement of the coil. In addition, things such as temperature or other conditions may change the implant tuning and / or the external coil tuning. In an exemplary embodiment, again with respect to the above reminder that will be expanded upon temporarily, the impedance of the recipient's tissue may have changed since the previous power transfer (although again, this may generally be negligible in the short term as the impedance of the tissue may not change quickly enough over the course of a few milliseconds or 5 milliseconds or 10 milliseconds (short term) to affect the link), the required stimulation current may change, the ambient sound conditions may change, and the implant electronic load changes may change. It is true that these things can affect the link in the medium term (e.g., more than a second or two) by larger amounts than can be recovered in milliseconds (e.g., the average length of maximum power for power transfer may be longer during the medium term), and these can also affect the link in the long term (e.g., more than 5 minutes). But these phenomena may affect the link in the short term, but the impact is small. A scenario that can change the power requirements of the implant in the medium term and / or long term can be the stimulation strategy applied by the cochlear implant system. Moreover, the required stimulation current can greatly affect the power requirements of the implant. In fact, the current output is a large (if not the largest) power intensive feature of the cochlear implant. A corollary to this is that the cochlear implant is located in a sound environment. The louder / more complex the sound, the greater the load on the implant. All of these things can change rapidly. Some additional factors that may cause large implant load transients (which may cause the implant voltage to drop rapidly, where the teachings herein may react quickly to prevent the voltage from dropping to the point it would otherwise drop to, and thereby avoid a reset, all of which are exemplary) may be sporadic communications over the wireless link, periodic diagnostics that are occasionally run in the implant, access to non-volatile memory for the purposes of data logging or reading data (e.g., mapping, firmware, etc.), and periodic functions such as battery management, data integrity checks, monitors, etc.

[0091] And note that there are corollaries for retinal implants, such as bright lights (similar to loud sounds affecting the load on the implant), load changes, etc. Also, for example, flap thickness, implant tuning, and external coil tuning can affect power delivery with respect to a retinal prosthesis.

[0092] In view of the above, in an exemplary embodiment, there is a device, such as a hearing prosthesis including a cochlear implant or some other type of sensory prosthesis such as a retinal implant, comprising an external component, such as a behind-the-ear device including a signal processor and a microphone or a light processor and a light capture device, to which a transcutaneous radio frequency inductive communication coil is connected. Figure 1 . This external component of the prosthesis is configured to provide power (transdermally) to an implanted device implanted in the human body, such as, by way of example only and not limitation, an implantable portion of a cochlear implant electrode array. This implantable component also includes a radio frequency inductive communication coil. In an exemplary embodiment, the implant component can transmit data to the external component. More specifically, the external component can transmit power and / or data to the implant via a forward link, and at least in some embodiments, the external component can transmit at least data from the implant to the external component via a backward link. In some embodiments, the external component pauses transmission in a manner synchronized with the logic circuit of the external component, or otherwise pauses transmission in a manner that can be detected, or pauses transmission when the external component notifies the implant that the pause will begin or has begun, and then the implant can communicate with the external component.

[0093] The implant device is a power consuming device which may or may not include a battery (but will include a capacitor in many embodiments). In some embodiments, the implant device cannot operate for more than a few seconds (if at all) without an external component providing power to it (when the capacitor is fully discharged and not recharged). In an exemplary embodiment, the implantable component, or more accurately, the electronics of the implantable component, has a voltage level during operation that will vary with the load on the electronics and the amount of power transmitted to the implant by the external component. The implantable component is designed to operate within the minimum voltage and maximum voltage of its electronics. In this regard, the implant is typically designed so that the minimum voltage is an amount greater than the implant reset voltage. The implant reset voltage is a voltage where if the implantable component drops below this voltage, the implantable component resets itself, which can effectively turn off the implant and then turn it back on. Therefore, in some embodiments, the implant reset voltage for this purpose can be 1 or 1.5 or 2 or 2.5 or 3 or 3.5 or 4V or more or less, or any value or range of values ​​therebetween in increments of 0.05 volts. The minimum voltage of the operating range of the implantable component can be above the reset voltage by 0.25 or 0.5 or 0.75 or 1 or 1.25 or 1.5 or 1.75 or 2 V or more or less, or any value or range of values ​​therebetween in increments of 0.05 V. The maximum voltage of the operating range can be below the so-called manufacturing voltage or shunt voltage by 0.25 or 0.5 or 0.75 or 1 or 1.25 or 1.5 or 1.75 or 2 V or more or less, or any value or range of values ​​therebetween in increments of 0.05 V, which can be 7 or 7.5 or 8 or 8.5 or 9 or 9.5 or 10 or 10.5 or 11 or 11.5 or 12 or 13 or 14 V or more, or any value or range of values ​​therebetween in increments of 0.05 V.

[0094] The target voltage is between the minimum operating voltage and the maximum operating voltage (including the minimum operating voltage and the maximum operating voltage). In an exemplary embodiment, the target voltage will be set to 5.5 volts, by way of example only. However, as will be described in more detail below, the system can be configured to adjust the target voltage according to the performance needs of the implant and / or the load to which the implant is subjected. For now, it will be assumed that the implant operates at a set voltage of 5.5.

[0095] The external component is configured to provide multiple levels of power output at any time, and the power of the output will be received by the implant in order to maintain the implant voltage at a given target voltage. In an exemplary embodiment, the external component is configured to dynamically change the power output level to the implant device. The dynamic change is based on data, and the data is based on the load of the implant device. The data can be obtained by reverse link telemetry as described above. Alternatively and / or in addition, the data can be obtained by analyzing the properties of the current and / or voltage of the coil of the external component, wherein these properties can be used as potential variables to estimate or otherwise evaluate the voltage of the implant at any given point in time.

[0096] In the exemplary embodiment detailed above, the external component is configured to provide power output in a digital binary manner relative to its power output level. It should be noted that the power output does not include the absence of power output. Therefore, the above digital binary manner does not include zero power output as one of the two components. Instead, the digital binary manner includes a first output level and a second output level. As briefly detailed above, the first output level can be the maximum power output of the external component, and the second output level can be the minimum power output of the external component. These minimum and maximum power output components can be set accordingly for the transdermal transmission power scheme being applied. In an exemplary embodiment, the first output level can be a value that is at or above 75, 80, 85, 90 or 95% of the maximum possible power output of the external component or any value or range of values ​​in 1% increments therebetween. For example, this would be the maximum power output without all software and / or firmware constraints (where the software can limit the output—in fact, in an exemplary embodiment, that is, how the first output level is set—the external component can output more, but it is blocked by software and / or firmware). In an exemplary embodiment, the first power level can be at or above the maximum steady-state load of the implant (e.g., within 1, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5, 5.5, 6, 6.5, 7, 7.5, 8, 8.5, 9, 9.5, or 10% of the maximum steady-state load (provided it is at or above that load)).

[0097] In embodiments, the second output level may be a value at or below 60, 55, 50, 45, 40, 35, or 30% of the maximum possible electrical output of the external component, or any value or range of values ​​therebetween in 1% increments. In embodiments, the second output level may be at or above the minimum steady-state load of the implant (e.g., within 1, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5, 5.5, 6, 6.5, 7, 7.5, 8, 8.5, 9, 9.5, or 10% of the maximum steady-state load provided it is at or below that load). In some embodiments, the second output level may be at or below the minimum steady-state load of the implant (and again within any of the just-mentioned ranges).

[0098] Therefore, reference Fig. 9 The RF envelope of the external component, the high value may be 90% of the maximum possible power output of the external component, and the low value may be 50% of the maximum possible power output of the external component. Fig. 9 The RF envelope of the implant component, the high value can be a value within 4% of the maximum steady-state load of the implant component, and the low value can be a value within 4% (or 5% - these values ​​need not be the same) of the minimum steady-state load of the implant component.

[0099] In an embodiment, the maximum possible power output of the external component may be the power output obtainable when a control component of the external component that enables dynamic variation of the power output level in a digital binary manner is eliminated.

[0100] In an embodiment, the digital binary format includes a maximum power output and a minimum level power output. In an embodiment, this is set for a given power transmission scheme.

[0101] In an embodiment, the external component is configured to dynamically change the power output level to the implant device in a digital binary manner regardless of the load of the implant. In an embodiment, the external component is configured to dynamically change the power output level to the implant device in a digital binary manner at least at the value of the load of the implant, the value of the load of the implant is between any value or range of values ​​(including end values) of 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 90, 85, 90, 95 or 100% of the maximum operating load of the implant. In an embodiment, the external component is configured to dynamically change the power output level to the implant device in a digital binary manner at least at the value of the voltage of the implant between (including the minimum operating voltage and the maximum operating voltage) and / or at the reset voltage or above the reset voltage to the shunt voltage or below the shunt voltage or any value or range of values ​​therebetween in increments of 0.01 volts.

[0102] In an embodiment, the external component is configured to immediately (e.g., Figure 8 ) and / or effectively immediately increase the output power level by at least 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, 100, 105, 110, 115, 120, 125, 130 or 135% or more, or any value or range of values ​​in 1% increments therebetween (e.g., when changing from a low power output to a high power output), and immediately and / or effectively immediately decrease the output power level by at least 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75 or 80% or more, or any value or range of values ​​in 1% increments therebetween (e.g., when changing from a high power output to a low power output). In an exemplary embodiment, the increase and / or decrease is set and is always the case for all periods of operation of the device. In embodiments, the increasing and / or decreasing is the case for at least 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 60, 70, 80, 90, 120, 150, 200, 250, 300, 350, 400, 450, 500, 600, 700, 800, 900, or 1000 seconds or minutes of operation (e.g., without resetting the implant), wherein there are at least 10 , 15, 20, 25, 30, 35, 40, 45, 50, 60, 90, 120, 150, 200, 250, 300, 350, 400, 450, 500, 600, 700, 800, 900, 1000, 1250, 1500, 1750, 2000, 2500, 3000, 3500 or 4000 or more (or ten, 100 or 1000 times these amounts) increases and / or decreases.

[0103] In an embodiment, the digital binary mode includes a first level and a second level. Although the above-described embodiments focus on that these levels are maximum and minimum values, in other embodiments, this is not necessarily the case. In an embodiment, these levels can be levels with such values ​​(or falling within the range of values, the value changes from the lowest value of the range by no more than 0.1, 0.2, 0.3, 0.4, 0.5, 0.75, 1, 1.25, 1.5, 1.75, 2, 2.25, 2.5, 2.75, 3, 3.5, 4, 4.5, 5, 5.5, 6, 6.5, 7, 7.5, 8, 9, 10, 11 or 12%, or any value or range of values ​​with 0.01% as increments therebetween), the value corresponds to the longest time period of a given output level and the second longest time period of a given output level (if different from the longest time period) (if the same (unlikely event), the first level and the second level can be applied arbitrarily). In fact, the first level and the second level can be the first mode and the second mode (such as mean value, median and mode mean) of the use period of the implant. In exemplary embodiments, the period of use of the implant can extend over any of the time periods detailed herein and / or can be different, such as, by way of example only and not limitation, at least and / or greater than 1, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5, 5.5, 6, 6.5, 7, 7.5, 8, 8.5, 9, 9.5, 10, 10.5, 11, 12, 13, 14, 15, 16, 17, 18, 19 or 20 hours, or any value or range of values ​​therebetween in 0.1 hour increments, of continuous operation of the implant (the implant is not reset during these periods). In an embodiment, the period of use of the implant can be measured as 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25 consecutive days or weeks or months, or any value or range of values ​​in 1 day increments therebetween (this is not continuous / consistent operation - this considers the two power levels being applied for the longest period of time within that time, even if the device has been turned off / not used during the intervals within the period under investigation).

[0104] Thus, in an embodiment, there is a device in which the digital binary manner includes a first power output level and a second power output level different from the first power output level, and the first power output level is the power level output for the longest time period throughout the application during continuous use of the external component (e.g., no reset) and / or continuous use of the external component to power the implant / prevent implant reset, and the second power output level is the power level output for the second longest time period throughout the application during continuous use. In an embodiment, instead of "continuous use", the time period can be any time period in this document. It can be a time period between recharging of the external component or battery replacement of the external component, or a time period when the external component is active and the external coil is in inductive communication with the implant coil.

[0105] In an embodiment, one of the first power level or the second power level is lower than the other, and the other of the first power level or the second power level is higher than one of the first power level or the second power level by at least 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70 or 75% or any value or range of values ​​therebetween in increments of 0.1%.

[0106] In an embodiment, the power level associated with the longest period of power levels will be the minimum / low power output. In an embodiment, the power level associated with the longest period of time or the second longest period of time will be the maximum / high power output. In an embodiment, during one or more of the investigated time periods / periods herein (excluding periods of minimum / low power), the period of high / maximum power output will collectively be longer than the next longest period of time and / or longer than all other periods (again excluding low / minimum power output) by at least 20, 25, 30, 35, 40, 45, 50, 60, 70, 80, 90, 100, 125, 150, 175, 200, 225, 250, 275, 300, 350, 400, 500, 600, 700, 800, 900, 10 ...500, 500, 500, 500, 500, 5 450, 500, 550, 600, 700, 800, 900, 1000, 1250, 1500, 1750, 2000, 2250, 2500, 3000, 4000, 5000, 6000, 7000, 8000, 9000, 10000, 12500, 15000, 20000, 25000, 30000, 35000 or 40000%, or any value or range of values ​​in increments of 1%.

[0107] As seen above, embodiments may include transitioning from minimum power output to maximum power output, and / or vice versa, within a single cycle (milliseconds in some embodiments). Embodiments may include transitioning from minimum power output to maximum power output, and / or vice versa, within 0.5, 1, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5, 5.5, 6, 6.5, 7, 7.5, 8, 8.5, 9, 9.5, 10, 11, 12, 13, 14, or 15 ms, or any value or range of values ​​therebetween in increments of 0.05 ms, and / or vice versa for transitioning from maximum power to minimum power (and these values ​​need not be the same, an upward transition may occur faster than a downward transition, or vice versa). The completed transition may occur within 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, or 15 cycles.

[0108] Thus, as can be seen above, at least some embodiments include no ramp transitions from one power level to another, and some embodiments include steep ramp transitions.

[0109] Embodiments with the foregoing in mind include adaptive power transfer systems wherein, in some such examples, the adaptive power transfer system adapts to varying loads on the implant to maintain the implant at a given voltage (e.g., other “target” / operating parameters may be used as a basis for triggering adaptation of the system).

[0110] In an exemplary embodiment, the ramp-up time from the minimum / low power transfer level to the high power / maximum power level is less than and / or equal to 0.1, 0.2, 0.3, 0.4, 0.5, 0.6, 0.7, 0.8, 0.9, 1.0, 1.25, 1.5, 1.75, 2, 2.25, 2.5, 2.75, 3, 3.5, 4, 4.5, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14 or 15% of the total time of the immediately preceding lower power / minimum power transfer time period and / or the total time of the immediately preceding high power / maximum power transfer time period. In an embodiment, this is the case for transitions from low power to high power at least 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29 or 30 times, or any value or range of values ​​in increments of 1 second therebetween, within a time period that does not extend for more than 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29 or 30 times, or any value or range of values ​​in increments of 1 second therebetween. This may be the case for 70 or 75 or 80 or 85 or 90 or 95% or more of all such transitions during a day of use of the cochlear implant. This may also be the case for the reverse transition from maximum power to minimum power.

[0111] Fig. 9A An exemplary ramp up and ramp down are shown. As can be seen, the first ramp up spanning two cycles (2ms) will not meet the 10% requirement for the time it is less than the ongoing maximum power, but the remaining ramp up will meet that requirement (as well as the previous minimum power), and the first ramp down will meet the 10% requirement for both the previous high power and the ongoing low power.

[0112] In an exemplary embodiment, during ramp up or ramp down, there is no identical power output level for two cycles and / or 3 or 4 or 5 or 6 or 7 or 8 or 9 or 10 cycles during the ramp up or ramp down period. In an embodiment, when there is a previous ramp up and / or an ongoing ramp down, the maximum power level output is maintained for at least and / or equal to 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14 or 15 cycles or any value or range of values ​​therebetween in increments of 1 cycle. In this document, a cycle can be 1 ms, or longer or shorter, as detailed herein. For purposes of textual economy, references to cycles correspond to alternative disclosures of time periods associated therewith for respective time periods of cycles disclosed herein, and vice versa.

[0113] Thus, it can be seen that embodiments of dynamically changing power output levels in a digital binary manner can include ramp-up periods and ramp-down periods interleaved between binary power outputs. As described above, in some embodiments, these ramp-ups and ramp-downs are very limited in time, so limited that some can be effectively performed immediately.

[0114] As described above, embodiments provide for the external component to include an inductive power transfer coil, and the external component to be configured to digitally dynamically vary the duty cycle of engagement of the coil, thereby dynamically varying the power output level to the implanted device in a digital binary manner.

[0115] In an embodiment, there is a device, such as any of the devices detailed above, comprising an external component, such as a prosthesis, configured to provide power to an implanted device implanted in a human body, wherein the external component is configured such that a primary power variation scheme is based on varying the power output to the implanted device by varying the length of a period of continuous maximum power output. The period of continuous maximum power is Figure 8 Those maximum power periods shown in , which are separated by periods of minimum power output, which periods of minimum power output happen to be continuous as shown. "Major power variation scheme" means that this is a designed power scheme that causes external components to operate accordingly in a purposeful manner. This is in contrast to scenarios such as environmental circumstances that simply cause external components to operate in the presence of continuous maximum power output of varying lengths. In other words, a major power variation scheme is not a scheme that allows its features to occur, but a scheme that causes its features to occur. In fact, this is the case when these features may not exist during another operating scheme. By way of example only and not limitation, Figure 7 The power variation scheme of the arrangement does not have a primary power variation scheme based on varying the power output to the implanted device by varying the length of the time period of continuous maximum power output. Rather, its primary power variation scheme is based on varying the power output to the implanted device by increasing and / or decreasing individual power output levels in a discrete manner. It is true that the length of time of the possible maximum power output can be varied, but this is not the operating principle of the power variation scheme.

[0116] In an embodiment, the system is configured to implement multiple main power change schemes that are different from each other. For example, the external components can be configured to implement Figure 7 The embodiment operates according to the power scheme and also implements Figure 8In an embodiment, a user of the external component can control the external component to switch from one power scheme to another power scheme. In an exemplary embodiment, this can be done automatically based on the load and / or settings of the system. By way of example only and not limitation, if the implant is switched from monopolar stimulation to multipolar stimulation, the power requirements of the implant can be increased by two or three times or more. In an exemplary embodiment, the implantable component can switch from a primarily power variation scheme that varies the power output level based on the power requirements of the implant to a primarily power variation scheme that does not change the level for time periods of continuous maximum power output. In an exemplary embodiment, the implantable component can automatically switch.

[0117] As described above, in exemplary embodiments, the system may be a system in which there is only one main power variation scheme, and this is the scheme that changes the length of the time period of continuous maximum power output. In exemplary embodiments, the system may be a system in which two or more main power variation schemes are stored in its memory, but there is one main power variation scheme that is activated. In exemplary embodiments, a healthcare professional or the like must intervene to change the main power variation scheme that is implemented. Again, in at least some exemplary embodiments, the power scheme that is implemented is software and / or firmware based, so the device can be transformed from another, or at least in some embodiments, the device can be modified to operate according to a given power variation scheme.

[0118] It should be noted that the primary power variation scheme may be different from the scheme that changes the length of the time period and / or may include other features. By way of example only and not limitation, the primary power variation scheme may include the above-described binary maximum and minimum power transfers. And this primary power variation scheme need not be mutually exclusive with a primary power variation scheme based on changing the power output by changing the length of the time period of continuous maximum power output.

[0119] In an embodiment, the primary power variation scheme further comprises changing the length of the time period of minimum power output. And in some embodiments, the primary power variation scheme has corresponding time periods of minimum power output interleaved with corresponding time periods of maximum power output. In an embodiment, there may be ramp-up and / or ramp-down periods between these lengths of the time periods of minimum and maximum power output. In some embodiments, the transition between the time periods of minimum power output and maximum power output may be immediate and / or effectively immediate. In an embodiment, the time periods of minimum power output and maximum power output are continuous with each other.

[0120] In at least some embodiments, the primary power variation scheme increases power to a maximum power output in a non-ramp and / or effectively non-ramp manner, and / or decreases power to a minimum power output in a non-ramp and / or effectively non-ramp manner. Thus, embodiments may include a primary power variation scheme that changes power output in a non-ramp and / or effectively non-ramp manner.

[0121] Embodiments may include a primary power variation scheme that varies the ratio of the respective length of time of maximum power output to the respective length of time of minimum power output. In an exemplary embodiment, these ratios are the ratios of two consecutive power transmissions.

[0122] Consistent with the teachings detailed above, in an exemplary embodiment, the external component is configured to change the power output in the primary power scheme based on data based on the power load of the implanted device. This can be based on feedback from the implant via a backlink, or can be based on latent variables.

[0123] Embodiments include methods. Fig.11 An exemplary flow chart of an exemplary method (method 1100) according to an exemplary embodiment is shown. Method 1100 includes method action 1110, which includes the action of automatically obtaining data based on data affected by the power load on the power-consuming implanted medical device implanted in the human body. For example, this can be an excessive or insufficient indication of obtaining a voltage level and / or an implant exceeding a target voltage or being below a target voltage. This can be an actual load value. This can be obtained through a reverse link, or can be obtained through potential variables or by evaluating the characteristics of, for example, an external coil. Any device, system and / or method that can enable the execution of method action 1110 can be used, as long as the teachings herein can be implemented in this way. In an embodiment, method action 1110 is performed every cycle or every other cycle or every three cycles, or is performed by any algorithm that can have practical value.

[0124] Method 1100 also includes method action 1120, which includes the action of automatically analyzing the obtained data. This can be performed by an external component, or it can be performed by an implantable component (or both). The result can be transmitted to the outside, or a simple command can be transmitted to the external component. Regarding the latter, the implantable component can provide the result of the analysis to, for example, an external component via a backward link. This can be performed automatically by a processor or a logic circuit, etc. A lookup table can be used to analyze the obtained data. As an example only but not as a limitation, if the obtained data obtained in method action 1110 indicates that the voltage of the implant is lower than the target voltage, the analysis can indicate that the external component should apply or otherwise increase the power transmission to the implanted component. And this leads to method action 1130, which includes the action of providing power to the implanted medical device transdermally by increasing the power to the implant from the minimum amount to the maximum amount or reducing the power to the implant from the maximum amount to the minimum amount according to the result of the analysis. In an embodiment, method action 1120 is performed every cycle or every other cycle or every three cycles, or is performed by any algorithm that can have practical value.

[0125] In an embodiment, a method is provided wherein the acts of automatically acquiring and analyzing (acts 1110 and 1120) are performed X times over a period of 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15 seconds or minutes or any value or range of values ​​therebetween in 1 second increments (or any time period detailed herein for purposes of text economy), and Y results of the analysis of the acquired data are a need to increase the level of power provided transdermally to the implanted medical device, wherein X and Y (and they need not be the same) may be ... , 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, 40, 50, 60, 70, 80, 90, 100, 120, 140, 160, 180, 200, 250, 300, 350, 400, 450, 500, 550, 600, 700, 800, 900 or 1000 or more, or any value or range of values ​​in increments of 1 therebetween. (And it should be noted that actions 1110 and 1120 can be performed more than X times - these are the number of times the method is satisfied.) Moreover, in this embodiment, the corresponding increase in the level of power provided transdermally to the implanted medical device increases by at least 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70 or 75% within 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14 or 15 milliseconds, or any value or range of values ​​in 1 ms increments therebetween, or any value or range of values ​​in 1% increments therebetween.

[0126] In an embodiment, during a period corresponding to (in some embodiments, at least as long as) any of the above time periods during which the actions of automatically obtaining and analyzing are repeated (e.g., any number of times described above), the load of the implanted medical device changes upward or downward by at least 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, or 70%, or any value or range of values ​​in 1% increments therebetween (the value of each change need not be the same) by at least 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, 31, 32, 33, 34, 35, 36, 37, 38, 39, 40, 41, 42, 43, 44, 45 400, 450, or 500 times or more or any value or range of values ​​in increments of 1 therebetween. The voltage of the implanted medical device during the time period and / or the average and / or median voltage of the implanted medical device deviates from the highest voltage during the time period by no more than 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29 or 30%, or any value or range of values ​​in increments of 1% therebetween.

[0127] In embodiments, prior to obtaining the data based on the data affected by the electrical load, the implanted medical device experiences the onset of a load transient that increases the load by at least 1.25, 1.5, 1.75, 2, 2.25, 2.5, 3, 3.5, 4, 4.5, or 5 times for 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30, 31, 32, 33, 34, or 35 milliseconds or any value or range of values ​​in 1 millisecond increments therebetween, and the data obtained is affected by at least a portion of the load transient. For example, the voltage of the implant may decrease below a target, and thus the data based on the data affected by the electrical load on each power-consuming implanted medical device may be the voltage of the implant. Alternatively and / or in addition, it may indicate that the voltage of the implant is below a target voltage. The original load value may be the data upon which the data is based. Other data may be present. In embodiments, the act of providing power transdermally provides sufficient power such that the voltage of the implanted medical device returns to a value within 10, 9, 8, 7, 6, 5, 4, 3, 2, or 1% of the value just before the load transient began, or any value or range of values ​​in 0.1% increments therebetween, within 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, or 15 milliseconds of the transient being completed, or any value or range of values ​​in 1 millisecond increments therebetween. In embodiments, during the transient, the voltage of the implanted medical device does not deviate from the target voltage or the voltage just before the transient by more than 40, 35, 30, 25, 20, 15, 10, 9, 8, 7, 6, 5, 4, 3, 2, or 1%, or any value or range of values ​​therebetween. In embodiments, during a transient, the average and / or median deviation from a target voltage or a voltage just prior to the transient does not exceed 30, 25, 20, 15, 10, 9, 8, 7, 6, 5, 4, 3, 2, or 1%.

[0128] As an example, if the implant consumes 5 mW during the first time interval, the load of the implant is increased to 25 mW (which may occur if the stimulation strategy suddenly changes from monopolar stimulation to multipolar stimulation). This load increase may occur in less than 5 ms. The voltage of the implant just before the load increase may be 5.7 volts. An embodiment is such that the voltage of the implant does not drop below 3.42 volts (a 40% drop).

[0129] In an embodiment, a power-consuming implanted medical device has a voltage operating range having a lower limit that is above a reset voltage and an upper limit that is below a shunt voltage, and prior to obtaining data based on data affected by the power load, the implanted medical device experiences the onset of a load transient that increases the load by any of the above amounts within any of the above time periods, wherein at least the increased load (e.g., quadrupled load) exists for at least 0.5, 1, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 20, 25, 30, 35, 40, 45, or 50 seconds or more or any value or range of values ​​in 0.1 second increments therebetween, and the voltage of the implanted medical device remains within the operating range during this time period.

[0130] In an embodiment, the implantable medical device is an implantable component of a partially implantable cochlear implant, the act of transcutaneously providing power to the implantable medical device is performed by an external component of the partially implantable cochlear implant, the implantable medical device is operated at a maximum load for at least 0.5, 1, 1.5, 2, 2.5, 3, 3.5, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, or 15 seconds, or any value or range of values ​​therebetween, during which the acts of automatically obtaining and analyzing are repeatedly performed (e.g., any number of times as described above). In this embodiment, the current output from the electrodes of the implantable component is equal to the set current value for all ambient sounds captured during the period. In embodiments, during the time period of maximum load, for at least 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85 or 90% of the electrodes of the channel, the current output of the electrodes of the channel is at least halfway or at least three quarters between the comfort level or the threshold level and the comfort level for frequencies below 500, 1,000, 1500, 2,000, 2,500 or 3,000 Hz or any value or range of values ​​therebetween in 1 Hz increments. In embodiments, the cochlear implant is a fully implantable cochlear implant.

[0131] Embodiments may include adjusting the target voltage to provide more "gap" between the lower operating range (and therefore reset) and the target voltage. This may reduce efficiency, but if managed appropriately, the reduction in efficiency may be more limited. Fig.10An exemplary scenario of target voltage 1030 being adjusted over time is shown. Line 1010 corresponds to a set baseline target voltage. This is an ideal target voltage, or otherwise a target voltage that the implant will have during most, if not substantially all, of its operational life. The target voltage may be a lower limit of the above-mentioned operating voltage, or may be a voltage that is higher than the lower limit of the operating voltage. If the lower limit of the operating voltage is set to be sufficiently higher than the reset voltage, the set baseline target voltage at line 1010 may be the lower limit of the operating voltage, because there will be sufficient flexibility so that if the voltage drops below the lower limit operating voltage in a short period of time until the teachings detailed herein can cause the voltage to be raised, the drop will not reach the reset voltage, because the teachings detailed herein can intervene fairly quickly to slow down and otherwise terminate the reduction of the target voltage. In this regard, in an exemplary embodiment, there is operation of the implant within any one or more of the operating time periods detailed above wherein the deviation from the target voltage in the downward direction never exceeds 1, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, or 30%, or any value or range of values ​​therebetween in 0.1% increments, even at the maximum permissible voltage of the implant. The present invention is capable of load output (e.g., maximum current (comfort level current) under multipolar stimulation), and for any value or range of values ​​greater than 1, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22 or 23 ms or in increments of 1 ms therebetween, in some embodiments for a set baseline target voltage, and in other embodiments for other adjusted target voltages, a situation where the voltage is below the target is never the case.

[0132] And regarding the adjusted target voltage, refer again to Fig.10, the system can be configured to adjust the target voltage according to the real-time implant power needs. More specifically, it can be seen that the implant voltage is initially set to voltage 1090, which is the lowest voltage setting (line 1020 represents the maximum operating voltage, which is a level sufficiently lower than the shunt voltage). During the first time interval, the time that the implant remains lower than the target voltage is within an acceptable or otherwise designed time frame. Then, there is a new situation, and there is practical value in raising the target voltage to level 1091 as shown. Now, even if the scenario of using the implant makes the implant voltage be reduced to below the target voltage, there is more "space" between the target voltage and the reset voltage relative to the situation where the target voltage is set to 1090. It can be seen that the target voltage can be even further increased to level 1092. This provides even more "space" between the newly set target voltage and the reset voltage. Level 1093 provides even more space between the target voltage and the newly set voltage. As can be seen, in the scenario of use, the load on the implant or the predicted load on the implant otherwise decreases, so the system reduces the target voltage back to the baseline target voltage represented by level 1094 on line 1010. Then, due to further changing conditions where a very very high load is applied to the implant, the implant can increase the target voltage from the baseline all the way to the maximum operating voltage shown at level 1095 located on line 1020. This represents the maximum implant voltage within the operating range, and its maximum value is a practical amount lower than the shunt voltage. When the situation changes, the set voltage is reduced by more than 50% of the range between the maximum voltage and the minimum voltage to level 1096, and then when the situation changes further, the target voltage is reduced to the baseline target voltage 1097, as shown. Therefore, embodiments can utilize the above teachings with dynamically changing target voltages. This can have practical value for setting the implant in a power state that allows the maximum current or otherwise desired current to flow from the electrode. This can be practical for maintaining the desired volume perceived by the recipient, where a reduction in current can be perceived as a reduction in volume. In other words, by changing the target voltage and otherwise increasing the target voltage above the baseline, it can be further ensured that the implant will have sufficient voltage levels to provide the desired or otherwise necessary current to evoke hearing perception.

[0133] It should be noted that any method actions and / or functions disclosed herein correspond to the disclosure of a non-transitory computer-readable medium having thereon a program, code for executing such method actions, provided that it is within the skill of the art to do so.

[0134] Exemplary systems include one or more exemplary devices that can implement the teachings detailed herein, which can utilize automation in at least some embodiments. That is, exemplary embodiments include using any of the teachings herein to perform one or more or all of the methods and variations thereof detailed herein at least partially in an automated or semi-automated manner. Conversely, embodiments include devices and / or systems and / or methods that specifically prohibit automation due to a lack of enabling of automated features or the complete lack of such capabilities in the first instance.

[0135] It should also be noted that any disclosure of a device and / or system detailed herein also corresponds to disclosure of providing the device and / or system and / or utilizing the device and / or system in other ways.

[0136] In an exemplary embodiment, one or more devices and / or systems and / or subsystems, etc., disclosed herein and variations thereof include a processor or computer chip or logic chip, which may be a standard microprocessor supported by software or firmware, etc., programmed to perform one or more actions and functions herein, or the chip may be configured to perform one or more actions and functions herein. The processor and / or chip may include input and / or output connections. By way of example only and not limitation, in an exemplary embodiment, the microprocessor may have access to a lookup table, etc., with data and / or may compare features of an input signal and compare these features with features in a lookup table, and make a determination about the input signal by the relevant data associated with these features in the lookup table, and thus make a determination, etc. A numerical analysis algorithm may be programmed in a processor, etc. to implement the teachings herein.

[0137] It should be noted that the teachings detailed herein can be implemented in any processor-based device capable of implementing the teachings herein. In an exemplary embodiment, a sensory prosthesis such as a hearing prosthesis or an optical prosthesis can be modified by adjusting circuitry or otherwise providing programming to a given processor to implement the teachings detailed herein.

[0138] It should also be noted that any disclosure herein of any process for making or otherwise providing a device corresponds to the disclosure of the device and / or system produced thereby. It should also be noted that any disclosure herein of any device and / or system corresponds to the disclosure of a method for producing or otherwise providing or otherwise making such a device and / or system.

[0139] Any embodiment or any feature disclosed herein may be combined with any one or more or other embodiments and / or other features disclosed herein, unless expressly indicated and / or unless the art does not allow this. Any embodiment or any feature disclosed herein may be expressly excluded from use in combination with any one or more other embodiments and / or other features disclosed herein, unless such combination is expressly indicated and / or unless the art does not allow this exclusion.

[0140] Any functional or methodological acts detailed herein correspond to disclosures for doing so in an automated or semi-automated manner.

[0141] Although various embodiments of the present invention have been described above, it should be understood that they are presented by way of example only and not limitation. It will be apparent to those skilled in the relevant art that various changes in form and detail may be made therein without departing from the spirit and scope of the present invention.

Claims

1. A device comprising: An external component of a prosthesis configured to provide power to an implanted device implanted in a human body, wherein the external component is configured so that the power output level to the implanted device changes dynamically in a digital binary manner based on data, the data being based on a load of the implanted device.

2. The device according to claim 1, wherein: The external component is configured to dynamically change the power output level to the implant device in the digital binary manner regardless of the load of the implant.

3. The device according to claim 1 or 2, wherein: The digital binary format includes a maximum power output and a minimum level power output.

4. The device according to claim 1 or 2, wherein: The digital binary mode includes a first output level at or above 80% of the maximum possible power output of the external component and a second output level at or below 60% of the maximum possible power output of the external component, wherein the maximum possible power output is the power output that can be obtained when the control component of the external component that dynamically changes the digital binary mode of achieving the power output level is eliminated.

5. The device according to claim 1, 2, 3 or 4, wherein: The external part is an external part of the cochlear implant.

6. The device according to claim 1, wherein: The external component is configured to effectively and instantly increase the output power level by at least 60% and to effectively and instantly decrease the output power level by at least 35%.

7. The device of claim 1, 2, 3, 4, 5 or 6, wherein: The external component includes an inductive power transfer coil; and The external component is configured to digitally dynamically vary the duty cycle of engagement of the coil, thereby dynamically varying the power output level to the implant device in the digital binary manner.

8. The device of claim 1, 2, 3, 4, 5, 6 or 7, wherein: The digital binary format includes a first power output level and a second power output level different from the first power output level; and The first power output level is the power level output for the longest period of time throughout the application during continuous use of the external component to power the implant; and The second power output level is a power level output for a second longest period of time in the entire application during continuous use of the external component.

9. The device of claim 1, 2, 3, 4, 5, 6, 7 or 8, wherein: The device is a cochlear implant.

10. The device of claim 1, 2, 3, 4, 5, 6, 7 or 8, wherein: The device is a bone conduction device or a middle ear implant.

11. An apparatus comprising: An external component of a prosthesis configured to provide power to an implanted device implanted in a human body, wherein the external component is configured so that a primary power variation scheme is based on varying the power output to the implanted device by varying the length of a time period of continuous maximum power output.

12. The device according to claim 11, wherein: The major power variation scheme also includes varying the length of the time period of minimum power output.

13. The device according to claim 11 or 12, wherein: The primary power variation scheme has corresponding periods of minimum power output interleaved with corresponding periods of maximum power output.

14. The device according to claim 11, 12 or 13, wherein: The primary power change scheme increases power to the maximum power output in an effectively non-ramp manner.

15. The device according to claim 11, 12 or 13, wherein: The primary power variation scheme varies power output in an effectively non-ramp manner.

16. The device according to claim 11, wherein: The main power variation scheme changes the ratio of the corresponding length of time of maximum power output to the corresponding length of time of minimum power output.

17. The apparatus of claim 11, 12, 13, 14, 15 or 16, wherein: The external component is configured to vary the power output in the primary power scheme based on data, the data being based on the power load of the implanted device.

18. The apparatus of claim 11, 12, 13, 14, 15, 16, 17 or 18, wherein: The device is a cochlear implant.

19. The apparatus of claim 11, 12, 13, 14, 15, 16, 17 or 18, wherein: The device is a bone conduction device or a middle ear implant.

20. The apparatus of claim 11, 12, 13, 14, 15, 16, 17 or 18, wherein: The device is a retinal implant.

21. A method comprising: automatically obtaining data based on data affected by an electrical load on a power-consuming implanted medical device implanted in a human body; Automatic analysis of acquired data; as well as Power is transcutaneously provided to the implanted medical device by increasing power to the implant from a minimum amount to a maximum amount or decreasing power to the implant from the maximum amount to the minimum amount based on the results of the analysis.

22. The method of claim 21, wherein: performing the automatic acquisition and analysis ten times within a one minute period, and ten results of said analysis of the acquired data are a need to increase the level of power provided transdermally to said implanted medical device; and The corresponding increase in the level of power provided transdermally to the implanted medical device increases by at least 50% within 5 milliseconds.

23. The method according to claim 21 or 22, further comprising: Prior to obtaining data based on data affected by the electrical load, the implanted medical device experiences the onset of a load transient that at least quadruples the load within 10 milliseconds, the obtained data being affected by at least a portion of the load transient, wherein The act of providing power transdermally provides sufficient power such that within 10 milliseconds of quadrupling the load, the voltage of the implanted medical device returns to a value within 5% of the value just before the load transient began.

24. The method of claim 21, wherein: The load of the implanted medical device is changed upward and downward by at least 30% at least 5 times within a 1 minute period during which the actions of automatically obtaining and analyzing are repeatedly performed; and The voltage of the implanted medical device does not deviate from a maximum voltage by more than 25% during the 1 minute period.

25. The method of claim 21, wherein: The load of the implanted medical device is changed upward and downward by at least 30% at least 5 times within a 1 minute period during which the actions of automatically obtaining and analyzing are repeatedly performed; and The voltage of the implanted medical device does not deviate from the maximum voltage by more than 10% during the 1 minute period.

26. The method of claim 21, 22, 23, 24 or 25, wherein: The implantable medical device is an implantable component of a partially implantable cochlear implant; The act of transcutaneously providing power to the implanted medical device is performed by an external component of the portion of the implantable cochlear implant; The implanted medical device is operated at a maximum operating load for at least 10 seconds, during which the actions of automatically acquiring and analyzing are repeatedly performed; and The current output from the electrodes of the implantable component is equal to the set current value for all ambient sounds captured during the 10 seconds.

27. The method of claim 21, wherein: Prior to obtaining data based on data affected by the electrical load, the implanted medical device experiences the onset of a load transient that at least quadruples the load within 10 milliseconds, the obtained data being affected by at least a portion of the load transient, wherein The act of providing power transdermally provides sufficient power such that during the load transient, the voltage of the implanted medical device decreases by no more than 30% compared to the voltage of the implanted medical device just before the load transient.

28. The method of claim 21, wherein: The power-consuming implantable medical device has a voltage operating range having a lower limit above a reset voltage and an upper limit below a shunt voltage; Prior to obtaining data based on data affected by the electrical load, the implanted medical device experiences the onset of a load transient that at least quadruples the load within 10 milliseconds, the at least quadrupled load is present for at least 3 seconds, and the voltage of the implanted medical device remains within the operating range for at least 3 seconds; and The implantable medical device is an implantable part of a cochlear implant.

29. A cochlear implant external component, comprising: case; a radio frequency induction coil connected to the housing or supported in the housing, the radio frequency induction coil being configured to provide power to an implanted device implanted in a human body; Battery; as well as A circuit configured to provide power from the battery to the radio frequency induction coil, wherein The circuit is configured such that the power output level to the implant device is dynamically changed in a digital binary manner based on data, the data being based on a load of the implant device.

30. An apparatus wherein at least one of the following is true: The device is an external component of a prosthesis, the external component configured to provide power to an implanted device implanted in a human body, wherein the external component is configured such that a power output level to the implanted device is dynamically changed in a digital binary manner based on data, the data being based on a load of the implanted device; said external component being configured to dynamically change said power output level to said implant device in said digital binary manner regardless of said load of said implant; The digital binary mode includes a maximum power output and a minimum level power output; the digital binary mode comprising a first output level at or above 80% of a maximum possible power output of the external component and a second output level at or below 60% of the maximum possible power output of the external component, the maximum possible power output being a power output obtainable if a control component of the external component that achieves a dynamic change in the digital binary mode of power output level is eliminated; The external component is an external component of a cochlear implant; The external component is configured to effectively and immediately increase the output power level by at least 60% and to effectively and immediately decrease the output power level by at least 35%; The external component includes an inductive power transfer coil; said external component being configured to digitally and dynamically vary a duty cycle of engagement of said coil, thereby dynamically varying said power output level to said implanted device in said digital binary manner; The digital binary format includes a first power output level and a second power output level different from the first power output level; The first power output level is a power level output for a longest period of time throughout the application during continuous use of the external component to power the implant; The second power output level is a power level output for a second longest period of time throughout the application during continuous use of the external component; an external component of a prosthesis configured to provide power to an implanted device implanted in a human body, wherein the external component is configured such that a primary power variation scheme is based on varying power output to the implanted device by varying the length of a time period of continuous maximum power output; The major power variation scheme also includes varying the length of the time period of minimum power output; The primary power variation scheme has respective periods of minimum power output interleaved with respective periods of maximum power output; The primary power change scheme increases power to the maximum power output in an effectively non-ramp manner; The primary power variation scheme varies power output in an effectively non-ramp manner; The main power variation scheme changes the ratio of the corresponding length of time of the maximum power output to the corresponding length of time of the minimum power output; The external component is configured to change the power output in the primary power scheme based on data, the data being based on the power load of the implanted device; The device is configured to automatically obtain data based on data affected by a power load on a power-consuming implanted medical device implanted in a human body; The device is configured to automatically analyze the acquired data; the device being configured to transdermally provide power to the implanted medical device by increasing power to the implant from a minimum amount to a maximum amount or decreasing power to the implant from the maximum amount to the minimum amount based on a result of the analyzing; the device is configured so as to operate such that the acts of automatically acquiring and analyzing are performed ten times within a period of 1 minute, and ten results of said analysis of acquired data are a need to increase the level of power transdermally provided to said implanted medical device, and the corresponding increase in said level of power transdermally provided to said implanted medical device is an increase of at least 50% within 5 milliseconds; The device is configured so that within a 1 minute period during which the actions of automatically obtaining and analyzing are repeatedly performed, the load of the implanted medical device changes upward and downward by at least 30% at least 5 times, and the voltage of the implanted medical device does not deviate from the highest voltage by more than 25% during the 1 minute period; The device is configured so that within a 1 minute period during which the actions of automatically obtaining and analyzing are repeatedly performed, the load of the implanted medical device changes upward and downward by at least 30% at least 5 times, and the voltage of the implanted medical device does not deviate from the highest voltage by more than 10% during the 1 minute period; The implantable medical device is an implantable component of a partially implantable cochlear implant; the device being configured such that prior to obtaining data based on data affected by the electrical load, the implanted medical device experiences the onset of a load transient that at least quadruples the load within 10 milliseconds, the obtained data being affected by at least a portion of the load transient, wherein the act of providing electrical power transdermally provides sufficient electrical power such that during the load transient, a voltage of the implanted medical device decreases by no more than 30% compared to a voltage of the implanted medical device immediately prior to the load transient; The power-consuming implantable medical device has a voltage operating range having a lower limit above a reset voltage and an upper limit below a shunt voltage; The device uses a transdermal power transfer scheme with a duty cycle implant power mechanism that delivers maximum power or minimum power depending on whether the load / demand of the implant has been met or otherwise satisfied; The device meets implant power needs by dynamically changing the percentage of time of maximum power RF frames relative to minimum power RF frames; The device utilizes only the on-time and off-time of the maximum duty cycle implant power regulation; The device utilizes a transdermal power transfer protocol wherein the duty cycle is varied in the binary manner to adjust the voltage of the implant to meet a set target voltage of the implant, and / or a system implementing the transdermal power transfer protocol continuously and / or periodically evaluates the voltage of the implant to determine whether the implant voltage is above and / or below a target implant voltage; The device uses a system configured such that if the implant voltage is determined to be below a target voltage for the implant, the system applies maximum power to be transferred from the external component to the implant, and / or if the implant voltage is determined to be above its target voltage, the system applies minimum power to be transferred from the external component to the implant; The device effectively ensures automatic compensation of any load variations of the implant; the device controls the power delivered to the implant in dependence on a target voltage for the implant, such as when the voltage of the implant drops below the target voltage, the system controls the external component to deliver maximum power to the implant, and when the implant voltage meets or exceeds the target voltage, because the power delivered from the external component to the implant is sufficient to address the current load condition of the implant and / or because the load has decreased for any reason, the device controls the external component to deliver the minimum power to the implant, and the device is configured to continue this in an iterative manner during use of the implant to evoke hearing perception or otherwise during a period of time when the implant is activated; The device samples the implant voltage at least every 1 or 2 or 3 or 4 or 5 or 6 or 7 or 8 ms; The device is an external component of a retinal prosthesis; The device is an external component of a cochlear implant; said device being configured to provide said power output in a digital binary manner relative to said power output level thereof; The first output level can be a value at or above 75, 80, 85, 90 or 95% of the maximum possible power output of the external component or any value or range of values ​​therebetween in increments of 1%; the first power level being capable of being at or above a maximum steady-state load of the implant (e.g., within 1, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5, 5.5, 6, 6.5, 7, 7.5, 8, 8.5, 9, 9.5, or 10% of the maximum steady-state load provided it is at or above that load); The second output level can be a value at or below 60, 55, 50, 45, 40, 35 or 30% of the maximum possible power output of the external component or any value or range of values ​​therebetween in increments of 1%; the second output level can be at or above a minimum steady-state load of the implant (e.g., within 1, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5, 5.5, 6, 6.5, 7, 7.5, 8, 8.5, 9, 9.5, or 10% of the maximum steady-state load provided it is at or below that load); The second output level is capable of being at or below the minimum steady-state load of the implant; said external component being configured to dynamically change in said digital binary manner said power output level to said implant device at least at a value of said implant load between any value or range of values ​​spanning 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 90, 85, 90, 95 or 100% of a maximum operating load of said implant, inclusive; said external component being configured to dynamically change said power output level to said implant device in said digital binary manner at least at a value of said implant voltage between (inclusive of) a minimum operating voltage and a maximum operating voltage and / or at said reset voltage or above said reset voltage to at or below said shunt voltage or any value or range of values ​​therebetween in increments of 0.01 volts; The external component is configured to immediately and / or effectively immediately increase the output power level by at least 30, 35, 40, 45, 50, 55, 60, 65, 70, 75, 80, 85, 90, 95, 100, 105, 110, 115, 120, 125, 130 or 135% or more or any value or range of values ​​in 1% increments therebetween (e.g., when changing from a low power output to a high power output), and immediately and / or effectively immediately decrease the output power level by at least 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70, 75 or 80% or more or any value or range of values ​​in 1% increments therebetween (e.g., when changing from a high power output to a low power output), wherein the increase and / or decrease is set and is always the case for all periods of operation of the device, and / or the increase and / or decrease is for This is the case for at least 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, 60, 70, 80, 90, 120, 150, 200, 250, 300, 350, 400, 450, 500, 600, 700, 800, 900, or 1000 seconds or minutes of operation (e.g., without resetting the implant), wherein there are at least 10, 15, 20, 30, 45, 50, 60, 70, 80, 900, or 1000 seconds or minutes of operation during the time period. , 25, 30, 35, 40, 45, 50, 60, 90, 120, 150, 200, 250, 300, 350, 400, 450, 500, 600, 700, 800, 900, 1000, 1250, 1500, 1750, 2000, 2500, 3000, 3500 or 4000 or more (or ten, 100 or 1000 times these amounts) increases and / or decreases; One of the first power level or the second power level is lower than the other, and the other of the first power level or the second power level is higher than the one of the first power level or the second power level by at least 20, 25, 30, 35, 40, 45, 50, 55, 60, 65, 70 or 75% or any value or range of values ​​therebetween in increments of 0.1%; or The device is configured to transition from the minimum power output to the maximum power output within 0.5, 1, 1.5, 2, 2.5, 3, 3.5, 4, 4.5, 5, 5.5, 6, 6.5, 7, 7.5, 8, 8.5, 9, 9.5, 10, 11, 12, 13, 14 or 15 ms or any value or range of values ​​in increments of 0.05 ms therebetween, and / or vice versa for the transition from maximum power to minimum power (and the values ​​need not be the same, an upward transition can occur faster than a downward transition, or vice versa), and / or the completed transition can occur within 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14 or 15 cycles.

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