Apparatus and method for providing electrical energy to a target person

Abstract

This invention relates to a device configured to provide transcutaneous electrical energy to an implant placed within a subject. [Solution] The device includes a power adapter having a housing and a circuit at least partially disposed within the housing. The housing is configured to be coupled to an implantable device for placement in the body. The circuit is configured to be electrically connected to the power circuit of the implantable device when the housing is coupled to the implantable conductor. When the housing is coupled to the implantable conductor and implanted in the body, the circuit is configured to (1) receive a first energy transcutaneously from a power source, (2) convert the first energy into a second energy, and (3) transfer the second energy to the implantable device so that the second energy powers the implantable device.

Description

Technical Field

[0001] Cross - Reference to Related Applications This application claims the priority and benefit of U.S. Patent Application No. 16 / 504,623, entitled "Implantable Power Adapter", filed on July 8, 2019, the entire disclosure of which is incorporated herein by reference.

[0002] This application also claims the priority and benefit of U.S. Provisional Patent Application No. 62 / 976,698, entitled "Apparatus and Methods for Providing Electric Energy to a Subject", filed on February 14, 2020, the entire disclosure of which is incorporated herein by reference.

Background Art

[0003] This disclosure generally relates to the field of electrical transmitters or stimulators used alone or in combination with implantable electrical devices, and more particularly to an external electrical transmitter configured to provide transcutaneous electrical energy to an implant disposed in and / or within a part of a subject, and a power adapter configured to be used with such an implant.

[0004] It is known to provide basic transcutaneous electrical nerve stimulation to a subject's body. Generally, an external transmitter or stimulator (or its electrical contacts) can be positioned in contact with the subject's skin and can either directly stimulate a target site or nerve, or supply electrical energy to an implanted device which in turn stimulates a target site or nerve. In some known implementations, an implanted device receives power and / or energy from an external transmitter that can transcutaneously apply and / or supply a low-frequency current, which is received and / or "picked up" by one or more electrodes or conductive parts of the implanted device. Thus, the energy transfer may be similar to transcutaneous energy transfer used in some known devices for directly delivering transcutaneous electrical nerve stimulation.

[0005] However, providing low-frequency current to a target site in a subject and / or an implanted device may cause pain, muscle contraction and / or activation, discomfort, and / or other undesirable sensations in or within a non-target site in the subject. While the sensation (e.g., bodily) to transcutaneous electrical stimulation decreases as the frequency of the stimulation increases, which may reduce undesirable sensations, if the device transmits electrical stimulation with undesirable characteristics (e.g., relatively high frequencies), it may reduce the effectiveness of the implanted device. In addition to sensation, providing transcutaneous electrical stimulation to a target site in a subject (e.g., directly or via an implanted device) using an external transmitter or stimulator may cause charge buildup in the skin and / or result in undesirable heating of the external transmitter or stimulator, for example, related to switching between the positive and negative phases of the stimulation.

[0006] Therefore, there is a need for an external transmitter or stimulator that can deliver transcutaneous energy to the target site of the subject and / or an implanted device implanted in the subject, while limiting undesirable interactions with other parts of the body or non-target areas. Furthermore, there is a need for an implanted device and / or a power adapter to be used with the implanted device that receives transcutaneous energy having a desired set of properties in order not to cause pain, muscle contraction and / or activation, discomfort, and other undesirable sensations in the subject's body (e.g., non-target site or tissue). [Overview of the Initiative]

[0007] In some embodiments, the device includes a housing and a circuit at least partially disposed within the housing. The housing may be configured to be coupled to an implantable conductor for placement in the body. The circuit may be configured to be electrically connected to a pickup electrode of the implantable conductor when the housing is coupled to the implantable conductor. When the housing is coupled to the implantable conductor and implanted in the body, the circuit (1) receives a first energy transcutaneously from a power source, (2) converts the first energy to a second energy, and (3) transmits the second energy to the pickup electrode so that the implantable conductor can apply the second energy at a second frequency to a site in the body via a stimulating electrode. [Brief explanation of the drawing]

[0008] Unless otherwise specified, the drawings are not necessarily to scale. The drawings are merely schematic and are not necessarily intended to depict specific parameters of the invention. The drawings are intended to depict only typical embodiments of the disclosed systems, apparatus, and methods.

[0009] [Figure 1A] This is a schematic block diagram showing a power adapter coupled to an implant according to one embodiment. [Figure 1B]This is a schematic block diagram showing an implant without a power adapter, according to one embodiment. [Figure 2] This is a schematic block diagram showing a power adapter according to one embodiment. [Figure 3] This is a schematic block diagram showing an example of using a device combined with a transmitter according to one embodiment. [Figure 4] This is a flowchart showing a method of using a power adapter according to one embodiment. [Figure 5A-5B] This is a schematic diagram illustrating the effect of using a power adapter in combination with a transmitter according to one embodiment. [Figures 5C-5E] This waveform shows the potential waveform used for a power adapter according to one embodiment. [Figure 5F] This is a graph showing the relationship between charge and frequency when individually applied, according to one embodiment. [Figures 6A-6F] Various diagrams of a power adapter and / or implant according to one embodiment are shown. [Figures 7A-7B] A side view and a partial cross-sectional perspective view of the power adapter and implant, respectively, according to one embodiment, are shown. [Figures 8A-8C] This is a schematic diagram showing the circuitry of a power adapter according to various embodiments. [Figure 9A-9B] This is a schematic diagram showing the circuitry of a power adapter according to various embodiments. [Figure 10A-10B] This is a schematic diagram showing the circuitry of a power adapter according to various embodiments. [Figure 11A] An unrectified waveform (e.g., an AC waveform) according to one embodiment is shown. [Figure 11B] A unidirectional rectified waveform according to one embodiment is shown. [Figure 11C] A bidirectional rectified waveform according to one embodiment is shown. [Figures 12A-12D] This is a schematic diagram showing at least some of the power adapters according to various embodiments. [Figure 13] A transmitter and a power adapter coupled to an implant, according to one embodiment, are shown. [Figure 14A] FIG. 1 is a schematic diagram showing a kit including an implantable device and related instruments according to one embodiment. [Figure 14B] FIG. 2 is a schematic diagram showing a kit including an instrument for coupling a power adapter to an implant according to one embodiment. [Figures 15A-15B] FIG. 3 is a schematic diagram showing at least a part of an external pulse transmitter electrically connected to a load according to one embodiment. [Figures 16A-16D] FIG. 4 is a graph showing various relationships between a compliance voltage and a load voltage according to one embodiment. [Figures 17A-17D] FIG. 5 is a schematic diagram showing a part of the circuit included in the external pulse transmitter of FIGS. 15A and 15B in a first configuration, a second configuration, a third configuration, and a fourth configuration, respectively. [Figure 17E] FIG. 6 is a graph showing the current and voltage across a load when a part of the circuit of FIGS. 17A - 17D transitions between a first configuration, a second configuration, a third configuration, and a fourth configuration. [Figure 18] FIG. 7 shows a waveform generated by an external pulse transmitter according to one embodiment. [Figures 19A-19B] FIG. 8 is an oscilloscope graph showing a first waveform and a second waveform each generated by an external pulse transmitter according to one embodiment. [Figure 20] FIG. 9 is a schematic diagram showing at least a part of a power adapter according to one embodiment. [Figure 21] FIG. 10 is a schematic diagram showing at least a part of a power adapter according to one embodiment.

DETAILED DESCRIPTION OF THE INVENTION

[0010] Embodiments and / or methods described herein relate to an external electrical transmitter or stimulator configured to provide transcutaneous electrical energy to a target site of a subject and / or an implantable device implanted in the subject, and a power adapter configured for use with at least several implantable devices. In some embodiments, for example, a method of providing transcutaneous electrical energy to an implant implanted in a subject using an external electrical transmitter includes providing a first electrical pulse while the stimulator is in a first configuration in which a power source (e.g., a voltage source and / or a current source) is electrically connected to a load. The first electrical pulse has a positive voltage. The load may be, for example, a portion of the subject's skin placed between the external electrical transmitter and the implant, and may have a capacitive element (or characteristic) that results in the accumulation of charge at both ends of the load. The stimulator transitions to a second configuration in which the power source is electrically isolated from the load, thereby allowing the load to discharge the charge accumulated at both ends of the load. After a predetermined time, the stimulator transitions to a third configuration in which the power source is electrically connected to the load, different from the first and second configurations. The method includes providing a second electrical pulse while the stimulation circuit is in a third configuration. The second electrical pulse has a negative voltage (or vice versa).

[0011] In some embodiments, the device includes a housing and a circuit disposed at least partially within the housing (e.g., as part of a power adapter). The housing may be configured to be coupled to an implantable conductor for placement in the body. The circuit may be configured to be electrically connected to a pickup electrode of the implantable conductor when the housing is coupled to the implantable conductor. When the housing is coupled to the implantable conductor and implanted in the body, the circuit (1) receives a first energy transcutaneously from a power source (e.g., an external electrical transmitter), (2) converts the first energy to a second energy, and (3) transmits the second energy to a pickup electrode so that the implantable conductor can apply the second energy at a second frequency to a site in the body via a stimulating electrode.

[0012] In some embodiments, the device includes a power adapter having a housing and a circuit at least partially disposed within the housing. The housing may be configured to be coupled to an implantable device for placement in the body. The circuit may be configured to be electrically connected to the implantable device when the housing is coupled to the implantable conductor. When the housing is coupled to the implantable conductor and implanted in the body, the circuit may be configured to (1) receive a first energy having a first set of characteristics transcutaneously from a power source (e.g., an external electrical transmitter), (2) convert the first energy into a second energy having a second set of characteristics different from the first set of characteristics, and (3) transfer the second energy to the implantable device so that the second energy powers the implantable device.

[0013] In some embodiments, the method includes receiving a first energy having a first set of characteristics transcutaneously from an external electrical transmitter. The first energy is converted via a rectifier circuit to a second energy having a second set of characteristics different from the first set of characteristics. The second energy is transferred from the rectifier circuit to the stimulating electrodes of an implanted conductor so that the implanted conductor applies the second energy to a target nerve inside the body via stimulating electrodes.

[0014] Figure 1A is a schematic block diagram showing a power adapter 100 coupled to an implant 104 according to one embodiment. As shown in Figure 1A, the power adapter 100 includes a housing 110, a circuit 120 at least partially disposed within the housing 110, and an electrode 123. The power adapter 100 may be configured to be coupled to or interconnected with the implant 104 in and through the housing 110, as shown in Figure 1A. The power adapter 100 may be configured to operate in conjunction with the implant 104 and when coupled to the implant 104 in a bodily environment such as an environment 101 that can be defined by a boundary such as skin / septum S as shown in Figure 1A, and inside the body.

[0015] Figure 1B is a schematic block diagram showing implant 104 without a power adapter (e.g., power adapter 100 shown in Figure 1A) coupled to it. As shown in Figure 1B, implant 104 includes electrodes 19a and 19b. Power adapter 100 can be configured to operate in an environment 101, for example, by supplying power, so that implant 104 can perform or carry out medical procedures, tasks, operations, or measurements in the body, in combination with implant 104 and a device such as an external electrical transmitter 102, when coupled to implant 104 (e.g., with and / or on electrode 19a as shown in Figure 1A). More specifically, as will be further described herein, electrode 123 can be configured to receive electrical energy from an external electrical transmitter 102, circuit 120 can convert the frequency and / or waveform of the electrical energy, and power adapter 100 can supply the converted electrical energy to electrode 19a.

[0016] For example, the power adapter 100 may be configured to receive energy E1 (hereinafter referred to as "first energy") from an external electrical transmitter 102 via electrodes 123, such as energy, power, or signal (collectively, "energy"), in the form of a first form or quantity having a first characteristic or set of characteristics (e.g., a first frequency, a first waveform, a first burst pattern, and / or similar). Due to the first characteristics, the first energy E1 may not be suitable for powering the implant 104 and / or otherwise supplied to or used by the implant 104. Therefore, in order to provide energy suitable for use by the implant 104 so that the implant 104 can perform medical procedures in the body, the power adapter 100 may be configured to convert the first energy E1 into a second energy E2 such as a second form or amount having a second characteristic or set of characteristics (e.g., a second frequency, a second waveform, a second burst pattern and / or similar) of energy, power, or signal ("Energy") by deformation, modification, derivation, adaptation, and / or other means. As shown in Figure 1A, the power adapter 100 may be configured to convert the first energy E1 into the second energy E2 so that the second energy E2 is suitable for use by the implant 104 by second characteristics, so that the implant 104 can use the second energy E2 to perform medical procedures in the body (e.g., including providing stimulation, activation, or excitation of tissues, nerves, or muscles in the body via the second energy E2, or providing blockage of excitation or activation of tissues, nerves, or muscles). The power adapter 100 may be configured to transfer or input a second energy E2 to the implant 104 to enable the implant 104 (for example, by supplying power to the implant 104 or controlling the implant 104) when performing or executing a medical procedure in the body.More specifically, when the power adapter 100 is coupled to the implant 104, the circuit 120 is electrically coupled to the electrode 19a (for example, via a conductor not shown in Figure 1A), thereby providing the second energy E2 generated by the circuit 120 as input to the electrode 19a.

[0017] The housing 110 can be configured to be coupled to the implant 104 for placement inside the body together with the implant 104. The electrodes 123 of the power adapter 100 can be configured to receive a first energy E1 (e.g., a high-frequency electrical burst, a low-frequency pulse, etc.) percutaneously into the body for conversion and to transfer it to the implant 104 for use as described herein (e.g., used by the implant 104 in the form of a burst or pulse). The skin / septum S may include barriers, septa, skin, etc., in the body of a subject, including, for example, a person, a patient, etc. The body of a subject may include an environment (e.g., an internal environment), such as the environment 101.

[0018] The external electrical transmitter 102 may be, or may include, an external pulse transmitter (EPT), a power supply or power supply device, an energy source or energy supply device, a voltage source or voltage supply device, a (wireless) energy transmission device, a signal transmitter, and / or similar. The external electrical transmitter 102 may be any suitable configuration. Various terms are used herein to refer to the external transmitter and should be understood to be interchangeable unless the context explicitly indicates otherwise. For example, such terms may include “external electrical transmitter,” “external electrical stimulator,” “external pulse transmitter,” “external pulse generator,” “electrical pulse generator,” “electrical transmitter,” “electrical stimulator,” “power supply,” “transcutaneous electrical nerve stimulator (TENS),” and / or similar. For brevity, the term “transmitter” is used herein to refer to such devices in general.

[0019] The transmitter 102 can be configured to transmit energy (e.g., a first energy E1) to the subject's body, which can be received, for example, by a power adapter 100 and used within and / or by the implant 104 (for example, when the power adapter 100 is coupled to the implant 104). For example, the transmitter 102 can be configured to transmit energy to the body for reception or pickup (e.g., a portion of the energy) by the power adapter 100. The energy can then be received by the power adapter 100 and transferred from the power adapter 100 to the implant 104 (e.g., a second energy E2 shown in Figure 1A). In some cases, the energy can be converted into a form suitable for powering and using the implant 104, such as to enable the implant 104 to perform medical procedures in the body (e.g., from a first form of energy to a second form of energy). In other examples, the power adapter 100 can be arranged in a pass-through configuration and / or in a pass-through state, such that the energy received from the transmitter is transferred to the implant without substantially altering the properties of the energy. Therefore, the second energy E2 transferred from the power adapter 100 to the implant 104 may have characteristics similar to or different from those of the first energy E1 received from the transmitter 102.

[0020] The transmitter 102 may be configured to transmit energy transcutaneously to the subject's body in varying levels of current or charge, as well as at current and / or frequency levels, in order to avoid causing harmful sensory or motor activation or stimulation within the body and by the body (e.g., a response in or within an undesirable location on the body near the electrodes of the transmitter 102, referred herein as a “local response”). In some cases, the transmitter 102 may deliver energy transcutaneously via a hydrogel, a damp cloth, and / or other electrodes attached to the skin. In some cases, the transmitter 102 may be configured to transmit energy at a predetermined frequency or frequency range and in a predetermined waveform via a time-varying voltage (or potential), current (or charge), or electromagnetic field output. In some implementations, the output from the transmitter 102 may include, for example, a time-varying flow of charge. A time-varying flow of charge may include, for example, electrical bursts, electrical pulses, and / or similar ("electrical bursts" or "bursts") in the form of a series of high-frequency bursts, such as a sequence of high-frequency bursts, including electrical, electromagnetic, and / or magnetic bursts. In some implementations, the output of transmitter 102 may include a series of low-frequency bursts, each burst containing a single low-frequency pulse. In some implementations, the output of transmitter 102 may include a series of bursts, any suitable combination of one or more low-frequency energy bursts and one or more high-frequency energy bursts. In some cases, one or more low-frequency energy bursts may have one or more properties configured to produce a desired local response within and by the body, such as increased blood flow in a part of the body adjacent to or near transmitter 102, while one or more high-frequency energy bursts may be received, for example, by a power adapter 100.

[0021] In some implementations, a predetermined frequency or frequency range may include, for example, a frequency or frequency range of approximately 10 kilohertz (kHz) to 100 kHz. The predetermined frequency or frequency range may include a frequency or frequency range that allows the energy output from transmitter 102 to be applied to the subject's body, etc., without otherwise causing undesirable responses or stimuli ("responses"), such as undesirable local motor responses in and by the body near the transmitter's electrodes. For example, Figure 5F is a graph showing relative stimulation intensity as a function of stimulation frequency. In some implementations, transmitter 102 may be configured to deliver energy or stimulation at frequencies within a shaded region identified as the "operational window." Furthermore, as the frequency increases, the stimulation intensity also increases before causing undesirable local responses, as will be described in more detail herein.

[0022] In some implementations, transmitter 102 may be configured to transmit energy (e.g., a first energy E1) at a frequency and charge configured to avoid eliciting a sensation or response (e.g., a local response) within or by body tissue. In some implementations, transmitter 102 may be configured to transmit energy (e.g., a first energy E1) at a frequency and charge configured to elicit a desired local response (e.g., increased blood flow or another desired local response). In some implementations, transmitter 102 may be configured to transmit energy (e.g., a first energy E1), where a first portion of the energy is transmitted at a first frequency and / or charge configured to avoid eliciting a local response, and a second portion of the energy is transmitted at a second frequency and / or charge configured to elicit a desired local response. In some implementations, transmitter 102 may be configured to transmit the first portion of the energy and the second portion of the energy in any suitable combination, pattern, interval, sequence and / or similar.

[0023] In some implementations, the given waveform may include, for example, a sine wave, a square wave, a triangular wave, or any other suitable waveform (described in further detail herein with reference to Figures 5C-5E). The given waveform may also include any other suitable type of waveform. The transmitter 102 may be configured to transmit energy by operating parameters, which may include, for example, pulse width, pulse frequency, current magnitude, current density, power magnitude, power density, etc.

[0024] The transmitter 102 may be configured to transmit energy by applying an output to the subject's body at or to a location, area, or place in the body that surrounds, covers, or is adjacent to a location or place in the body where the power adapter 100 or implant 104 is located (e.g., implanted), as shown in Figure 1A. For example, the transmitter 102 may be configured to transmit energy by applying an output to the body transcutaneously, such as by being at least partially located inside the body and along or to a path (e.g., an electrical path, a conductive path) that interconnects the transmitter 102, the power adapter 100, and the implant 104. That is, the path may be partially defined by the body (the transmitter 102 is configured to transmit energy to this body), such as the part of the body between the transmitter 102, the power adapter 100, and the implant 104.

[0025] Implant 104 represents an implantable device, such as an implantable conductor and / or similar ("implant" or "implantable device" or "implantable conductor"). Implant 104 may be configured to be powered by an external device, such as an external transmitter or power supply (e.g., transmitter 102), via a power adapter (e.g., power adapter 100), and / or otherwise to use energy received from them, in order to perform a medical procedure in the body of a subject (e.g., environment 101), as described herein. In some implementations, implant 104 may include an onboard energy source, an energy storage device, and / or a battery, and / or similar. Such a battery may, for example, store energy received transcutaneously and / or be recharged by energy received transcutaneously.

[0026] For example, in some cases, the implant 104 may be an implantable conductor or may include an implantable conductor such as an implantable stimulator or stimulator configured to operate in the body and to be powered by an external device such as a transmitter 102 via a power adapter 100. In these cases, the implantable stimulator or stimulator may be, for example, a nerve stimulator, an artificial pacemaker and / or similar, or include them. In other cases, the implant 104 may be an implantable conductor such as a fluid transport device, or a fluid transporter such as a pump or compressor (e.g., an insulin pump), or a vacuum device, suction device, or decompression device, or include them. In other cases, the implant 104 may be, or include, an implantable conductor such as a sensor, transducer, monitor, and / or recorder, for example, an electrocardiogram (ECG) sensor, a heart rate monitor, a Holter monitor and / or similar. Otherwise, the implant may be, or include, any appropriate type and number of implantable conductors.

[0027] As shown in Figure 1B, the implant 104 includes electrodes 19a and 19b interconnected on a conductor 18. The implant 104 may include inputs and outputs, such as on electrodes 19a and 19b, respectively. For example, the implant 104 may be configured to receive energy at an input (e.g., electrode 19a) and provide energy at an output (e.g., electrode 19b). Energy may be transported between the input (e.g., electrode 19a) and the output (e.g., electrode 19b) via the implanted conductor (e.g., conductor 18) of the implant 104. The implant 104 may be configured to receive energy percutaneously and at electrode 19a from a transmitter such as transmitter 102. Energy may be received, for example, to power the implant 104 and control the implant 104 (e.g., as in performing a medical procedure) and / or for similar purposes.

[0028] In some implementations, the implant 104 may be configured to receive energy from the transmitter 102 via a power adapter 100. For example, in some cases, such as when the power adapter 100 is connected to the implant 104 as shown in Figure 1A, the power adapter 100 may be configured to receive a first energy E1 (having, for example, a first frequency, a first waveform, and / or other characteristics) from the transmitter to convert this first energy E2 (having, for example, a second frequency, a second waveform, and / or other characteristics) into a second energy E2, and to transfer the second energy E2 from the power adapter 100 to the implant 104, such as an input to the implant 104 at electrode 19a, so that the implant 104 receives the second energy E2 (for example, for output at electrode 19b). In some implementations, when the power adapter 100 is not connected to the implant 104 (for example, as shown in Figure 1B), electrode 19a can receive the second energy E2 directly. By connecting the power adapter 100 to the implant 104 and onto the electrode 19a, the implant 104 can be retrofitted and / or adapted to receive the first energy E1 rather than the second energy E2. That is, when the power adapter 100 is connected to the implant 104, as shown in Figure 1A, the power adapter 100 can prevent the electrode 19a from directly receiving energy. The energy output by the electrode 19b can be detected and / or received by the transmitter 102 (e.g., by a skin electrode (not shown in Figure 1A or 1B)) to complete the electrical circuit including the transmitter 102, the housing 110, and the implant 104.

[0029] Electrodes 19a and 19b may each include one or more electrodes, one or more electrical contacts, one or more electrical terminals, etc. Electrode 19a may include an input electrode, and electrode 19b may include an output electrode. For example, electrode 19a may include an input electrode such as a receiving electrode, a pickup electrode, and / or the like (referred to herein as “pickup electrode”). In some embodiments, such as when implant 104 is a stimulating device, electrode 19b may include an output electrode such as a stimulating electrode or a stimulation electrode, a stimulation lead wire, and / or the like (referred to herein as “stimulating electrode” or “stimulation electrode”). In some implementations, electrode 19a may include and / or be formed from titanium (Ti) compounds, titanium nitride (TiN) compounds, platinum-iridium (Pt-Ir) compounds, and / or similar materials. In some embodiments, electrode 19b may include and / or be formed from platinum (Pt) compounds, iridium (Ir) compounds, platinum-iridium (Pt-Ir) compounds, or alloys. Conductor 18 may include any suitable conductor, electrical lead wire, and / or conductive material that can interconnect electrodes 19a and 19b. For example, conductor 18 may include a path such as a conductive path or electrical path configured to interconnect electrodes 19a and 19b on implant 104. Conductor 18 may include and / or be formed from materials such as inert or non-reactive substances, or any other material suitable for use on the subject's body, according to embodiments described herein.

[0030] The housing 110 may be or include any suitable type of housing or casing. For example, the housing 110 may be configured to house or otherwise include one or more circuits (e.g., circuit 120) and may have a housing such as a sealed casing or can having a feedthrough, internal contacts (e.g., conductors), one or more mating functions (e.g., grip mechanism assemblies) configured to be electrically and mechanically coupled to and in contact with a pickup electrode (e.g., electrode 19a of implant 104), and a sleeve (e.g., mechanical and / or electrical protection). The housing 110 may be configured to house, for example, one or more circuits including circuit 120 at least partially. The housing 110 may be configured to be coupled to an implant such as implant 104 for placement together with implant 104 (and circuit 120) within the body of a subject. The housing 110 may be configured to mechanically insulate circuit 120 from the body, including the internal environment such as environment 101. For example, the housing 110 may be configured such that the circuit 120 is isolated from the environment, such as the environment 101 inside the subject's body, by implanting the implant 104 in the body, for example, when the housing 110 is coupled to the implant 104 and disposed in the environment 101. The housing 110 may include any suitable housing that can be attached, coupled, connected, interconnected, or otherwise added to an implant such as the implant 104 by mechanical, electrical, or other means, as described herein. The housing 110 may include any suitable type and number of components, including resistors, capacitors, transistors, diodes, inductors, energy sources, energy storage devices, and / or the like. In some embodiments, the housing 110 does not include energy sources, energy storage devices, and / or the like, which may be, for example, batteries or other chemical energy sources.In other embodiments, the housing may include an energy storage device (e.g., a battery, an energy storage capacitor, etc.) that can be used to supply power to the implant 104 and / or be recharged by receiving transcutaneous energy transfer, as described herein. In some implementations, the housing 110 may be, for example, a sealed can configured to at least partially house the circuit 120, or include such a can.

[0031] Circuit 120 may be or include an integrated circuit (IC) and / or similar. Circuit 120 may be configured to be electrically connected to an implantable device such as an implant 104 when the housing 110 is coupled to the implant 104 by an electrode 19a or the like. For example, circuit 120 may be configured to be electrically connected to the implant 104 when the housing 110 is coupled to the implant 104 by, for example, the implant 104's pickup electrode (e.g., electrode 19a), thereby allowing circuit 120 to provide energy (e.g., converted power, regulated signal) to the implant 104. Energy may be provided by circuit 120 and to the implant 104 via an input to the implant 104 at the pickup electrode (e.g., via a conductor or electrical interface that electrical communicates with electrode 19a). Circuit 120 may be configured to receive energy (e.g., for energy conversion and transfer of converted energy to the implant 104) from a transmitter such as transmitter 102, as described herein. Circuit 120 may include various components as described herein with reference to Figure 2.

[0032] For example, during use, the power adapter 100 may be configured to be implanted in the subject's body in a state of being coupled to or interconnected with the implant 104. For example, the power adapter 100 may be configured to be coupled to the implant 104 by attaching the housing 110 to the pickup electrode (electrode 19a) of the implant 104. In some cases, the power adapter 100 may be configured to be retrofitted to an existing implant in the subject's body, such as the implant 104. For example, the power adapter 100 may be configured to be fitted to an existing implant by crimping or the like. Once the power adapter 100 is implanted in the body together with the implant 104, operating parameters, including, for example, stimulation parameters, can be set as described herein (for example, on the transmitter 102). Thus, the power adapter 100 may be configured for use by a subject in the body (with the power adapter 100 implanted together with the implant 104) together with the transmitter 102 and the implant 104.

[0033] In other implementations, the power adapter 100 may be integrated with the implant 104. For example, in some implementations, the power adapter 100 may be provided as part of the implant 104 or embedded in the implant 104, for example, in a pre-coupled or pre-interconnected state with the implant (e.g., via interconnection to the electrode 19a). Similarly, in such implementations, the function of the power adapter 100 (as described herein) may be part of the implant and / or integrated into the implant. In such implementations, a separate power adapter 100 for receiving transcutaneous energy transfer is not required and / or used.

[0034] In some implementations, where the implant 104 is a stimulating device and the electrode 19B includes an output electrode such as a stimulating electrode, the power adapter 100 may be configured to convert the first energy E1 (e.g., from the transmitter 102) into a second energy E2 to input a second energy E2 to the implant 104 so that the implant 104 can perform a medical procedure. In such implementations, the medical procedure may include, for example, a procedure in which the implant 104 is configured to provide stimulation, activation, excitation, etc. ("stimulation") to the tissues, nerves, or muscles of the subject's body. In such implementations, the implant 104 may be configured to perform a medical procedure in the body via the output of the second energy E2 at the electrode 19b. In such implementations, the second energy E2 may include, for example, a series of low-frequency pulses or low-frequency bursts and / or a series of high-frequency pulses or high-frequency bursts. Specifically, the second energy E2 may include, for example, interlaced delivery, stimulation, bursts, and / or pulses of low-frequency and high-frequency energy. Medical procedures can be performed, for example, to activate skin receptors, muscles, and / or nerves in the body.

[0035] Figure 2 is a schematic block diagram showing a power adapter 200 according to one embodiment. As shown, the power adapter 200 includes a housing 210 and a circuit 220 at least partially disposed within the housing 210. The power adapter 200 may be configured to be disposed in the body for operation in the body environment (e.g., environment 101) and inside the body, and to be coupled to or interconnected with an implant (e.g., implant 104). The circuit 220 may be configured to be electrically interconnected (e.g., via electrode 223b) with the stimulating electrode of the implant when the housing 210 is coupled to the implant (e.g., implant 104) and implanted in the body. The power adapter 200 may be structurally and / or functionally similar to other power adapters (e.g., power adapter 100) shown and described herein.

[0036] Circuit 220 includes a rectifier circuit 221 and an electrode 223a (e.g., a pickup electrode). The rectifier circuit 221 may be, or include, a half-wave rectifier circuit or a full-wave rectifier circuit, for example. For example, in some cases, the rectifier circuit 221 may include a resistor 222, a diode 224, and a capacitor 226. In other implementations, which are not shown or described with respect to Figure 2 (e.g., as shown and described with respect to 9A, 9B, and / or 10), the circuit may include additional capacitors and / or inductors to provide protection at frequencies used for magnetic resonance (MR) devices, such as magnetic resonance imaging (MRI) devices. The rectifier circuit 221 may be configured to selectively convert received energy (e.g., received from transmitter 102 via electrode 223a). For example, the rectifier circuit 221 may be configured to convert a first energy by rectifying the first energy to provide a second energy (e.g., via electrode 223b). In some cases, the second energy may be substantially positive DC or substantially negative DC. For example, the rectifier circuit 221 may be configured to transform and filter the received signal in a manner similar to that of an amplitude modulation (AM) receiver.

[0037] Capacitor 226 may be, or include, a direct current (DC) blocking capacitor. Capacitor 226 may be configured to maintain the level of charge balance of the rectifier circuit 221. For example, capacitor 226 may be configured to provide charge balance of the energy transmitted from the rectifier circuit 221. In some implementations, such as when the implant 104 is a stimulating device, the type or characteristics of capacitor 226 may be selected based on characteristics (e.g., operating conditions), such as the tissue electrode capacitance of the implant 104's pickup electrode (e.g., electrode 19a) and stimulating electrode (e.g., electrode 19b) relative to the internal tissues of the subject's body (e.g., within the environment 101). In such implementations, capacitor 226 may be effectively connected in series with the pickup electrode and the stimulating electrode. In a series connection of capacitors, the capacitor with the smallest amount of capacitance (i.e., the capacitor with the smallest capacitance measurement) determines the total capacitance of the capacitors (e.g., substantially equal to the capacitance of the capacitor with the smallest relative capacitance). Therefore, the capacitor 226 may be selected or configured to have a specific value or measurement of capacitance so as not to reduce the overall capacitance of the path (for example, the path interconnecting the capacitor 226, the pickup electrode, and the stimulation electrode) based on the effective capacitance of the tissue electrode capacitances of the pickup electrode and the stimulation electrode.

[0038] For example, if the tissue electrode capacitance is approximately 4 microfarads (μF), the capacitor 226 can be selected or configured to have a capacitance value or measurement of approximately 4 μF or greater. In this example, the value of the capacitor 226 may be selected or configured based on the tissue electrode capacitance of the tissue inside the body, as well as the pickup electrode (e.g., electrode 19a) and stimulating electrode (e.g., electrode 19b) of the implant 104. In some implementations, the capacitor 226 can be selected or configured to have a capacitance value or measurement. This capacitance value or measurement does not decrease but supports and / or maintains the overall capacitance of the conductive path of the implant 104 (e.g., the path interconnecting the pickup electrode with the stimulating electrode).

[0039] Diode 224 may be, or include, a rectifier diode. In some implementations, diode 224 may be, or include, a Schottky diode, a silicon diode, and / or similar rectifier diodes. In some implementations, the type or characteristics of diode 224 may be selected based on characteristics such as, for example, the magnitude of the voltage drop across diode 224 (e.g., forward). For example, the type of diode 224 may be selected to reduce the magnitude of the voltage drop across diode 224. In this example, the type of diode 224 may be, or include, a Schottky diode (e.g., instead of a silicon diode) in order to reduce the magnitude of the voltage drop across diode 224 (e.g., compared to that of a silicon diode), and thus achieve a higher pickup ratio (e.g., compared to that of a silicon diode). In some implementations, the type of diode 224 may be selected based on, or to facilitate, any suitable characteristics such as the amount of leakage current, the amount of back leakage current, the discharge rate (of, for example, capacitor 226) between applied electrical bursts, and / or similar. For the purposes of this disclosure, the “pickup” ratio refers to the amount of energy received by the implant relative to the amount of energy transmitted by the external transmitter. For example, a pickup ratio of 0.5 indicates that the amount of energy received by the implant is approximately half the amount of energy transmitted by the external pulse transmitter.

[0040] Resistor 222 provides a discharge path (from rectifier circuit 221) to capacitor 226. In some implementations, the type or characteristics of resistor 222 may be selected based on the characteristics of rectifier circuit 221, including, for example, the discharge path characteristics of rectifier circuit 221. For example, resistor 222 may be selected to have a measured resistance or value greater than the effective resistance of diode 224 in order to prevent bypassing of diode 224 (e.g., by current) in use (e.g., in power adapter 200 with implants such as implant 104). In some implementations, the type or characteristics of resistor 222 may be selected based on, for example, the application frequency or frequency range of energy (e.g., electrical signals, electrical bursts) from transmitter 102, the burst repetition frequency of the energy application frequency or frequency range, the burst duration of the energy application frequency or frequency range, and / or similar.

[0041] Figure 3 is a schematic block diagram showing an example of the use of a power adapter 300 in combination with a transmitter 302 according to one embodiment. As shown, the power adapter 300 includes a housing 310 (labeled “add-on receiver”) and circuitry (not shown) at least partially disposed within the housing 310. The power adapter 300 may be structurally and / or functionally similar to other power adapters described herein (e.g., 100, 200).

[0042] Transmitter 302 may be configured to transmit, or otherwise provide, energy to the power adapter 300 via path 303 (to supply power and / or energy to the implant 304). In some implementations, the electrical pulse generators (e.g., transmitters 102, 302) may include, for example, a power supply. Path 303, through which energy is received, transferred, and applied, may include, for example, parts of the subject's body between transmitter 302 (e.g., the transmitter's gel electrodes and / or cloth electrodes (not shown)) and the power adapter 300 (when deployed in the body with the implant 104).

[0043] For example, the power adapter 300, housing 310, and circuitry can be structurally and / or functionally similar to the power adapter 100, housing 110, and circuitry 120, respectively, as described herein. The power adapter 300 can be configured to be coupled to an implant, such as implant 304, via housing 310, and to be deployed in the body with the implant 304, such as under the skin and within the body environment 301. The power adapter 300 can be configured to be attached to or coupled to implant 304 such that (for example, when implant 304 and power adapter 300 are implanted in the body) the pickup electrode of implant 304 is electrically isolated from the environment 301. The power adapter 300 can be configured to receive energy from transmitter 302 for conversion and transfer to implant 304 and apply it to a target site or object in the body via the stimulating electrode of implant 304.

[0044] Transmitter 302 may be structurally and / or functionally similar to transmitter 102 as described herein. For example, transmitter 302 may include an external transmitter (indicated as "transmitter") and a patch (not shown) containing one or more gel electrodes (indicated as "gel electrodes"). In some implementations, the external transmitter may include, for example, a high-frequency transmitter. Although shown as gel electrodes in Figure 3, in some implementations, the patch may include, for example, gel patches, hydrogel patches, cloth patches, and / or similar electrodes. In some implementations, the patch may include disposable patches. Transmitter 302 may be configured to transmit energy transcutaneously (for reception by, for example, a circuit disposed in housing 310) to the subject's body, such as by applying the output of transmitter 302 to the body through the patch.

[0045] Implant 304 may be structurally and / or functionally similar to implant 104 as described herein. For example, implant 304 may include a conductor or lead wire (indicated as “lead”), a stimulating electrode (indicated as “stimulating electrode”), and a pickup electrode (not shown), to which a power adapter 300 may be attached or coupled, as described herein with reference to Figure 1 and shown in Figure 3. The lead wire of implant 304 may include, for example, a conductive path for interconnecting the stimulating electrode and the pickup electrode. The lead wire of implant 304 may be, or include, a conductor such as a coiled wire (Pt-Ir) conductor disposed within a silicone sheath or tube. For example, the lead wire of implant 304 may be insulated (e.g., from tissue in the environment 301) by a silicone tube and by a silicone backfill disposed and configured to close the tube at both ends. The implant 304 can be configured to receive energy (e.g., electrical signals, electromagnetic signals, magnetic signals) from the transmitter of the transmitter 302 percutaneously and via a power adapter 300 (e.g., disposed on the pickup electrode of the implant 304). For example, the implant 304 can be configured to receive energy and apply stimulation (e.g., an electrical burst, an electrical pulse) to a target site or object in the subject's body via a stimulating electrode. In some implementations, the implant 304 may include, for example, three or more stimulating electrodes (e.g., electrode 19b, etc.).

[0046] During use, the power adapter 300 can be configured to receive transcutaneous high-frequency bursts of energy (e.g., electrical energy) transcutaneously from the transmitter 302. The energy may be received at a first frequency of, for example, about 10 kHz to 100 kHz or higher, or otherwise may include it. In other cases, the first frequency may be 100 kHz to 3 megahertz (MHz). In yet other cases, the first frequency may be 10 MHz or lower and / or any other suitable frequency. The received energy can be converted by the power adapter 300 into a form suitable for use in providing stimulation, activation, or excitation (e.g., to tissues, nerves, muscles) within the subject's body. For example, the received energy may be converted by the power adapter 300 into a second energy (e.g., a stimulating current) having a second frequency lower than the first frequency, for example, about 1 kHz. In other implementations, the second frequency may be 1 kHz to 10 kHz. In yet another implementation, the second frequency may be 500 Hz to 30 kHz. Energy conversion may include, for example, rectification and charge balancing via a power adapter 300. The converted energy can be transferred from the power adapter 300 to the stimulating electrode of the implant 304 and applied by the stimulating electrode to a target in the body (e.g., a nerve).

[0047] For example, the implant 304 may be or include a lead wire, such as a flexible conductor, having a length of approximately 15 cm and a diameter of approximately 1.2 mm. The stimulating electrode of the implant 304 can be positioned in or near a target object in the body, such as a nerve. The pickup electrode of the implant 304 can be covered by attaching a power adapter 300 to the end of the implant 304 where the pickup electrode is located. The target object may be any suitable point, site, or part of interest, such as a nerve (e.g., a peroneal nerve, peripheral nerve, etc.). In some implementations, the implant 304 may include one or more stimulating electrodes, for example, having dimensions of approximately 1 mm in length. In some implementations in which the implant 304 includes three or more stimulating electrodes, the stimulating electrodes may be positioned at intervals of approximately 1 mm along the lead wire of the implant 304. In some implementations, one or more stimulating electrodes of the implant 304 can be manufactured or assembled by winding a conductor (e.g., the lead wires of the implant 304) around the outside of a silicone tube (e.g., a silicone sheath) and the ends of the lead wires, as shown in Figure 3. The conductive surface of the stimulating electrode (e.g., the stimulating end of the implant 304) can be configured to contact the surrounding tissue in the environment 301 when implanted in the body (e.g., together with the power adapter 300). In some implementations, the implant 304 may include an anchor (e.g., a hook, tine) having, for example, a diameter of about 1.5 mm. The anchor can be configured to fix the implant 304 in place, or otherwise to prevent the lead wires from moving in the environment 301 when the implant 304 is implanted and positioned in the subject's body together with the power adapter 300. For example, the anchor may include a silicone anchor having four prongs or hooks and can be disposed at the stimulating end of the implant 304.

[0048] In some implementations, the transmitter 302 can optionally be configured to be used via software (e.g., residing on a device external to the transmitter) or to be programmed for use via software. For example, the software may reside on any suitable type of computing device (e.g., a mobile device, tablet computer, server) or otherwise be hosted on any suitable type of computing device. For example, the software may be run on a computing device to generate signals (e.g., including commands) and send them to the transmitter 302 for execution (e.g., on the transmitter 302), and the transmitter 302 may be configured to receive one or more signals from the computing device, for example, signals corresponding to commands configured to be executed on the transmitter 302. The signals may include, for example, machine-readable or processor-readable code and / or instructions configured to be stored on and / or executed on the transmitter 302. In some implementations, the code may include instructions configured to be executed on the transmitter 302, such as setting or specifying one or more operating parameters, stimulus parameters, and / or similar on and / or in the transmitter 302. For example, one or more operating parameters of the transmitter 302 may include a specific stimulation routine applied (e.g., via implant 304), a specific stimulation intensity applied (e.g., transcutaneously to the body), and the applicable frequency or frequency range of the applied energy. The software can be configured to be used by users or operators such as clinicians, patients, and / or similar entities.

[0049] In some implementations, software that can be optionally configured or programmed to use the transmitter 302 may be stored in a computing device, such as a tablet computing device. In some cases, the computing device may be configured to communicate with the transmitter 302 via a communication link, such as a Bluetooth Low Energy (BLE) communication link. In some cases, the software may be configured to allow access to data, such as patient demographic information, session data, and patient stimulation profiles. In some cases, the software may be resident and / or otherwise hosted for use via a smartphone platform (e.g., iOS, Android). In some cases, the software may include, for example, a mobile app. In some implementations, the software may be configured to allow tracking, system error or failure notification, and / or similar functions. In some implementations, the software may be configured to control various functions of the transmitter 302, including, for example, the selection of a stimulation program or routine (e.g., as predefined by a user such as a clinician), activation and deactivation of stimulation (e.g., turning the transmitter 302 on and off), and increasing or decreasing the (applied) stimulation intensity. In some implementations, the software may be configured to provide displays (e.g., visual, auditory) of operational status, such as the selected stimulation program, the selected stimulation intensity level, and the quality of electrode connections, among other types of error or operational status displays (e.g., via transducers such as displays and speakers).

[0050] Figure 4 is a flowchart showing a method 401 using a power adapter according to one embodiment. The power adapter can be structurally and / or functionally similar to any of the power adapters described herein (e.g., 100, 200, and / or 300).

[0051] In 42, Method 401 includes receiving a first energy percutaneously and from an electrical pulse generator (e.g., transmitters 102 and / or 302) at a first frequency and / or a first waveform (e.g., via power adapters 100, 200, and / or 300). In 44, Method 401 includes converting the first energy to a second energy via a rectifier circuit (e.g., rectifier circuit 221). In some implementations, the second energy may have a second frequency different from the first frequency and / or a second waveform different from the first waveform. In 46, Method 401 includes transferring the second energy from the rectifier circuit to a stimulating electrode (e.g., electrode 19b shown in Figures 1A and 1B) of an implantable conductor (e.g., implant 104 and / or 304) so ​​that the second energy is applied to a target in the body (e.g., a subject) via a stimulating electrode at a second frequency. Internal targets may include, for example, nerves, internal body parts, and / or similar entities.

[0052] In some implementations, the second energy may be transferred from a rectifier circuit (e.g., rectifier circuit 221) to a pickup electrode (e.g., electrode 19a) of an implantable conductor (e.g., implant 104), and subsequently transferred and routed through the implantable conductor (e.g., conductor 18 of implant 104) to a stimulating electrode (e.g., electrode 19b), where it can be applied to a target nerve in the body. In some implementations, the second energy may be transferred from the rectifier circuit to the implantable conductor, and in particular to the stimulating electrode, enabling the application of the second energy to a target inside the body. In some implementations, the first energy may include, for example, alternating current. In some implementations, the second energy may include, for example, pulsating direct current. In some implementations, the first frequency may include, for example, a frequency of about 30 kHz to 100 kHz. When the device is not coupled to an implanted conductor (e.g., via housings 110, 210, and / or 310), the pickup electrodes of the implanted conductor can be configured to receive a third energy transcutaneously (e.g., from an electrical pulse generator) at substantially a second frequency and / or a second waveform.

[0053] Figures 5A and 5B are schematic diagrams illustrating the effect of using the power adapter 500 in combination with a transmitter (e.g., transmitter 502b) and implant 504 according to one embodiment. The power adapter 500 may be structurally and / or functionally similar to other power adapters described herein (e.g., power adapters 100, 200, and / or 300). The implant 504 may be structurally and / or functionally similar to implants or embedded conductors described herein (e.g., implants 104 and / or 304).

[0054] Referring to Figure 5A, the transmitter 502a (labeled “External Transmitter (Low Frequency)”) may be configured to apply transcutaneous stimulation (e.g., a first energy) into the subject’s body via an electrode patch 57a (e.g., disposed on the skin surface). The transmitter 502a may be, or include, an e.g., a low-frequency external transmitter and / or similar, configured to operate in conjunction with the implant 504 (e.g., without the power adapter 500). The transmitter 502a may be structurally and / or functionally similar to any of the transmitters described herein (e.g., transmitter 102).

[0055] The transmitter 502a may be configured to transmit energy by applying an output to the body (e.g., on the skin surface of the body) transcutaneously (e.g., via electrode patch 57a), such as being at least partially located inside the body and along or to a path (e.g., an electrical path, a conductive path) interconnecting the transmitter 502a and the implant 504. The path may include, for example, electrode patch 57a, a first part of the body 50a, the implant 504 (e.g., via electrodes 59a and 59b), a second part of the body 50b, electrode patch 57b, and the transmitter 502a. A portion of the applied transcutaneous stimulation (e.g., 10% to 20%) may be picked up or received by the implant 504 at electrode 59a and transferred and / or routed along the implant 104 to electrode 59b (e.g., via conductor 18). Electrode 59a may include, for example, a pickup electrode. Electrode 59b may include, for example, a stimulating electrode.

[0056] In some implementations, the implant 504 may include insulators such as silicone backfill and tubing arranged around the lead body of the implant 504 (e.g., the conductor 18 shown in Figures 1A and 1B) so that energy (e.g., an electrical pulse received via electrode 59a) can be efficiently transmitted to the conductive surface of the stimulating electrode contact (e.g., electrode 59b), where a current can then be applied to a target, such as a target peripheral nerve or another suitable site in the body, as described herein. In some implementations, the lead body of the implant 504 (e.g., the conductor 18 shown in Figures 1A and 1B) may include, for example, a Pt-Ir lead wire.

[0057] In some implementations, the energy frequencies 51a at the pickup electrode and 51b at the stimulating electrode may be similar, substantially equal, or identical. In some implementations, the waveforms may also be similar, substantially equal, or identical, except for the signal amplitude. The transmitter 502a may be configured to apply and deliver energy transcutaneously at a low application frequency or frequency range (e.g., less than 10 kHz) for stimulation at and by the electrode 59b at a low application frequency.

[0058] Referring to Figure 5B, the transmitter 502b (labeled “External Transmitter (Radio Frequency Burst)”) may be configured to transmit or transmit a first energy (e.g., energy including a radio frequency burst) into the body of the subject via an electrode patch 57a (e.g., disposed on the skin surface) as described herein. Transmitter 502b may be, for example, a radio frequency external transmitter and / or similar, or include them, configured to operate in conjunction with the implant 504 via a power adapter 500. Transmitter 502b may be structurally and / or functionally similar to the transmitters described herein (e.g., transmitters 102 and / or 302).

[0059] The transmitter 502b may be configured to transmit a first energy at a frequency of approximately 10 kHz to 100 kHz in order to prevent the inhabitant from experiencing sensations within the subject's body. The transmitter 502b may also be configured to transmit a first energy at a frequency that prevents the nerves surrounding the site where transcutaneous stimulation is applied to the body from being directly activated. The transmitter 502b may be configured to transmit energy transcutaneously (e.g., via electrode patch 57a) by being at least partially located within the body and applied to the body (e.g., on the skin surface of the body) along or against a path (e.g., an electrical path, a conductive path) that interconnects the transmitter 502b, the power adapter 500, and the implant 504. The pathway may include, for example, an electrode patch 57a, a first part of the body 50a, a power adapter 500 (e.g., via electrodes 123 in Figure 1 and / or 223a in Figure 2, respectively), an implant 504 (e.g., via electrodes 59a and 59b), a second part of the body 50b, an electrode patch 57b, and a transmitter 502b.

[0060] A portion of the applied transcutaneous stimulation, for example about 10% to 20%, from the transmitter 502b, can be picked up by the pickup electrode of the power adapter 500 in the form of first energy 52a (for example, having a first frequency and / or a first waveform), and converted into second energy 52b (for example, having a second frequency and / or a second waveform) by the rectifier circuit (e.g., rectifier circuit 221) of the circuit (e.g., circuits 120 and / or 220) of the power adapter 500 (e.g., at least partially located within the housing 510 of the power adapter 500). The second energy 52b may include, for example, low-frequency bursts, high-frequency bursts, and / or similar. The second energy 52b can be routed to electrode 59b via one or more electrodes of electrode 59b for application to a target such as a target peripheral nerve, or to any other suitable location on the body for purposes such as pain treatment. In some implementations, the second energy 52b may include, for example, a sine wave, a rectangular wave, a triangular wave, etc. For example, the power adapter 500 (via a circuit arranged in the housing 510) may be configured to operate like an AM radio receiver by demodulating energy containing signals such as high-frequency bursts (e.g., carrier waves) and by detecting low-frequency (e.g., modulated) signals. Thus, the power adapter 500 may be configured to be retrofitted and / or adapted for use in or with an implant (e.g., implant 504), which is normally configured to receive energy at a first frequency (e.g., low frequency) and / or have a first waveform, thereby enabling the implant to receive energy at a second frequency (e.g., low-frequency pulses, high-frequency bursts) and / or have a second waveform.

[0061] In some implementations, as shown in Figure 5B, the rectifier circuit of the circuit at least partially disposed in the housing 510 of the power adapter 500 may include a rectifier diode (e.g., diode 224) oriented to the cathode so as to provide cathode stimulation via the stimulating electrode (of implant 504). In some implementations, the rectifier circuit of the circuit at least partially disposed in the housing 510 of the power adapter 500 may include a rectifier diode (e.g., diode 224) oriented to the cathode so as to provide cathode stimulation via the stimulating electrode (of implant 504). The activation threshold for nerves (e.g., sensory, motor) in the cathode orientation (e.g., negative pulse delivered to the stimulating electrode) is lower than the activation threshold for the rectifier diode (e.g., diode 224) in the anode orientation because it causes more effective depolarization of the cell membrane and subsequent nerve activation. In some implementations, the housing 510 may be or include a sealed housing made of titanium. The first energy (e.g., current at a first frequency) applied by transmitter 502b can be returned to the transmitter transcutaneously and from the stimulating electrode in the form of a second energy (e.g., current at a second frequency) to complete an electrical circuit. For example, a rectifier diode (e.g., diode 224) can be oriented to connect to the stimulating electrode of implant 504. In other embodiments, the rectifier diode (e.g., diode 224) may be oriented anodically so that anodic stimulation is provided via the stimulating electrode (of implant 504).

[0062] In some implementations, the transmitter 502b may provide a first energy having a first waveform, which may include, for example, multiple sets of bursts or pulses, and the first energy may then be rectified by the power adapter 500 into a second energy having a second waveform. Figures 5C-5E show exemplary waveforms 52c, 52d, and 52e, respectively, illustrating potential waveforms used for the power adapter in different implementations. As shown in Figure 5C, the transmitter 502b may provide energy having a waveform 52c, which may be provided as well as the first energy 52a. The characteristics of waveform 52c may include, for example, a first frequency and / or a square waveform. More specifically, waveform 52c has a square or rectangular waveform with a first frequency and is represented by two sets of bursts or pulses alternating in phase (e.g., positive and negative phases). The first energy 52a can be provided to the power adapter 500 using waveform 52c. Next, the power adapter 500 may convert the first energy 52a into a second energy 52b having a second frequency and / or a second waveform.

[0063] Figures 5D and 5E show waveforms 52d and 52e, which are examples of waveforms for a second energy 52b (for example, input to electrode 59a by power adapter 500 and applied by implant 504 via output at electrode 59b), respectively. Specifically, waveform 52d in Figure 5D is a rectified version (e.g., using envelope detection rectification) of waveform 52c in Figure 5C. Waveform 52d is shown as two sets of bursts or pulses having an asymmetric waveform and single-phase (e.g., one of positive or negative phase). More specifically, the square wave burst of waveform 52c is rectified to produce square waveform 52d, which is effectively a square waveform with a lower frequency than the square wave burst of waveform 52c. As another example, waveform 52e in Figure 5E can be produced using a simple rectification of waveform 52c. A given waveform 52e is represented by two sets of bursts or pulses having a square waveform and single phase (e.g., one of positive or negative phase). For example, waveform 52e may include the positive component of waveform 52c, with the negative portion of waveform 52c removed. In some cases, the frequency of waveform 52e (e.g., of the second energy) may be similar to, substantially equal to, or identical to the frequency of waveform 52c (e.g., of the first energy). While waveforms 52c, 52d, and 52e are each represented by two sets of bursts or pulses, it should be understood that waveforms 52c, 52d, and 52e may include any number of bursts or pulses. Furthermore, while bursts or pulses are shown in particular in Figures 5C-5E, it should be understood that they are provided merely as examples and not as an extension.

[0064] Figure 5F is a graph showing the relationship between charge per burst and frequency when applied transcutaneously to an individual, according to one embodiment. As shown in Figure 5F, a predetermined frequency or frequency range (for example, when the first energy is output from transmitter 502b) may include, for example, a frequency or frequency range of approximately 10 kHz to 100 kHz. Otherwise, the predetermined frequency or frequency range may include a frequency or frequency range of energy and / or charge that the energy output from transmitter 102 can be applied to the subject's body, etc., without causing any local motor response or sensory stimulation ("response") by the body and by the body. For example, the predetermined frequency or frequency range, and the amount of energy and / or charge, may be selected or determined to achieve a target response (indicated as "target response") as a function of frequency with respect to the magnitude of the applied energy. The magnitude of the applied energy may be specified, for example, with respect to the magnitude of the current or with respect to the delivered charge measured in coulombs.

[0065] As shown in Figure 5F, as the frequency increases, the amount of energy and / or charge that can be applied to an individual without an undesirable local response may also increase. Line A shown in Figure 5F is an example of a frequency at which transmitter 502a in Figure 5A can transmit a first energy 51a to an implant that does not include a power adapter, such as power adapter 500. Line B shown in Figure 5F is an example of a frequency at which transmitter 502b in Figure 5B can transmit a first energy 52a to an implant that is coupled to or includes power adapter 500 (e.g., implant 504). In some cases, at higher frequencies, a larger margin (e.g., "operating window") may exist between the energy sufficient to elicit a response in target tissue near the implant and the energy sufficient to elicit an undesirable local response beneath the skin electrode.

[0066] Transmitter 502a is described above as transmitting a first energy 51a having a relatively low frequency, and transmitter 502b is described above as transmitting a first energy 52a having a relatively high frequency; however, in some embodiments, the transmitters may be configured to include any suitable combination of energy 51a (e.g., a relatively low frequency) and energy 52a (e.g., a relatively high frequency). In such implementations, the transmitters can transmit the energy in any suitable pattern, combination, sequence, interlaced or uninterlaced series, time-dependent bursts or pulses, random bursts or pulses, and / or similar. In some cases, the relatively low-frequency energy may be configured to produce and / or otherwise induce a desired local response, such as an increase in blood flow or other desired response in a part of the body adjacent to and / or near the transmitter, while the relatively high-frequency energy may be received by a power adapter and transmitted to the implant, as described above.

[0067] Figures 6A–6F show various diagrams of a power adapter 600 and / or implant 604 according to one embodiment. The power adapter 600 may be structurally and / or functionally similar to other power adapters shown and described herein (e.g., 100, 200, 300, and / or 500). The implant 604 may be structurally and / or functionally similar to other implants shown and described herein (e.g., 104, 304, and / or 504). For example, the implant 604 may include a pickup electrode 69a and a stimulating electrode 69b, as shown in Figure 6A.

[0068] In some implementations, the housing 610 may be configured to be coupled to the implant 604, tightly coupled to the implant 604, and / or coupled on the implant 604, for example, to couple to the implant 604, tightly coupled to the implant 604, and / or coupled on the implant 604, so as shown in Figures 6E and 6F. For example, the housing 610 may be tightly coupled to the implant 604 and coupled on the implant 604 so as to couple to couple to at least partially (e.g., not tightly) couple to one or more electrodes of the implant 604 as described herein, such as the pickup electrode. In this example, when coordinating one or more electrodes of the implant 604, the housing 610 may be configured to insulate (e.g., electrically insulate) one or more (e.g., covered) electrodes from surrounding tissue (e.g., such as in the environment 101) when deployed in the body together with the implant 604. In some implementations, the one or more electrodes of the implant 604 that are covered (e.g., by the housing 610) may include, for example, a pickup electrode. In some implementations, the housing 610 may be configured to be coupled to the implant 604, tightly coupled to the implant 604, and coupled on the implant 604 with a retaining force of approximately 6.5 Newtons (N).

[0069] The pickup electrode 69a of implant 604 is shown in Figure 6D. As shown in Figure 6E, the power adapter 600 may be mounted in close contact with and on the pickup electrode of implant 604. As shown in Figure 6F, the circuit 620 may be at least partially housed within a housing 610, where the housing 610 includes a housing (1) configured to function, for example, as the pickup electrode of the power adapter 600. The housing 610 may be configured to enclose the circuit 620 within the housing (1). Furthermore, as shown in Figure 6F, the power adapter 600 may include a feedthrough conductor (2) through which the (converted) energy from the circuit 620 is transferred to the stimulating electrode of implant 604. Furthermore, as shown in Figure 6F, the power adapter 600 may include a conductor (4). The conductor (4) may be press-fitted, for example, against the pickup electrode (5) of implant 604. The housing 610 can be configured to connect to the implant 604, and when connected to the implant 604, it can be fitted onto the pickup electrode of the implant 604. The housing 610 may include a silicone sleeve (3) to electrically isolate the pickup electrode from surrounding tissue (for example, when the housing 610 is connected to the implant 604 and placed in the body). The silicone sleeve (3) may be configured to provide frictional or retaining force to the connection between the housing 610 and the implant 604 when connecting the housing 610 to the implant 604. For example, the silicone sleeve (3) may be configured to apply pressure and friction to the connection or interface between the power adapter 600 and the implant 604 when connecting the housing 610 to the implant 604.

[0070] Figures 7A and 7B show a side view and a partial cross-sectional view, respectively, of a power adapter 700 and a portion of the implant 704 according to one embodiment. The power adapter 700 may be structurally and / or functionally similar to other power adapters shown and described herein (e.g., 100, 200, 300, 500, and / or 600). The implant 704 may be structurally and / or functionally similar to other implants shown and described herein (e.g., 104, 304, 504, and / or 604). For example, the implant 704 may include a pickup electrode and a stimulating electrode (not shown), as described above with reference to implant 604 in Figure 6A.

[0071] In some implementations, the housing 710 of the power adapter 700 may be configured to bond to the implant 704, to be tightly bonded to the implant 704, and / or to be bonded on the implant 704, for example, as shown in Figures 7A and 7B, such that the housing 710 at least partially covers the end of the implant 704. For example, the housing 710 may be tightly bonded to the implant 704 and to be bonded on the implant 704, so as to at least partially (e.g., non-sealed) cover one or more electrodes of the implant 704 as described herein. In this example, when covering one or more electrodes of the implant 704, the housing 710 may be configured to insulate (e.g., electrically insulated) one or more (e.g., covered) electrodes from surrounding tissue (e.g., such as in the environment 101) when deployed in the body together with the implant 704. In some implementations, the one or more electrodes of the implant 704 covered (e.g., by the housing 710) may include, for example, a pickup electrode. In some implementations, the housing 710 may be configured to be coupled to the implant 704, tightly coupled to the implant 704, and coupled on the implant 704 with a retaining force of approximately 6.5 Newtons (N).

[0072] As shown in Figure 7B, the power adapter 700 can be mounted in close contact with and on the pickup electrode 705 of the implant 704. The circuit 720 can be at least partially disposed within the housing 710 and may be configured to function as the pickup electrode of the power adapter 700 in combination with the pickup electrode 705. The housing 710 may be configured to seal the circuit 720 within the housing 710. As shown, the housing 710 may include a first sleeve 703A and a second sleeve 703B. The first sleeve 703A may be, for example, a sleeve, cover, housing, etc., formed from any suitable material. For example, the first sleeve 703A may be formed from thermoplastic polyurethane (e.g., Tecotan), polyetheretherketone (PEEK), and / or similar materials. Similarly, the second sleeve 703B may be a sleeve, cover, housing, etc., formed from any suitable material (e.g., a material similar to or different from the material of the first sleeve 703A). For example, the second sleeve 703B may be formed from silicone and / or a similar material. In some embodiments, at least one of the first sleeve 703A and / or the second sleeve 703B may be configured to electrically insulate the pickup electrode 705 from surrounding tissue (for example, when the housing 710 is coupled to the implant 704 and disposed in the body). Furthermore, the first sleeve 703A and the second sleeve 703B may be configured, individually or in combination, to provide frictional or retaining force to the coupling between the housing 710 and the implant 704. For example, the sleeves 703A and / or 703B may be configured to apply pressure and friction to the coupling or interface between the power adapter 700 and the implant 704 when coupling the housing 710 to the implant 704.

[0073] As shown in Figure 7B, the power adapter 700 may include a feedthrough conductor 702 through which (converted) energy from the circuit 720 is transferred to the stimulating electrode of the implant 704. The power adapter 700 may further include a conductor 706. The conductor 706 may be press-fitted, for example, against the pickup electrode 705 of the implant 704. The conductor 706 may be electrically connected to the feedthrough conductor 702, thereby enabling the conductor 706 to transmit power between the feedthrough conductor 702 and the pickup electrode 705 of the implant 704. The interface between the feedthrough conductor 702 and the conductor 706, or the space 707 within the housing 710 around that interface, may be filled with epoxy and / or silicone, and configured to electrically insulate the interface between them. Thus, the power adapter 700 may be structurally and / or functionally similar to the power adapter 600.

[0074] Figure 8A is a schematic diagram showing a power adapter circuit 821A according to one embodiment. Circuit 821A may be structurally and / or functionally similar to other circuits or parts of other circuits described herein (e.g., circuit 221).

[0075] As shown, circuit 821A includes a resistor R (e.g., resistor 222) in parallel with a diode D (e.g., diode 224) and a capacitor C (e.g., capacitor 226) in series with a capacitor R (e.g., resistor 222). Diode D may include a rectifier diode. Capacitor C may include a DC blocking capacitor, as described above with respect to capacitor 226 in Figure 2. In some embodiments, capacitor C may be located on either side of diode D. Diode D can be oriented in a cathode or anode orientation. For example, in cathode orientation, when circuit 821A is connected to an implant (e.g., implant 104), the cathode of diode D may be connected to the implant (e.g., at electrode 19a). As another example, in anode orientation, when circuit 821A is connected to an implant (e.g., implant 104), the anode of diode D may be connected to the implant (e.g., at electrode 19a of implant 104). Resistor R may be placed in parallel with the diode to allow the discharge of capacitor C during the positive phase (e.g., the second energy) of the pulse.

[0076] Figures 8B and 8C are schematic diagrams showing individual circuits 821B and 821C of a power adapter according to one embodiment, respectively. Circuits 821B and 821C may be configured to include an ESD protection circuit to provide electrostatic discharge (ESD) protection. Otherwise, circuits 821B and 821C may be structurally and / or functionally similar to parts of other circuits or other circuits described herein (e.g., circuit 221).

[0077] As shown, circuits 821B and 821C may include a capacitor C (e.g., capacitor 226) in series with a resistor R (e.g., resistor 222) and a diode D (e.g., diode 224), with the resistor R in parallel with the diode D. Furthermore, each of circuits 821B and 821C may include an electrostatic discharge (ESD) protection circuit as shown in Figure 8B. For example, as shown in Figure 8B, circuit 821B may include an ESD protection circuit connected in parallel with the diode D (and resistor R). Thus, the ESD protection circuit of circuit 821B may be configured to protect the diode D. As another example, as shown in Figure 8C, circuit 821C may include an ESD protection circuit connected in parallel with the diode D and capacitor C (and resistor R). In some implementations, ESD protection circuits may include, for example, Zener diodes, transient voltage suppression (TVS) diodes, bidirectional Zener diodes (e.g., two diodes connected in series from front to front or back to back) and / or similar diodes. ESD protection circuits may be configured to reduce exposure to the risk of accidental electrostatic discharge during manufacturing and embedding, and further reduce the need for other ESD protection.

[0078] Figures 9A and 9B are schematic diagrams showing individual circuits 921A and 921B of a power adapter according to one embodiment. Circuits 921A and 921B may be structurally and / or functionally similar to parts of other circuits or other circuits described herein (e.g., circuit 221).

[0079] As shown, each circuit 921A and 921B includes a capacitor C (e.g., capacitor 226) in series with a resistor R (e.g., resistor 222) and a diode D (e.g., diode 224), with the resistor R in parallel with the diode D. Furthermore, each circuit 921 may include a capacitor Cmri configured to provide magnetic resonance imaging (MRI) protection. For example, as shown in Figure 9A, circuit 921A may include a capacitor Cmri connected in parallel with the diode D (and resistor R). As another example, as shown in Figure 9B, circuit 921B may include a capacitor Cmri connected in parallel with the diode D and capacitor C (and resistor R). Thus, a capacitor Cmri connected in either circuit 921A or 921B may be configured to provide a relatively high impedance at low frequencies (50 kHz). Furthermore, at higher frequencies (e.g., 64 MHz, 128 MHz), such as in MRI machines, the capacitor Cmri can be configured to provide low impedance, effectively preventing rectification by effectively short-circuiting (i.e., short-circuiting) the diode D. Thus, only unrectified current is delivered to the stimulating electrode (e.g., from either circuit 921A or 921B). Moreover, unrectified current at 64 MHz or 128 MHz (unlike rectified current) does not activate nerves and does not cause unintended stimulation and / or unpleasant sensations during MRI procedures. For example, the capacitor Cmri can be selected to have a capacitance of approximately 100 picofarads (pF), which may result in impedances of approximately 30,000 ohms at 50 kHz, 25 ohms at 64 MHz, and 12 ohms at 128 MHz. The aforementioned frequencies are MRI frequencies (for 1.5T and 3.0T MRI machines, respectively), and the rectifier circuit is bypassed via a Cmri short circuit (e.g., 921A and 921B). Therefore, at these frequencies, circuits 921A and 921B are configured not to provide rectified pulses to the stimulating electrodes of the implant (e.g., implant 104).

[0080] Figures 10A and 10B are schematic diagrams showing individual circuits 1021A and 1020B of a power adapter according to one embodiment. Circuits 1021A and 1021B may be structurally and / or functionally similar to parts of other circuits or other circuits (e.g., circuit 221) described herein.

[0081] As shown, each circuit 1021A and 1021B includes a capacitor C (e.g., capacitor 226) in series with a resistor R (e.g., resistor 222) and a diode D (e.g., diode 224), with the resistor R in parallel with the diode D. As shown in Figure 10A, circuit 1021A may include an inductor Lmri, disposed and connected in series with the rest of the circuit. Compared to adding a capacitor (e.g., Cmri) to the circuit (e.g., as shown in Figures 9A and 9B), the inductor Lmri may be configured to block higher frequencies, reduce current through the receiver, and prevent heating (e.g., of the power adapter 100 and / or implant 104) due to undesirable stimuli and current flow. For example, the inductor Lmri is selected to have an inductance of about 5 nanohenries (nHy) to provide 2 ohms at 50 kHz, 2 k ohms at 64 MHz, and 4 k ohms at 128 MHz. In some implementations, the Lmri inductor may have dimensions of approximately 2.5 mm × 2.5 mm × 3.8 mm. The aforementioned frequencies are the MRI frequencies that are blocked by the inductor, which can block the MRI frequencies within circuit 1021A (for example, as described above with respect to circuits 921A and 921B). Therefore, at these frequencies, circuit 1021A is configured not to provide pulses to the stimulating electrodes of the implant (e.g., implant 104), thereby protecting the patient while inside the MRI machine.

[0082] In Figure 10A, circuit 1021A is shown to include an inductor Lmri as a replacement for the capacitor Cmri included in circuits 921A and 921B, but in some embodiments, the circuit may include both an inductor and a capacitor (e.g., an LC circuit). For example, as shown in Figure 10B, circuit 1021B includes a capacitor Cmri and an inductor Lmri, each of which may be configured to provide magnetic resonance imaging (MRI) protection alone or in combination. As described above with respect to circuit 1021A, the inductor Lmri of circuit 1021B is connected in series with the rest of the circuit. Thus, at least one of the capacitor 1021A and / or the inductor 1021B can limit, prevent, and / or substantially prevent circuit 1021B from providing pulses to the stimulating electrodes of an implant (e.g., implant 104), thereby protecting the patient while in the MRI machine.

[0083] Figures 11A to 11C show waveforms representing potential waveforms used for a power adapter according to one embodiment. Any power adapter described herein can use, receive, convert, and / or output energy having any suitable characteristics or set of characteristics, which may include, for example, one or more characteristics related to the waveform. For example, Figure 11A shows waveform 1102a according to one embodiment. Waveform 1102a may be an unrectified waveform, for example, related to and / or otherwise having an alternating current. As described in detail above, the transmitter described herein may be configured to generate and provide energy (e.g., first energy) to the power adapter. In some cases, the first energy may have a waveform similar to or substantially the same as waveform 1102a shown, for example, in Figure 11A.

[0084] The power adapters described in detail herein may be configured to receive a first energy and convert and output a second energy. For example, a power adapter may include one or more circuits having any suitable components, as described in detail above with respect to a particular embodiment. In some implementations, a power adapter may be configured to convert energy received from a transmitter (e.g., first energy) into energy having one or more different characteristics (e.g., second energy). For example, in some embodiments, the power adapter and / or at least a part thereof may be configured to rectify the first energy received from the transmitter so that a second energy having a rectified waveform (e.g., a half-wave rectified waveform or a full-wave rectified waveform) is transferred, for example, to a pickup electrode of an implant. In some cases, the rectification may be, for example, unidirectional rectification (also called half-wave rectification). For example, Figure 11B shows, for example, waveform 1102b resulting from unidirectional or half-wave rectification of waveform 1102a. In other examples, the rectification may be, for example, bidirectional rectification (also called full-wave rectification). For example, Figure 11C shows waveform 1102c resulting from bidirectional or full-wave rectification of waveform 1102a.

[0085] Figures 12A to 12D are schematic diagrams showing power adapters in various embodiments. As described above with reference to Figures 11A to 11C, in some implementations, the power adapters described herein may be configured to rectify energy received transcutaneously from a transmitter. More specifically, Figure 12A shows a power adapter 1200a coupled to implant 1204a. The power adapter 1200a and implant 1204a can be similar, at least in form and / or function, to any of the power adapters and implants described in detail herein. The power adapter 1200a may include a circuit 1220a and one or more electrodes 1223a configured to receive energy from a transmitter (for example, as described above with respect to electrodes 123 and / or 223a). In the embodiment shown in Figure 12A, the power adapter 1200a and / or circuit 1220a can be configured to perform, for example, unidirectional or half-wave rectification on the energy received from the transmitter (e.g., first energy), and can provide the pickup electrode 1205a of the implant 1204a with energy having a unidirectional (e.g., shown in Figure 11B) half-wave rectified waveform (e.g., second energy).

[0086] Figure 12B shows a power adapter 1200b coupled to implant 1204b according to one embodiment. The power adapter 1200b and implant 1204b can be similar, at least in form and / or function, to any of the power adapters and implants described in detail herein. As shown, the power adapter 1200b may include a circuit 1220b, one or more proximal electrodes 1223b, and a distal electrode 1228b. Electrodes 1223b and 1228b may be configured to receive energy from a transmitter, as described in detail above. In the embodiment shown in Figure 12B, the power adapter 1200b may be configured as a lead wire, etc., with the circuit 1220b disposed at or near the proximal end and the distal electrode 1228b disposed at or near the distal end. Furthermore, the power adapter 1200b and / or circuit 1220b can be configured to perform, for example, bidirectional or full-wave rectification on the energy received from the transmitter (e.g., first energy), and to provide the bidirectional or full-wave rectified energy (e.g., second energy) to the pickup electrode of implant 1204b. For example, in the example shown in Figure 12B, the proximal electrode 1223b and distal electrode 1228b may be configured to communicate electrically with the transmitter and transfer energy between them (e.g., via two electrical connections, wires, interconnects, etc.). In some embodiments, circuit 1220b may include two or more diodes that can enable, for example, the power adapter 1200b and / or circuit 1220b to perform bidirectional or full-wave rectification on the energy received from the transmitter (e.g., first energy). Therefore, the power adapter 1200b may be configured to provide bidirectional or full-wave rectified energy to the pickup electrode 1205b of the implant 1204b (e.g., second energy).

[0087] Although the power adapter 1200b is shown and described as including circuit 1220b at or near the proximal end and distal electrode 1228b at or near the distal end, in other embodiments, the power adapter configured to perform bidirectional full-wave rectification of the energy received from the transmitter can be in any suitable arrangement. For example, Figure 12C shows a power adapter 1200c coupled to implant 1204c according to one embodiment. In this example, the power adapter 1200c includes circuit 1220c and distal electrode 1228c at or near the distal end of the power adapter 1200c and proximal electrode 1223c at or near the proximal end of the power adapter 1200c. In some implementations, the power adapter 1200c may be similar to the power adapter 1200b, at least in function, and thus may be configured to provide bidirectional full-wave rectified energy to the pickup electrode of implant 1204c. In some embodiments, a single electrical connection (instead of two electrical connections as shown in Figure 12B, for example) may be made between the proximal electrode 1223c and the distal electrode 1228c by providing a circuit 1220c at or near the distal end of the power adapter 1200c.

[0088] Figure 12D shows a power adapter 1200d coupled to implant 1204d according to one embodiment. In this example, the power adapter 1200d includes a circuit 1220d and a distal electrode (not shown in Figure 12D) at or near the distal end of the power adapter 1200d, as described above with respect to power adapter 1200c shown in Figure 12C. In the example shown in Figure 12D, the power adapter 1200d may include a pair of proximal electrodes 1223d at or near the proximal end of the power adapter 1200d. In some implementations, the power adapter 1200d may be similar to power adapters 1200b and / or 1200c, at least in function, and thus may be configured to provide bidirectionally rectified energy to the pickup electrode of implant 1204d. In some implementations, including various arrangements of one or more proximal electrodes (e.g., proximal electrode 1223d), the power adapter 1200d can be used with transmitters of various shapes and / or sizes.

[0089] Figure 13 shows a power adapter 1300 coupled to an implant 1304, and a transmitter 1302 configured to provide energy transcutaneously to the power adapter 1300, according to one embodiment. For example, as described above with respect to power adapters 1200b, 1200c, and / or 1200d, the power adapter 1300 shown in Figure 13 may be configured to perform bidirectional rectification of the energy received from the transmitter 1302. More specifically, the power adapter 1300 may be configured as a lead wire that can be coupled to the implant 1304, as described in detail above. For example, the power adapter 1300 may be configured as a lead wire having a proximal electrode 1323 located at or near the proximal end of the lead wire and a circuit 1320 located at or near the distal end of the lead wire.

[0090] In some embodiments, the lead wires may be about 7.0 centimeters (cm) long. In other embodiments, the lead wires may be longer or shorter than 7.0 cm. In some embodiments, the length of the lead wires and / or the power adapter 1300 may be based at least in part on the size and / or shape of the transmitter 1302 used together. For example, as shown in Figure 13, the power adapter 1300 may be positioned such that the proximal electrode 1323 is at least partially aligned with the first patch, first side, and / or other suitable part (e.g., the first part) of the transmitter 1302, and the electrodes of the circuit 1320 and / or the circuit 1320 (not shown in Figure 13) are at least partially aligned with the second patch, second side, and / or other suitable part (e.g., the second part) of the transmitter 1302. Therefore, the power adapter 1300, the transmitter 1302, and parts of the body disposed between them can form a circuit and / or at least a part of a circuit, thereby enabling the power adapter 1300 to perform bidirectional rectification on the energy received from the transmitter 1302 (e.g., first energy). Furthermore, with the power adapter 1300 coupled to, for example, the pickup electrode of the implant 1304, the power adapter 1300 may be configured to provide bidirectionally rectified energy (e.g., second energy) to the implant 1304 as described in detail herein.

[0091] Figure 14A is a schematic diagram showing a kit 1405A including an implant according to one embodiment. As shown, kit 1405A may include a lead wire adapter (labeled “Lead Adapter”), an implant (labeled “StimRouter Lead in Loader”), a tunneling needle stylet, a stimulation probe, a tunneling needle, an introducer set, and one or more lead stimulation electrodes and anchors. Kit 1405A may also include a power adapter (not shown in Figure 14A) which may be structurally and / or functionally similar to other power adapters shown and described herein (e.g., 100, 200, 300, 500, and / or 600). The implant may be structurally and / or functionally similar to other implants shown and described herein (e.g., 104, 304, 504, and / or 604). Although Kit 1405A is shown as comprising seven or more individual devices, other arrangements and / or configurations according to embodiments of the present disclosure may comprise any number of devices and / or fixtures.

[0092] Kit 1405A represents a tool set containing various instruments and tools to facilitate the placement of implants into a patient's body.

[0093] Lead wire adapters may include lead wire adapters configured to connect implants (e.g., 104, 304, 504, and / or 604) to transmitters (e.g., transmitter 102) during implantation procedures in surgery. When provided as part of Kit 1405A, implants may include electrodes or probes and may be provided with energy (e.g., signal, power) input terminals (e.g., pickup electrodes) and energy (e.g., signal, power) output terminals (e.g., stimulating electrodes, conversion terminals, sensing terminals) as described herein. Implants may be provided with a loading or deployment device or loader configured to facilitate implantation into the body.

[0094] Loading or deployment devices may be configured to maintain the implant in a sterile state before and during final use, and to reduce the risk of contamination during implantation of the implant (along with the power adapter) into the body. Loading or deployment devices may be configured to facilitate implantation (for example, with the stimulating electrode end at the tip).

[0095] An introducer set may include, for example, an incision and formation tool, a hollow tube (for example, through which a power adapter and implant are placed inside the subject's body), and a seal. For example, an introducer set may include a trocar containing an occlusion device, a tube such as a cannula, and a medical seal. A tunneling needle and tunneling needle stylet may include a tunneling needle configured to facilitate access to the body, for the subsequent implantation of an implant (e.g., a power adapter) into the body.

[0096] The anchor may include, for example, a silicone anchor. The anchor may also include an anchor formed from any suitable material, such as a non-reactive or inert material. The anchor may be configured to fix the implant (e.g., together with the power adapter) in place within the body when deployed. For example, the anchor may include a four-pin anchor configured to prevent or reduce the movement of the lead wires after implantation. Kit 1405A may also include any other suitable tools or instruments to facilitate access to the subject's body and the deployment (e.g., by implantation) of the power adapter and implant within the body, as described in the embodiments disclosed herein. For example, Kit 1405A may include tools and instruments (available and supplied under various conditions), such as those listed in Table 1 below. [Table 1]

[0097] Figure 14B is a schematic diagram showing a kit 1405B including a power adapter according to one embodiment. Kit 1405B represents a tool set including various instruments and / or tools that can be used to facilitate coupling and / or mounting of the power adapter to an implant. As shown, Kit 1405B may include a “pocket needle,” a “pocket stylet,” a “silicone sleeve deployment tool,” a “pulse generator and receiver pusher,” and a “pulse generator and receiver mounting tool.” Kit 1405B may also include a power adapter (not shown in Figure 14B) that may be structurally and / or functionally similar to any of the power adapters described herein (e.g., power adapters 100, 200, 300, 500, and / or 600), and / or an implant (not shown in Figure 14B) that may be structurally and / or functionally similar to any of the implants described herein (e.g., implants 104, 304, 504, and / or 604). Although Kit 1405B is shown as including several individual devices, other configurations and / or configurations according to embodiments of the present disclosure may include any number of devices and / or instruments.

[0098] In some implementations, pocket needles and pocket stylets may be configured to facilitate access within the body. More specifically, pocket needles and pocket stylets can be used to access implants that have been previously inserted into the body (e.g., not yet coupled to a power adapter). Pulse generators and receiver pushers can be used to advance power adapters into implants positioned in the body, and pulse generators and receiver mounting tools can be used to attach power adapters to implants (e.g., physically and electrically). Silicone sleeve deployment tools can be used to apply silicone sleeves to power adapters and / or at least a portion of implants (e.g., as described above with respect to sleeves 703A and 703B shown in Figure 7B).

[0099] In some cases, kits 1405A and 1405B may be sold, packaged, and / or shipped together as a combined unit or kit. In other cases, kit 1405A may be sold, packaged, and / or shipped separately from kit 1405B.

[0100] Any implantable device, power adapter, and / or similar can be configured to receive electrical energy from any suitable external transmitter. In some implementations, the external transmitter (also called “external pulse transmitter” or “EPT”) can be configured to provide bursts, pulses, and / or flows of charge to the subject’s body which may be received or “picked up” by any one or a combination thereof of the power adapters and / or implants described herein. In other implementations, the EPT may be a transcutaneous stimulator configured to provide stimulation (e.g., bursts, pulses, and / or flows of charge) to a target site or target nerve in the subject without using an implantable device. For example, such an EPT may be a transcutaneous electrical nerve stimulator (TENS) device, a neuromuscular electrical stimulator (NMES) device, and / or similar.

[0101] In some embodiments, a suitable EPT may be substantially similar to the transmitter 102 described above with reference to Figures 1A and 1B. In some cases, it may be desirable for the EPT to deliver energy transcutaneously with a predetermined set of characteristics. In some implementations, the predetermined set of characteristics may include, for example, frequency or frequency range, voltage or voltage range, current or current range, waveform or waveform range, symmetric or asymmetric pulse, etc. Furthermore, in some implementations, a predetermined set of characteristics may be selected to reduce or avoid harmful sensory or motor stimuli (e.g., undesirable local responses), energy loss in the form of undesirable heating or heat of the EPT, undesirable charge accumulation in the skin and / or tissue (e.g., load circuit), undesirable charge imbalance, and / or similar.

[0102] Examples of suitable transmitters (or parts thereof, their functions, and / or embodiments), as well as methods of use and / or implementations thereof, are provided below. While specific embodiments and / or implementations are provided below, it should be understood that they are illustrative and not limiting. While the embodiments and / or implementations are described as being used in conjunction with implantable devices (such as any of those described above), it should be understood that transmitters may be configured to provide transcutaneous stimulation to a target site of a subject without the additional use of an implantable device, although their form and / or function may be substantially similar to those described. Similarly, it should be understood that transmitters may be used in combination with implants, with or without a power adapter (such as those described above). While the embodiments and / or implementations are described as having specific features, other embodiments with additional features or other combinations of features are possible, and other implementations are contemplated within the scope of this disclosure.

[0103] For example, Figures 15A to 15B are various schematic diagrams showing at least a portion of an external pulse transmitter (EPT) 1502 electrically connected to a load 1501 according to one embodiment. The EPT 1502 may be any suitable transmitter, such as any of the transmitters described herein. For example, in some embodiments, the EPT 1502 and / or a portion or embodiment thereof may be similar to and / or substantially the same as transmitter 102 and / or a portion or embodiment thereof. Thus, such similar portions of the EPT 1502 may not be described in further detail herein. In some implementations, the EPT 1502 may be configured to deliver electrical energy transcutaneously to an embedded device, such as any of the power adapters and / or implants described herein. Furthermore, in the embodiment shown in Figure 15A, the EPT 1502 may be configured to reduce, minimize, and / or at least partially control the amount of heat associated with and / or generated by the use of the EPT 1502, as described in further detail herein.

[0104] As shown in Figure 15A, the EPT 1502 may include one or more circuits configured to provide stimulation, energy, voltage, current, etc., to a connected load 1501. In some implementations, for example, the EPT 1502 is in electrical contact with the skin of the subject wearing the EPT 1502. Thus, a portion of the patient's skin and tissue can form a load 1501 electrically connected to the EPT 1502. More specifically, the subject's skin and tissue have an impedance that can be represented as a capacitor (C load) in series with a resistor (R load), as shown in Figure 15A, and the EPT 1502 may be connected to a load 1501 such that the stimulation, energy, voltage, current, etc., generated by the EPT 1502 results in a current flow across the load 1501 having a load voltage (V load). In some cases, for example, the load 1501 (e.g., the patient's skin and tissue) may have an impedance that can be represented as a 300-ohm resistor in series with a 30 nanofarad (nF) capacitor.

[0105] For example, Figure 15B shows at least a portion of a stimulation circuit 1580 included in the EPT 1502, configured to provide stimulation, energy, current, etc., to a load 1501. The stimulation circuit 1580 includes at least a battery 1591, a capacitor 1592, a voltage converter 1593, and a current source 1594. The EPT 1502 and / or the stimulation circuit 1580 also include a controller 1590 configured to control at least the voltage converter 1593 and the current source 1594. The controller 1590 can be any suitable hardware-based, software-based, and / or firmware-based controller configured to control the operation of at least the voltage converter 1593 and the current source 1594. In some embodiments, for example, the controller 1590 may include, for example, a microprocessor configured to execute a set of instructions and / or code stored in memory (not shown in Figure 15B).

[0106] Battery 1591 can be any suitable battery configured to output a known and / or desired voltage. In other words, battery 1591 can be any suitable size or type of battery and can be configured to function as a voltage source in the stimulation circuit 1580 and / or as a voltage source in the stimulation circuit 1580. The voltage converter 1593 is electrically connected to battery 1591 and is configured to upconvert the voltage supplied by battery 1591 to a desired higher voltage (e.g., compliance voltage (Vc)) suitable for driving a desired amount of current through the load 1501. Furthermore, the voltage converter 1593 can supply a high-voltage current flow to charge the capacitor 1592 of the EPT 1502. In some implementations, the compliance voltage Vc can be determined at least in part on the amount of current generated by the current source and the impedance of the attached load 1501. For example, in some implementations, the compliance voltage Vc can be about 20 volts (V) to about 120 V. Capacitor C can be, for example, a high-voltage capacitor and / or any other suitable capacitor. In some implementations, for example, capacitor C can have sufficient capacitance to drive the desired charge or current across load 1501 without a significant voltage drop across capacitor C. In some implementations, capacitor C can have a capacitance of about 2 μF to about 10 μF.

[0107] As described above, in some implementations, the EPT1502 may be configured to reduce, minimize, and / or at least partially control the amount of heat associated with and / or generated by the use of the EPT1502. In many physiological applications, it is desirable to deliver a constant current during a stimulation pulse, which may cause a change in the voltage drop across the current source during the stimulation pulse. In some cases, heat may arise from a constant amount of voltage drop across the current source 1594, in which case a larger amount of voltage drop will result in a larger amount of heat. In other words, the difference between the compliance voltage and the load voltage may result in power being consumed in the form of heat.

[0108] Figure 16A is a graph 1595A showing the compliance voltage (solid line) and load voltage (dashed line) during symmetric stimulation (for example, when the positive phase or positive pulse of the stimulus has the same duration and the same load current as the negative phase or pulse of the stimulus, but with opposite polarity). The vertical y-axis represents voltage (V), and the horizontal x-axis represents time x10 -4 Expressed in seconds. In the example shown in Figure 16A, the load is a resistor, and the load voltage strictly follows the compliance voltage during both the positive and negative phases of the stimulus.

[0109] However, as described above, the patient's skin and tissues (e.g., load 1501) can be modeled as a resistor in series with a capacitor. Figure 16B is a graph 1595B showing the compliance voltage (solid line) and load voltage (dashed line) during symmetric stimulation when a high-voltage capacitor is added to the resistor. The vertical y-axis represents voltage (V), and the horizontal x-axis represents time x10 -4 Expressed in seconds. The addition of the capacitor causes the load voltage to change significantly from the compliance voltage during the stimulation pulse. During the positive phase, the load capacitor starts charging from zero, but during the negative phase, the load capacitor starts from a value other than zero. For example, as shown in Figure 16B, the compliance voltage is approximately 3.0 × 10⁻⁶. -4 seconds ~ approx. 3.5×10 -4 It is zero in seconds, while the load voltage is approximately 4.4 x 10 -4 It reaches zero in seconds. During constant current stimulation, the amount of wasted energy in each pulse (which manifests as heat) is equal to the integral of the difference between the compliance voltage Vc and the load voltage V load, multiplied by the value of the delivered current.

[0110] As a result, the difference between the load voltage and the compliance voltage becomes larger in the negative phase. Since power consumption is proportional to the difference between the compliance voltage and the load voltage, as a result, (1) the larger the load capacity, the greater the amount of heat generated, (2) the amount of heat generated in the negative phase is greater than the amount of heat generated in the positive phase, and (3) asymmetric stimuli (for example, the positive phase or positive pulse of the stimulus has different duration, voltage, and / or waveform, but opposite polarity) generate more heat than symmetric stimuli (for example, because the compliance voltage is the same magnitude between both the positive and negative phases). For example, Figure 16C is a graph 1595C showing the compliance voltage (solid line) and load voltage (dashed line) during asymmetric stimulation. The vertical y-axis represents voltage (V), and the horizontal x-axis represents time x10 -3 Expressed in seconds. As shown, when the positive compliance voltage is equal to the negative compliance voltage, the load voltage changes significantly from the compliance voltage during the course of the stimulation pulse.

[0111] However, in some cases, the difference between the compliance voltage and the load voltage can be reduced by using asymmetric stimuli, for example, by varying the compliance voltage between the positive and negative phases. For example, Figure 16D is a graph 1595D showing the compliance voltage (solid line) and load voltage (dashed line) during asymmetric stimulation. The vertical y-axis represents voltage (V), and the horizontal x-axis represents time x10 -3 Expressed in seconds. In this example, heat during asymmetric stimulation can be reduced by reducing the magnitude of the compliance voltage in the negative phase. In other words, reducing the magnitude of the compliance voltage in the negative phase can account for, compensate for, and / or otherwise offset the decrease in the load voltage in the negative phase caused by the load capacitor. Therefore, as the difference between the variable compliance voltage and the load voltage decreases, less heat is generated. Furthermore, reducing the compliance voltage also reduces the amount of battery energy consumed by the EPT1502.

[0112] In some implementations, the EPT 1502 may be configured to transmit charge to a target site of the subject and / or an implanted device (e.g., any of those described herein, with or without a power adapter) while limiting, reducing, and / or substantially preventing charge accumulation and / or charge imbalance within or across the load 1501 (e.g., skin and tissue). In some implementations, the EPT 1502 may be configured to deliver constant current stimulation or energy to a target site of the subject and / or an implanted device. For example, Figures 17A–17D show the switch or bridge portion of a stimulation circuit 1580 included in the EPT 1502. The switch or bridge portion of the stimulation circuit 1580 (referred to herein as switch circuit 1580A) may be any suitable type of switch configured to open and / or close one or more portions of the circuit to control the flow of current through the circuit.

[0113] For example, in the embodiments shown in Figures 17A to 17D, the switch circuit 1580A is configured as an "H switch" or "H bridge". The switch circuit 1580A can be electrically connected to a load 1501 and can be configured to transmit charge to the load 1501. More specifically, in the examples shown in Figures 17A to 17D, the switch circuit 1580A may be configured to provide and / or drive a constant current Iset through the load 1501. As shown, the switch circuit 1580A includes a first switch 1581A in series with a second switch 1581B. The switch circuit 1580A also includes a third switch 1581C in series with a fourth switch 1581D. Furthermore, the first switch 1581A and the second switch 1581B are arranged in parallel with the third switch 1581C and the fourth switch 1581D. Switch circuit 1580A is configured such that the first conductor or electrode of the load 1501 is electrically connected between the first switch 1581A and the second switch 1581B, and the second conductor or electrode of the load 1501 is electrically connected between the third switch 1581C and the fourth switch 1581D. Switch circuit 1580A is located between the voltage source (V compliance) and ground. In some implementations, an H-switch or H-bridge configuration may allow switch circuit 1580A to switch between a positive phase (or positive pulse), where charge flows from V compliance towards ground or across the load 1501 in a first direction or positive direction, and a negative phase (or negative pulse), where charge flows from V compliance towards ground or across the load 1501 in a second direction or negative direction (e.g., opposite to the positive direction).

[0114] Figure 17A shows the switch circuit 1580A in the first configuration. As shown, the first switch 1581A and the fourth switch 1581D are in a closed configuration or state, and the second switch 1581B and the third switch 1581C are in an open configuration or state, thereby allowing current to flow from the V compliance across the load 1501 toward ground in the positive direction. As described above with reference to Figure 15A, the load 1501 (e.g., patient skin and tissue) can be represented as a resistor in series with a capacitor. In some implementations, the load capacitor (e.g., the C load in Figure 15A) is charged during the positive phase (or positive pulse) of the stimulus. Thus, the first configuration can be associated with the positive phase of the stimulus, for example.

[0115] Figure 17B shows switch circuit 1580A in a second configuration. As shown, each of switches 1581A, 1581B, 1581C, and 1581D is in an open configuration or state. In some implementations, the second configuration may be associated with and / or result of a ground phase, discharge phase, neutral phase, zero voltage phase, and / or similar. In some implementations, the second configuration may be a phase interval, switching interval, and / or similar, relating to switching between the positive phase and the negative phase of a stimulus.

[0116] When each of switches 1581A, 1581B, 1581C, and 1581D is in an open configuration or state, the load 1501 is disconnected from and / or electrically isolated from the switch circuit 1580A and / or the compliance voltage V compliance associated with the switch circuit 1580A, and therefore no current is driven through the load. Furthermore, since the load 1501 (e.g., skin) does not contain an ideal capacitor, the load capacitor is able to self-discharge at least a portion of the charge stored by the load capacitor (e.g., stored in the subject's skin). In some cases, the switch circuit 1580A may be configured to maintain the second configuration until the current through the load 1501 falls below a predetermined threshold. In other cases, the switch circuit 1580A may be configured to maintain the second configuration for a predetermined time. In other cases, a user may set one or more parameters related to the control of the switch circuit 1580A (e.g., via the controller 1590 shown in Figure 15A). Therefore, the charge accumulated in load 1501 can be discharged before initiating the opposite phase (or negative pulse) of the stimulus.

[0117] Figure 17C shows the switch circuit 1580A in a third configuration. For example, in some implementations, the switch circuit 1580A may be configured to transition from the second configuration to the third configuration after a predetermined time and / or in response to the current through the load 1501 falling below a predetermined threshold. As shown, the second switch 1581B and the fourth switch 1581D are in a closed configuration or state, while the first switch 1581A and the third switch 1581C are in an open configuration or state. Thus, the load 1501 is electrically isolated or disconnected from the first part of the switch circuit 1580A (e.g., the compliance voltage V compliance associated with the switch circuit 1580A), but is electrically connected to the second part of the switch circuit 1580A. In some cases, the second part of the switch circuit 1580A may be an optional grounding or discharge portion of the switch circuit 1580A, which allows a constant current to be driven through the load 1501 by the discharge (e.g., to ground) of the load capacitor. More specifically, the discharge (e.g., to ground) of the load capacitor to drive a constant current through the load 1501 may result in the constant current being driven in the negative direction and / or in the negative phase. Thus, for example, the discharge of the load capacitor may initiate the negative phase of the stimulus. In some implementations, the amount of energy and / or heat associated with initiating the negative phase of the stimulus and / or similar can be reduced by discharging the charge stored in the capacitor of the load 1501 to initiate the negative phase of the stimulus.

[0118] Figure 17D shows the switch circuit 1580A in the fourth configuration. For example, in some implementations, the switch circuit 1580A can be configured to transition from the third to the fourth configuration in response to a desired amount of energy released from the load capacitor after a predetermined time, and / or in response to the current through the load 1501 falling below a predetermined threshold. As shown, the second switch 1581B and the third switch 1581C are in a closed configuration or state, and the first switch 1581A and the fourth switch 1581D are in an open configuration or state. Thus, the load 1501 is electrically connected to the compliance voltage V compliance, as shown in Figure 17D, to drive the current through the load 1501 in the negative direction (e.g., negative phase). In some cases, the amount of charge accumulated in the load 1501 can be reduced and / or limited by discharging the load capacitor before the switch circuit 1580A transitions to the fourth configuration, thereby reducing and / or limiting charge imbalance. In some implementations, the charge accumulated in the load 1501 can be discharged while the switching circuit 1580A is in a third configuration and used to drive and / or initiate a current in the negative direction (e.g., negative phase), thereby using less energy when the load 1501 is reconnected to the compliance voltage V compliance (Figure 17D), thereby reducing the amount of energy and / or heat associated with initiating the reverse phase and / or similar.

[0119] Figure 17E is a graph showing the current (I load) and voltage (V load) across load 1501 as the switching circuit 1580A transitions between its first, second, third, and fourth configurations. For example, during the positive phase of the stimulus (indicated by arrow A in Figure 17E) when the switching circuit 1580A is in the first configuration (Figure 17A), a constant current I load with positive phase is driven across load 1501, and the voltage V load across the load increases. During the interval between phases of the stimulus (indicated by arrow B in Figure 17E) when the switching circuit 1580A is in the second configuration (Figure 17B), no current I load is driven across load 1501, and the voltage V load across the load decreases in response to the self-discharge of the load capacitor. During the initial negative phase of the stimulus (indicated by arrow C in Figure 17E) when the switching circuit 1580A is in the third configuration (Figure 17C), a constant current I load is driven across the load 1501 as a result of the discharge of the load capacitor (e.g., to ground). This configuration can be, for example, a negative phase-to-ground discharge interval. Furthermore, in response to the discharge of the load capacitor to ground, the voltage V load across the load decreases. During the subsequent negative phase of the stimulus (indicated by arrow D in Figure 17E) when the switching circuit 1580A is in the fourth configuration (Figure 17D), a constant current I load is driven across the load 1501 (e.g., by compliance voltage V compliance, in the negative direction and / or negative phase). This configuration can be, for example, a negative phase-active discharge interval, where a constant current is driven through the load 1501 (e.g., in the negative direction and / or negative phase) by a current source energized by the compliance voltage, thereby actively discharging the load capacitor. Furthermore, the voltage across the load, V, continues to decrease in response to the load capacitor being discharged by the compliance voltage, V.

[0120] Although not shown in Figures 17A-17E, in some implementations, the switching circuit 1580A may be configured to return to the first configuration after the negative phase of the stimulus to initiate the positive phase of the stimulus. In some implementations, there may be a relatively long period (e.g., a predetermined period or time) between two consecutive stimulus pulses, during which the switching circuit 1580A may be in an interphase configuration and / or similar (e.g., similar to or the same as the configuration shown in Figure 17B). In other implementations, the switching circuit 1580A may be electrically connected to a load 1501, and the current source (Iset) may be set to zero so that no current is driven through the load 1501. In some cases, after a predetermined period or time, the switching circuit 1580A may be configured to transition or switch to the first configuration shown in Figure 17A, and the EPT 1502 may provide a positive pulse (or stimulus pulse with positive phase).

[0121] In some cases, the EPT1502 may be configured to deliver bursts, pulses, and / or flows of constant current stimulation that are charge-balanced and / or otherwise result in a net-zero charge on the load (e.g., skin and tissue). In other words, the EPT1502 can be configured to deliver energy transcutaneously through the load and to the implanted device, thereby causing little to no charge accumulation (e.g., charge imbalance) on the load. In some cases, it may be desirable to correct the charge imbalance at the beginning of a group or set of bursts rather than correcting the charge imbalance in each individual burst, which may otherwise present challenges due to the time required for fast switching (e.g., about 10 μs) and software feedback correction.

[0122] For example, Figure 18 shows waveforms 1686A illustrating two sets of bursts provided by, for example, EPT1502. As shown, the first set of bursts 1686A begins with a burst having a negative phase or negative pulse and ends with a burst having a positive phase or positive pulse, and the second set of bursts 1686B begins with a burst having a positive phase or positive pulse and ends with a burst having a negative phase or negative pulse. While this is just an example of the first set of bursts 1686A and the second set of bursts 1686B, it should be understood that EPT1502 can provide stimulation in any number of alternating series of the first set of bursts 1686A and the second set of bursts 1686B. Figure 19A is an oscilloscope graph 1685A showing the first set of bursts 1686A and the charge 1687A in the load associated with the first set of bursts 1686A. As shown, the first set of bursts 1686A results in a charge accumulation in the load. Similarly, Figure 19B is an oscilloscope graph 1685B showing the second set of bursts 1686B and the charge in the load 1687B associated with the second set of bursts 1686B. As shown, the second set of bursts 1686B is substantially the same magnitude as the charge accumulation associated with the first set of bursts 1686A, but results in a charge accumulation in the load of the opposite polarity. Thus, EPT 1502 may be configured to provide the second set of bursts 1686B to substantially offset the charge imbalance associated with the first set of bursts 1686A. Thus, the net charge associated with waveform 1652 is substantially zero (e.g., net charge in or experienced by the load, skin, tissue, and / or parts or combinations thereof). In other words, the residual or combined charge associated with the first set of bursts of waveform 1652 is substantially removed or canceled out by the inverse residual or combined charge associated with the second set of bursts of waveform 1652.

[0123] In some cases, the EPT1502 may be configured to provide bursts, pulses, currents, and / or energy to an implanted device, including a power adapter (such as one of those described herein) coupled to an implant (such as one of those described herein). In such cases, the power adapter may include a rectifier configured to rectify the energy received from the EPT1502 (e.g., having waveform 1652) into energy having any suitable and / or desired waveform. Thus, the reverse polarity of the first set of bursts 1686A and the second set of bursts 1686B does not affect the rectified energy delivered from the power adapter to the implant.

[0124] The embodiments and / or methods described herein generally include implantable devices configured to provide stimulation to a part of the body in a single profile, but other embodiments may configure power adapters, implants, and / or combinations thereof to provide stimulation to one or more parts of the body having any number of profiles, levels, characteristics, forms, etc. For example, Figure 20 is a schematic block diagram of a power adapter 1700 coupled to a first implant 1704A and a second implant 1704B. As described in detail above, in some implementations, the power adapter 1700 may be configured to rectify energy received transcutaneously from a transmitter (e.g., EPT 1502 and / or similar). The power adapter 1700 and implants 1704A and 1704B can be similar, at least in form and / or function, to any of the power adapters and implants described in detail herein.

[0125] As shown in Figure 20, the power adapter 1700 may include a receiving electrode 1705, a first bandpass filter (BPF1) 1706A, a second bandpass filter (BPF2) 1706B, a first circuit 1721A, and a second circuit 1721B. More specifically, the first bandpass filter 1706A is electrically connected in series between the receiving electrode 1705 and the first circuit 1721A, and the first circuit 1721A is then electrically connected in series to the first implant 1704A. Similarly, the second bandpass filter 1706B is electrically connected in series between the receiving electrode 1705 and the second circuit 1721B, and the second circuit 1721B is then electrically connected in series to the second implant 1704B. Each of the first circuit 1721A and the second circuit 1721B may be a rectifier circuit configured to rectify energy into a desired form, level, profile, waveform, etc. (e.g., half-wave rectification or full-wave rectification). For example, the first circuit 1721A may include a resistor R1 electrically coupled in parallel to diode D1, and the second circuit 1721B may include a resistor R1 electrically coupled in parallel to diode D2. In some embodiments, the first circuit 1721A and the second circuit 1721B may be substantially similar to any of the circuits described herein (e.g., the circuits described above with respect to Figures 8A-8C, 9A-9B, 10A-10B, and / or similar figures).

[0126] The bandpass filters 1706A and 1706B can be any suitable devices configured to filter or selectively control the flow of energy through them. For example, in some implementations, the first bandpass filter 1706A may be a filter centered on a first frequency, while the second bandpass filter 1706B may be a filter centered on a second frequency different from the first frequency. In this way, bursts of energy received from the transmitter (e.g., EPT 1502) by the receiving electrode 1705 having a carrier frequency substantially equal to or within the range of the first frequency pass through the first bandpass filter 1706A, while carrier frequencies that are not substantially equal to or within the range of the first frequency (e.g., a second frequency) are blocked by the first bandpass filter 1706A. Energy bursts received from the transmitter by the receiving electrode 1705 having a carrier frequency substantially equal to or within the range of the second frequency pass through the second bandpass filter 1706B, while carrier frequencies that are not substantially equal to or within the range of the second frequency (e.g., the first frequency) are blocked by the second bandpass filter 1706B.

[0127] Therefore, the first bandpass filter 1706A can be configured to deliver bursts of energy having a first frequency to the first circuit 1721A, which can then rectify the energy and deliver the first rectified energy to the first implant 1704A. As shown in Figure 20, the first implant 1704A includes a stimulating electrode 1707A configured to provide a stimulus having the first rectified energy to a part of the body. Furthermore, the first bandpass filter 1706A can be configured to remove and / or not provide bursts of energy having frequencies outside the range of the first frequency. For example, the first bandpass filter 1706A may be configured to remove and / or not provide bursts of energy having a second frequency to the first circuit 1721A.

[0128] Similarly, the second bandpass filter 1706B can be configured to deliver bursts of energy having a second frequency to the second circuit 1721A, which can then rectify the energy and deliver the second rectified energy to the second implant 1704B. The second implant 1704B includes a stimulating electrode 1707B configured to provide a stimulus having the second rectified energy to a part of the body. Furthermore, the second bandpass filter 1706B can be configured to remove and / or not provide bursts of energy having frequencies outside the range of the second frequency. For example, the second bandpass filter 1706B may be configured to remove and / or not provide bursts of energy having a first frequency to the second circuit 1721B. In this way, the energy received by the receiving electrode 1705 can be separated using the bandpass filters 1706A and 1706B, and the separate energies can be rectified into two separate rectified energies having any appropriate level, profile, characteristics, waveform, etc., using the circuits 1721A and 1721B. Thus, the power adapter 1700 can be used to provide selective stimulation for separating areas within the subject. Furthermore, if stimulation is desired at electrode 1707A but not at electrode 1707B, energy having a first frequency can be provided to the receiving electrode 1705, and if stimulation is desired at electrode 1707B but not at electrode 1707A, energy having a second frequency can be provided to the receiving electrode 1705.

[0129] Figure 21 is a schematic block diagram of the power adapter 1800 coupled to the first implant 1804A and the second implant 1804B. The power adapter 1800, the first implant 1804A, and the second implant 1804B may be substantially similar to the power adapter 1700, the first implant 1704A, and the second implant 1704B described above with reference to Figure 20. The power adapter 1800 includes, as described above, a receiving electrode 1805, a first bandpass filter 1806A, a second bandpass filter 1806B, a first circuit 1821A, and a second circuit 1821B. In the example shown in Figure 21, the power adapter 1800 includes a capacitor C, a first inductor L1, and a second inductor L2. The capacitor C and the first inductor L1 collectively form a first bandpass filter 1806A, and the capacitor C and the second inductor L2 collectively form a second bandpass filter 1806B. In some cases, the bandpass filters 1806A and 1806B may be filters centered on the frequency represented by the following equation 1.

number

[0130] In the example shown in Figure 21, the capacitance of capacitor C is the same for both the first bandpass filter 1806A and the second bandpass filter 1806B. Therefore, the bandpass filters 1806A and 1806B can be configured to filter energy at different frequencies by including an inductor L1 having a first amount of inductance and an inductor L2 having a second amount of inductance different from the first amount of inductance. In this way, the power adapter 1800 can provide energy to the first implant 1804A having a first profile, level, waveform, etc., while preventing the first implant 1804A from receiving energy at other frequencies, as described in detail above with respect to the power adapter 1700 and implants 1704A and 1704B shown in Figure 20, and can also provide energy to the second implant 1804B having a second profile, level, waveform, etc., while preventing the second implant 1804B from receiving energy at other frequencies.

[0131] The detailed embodiments of this disclosure are intended to describe and illustrate the claimed structures and methods, which are disclosed herein or can be embodied in various forms, and are not intended to be exhaustive in any way, nor are they limited to the disclosed embodiments. Many modifications and variations will become apparent without departing from the scope of the disclosed embodiments. The terminology used herein has been selected to best describe the principles, practical applications, or technical improvements to the present art of one or more embodiments, or to enable an understanding of the embodiments disclosed herein. As described herein, well-known features and technical details may be omitted to avoid unnecessarily obscuring the embodiments of this disclosure.

[0132] References in this specification to “one embodiment,” “embodiment,” and “exemplary embodiment” indicate that the described embodiments may include one or more specific features, structures, or characteristics, but it should be understood that these specific features, structures, or characteristics may or may not be common to all disclosed embodiments disclosed herein. Furthermore, such phrases do not necessarily refer to a specific embodiment itself. Moreover, if one or more specific features, structures, or characteristics are described in relation to a given embodiment, it is considered, where applicable, within the knowledge of a person skilled in the art that such features, structures, or characteristics may be affected in relation to other embodiments, whether or not they are explicitly described.

[0133] The parameters, dimensions, materials, and configurations described herein are intended to be examples only, and the actual parameters, dimensions, materials, and / or configurations will depend on the specific application in which the teachings of the present invention are used. Therefore, it should be understood that the embodiments described herein are presented merely as examples, and within the scope of the appended claims and their equivalents, the present invention may be carried out in ways other than those specifically described and claimed. Embodiments of this disclosure cover each of the individual features, systems, articles, materials, kits, and / or methods described herein. Furthermore, any combination of two or more such features, systems, articles, materials, kits, and / or methods is included within the scope of the present invention, provided that such features, systems, articles, materials, kits, and / or methods are not mutually inconsistent.

[0134] As used herein, the terms “about” and / or “approximately,” when used with numbers and / or ranges, generally refer to numbers and / or ranges that are close to the listed numbers and / or ranges. In some cases, the terms “about” and “approximately” may mean within ±10% of the listed values. For example, in some cases, “the approximate diameter of the instrument” may mean within ±10% of the length of the instrument. The terms “about” and “approximately” can be used interchangeably. Similarly, the term “substantially,” when used in combination with physical and / or geometric features, structures, properties, relationships, etc., is intended to convey that the features, structures, properties, relationships, etc., as thus defined, are nominally features, structures, properties, relationships, etc. As an example, a first quantity described as “substantially equal” to a second quantity is intended to convey that while equality may be desirable, some variation may occur. Such differences may arise from manufacturing tolerances, limitations, approximations, and / or other practical considerations.

[0135] While various embodiments have been described above, it should be understood that they are presented only as examples and not limiting. Where the schematic diagrams and / or embodiments described above show specific components arranged in a particular orientation or position, the arrangement of components may be modified. Although embodiments have been specifically shown and described, it will be understood that various modifications of form and detail are possible. While various embodiments have been described as having a particular combination of mechanisms and / or components, other embodiments are possible having any combination of mechanisms and / or components from any of the embodiments described herein.

[0136] The specific configurations of various components can also be modified. For example, the size and specific shapes of various components may differ from those of the embodiments shown, while still providing the functions described herein. More specifically, the size and shape of various components may be selected specifically for a desired or intended use. Thus, it should be understood that the size, shape, and / or arrangement of the embodiments and / or their components may be adapted to a given use unless the context explicitly states otherwise.

[0137] If the methods and / or events described above indicate that certain events and / or procedures occur in a specific order, the order of those events and / or procedures can be changed. Furthermore, certain events and / or procedures may be executed simultaneously in parallel processes where possible, or sequentially as described above.

Claims

1. It is a device, A housing configured to be coupled to an implantable conductor for placement inside the body, The housing comprises a circuit that is at least partially disposed within the housing and is configured to be electrically connected to the pickup electrode of the embedded conductor when the housing is coupled to the embedded conductor, The circuit is configured such that when the housing is coupled to the embedded conductor and embedded in the body, (i) Receiving a first energy transcutaneously from an electrical pulse generating device, (ii) Converting the first energy into a second energy, (iii) A device wherein the implantable conductor is configured to transmit the second energy to the pickup electrode so that the second energy can be applied to the body part via the stimulating electrode.

2. The apparatus according to claim 1, wherein the first energy is at a first frequency and the second energy is at a second frequency different from the first frequency.

3. The apparatus according to claim 1, wherein the first energy includes a first waveform, and the second energy includes a second waveform different from the first waveform.

4. The apparatus according to claim 1, wherein the first energy is at a first frequency, the second energy is at a second frequency, and the pickup electrode is configured to transcutaneously receive a third energy substantially at the second frequency when the embedded conductor is embedded in the body and not coupled to the housing.

5. The apparatus according to claim 1, wherein the first energy is in the frequency range of approximately 30 kHz to approximately 100 kHz.

6. The apparatus according to claim 1, wherein the first energy includes an alternating current and the second energy includes a pulsating direct current.

7. The apparatus according to claim 1, wherein the first energy includes an alternating current, and the second energy includes a plurality of bursts of energy.

8. The apparatus according to claim 1, wherein the first energy is at a high frequency, and the second energy comprises a plurality of bursts of energy, the plurality of bursts of energy comprising a combination of low-frequency energy bursts and high-frequency energy bursts.

9. The apparatus according to claim 1, wherein the first energy comprises a plurality of energy bursts, and the plurality of energy bursts comprises a combination of low-frequency energy bursts and high-frequency energy bursts.

10. The part of the body is a first part of the body, the first energy comprises a plurality of energy bursts, and the plurality of energy bursts comprises a combination of low-frequency energy bursts and high-frequency energy bursts. The circuit is configured to (1) receive the high-frequency energy burst, (2) convert the high-frequency energy burst into the second energy, and (3) transmit the second energy to the pickup electrode so that the embedded conductor can apply the second energy to the first part of the body via the stimulating electrode. The apparatus according to claim 1, wherein the low-frequency energy burst is configured to produce a local response in a second part of the body different from the first part of the body.

11. The apparatus according to claim 1, wherein the circuit includes a rectifier circuit.

12. The apparatus according to claim 1, wherein the circuit includes a DC blocking capacitor, a rectifier diode, a resistor, and a receiving electrode.

13. The apparatus according to claim 1, wherein the circuit includes a receiving electrode, and the circuit is configured to be electrically connected to the stimulating electrode when the housing is coupled to the implantable conductor and implanted in the body.

14. The apparatus according to claim 1, wherein the housing is configured to insulate the circuit from the body when the housing is coupled to the embedded conductor and embedded in the body.

15. The apparatus according to claim 1, wherein the material of the pickup electrode includes one of titanium or titanium nitride.

16. The apparatus according to claim 1, wherein the circuit includes a rectifier diode oriented so as to provide cathode stimulation via the stimulating electrode.

17. The apparatus according to claim 1, wherein the circuit includes a rectifier diode and a capacitor in parallel with the rectifier diode, the capacitor being configured to effectively short-circuit the rectifier diode at about 64 MHz.

18. The apparatus according to claim 1, wherein the circuit includes a rectifier diode and a capacitor in parallel with the rectifier diode, the capacitor being configured to effectively short-circuit the rectifier diode at about 128 MHz.

19. The apparatus according to claim 1, wherein the circuit includes a rectifier diode, a capacitor in parallel with the rectifier diode, and an inductor in series with the rectifier diode.

20. The apparatus according to claim 1, wherein the circuit includes a Zener diode for electrostatic discharge (ESD) protection.

21. It is a device, The power adapter comprises a housing and a circuit at least partially disposed within the housing, wherein the housing is configured to be coupled to an implantable device for placement inside the body. The circuit is configured to be electrically connected to the embedded device when the housing is coupled to the embedded conductor. The circuit is configured such that when the housing is coupled to the embedded conductor and embedded in the body, (i) Receiving a first energy having a first set of characteristics transcutaneously from a power source, (ii) Converting the first energy into a second energy having a second set of characteristics different from the first set of characteristics, (iii) A device configured to transfer the second energy to the implanted device such that the second energy supplies power to the implanted device.

22. The apparatus according to claim 21, wherein the circuit includes a rectifier circuit.

23. The apparatus according to claim 21, wherein the circuit includes a DC blocking capacitor, a rectifier diode, a resistor, and a receiving electrode.

24. The apparatus according to claim 21, wherein the first energy includes an alternating current and the second energy includes a pulsating direct current.

25. The apparatus according to claim 21, wherein the first energy has a frequency of about 30 kHz to about 100 kHz.

26. The apparatus according to claim 21, wherein the circuit includes a Zener diode for electrostatic discharge (ESD) protection.

27. It is a method, Receiving a first energy having at least a first characteristic transcutaneously from an electrical pulse generator, The first energy is converted via a rectifier circuit into a second energy having at least two characteristics different from the first characteristics, A method comprising transferring the second energy from the rectifier circuit to a stimulating electrode of an implantable conductor, thereby causing the implantable conductor to apply the second energy to a target nerve inside the body via the stimulating electrode.

28. The method according to claim 27, wherein the first characteristic is a first frequency, and the second characteristic is a second frequency different from the first frequency.

29. The method according to claim 27, wherein the first characteristic is a first waveform, the second characteristic is a second waveform, and the conversion of the first energy to the second energy includes half-wave rectification of the first waveform to generate the second energy having the second waveform.

30. The method according to claim 27, wherein the first characteristic is a first waveform, the second characteristic is a second waveform, and the conversion of the first energy to the second energy includes full-wave rectification of the first waveform to generate the second energy having the second waveform.

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