US20150028805A1 - Implant charging field control through radio link - Google Patents

Implant charging field control through radio link Download PDF

Info

Publication number
US20150028805A1
US20150028805A1 US14446280 US201414446280A US2015028805A1 US 20150028805 A1 US20150028805 A1 US 20150028805A1 US 14446280 US14446280 US 14446280 US 201414446280 A US201414446280 A US 201414446280A US 2015028805 A1 US2015028805 A1 US 2015028805A1
Authority
US
Grant status
Application
Patent type
Prior art keywords
charging
charger
effectiveness
time
implantable device
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Pending
Application number
US14446280
Inventor
Brian R. Dearden
Brian M. Shelton
James H. Wolfe
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Mann Alfred E Foundation for Scientific Research
Original Assignee
Mann Alfred E Foundation for Scientific Research
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/378Electrical supply
    • A61N1/3787Electrical supply from an external energy source
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/3605Implantable neurostimulators for stimulating central or peripheral nerve system
    • A61N1/36125Details of circuitry or electric components
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/37211Means for communicating with stimulators
    • A61N1/37217Means for communicating with stimulators characterised by the communication link, e.g. acoustic or tactile
    • A61N1/37223Circuits for electromagnetic coupling
    • A61N1/37229Shape or location of the implanted or external antenna
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01RMEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R19/00Arrangements for measuring currents or voltages or for indicating presence or sign thereof
    • G01R19/12Measuring rate of change
    • HELECTRICITY
    • H02GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02JCIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J5/00Circuit arrangements for transfer of electric power between ac networks and dc networks
    • H02J5/005Circuit arrangements for transfer of electric power between ac networks and dc networks with inductive power transfer
    • HELECTRICITY
    • H02GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02JCIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J50/00Circuit arrangements or systems for wireless supply or distribution of electric power
    • H02J50/10Circuit arrangements or systems for wireless supply or distribution of electric power using inductive coupling
    • HELECTRICITY
    • H02GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02JCIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J50/00Circuit arrangements or systems for wireless supply or distribution of electric power
    • H02J50/90Circuit arrangements or systems for wireless supply or distribution of electric power involving detection or optimisation of position, e.g. alignment
    • HELECTRICITY
    • H02GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02JCIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J7/00Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries
    • H02J7/0042Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries characterised by the mechanical construction
    • HELECTRICITY
    • H02GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02JCIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J7/00Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries
    • H02J7/0047Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries with indicating devices
    • HELECTRICITY
    • H02GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02JCIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J7/00Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries
    • H02J7/02Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries for charging batteries from ac mains by converters
    • H02J7/022Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries for charging batteries from ac mains by converters characterised by the type of converter
    • H02J7/025Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries for charging batteries from ac mains by converters characterised by the type of converter using non-contact coupling, e.g. inductive, capacitive
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/37211Means for communicating with stimulators
    • A61N1/37252Details of algorithms or data aspects of communication system, e.g. handshaking, transmitting specific data or segmenting data

Abstract

A charger that evaluates the effectiveness of the charging field generated by the charger at an implantable device. The charger includes a charging coil, a communication module, and a processor. The processor can include instructions to determine the effectiveness of the charging field based on one or several signals or communications received from the implantable device. The charger can use the determination of the effectiveness of the charging field to vary the strength of the charging field and/or to prompt the user to move the charger with respect to the implantable device.

Description

    CROSS-REFERENCES TO RELATED APPLICATIONS
  • This application claims the benefit of U.S. Provisional Application No. 61/859,484 entitled “IMPLANT CHARGING FIELD CONTROL THROUGH RADIO LINK,” and filed on Jul. 29, 2013, the entirety of which is hereby incorporated by reference herein.
  • BACKGROUND OF THE INVENTION
  • The prevalence of use of medical devices in treating ailments is increasing with time. In many instances, and as these medical devices are made smaller, these medical devices are frequently implanted within a patient. While the desirability of implantable devices is increasing as the size of the devices has decreased, the implantation process still frequently requires complicated surgery which can expose the patient to significant risks and protracted recovery times. In light of this, further methods, systems, and devices are desired to increase the ease of use of implantable of medical devices.
  • BRIEF SUMMARY OF THE INVENTION
  • One aspect of the present disclosure relates to a charger. The charger can include a charging coil that can magnetically couple with a corresponding charging coil of an implantable device, an indicator that can identify the effectiveness of a charging field created between the charging coil of the charger and the corresponding charging coil of the implantable device, and a processor that can receive a signal from the implantable device at a first time, direct the indicator to identify a first effectiveness level based on a determined effectiveness of the charging field at the first time, receive a signal from the implantable device at a second time, and direct the indicator to identify a second effectiveness level based on a determined effectiveness of the charging field at the second time.
  • In some embodiments of the charger, the indicator can include one of a visual and an audible indicator. In some embodiments, the visual indicator can include one of a light and a display.
  • In some embodiments of the charger, the processor determines the effectiveness of the charging field based on at least one of a voltage induced by the charging field at the charging coil of the implantable device and a current induced by the charging field at the charging coil of the implantable device. In some embodiments, the processor can direct the charging coil of the charger to generate a charging field and/or the processor can optimize the charging field before the first time. In some embodiments optimizing of the charging field can include determining if the charging field is inducing a voltage at the charging coil of the implantable device that is greater than the voltage of an energy storage device of the implantable device. In some embodiments, optimizing the charging field can include increasing the voltage on the charging coil of the charger if the charge filed is inducing a voltage at the charging coil of the implantable device that is less than the voltage of an energy storage device of the implantable device.
  • In some embodiments, the effectiveness of the charging field at the second time is greater than the effectiveness of the charging field at the first time, and in some embodiments, the effectiveness of the charging field at the second time is less than the effectiveness of the charging field at the first time.
  • One aspect of the present disclosure relates to a method of directing alignment of a charger with an implantable device. The method includes applying a first voltage to a charging coil of a charger, which application of the first voltage to the charging coil of the charger generates a charging field, receiving a first signal from the implantable device at a first time, which first signal includes information identifying a parameter of an effect of the charging field on the implantable device at the first time, directing an indicator to identify a first effectiveness level, receiving a second signal from the implantable device at a second time, which second signal includes information identifying the parameter of the effect of the charging field on the implantable device at the second time, and directing the indicator to identify a second effectiveness level.
  • In some embodiments directing the indicator to identify the second effectiveness level includes directing the identifier to identify an increased effectiveness when the second effectiveness level is greater than the first effectiveness level. In some embodiments directing the indicator to identify the second effectiveness level includes directing the identifier to identify a decreased effectiveness when the second effectiveness level is less than the first effectiveness level.
  • In some embodiments, the method includes receiving a third signal from the implantable device at a third time, which third signal includes information identifying a parameter of an effect of the charging field on the implantable device at the third time, and optimizing the voltage applied to the charging coil of the charger based on the third signal. In some embodiments, the receipt of the third signal at the third time precedes the receipt of the first signal at the first time.
  • In some embodiments, the method includes determining the effectiveness of the charging field at the first time, and determining the effectiveness of the charging field at the second time. In some embodiments, determining the effectiveness of the charging field is based on at least one of a voltage induced by the charging field at the charging coil of the implantable device and a current induced by the charging field at the charging coil of the implantable device. In some embodiments, the effectiveness of the charging field is determined by comparing the parameter of the effect of the charging field on the implantable device with a threshold value. In some embodiments, the charging field is effective if the parameter of the effect of the charging field on the implantable device is greater than the threshold value.
  • One aspect of the present disclosure relates to a system for delivering power to an implantable device. The system includes an implantable device that includes a network interface, and a charging module having a first charging coil, which charging module can monitor at least one charge parameter. The system can include a charger including a network interface that can receive the at least one charge parameter from the implantable device, a charging module including a second charging coil, which charging module can control the voltage of the second charging coil according to the received at least one charge parameter, and an indicator control module that can control an indicator to identify the effectiveness of the magnetic coupling between the implantable device and the charger.
  • In some embodiments, the indicator can identify the effectiveness of the magnetic coupling between the implantable device and the charger by identifying a change in the least one charge parameter over a period of time. In some embodiments the at least one charge parameter includes a voltage induced at the first charging coil. In some embodiments the at least one charge parameter includes a current induced at the charging coil of the implantable device.
  • One aspect of the present disclosure relates to a charger. The charger includes a charging coil that can magnetically couple with a corresponding charging coil of a peripherally implanted pulse generator, which peripherally implanted pulse generator includes a plurality of electrodes, an indicator that can identify the effectiveness of a charging field created between the charging coil of the charger and the corresponding charging coil of the implantable device, and a processor that can receive a signal from the peripherally implanted pulse generator at a first time, which signal indicates the effectiveness of the charging field at the first time, direct the indicator to identify a first effectiveness level, receive a signal from the peripherally implanted pulse generator at a second time, which signal indicates the effectiveness of the charging field at the second time, and direct the indicator to identify a second effectiveness level.
  • One aspect of the present disclosure relates to a charger. The charger includes a charging coil that can magnetically couple with a corresponding charging coil of recharging device, an indicator that can identify the effectiveness of a charging field created between the charging coil of the charger and the corresponding charging coil of the recharging device, and a processor that can receive a signal from the recharging device at a first time, direct the indicator to identify a first effectiveness level based on a determined effectiveness of the charging field at the first time, receive a signal from the recharging device at a second time, and direct the indicator to identify a second effectiveness level based on a determined effectiveness of the charging field at the second time.
  • In some embodiments, the recharging device is an implantable device. In some embodiments, the implantable device can be a peripherally implanted pulse generator including a plurality of electrodes
  • Further areas of applicability of the present disclosure will become apparent from the detailed description provided hereinafter. It should be understood that the detailed description and specific examples, while indicating various embodiments, are intended for purposes of illustration only and are not intended to necessarily limit the scope of the disclosure.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1 is a schematic illustration of one embodiment of an implantable neurostimulation system.
  • FIG. 2 is a schematic illustration of one embodiment of interconnectivity of the implantable neurostimulation system.
  • FIG. 3 is a schematic illustration of one embodiment of the architecture of the external pulse generator and/or of the implantable pulse generator that is a part of the implantable neurostimulation system.
  • FIG. 4 is a schematic illustration of one embodiment of the charger that is a part of the implantable neurostimulation system.
  • FIG. 5 is a perspective view of one embodiment of an implantable pulse generator and a charger.
  • FIG. 6 is a perspective view of one embodiment of a charging coil that can be used in an implantable pulse generator.
  • FIG. 7 is a perspective view of one embodiment of a charging coil that can be used in a charger.
  • FIG. 8 is a flowchart illustrating one embodiment of a process for providing an alignment indicator for a charger.
  • FIG. 9 is a flowchart illustrating one embodiment of a process for providing an alignment indicator for a charger based on detected variations in measured voltage and current.
  • FIG. 10 is a flowchart illustrating one embodiment of a process in which movement of a charger is detected during the charging process.
  • In the appended figures, similar components and/or features may have the same reference label. Where the reference label is used in the specification, the description is applicable to any one of the similar components having the same reference label.
  • DETAILED DESCRIPTION OF THE INVENTION
  • A significant percentage of the Western (EU and US) population is affected by Neuropathic pain (chronic intractable pain due to nerve damage). In many people, this pain is severe. There are thousands of patients that have chronic intractable pain involving a nerve. Neuropathic pain can be very difficult to treat with only half of patients achieving partial relief Thus, determining the best treatment for individual patients remains challenging. Conventional treatments include certain antidepressants, anti-epileptic drugs and opioids. However, side effects from these drugs can be detrimental. In some of these cases, electrical stimulation can provide effective treatment of this pain without the drug-related side effects.
  • A spinal cord stimulator is a device used to deliver pulsed electrical signals to the spinal cord to control chronic pain. Because electrical stimulation is a purely electrical treatment and does not cause side effects similar to those caused by drugs, an increasing number of physicians and patients favor the use of electrical stimulation over drugs as a treatment for pain. The exact mechanisms of pain relief by spinal cord stimulation (SCS) are unknown. Early SCS trials were based on the Gate Control Theory, which posits that pain is transmitted by two kinds of afferent nerve fibers. One is the larger myelinated Aδ fiber, which carries quick, intense-pain messages. The other is the smaller, unmyelinated “C” fiber, which transmits throbbing, chronic pain messages. A third type of nerve fiber, called Aβ, is “non-nociceptive,” meaning it does not transmit pain stimuli. The gate control theory asserts that signals transmitted by the Aδ and C pain fibers can be thwarted by the activation/stimulation of the non-nociceptive Aβ fibers and thus inhibit an individual's perception of pain. Thus, neurostimulation provides pain relief by blocking the pain messages before they reach the brain.
  • SCS is often used in the treatment of failed back surgery syndrome, a chronic pain syndrome that has refractory pain due to ischemia. SCS complications have been reported in a large portion, possibly 30% to 40%, of all SCS patients. This increases the overall costs of patient pain management and decreases the efficacy of SCS. Common complications include: infection, hemorrhaging, injury of nerve tissue, placing device into the wrong compartment, hardware malfunction, lead migration, lead breakage, lead disconnection, lead erosion, pain at the implant site, generator overheating, and charger overheating. The occurrence rates of common complications are surprisingly high: including lead extension connection issues, lead breakage, lead migration and infection.
  • Peripheral neuropathy, another condition that can be treated with electrical stimulation, may be either inherited or acquired. Causes of acquired peripheral neuropathy include physical injury (trauma) to a nerve, viruses, tumors, toxins, autoimmune responses, nutritional deficiencies, alcoholism, diabetes, and vascular and metabolic disorders. Acquired peripheral neuropathies are grouped into three broad categories: those caused by systemic disease, those caused by trauma, and those caused by infections or autoimmune disorders affecting nerve tissue. One example of an acquired peripheral neuropathy is trigeminal neuralgia, in which damage to the trigeminal nerve (the large nerve of the head and face) causes episodic attacks of excruciating, lightning-like pain on one side of the face.
  • A high percentage of patients with peripheral neuropathic pain do not benefit from SCS for various reasons. However, many of these patients can receive acceptable levels of pain relief via direct electrical stimulation to the corresponding peripheral nerves. This therapy is called peripheral nerve stimulation (PNS). As FDA approved PNS devices have not been commercially available in the US market, Standard spinal cord stimulator (SCS) devices are often used off label by pain physicians to treat this condition. A significant portion of SCS devices that have been sold may have been used off-label for PNS.
  • As current commercially-available SCS systems were designed for stimulating the spinal cord and not for peripheral nerve stimulation, there are more device complications associated with the use of SCS systems for PNS than for SCS. Current SCS devices (generators) are large and bulky. In the event that an SCS is used for PNS, the SCS generator is typically implanted in the abdomen or in the lower back above the buttocks and long leads are tunneled across multiple joints to reach the target peripheral nerves in the arms, legs or face. The excessive tunneling and the crossing of joints leads to increased post-surgical pain and higher device failure rates. Additionally, rigid leads can lead to skin erosion and penetration, with lead failure rates being far too high within the first few years of implantation. Many or even most complications result in replacement surgery and even multiple replacement surgeries in some cases.
  • One embodiment of an implantable neurostimulation system 100 is shown in FIG. 1, which implantable neurostimulation system 100 can be, for example, a peripherally-implantable neurostimulation system 100. In some embodiments, the implantable neurostimulation system 100 can be used in treating patients with, for example, chronic, severe, refractory neuropathic pain originating from peripheral nerves. In some embodiments, the implantable neurostimulation system 100 can be used to either stimulate a target peripheral nerve or the posterior epidural space of the spine.
  • The implantable neurostimulation system 100 can include one or several pulse generators. The pulse generators can comprise a variety of shapes and sizes, and can be made from a variety of materials. In some embodiments, the one or several pulse generators can generate one or several non-ablative electrical pulses that are delivered to a nerve to control pain. In some embodiments, these pulses can have a pulse amplitude of between 0-1,000 mA, 0-100 mA, 0-50 mA, 0-25 mA, and/or any other or intermediate range of amplitudes. One or more of the pulse generators can include a processor and/or memory. In some embodiments, the processor can provide instructions to and receive information from the other components of the implantable neurostimulation system 100. The processor can act according to stored instructions, which stored instructions can be located in memory, associated with the processor, and/or in other components of the implantable neurostimulation system 100. The processor can, in accordance with stored instructions, make decisions. The processor can comprise a microprocessor, such as a microprocessor from Intel® or Advanced Micro Devices, Inc.®, or the like.
  • In some embodiments, the stored instructions directing the operation of the processor may be implemented by hardware, software, scripting languages, firmware, middleware, microcode, hardware description languages, and/or any combination thereof. When implemented in software, firmware, middleware, scripting language, and/or microcode, the program code or code segments to perform the necessary tasks may be stored in a machine readable medium such as a storage medium. A code segment or machine-executable instruction may represent a procedure, a function, a subprogram, a program, a routine, a subroutine, a module, a software package, a script, a class, or any combination of instructions, data structures, and/or program statements. A code segment may be coupled to another code segment or a hardware circuit by passing and/or receiving information, data, arguments, parameters, and/or memory contents. Information, arguments, parameters, data, etc. may be passed, forwarded, or transmitted via any suitable means including memory sharing, message passing, token passing, network transmission, etc.
  • In some embodiments, the memory of one or both of the pulse generators can be the storage medium containing the stored instructions. The memory may represent one or more memories for storing data, including read only memory (ROM), random access memory (RAM), magnetic RAM, core memory, magnetic disk storage mediums, optical storage mediums, flash memory devices and/or other machine readable mediums for storing information. In some embodiments, the memory may be implemented within the processor or external to the processor. In some embodiments, the memory can be any type of long term, short term, volatile, nonvolatile, or other storage medium and is not to be limited to any particular type of memory or number of memories, or type of media upon which memory is stored. In some embodiments, the memory can include, for example, one or both of volatile and nonvolatile memory. In one specific embodiment, the memory can include a volatile portion such as RAM memory, and a nonvolatile portion such as flash memory.
  • In some embodiments, one of the pulse generators can be an external pulse generator 102 or an implantable pulse generator 104. While frequently referred to herein as an implantable pulse generator 104, this can also include an implantable device recharging device. The external pulse generator 102 can be used to evaluate the suitability of a patient for treatment with the implantable neurostimulation system 100 and/or for implantation of an implantable pulse generator 104.
  • In some embodiments, one of the pulse generators can be the implantable pulse generator 104, which can be sized and shaped, and made of material to allow implantation of the implantable pulse generator 104 inside of a body. In some embodiments, the implantable pulse generator 104 can be sized and shaped so as to allow placement of the implantable pulse generator 104 at any desired location in a body, and in some embodiments, placed proximate to a peripheral nerve such that leads (discussed below) are not tunneled across joints and/or such that extension cables are not needed.
  • The implantable pulse generator 104 can include one or several energy storage features. In some embodiments, these features can be configured to store energy, such as, for example, electric energy, that can be used in the operation of the implantable pulse generator 104. These energy storage features can include, for example, one or several batteries, including rechargeable batteries, one or several capacitors, one or several fuel cells, or the like.
  • In some embodiments, the electrical pulses generated by the pulse generator can be delivered to one or several nerves 110 and/or to tissue proximate to one or several nerves 110 via one or several leads. The leads can include conductive portions, such as electrodes or contact portions of electrodes, and non-conductive portions. The leads can have a variety of shapes, can be a variety of sizes, and can be made from a variety of materials, which size, shape, and materials can be dictated by the application or other factors. In some embodiments, the leads can be implanted proximate to a peripheral nerve. In one embodiment, both the implantable pulse generator 104 and the leads can be implanted in a peripheral portion of the patient's body, and can be configured to deliver one or several electrical pulses to the peripheral nerve.
  • In some embodiments, the leads can include an anodic lead 106 and/or a cathodic lead 108. In some embodiments, the anodic lead 106 and the cathodic lead 108 can be identical leads, but can receive pulses of different polarity from the pulse generator.
  • In some embodiments, the leads can connect directly to the pulse generator, and in some embodiments, the leads can be connected to the pulse generator via a connector 112 and a connector cable 114. The connector 112 can comprise any device that is able to electrically connect the leads to the connector cable 114. Likewise, the connector cable can be any device capable of transmitting distinct electrical pulses to the anodic lead 106 and the cathodic lead 108.
  • In some embodiments, the implantable neurostimulation system 100 can include a charger 116 that can be configured to recharge the implantable pulse generator 104 when the implantable pulse generator 104 is implanted within a body. The charger 116 can comprise a variety of shapes, sizes, and features, and can be made from a variety of materials. Like the pulse generators 102, 104, the charger 116 can include a processor and/or memory having similar characteristics to those discussed above. In some embodiments, the charger 116 can recharge the implantable pulse generator 104 via an inductive coupling.
  • In some embodiments, one or several properties of the electrical pulses can be controlled via a controller. In some embodiments, these properties can include, for example, the frequency, strength, pattern, duration, or other aspects of the timing and magnitude of the electrical pulses. In one embodiment, these properties can include, for example, a voltage, a current, or the like. In one embodiment, a first electrical pulse can have a first property and a second electrical pulse can have a second property. This control of the electrical pulses can include the creation of one or several electrical pulse programs, plans, or patterns, and in some embodiments, this can include the selection of one or several pre-existing electrical pulse programs, plans, or patterns. In the embodiment depicted in FIG. 1, the implantable neurostimulation system 100 includes a controller that is a clinician programmer 118. The clinician programmer 118 can be used to create one or several pulse programs, plans, or patterns and/or to select one or several of the created pulse programs, plans, or patterns. In some embodiments, the clinician programmer 118 can be used to program the operation of the pulse generators including, for example, one or both of the external pulse generator 102 and the implantable pulse generator 104. The clinician programmer 118 can comprise a computing device that can wiredly and/or wirelessly communicate with the pulse generators. In some embodiments, the clinician programmer 118 can be further configured to receive information from the pulse generators indicative of the operation and/or effectiveness of the pulse generators and the leads.
  • In some embodiments, the controller of the implantable neurostimulation system 100 can include a patient remote 120. The patient remote 120 can comprise a computing device that can communicate with the pulse generators via a wired or wireless connection. The patient remote 120 can be used to program the pulse generator, and in some embodiments, the patient remote 120 can include one or several pulse generation programs, plans, or patterns created by the clinician programmer 118. In some embodiments, the patient remote 120 can be used to select one or several of the pre-existing pulse generation programs, plans, or patterns and to select, for example, the duration of the selected one of the one or several pulse generation programs, plans, or patterns.
  • Advantageously, the above outlined components of the implantable neurostimulation system 100 can be used to control and provide the generation of electrical pulses to mitigate patient pain.
  • With reference now to FIG. 2, a schematic illustration of one embodiment of interconnectivity of the implantable neurostimulation system 100 is shown. As seen in FIG. 2, several of the components of the implantable neurostimulation system 100 are interconnected via network 110. In some embodiments, the network 110 allows communication between the components of the implantable neurostimulation system 100. The network 110 can be, for example, a local area network (LAN), a wide area network (WAN), a wired network, a custom network, wireless network, a telephone network such as, for example, a cellphone network, the Internet, the World Wide Web, or any other desired network or combinations of different networks. In some embodiments, the network 110 can use any desired communication and/or network protocols. The network 110 can include any communicative interconnection between two or more components of the implantable neurostimulation system 100. In one embodiment, the communications between the devices of the implantable neurostimulation system 100 can be according to any communication protocol including, for example those covered by Near Field Communication (NFC), Bluetooth, or the like. In some embodiments, different components of the system may utilize different communication networks and/or protocols.
  • With reference now to FIG. 3, a schematic illustration of one embodiment of the architecture of the external pulse generator 102 and/or of the implantable pulse generator 104 is shown. In some embodiments, each of the components of the architecture of the one of the pulse generators 102, 104 can be implemented using the processor, memory, and/or other hardware component of the one of the pulse generators 102, 104. In some embodiments, the components of the architecture of the one of the pulse generators 102, 104 can include software that interacts with the hardware of the one of the pulse generators 102, 104 to achieve a desired outcome.
  • In some embodiments, the pulse generator 102/104 can include, for example, a network interface 300, or alternatively, a communication module. The network interface 300, or alternatively, the communication module, can be configured to access the network 110 to allow communication between the pulse generator 102, 104 and the other components of the implantable neurostimulation system 100. In some embodiments, the network interface 300, or alternatively, a communication module, can include one or several antennas and software configured to control the one or several antennas to send information to and receive information from one or several of the other components of the implantable neurostimulation system 100.
  • The pulse generator 102, 104 can further include a data module 302. The data module 302 can be configured to manage data relating to the identity and properties of the pulse generator 102, 104. In some embodiments, the data module can include one or several databases that can, for example, include information relating to the pulse generator 102, 104 such as, for example, the identification of the pulse generator, one or several properties of the pulse generator 102, 104, or the like. In one embodiment, the data identifying the pulse generator 102, 104 can include, for example, a serial number of the pulse generator 102, 104 and/or other identifier of the pulse generator 102, 104 including, for example, a unique identifier of the pulse generator 102, 104. In some embodiments, the information associated with the property of the pulse generator 102, 104 can include, for example, data identifying the function of the pulse generator 102, 104, data identifying the power consumption of the pulse generator 102, 104, data identifying the charge capacity of the pulse generator 102, 104 and/or power storage capacity of the pulse generator 102, 104, data identifying potential and/or maximum rates of charging of the pulse generator 102, 104, and/or the like.
  • The pulse generator 102, 104 can include a pulse control 304. In some embodiments, the pulse control 304 can be configured to control the generation of one or several pulses by the pulse generator 102, 104. In some embodiments, for example, this information can identify one or several pulse patterns, programs, or the like. This information can further specify, for example, the frequency of pulses generated by the pulse generator 102, 104, the duration of pulses generated by the pulse generator 102, 104, the strength and/or magnitude of pulses generated by the pulse generator 102, 104, or any other details relating to the creation of one or several pulses by the pulse generator 102, 104. In some embodiments, this information can specify aspects of a pulse pattern and/or pulse program, such as, for example, the duration of the pulse pattern and/or pulse program, and/or the like. In some embodiments, information relating to and/or for controlling the pulse generation of the pulse generator 102, 104 can be stored within the memory.
  • The pulse generator 102, 104 can include a charging module 306. In some embodiments, the charging module 306 can be configured to control and/or monitor the charging/recharging of the pulse generator 102, 104. In some embodiments, for example, the charging module 306 can include one or several features configured to receive energy for recharging the pulse generator 102, 104 such as, for example, one or several inductive coils/features that can interact with one or several inductive coils/features of the charger 116 to create an inductive coupling to thereby recharge the pulse generator 102, 104.
  • In some embodiments, the charging module 306 can include hardware and/or software configured to monitor the charging of the pulse generator 102, 104. In some embodiments, the hardware can include, for example, a charging coil configured to magnetically couple with a charging coil of the charger 116. In some embodiments, these features can be configured to monitor the temperature of one or several components of the pulse generator 102, 104, the rate of charge of the pulse generator 102, 104, the charge state of the pulse generator 102, 104, or the like. These features can include, for example, one or several resistors, thermistors, thermocouples, temperature sensors, current sensors, charge sensors, or the like. In some embodiments, the charging module 306 can be configured to monitor, for example, voltage of the energy storage features, current flowing through, for example, a shunt circuit configured to channel excess current, one or several temperatures of, for example, the energy storage features and/or of the pulse generator 102, 104, the presence of a detectable charging field, the charge state of the energy storage features, and/or the like. In some embodiments, the one or several parameters can be provided to the network interface 300, and communicated via network 114 to other components of the implantable neurostimulation system 100.
  • The pulse generator 102, 104 can include an energy storage device 308. The energy storage device 308, which can include the energy storage features, can be any device configured to store energy and can include, for example, one or several batteries, capacitors, fuel cells, or the like. In some embodiments, the energy storage device 308 can be configured to receive charging energy from the charging module 306.
  • With reference now to FIG. 4, a schematic illustration of one embodiment of the charger 116 is shown. In some embodiments, each of the components of the architecture of the charger 116 can be implemented using the processor, memory, and/or other hardware component of the charger 116. In some embodiments, the components of the architecture of the charger 116 can include software that interacts with the hardware of the charger 116 to achieve a desired outcome.
  • In some embodiments, the charger 116 can include, for example, a network interface 350, or alternatively, a communication module. The network interface 350, or alternatively, a communication module, can be configured to access the network 110 to allow communication between the charger 116 and the other components of the implantable neurostimulation system 100. In some embodiments, the network interface 350, or alternatively, a communication module, can include one or several antennas and software configured to control the one or several antennas to send information to and receive information from one or several of the other components of the implantable neurostimulation system 100.
  • In some embodiments, the charger 116 can include an indicator control module 352. In some embodiments, the indicator control module 352 can be configured to receive data relating to one or several parameters measured at the implantable pulse generator 104. The indicator control module 352 can use this information to determine whether charging would be improved by repositioning and/or reorienting of the charger 116 with respect to the implantable pulse generator 104. In some embodiments, this determination can include determining the relative effectiveness of the charging at a second, current position as compared to a first, previous position, and controlling the indicator to indicate increased charging effectiveness if the charging is more effective at the second position than and the first position, or similarly controlling the indicator to indicate the decreased charging effectiveness if the charging is less effective at the second position than at the first position. In some embodiments, this can include comparing the data received from the implantable pulse generator 104 to stored data to determine whether the charging effectiveness of the current position of the charger 116 is sufficient or insufficient. In the event that the charging effectiveness is insufficient, then the indicator control module 352 can be configured to control the indicator to indicate this insufficiency of the charging effectiveness. Similarly, in the event that the charging effectiveness is sufficient, then the indicator control module 352 can be configured to control the indicator to indicate this sufficiency of the charging effectiveness.
  • The charger 116 can include a charging module 354. The charging module 354 can be configured to control and/or monitor the charging of one or several of the pulse generators 102, 104. In some embodiments, for example, the charging module 354 can include one or several protocols that can request information from the one or several pulse generators 102, 104 at one or several times before, during, and after charging. This information can be received by the charger 116 from the pulse generator 102, 104 and can be used to control the generation of and/or properties of the charging field. In some embodiments, the charging module 354 can include one or several features configured to transmit energy charging coils that can magnetically couple with the charging coil of the pulse generator 102, 104 to thereby recharge the pulse generator 102, 104.
  • In some embodiments, the charging module 354 can be configured to power the charging coil of the charger 116 at any desired power level across a continuous power spectrum, and in some embodiments, the charging module 354 can be configured to power the charging coil of the charger 116 at one of several discrete power levels across a digitized power spectrum. In one such embodiment, for example, the charging module can be configured to power the charging coil of the charger 116 at one of 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 30, 50, 100, or any other or intermediate discrete power levels.
  • With reference now to FIG. 5, a perspective view of one embodiment of the implantable pulse generator 104 and the charger 116 is shown. The charger 116 includes an elongate body 140. The elongate body 140 can be configured to be placed against the body of the patient such as, for example, directly against the skin of the patient, and/or proximate to the skin of the patient such as, for example, against a piece of clothing or apparel worn by the patient.
  • In some embodiments, the charger 116 can include at least one retention feature 142 that can be configured to hold the elongate body 140 in a desired position against the patient's body. In some embodiments, the retention feature 142 can be, for example, a strap, a band, or the like. In one such embodiment, for example, in which the charger 116 is placed on a portion of the body, such as, for example, the neck, torso, or limb, including, one of a leg, a foot, an arm, and a hand, the retention feature 142 can secure the charger 116 to that portion of the body and can secure the position and orientation of the charger 116 with respect to that portion of the body. In some embodiments, the retention feature 142 can be configured to hold the elongate body 140 of the charger 116 in a constant orientation with respect to the body of the patient. In some embodiments, a constant orientation may include some variations of the orientation of the elongate body 140 described by an angle measured from a longitudinal axis of the elongate body 140 in a first position to the longitudinal axis of the elongate body 140 in a second position. In some embodiments, this angle can be, for example, 1 degree, 5 degrees, 10 degrees, 15 degrees, 20 degrees, 30 degrees, 40 degrees, or any other or intermediate angle.
  • The charger 116 can include a charge head 144. The charge head 144 can include one or several features to facilitate the charging of the implantable pulse generator 104. In some embodiments, these features can include, for example, the charge head charging coil that will be discussed at greater length below.
  • As seen in FIG. 5, the charge head 144 includes a rotatable mount 146. In some embodiments, the rotatable mount 146 can be connected to the charging coil of the charge head 144 and can be configured to allow the rotation of the charging coil. The rotatable mount can include one or several features that can facilitate the rotation/re-orientation of the rotatable mount. These can include, for example, a feature configured to engage with, for example, a key, a screwdriver, a wrench, or the like, one or several features configured to facilitate digital manipulation such as, for example, one or several knurls, grips, or the like, or any other feature. In some embodiments, for example, the rotatable mount 146 can be configured to allow the manipulation of the angular position of the charge head charging coil with respect to, for example, the longitudinal axis of the elongate member 140.
  • As further seen in FIG. 5, the implantable pulse generator 104 can be positioned with respect to the charger 116 to allow recharging of the implantable pulse generator 104. In some embodiments, the implantable pulse generator 104 can be positioned so as to be within an effective distance or range from the charger 116. In some embodiments, this distance can be such that recharging of the implantable pulse generator 104 is effective, and the distance can be, for example, within 10 cm of the charge head 144, 5 cm of the charge head 144, 4 cm of the charge head 144, 3 cm of the charge head 144, 2 cm of the charge head 144, 1 cm of the charge head 144, 0.5 cm of the charge head 144, 0.1 cm of the charge head 144, and/or any other or intermediate distance from the charge head 144. In some embodiments, the implantable pulse generator 104 can be positioned such that the implantable pulse generator 104 is directly below the charge head 144 of the charger 116. This positioning is indicated in FIG. 5 by axis 150. Alternatively, in some embodiments, implantable pulse generator 104 can be positioned so as to not be directly below the charge head 144 of charger 116.
  • With reference now to FIG. 6, a perspective view of one embodiment of a charging coil 250 that can be used in the implantable pulse generator 104 is shown. The charging coil 250 can comprise a variety of shapes and sizes and can be made of a variety of materials. The charging coil can comprise a solenoid. In some embodiments, the charging coil 250 can be sized and shaped so as to fit within the implantable pulse generator 104, and specifically inside of a housing of the implantable pulse generator 104. In one embodiment, for example, the charging coil can be positioned proximate to a surface of the housing such that no other components of the implantable pulse generator 104 are between the charging coil 250 and this surface. In some embodiments, the implantable pulse generator 104 can be implanted such that this surface is proximate to the skin of the patient and/or the relatively more proximate to the skin of the patient than other portions of the implantable pulse generator.
  • In some embodiments, the charging coil 250 can be configured to magnetically couple with features of the charger 116 such as, for example, a charging coil of the charger 116 to recharge the one or several energy storage features of the implantable pulse generator 104.
  • In some embodiments, and to facilitate the magnetic coupling of the charging coil 250 of the implantable pulse generator 104 with the charging coil of the charger 116, the charging coil 250 of the implantable pulse generator 104 can have a high Q factor. In some embodiments, for example, the Q factor of the charging coil 250 can be, for example, at least 10, at least 20, at least 30, at least 40, at least 50, at least 60, at least 70, at least 80, at least 100, at least 120, at least 200, and/or any other or intermediate value.
  • The charging coil 250 can include a core 252. The core 252 can comprise a variety of shapes and sizes and can be made from a variety of materials. In some embodiments, the core 252 can be sized and shaped to facilitate the wrapping of one or several wires around the core 252 and/or the core 252 can be sized and shaped to achieve and/or facilitate in achieving a desired Q factor for the charging coil 250. In some embodiments, the core 252 can comprise a ferritic core, and in some embodiments, the core 252 can comprise a soft ferritic core.
  • In some embodiments, and as shown in FIG. 6, the core 252 can comprise an elongate member, and can specifically comprise an elongate cylindrical member that can have, a distal, first end 254 and a proximal, second end 256. As seem in FIG. 6, an axis 255, which can be a longitudinal axis, can extend along the centerline of the core 252 between the first end 254 and the second end 256, and the length of the core 252 can be measured and/or defined with respect to this axis 255. In some embodiments, the length of the core 252 can be, for example, approximately 0.1 inches, 0.2 inches, 0.3 inches, 0.4 inches, 0.5 inches, 0.6 inches, 0.7 inches, 0.8 inches, 0.9 inches, 1 inch, 1.5 inches, 2 inches, 5 inches, and/or any other or intermediate length. In some embodiments, the core can have a radius, measured from the axis 255 of approximately 0.01 inches, 0.02 inches, 0.03 inches, 0.04 inches, 0.05 inches, 0.06 inches, 0.07 inches, 0.08 inches, 0.09 inches, 0.098 inches, 0.1 inches, 0.15 inches, 0.2 inches, 0.5 inches, and/or any other or intermediate radius.
  • The charging coil 250 can further include a plurality of windings 258 around the core 252. The windings 258 can, together with the core 252, allow charging coil 250 to magnetically couple with charger 116 to recharge the energy storage features of the implantable pulse generator 104. In some embodiments, the windings 258 can be made by looping wire 260, which wire 260 can be any type of wire including, for example, a litz wire, and which can be any material having desired properties, and specifically can be a metal wire, one or more times around core 252. In some embodiments, the windings 258 can comprise any desired number of loops of wire, and can, for example, comprise 2 loops, 5 loops, 10 loops, 15 loops, 20 loops, 25 loops, 29 loops, 30 loops, 35 loops, 40 loops, 50 loops 100 loops, 200 loops, 1,000 loops, and/or any other or intermediate number of loops.
  • In some embodiments, and as depicted in FIG. 6, the wire 260 can be looped around core 252 so as to create a plurality of layers of loops at different radial distances from axis 255. As specifically depicted in FIG. 6, a first layer of loops 257 is positioned so as to contact core 252 and to be a first radial distance from axis 255, and a second layer of loops 259 is positioned so as to contact the first layer of loops 257 and be a second radial distance from axis 255. In some embodiments, the first layer of loops 257 can comprise 1 loop, 2 loops, 5 loops, 10 loops, 12 loops, 13 loops, 15 loops, 16 loops, 18 loops, 20 loops, 30 loops, 50 loops, 100 loops, and/or any other or intermediate number of loops, and the second layer of loops 259 can comprise 1 loop, 2 loops, 5 loops, 10 loops, 12 loops, 13 loops, 15 loops, 16 loops, 18 loops, 20 loops, 30 loops, 50 loops, 100 loops, and/or any other or intermediate number of loops. In the embodiment depicted in FIG. 6, the first radial distance is less than the second radial distance, and thus the radius of the loops of the first layer of loops 257 is less than the radius of the loops of the second layer of loops 259.
  • The charging coil 250 can include a capacitor 262. The capacitor 262 can comprise a variety of shapes and sizes and can have a variety of electrical properties. In some embodiments, for example, the capacitor 262 can comprise a high Q capacitor and in some embodiments, can be a high Q COG capacitor.
  • The capacitor 262 can, in connection with windings 258, create a tank circuit. In some embodiments, this tank circuit can be a high Q tank circuit. In some embodiments, for example, the Q factor of the high Q tank circuit can be, for example, at least 10, at least 20, at least 30, at least 40, at least 50, at least 60, at least 70, at least 80, at least 100, at least 120, at least 200, and/or any other or intermediate value. The tank circuit can increase the Q factor of the charging coil 250. This Q factor of the charging coil 250 increases as the distance between the windings 258 and the capacitor 262 decreases. Thus, in some embodiments, the capacitor can, and as shown in FIG. 6, be placed on the windings 258, and in some embodiments, the capacitor 262 can be placed in proximity to the windings 258 such as, for example, a distance of less than 5 cm from the windings 258, less than 4 cm from the windings 258, less than 3 cm from the windings 258, less than 2 cm from the windings 258, less than 1 cm from the windings 258, less than 0.5 cm from the windings 258, less than 0.1 cm from the windings 258, and/or any other or intermediate distance from the windings 258.
  • The charging coil 250 can include a first lead 264 and a second lead 266. The first and second leads 264, 266 can be used to electrically connect the charging coil 250 to other features and/or components of the implantable pulse generator 104. In some embodiments, the leads 264, 266 can extend from the capacitor 262, and in some embodiments, the leads 264, 266 can extend from the windings 258.
  • With reference now to FIG. 7, a perspective view of one embodiment of a charging coil 350 that can be used in a charger is shown. The charging coil 350 can comprise a variety of shapes and sizes and can be made of a variety of materials. In some embodiments, the charging coil 350 can comprise a solenoid. In some embodiments, the charging coil 350 can be sized and shaped so as to fit within the charger 116, and specifically within the charge head 144 of the charger 116. In some embodiments, the charging coil 350 can be configured to magnetically couple with features of the implantable pulse generator 104 such as, for example, the charging coil 250 of the implantable pulse generator 104 to recharge the one or several energy storage features of the implantable pulse generator 104.
  • In some embodiments, and to facilitate the magnetic coupling of the charging coil 350 of the charger 116 with the charging coil 250 of the implantable pulse generator 104, the charging coil 350 of the charger 116 can have a high Q factor. In some embodiments, for example, the Q factor of the charging coil 350 can be, for example, at least 50, at least 100, at least 150, at least 200, at least 250, at least 250, at least 350, at least 350, at least 450, at least 500, at least 1,000, and/or any other or intermediate value.
  • The charging coil 350 can include a core 352. The core 352 can comprise a variety of shapes and sizes and can be made from a variety of materials. In some embodiments, the core 352 can be sized and shaped to facilitate the wrapping of one or several wires around the core 352 and/or the core 352 can be sized and shaped to achieve and/or facilitate in achieving a desired Q factor for the charging coil 350. In some embodiments, the core 352 can comprise a metal core and/or a ferritic core, and in some embodiments, the core 352 can comprise a soft ferritic core.
  • In some embodiments, and as shown in FIG. 7, the core 352 can comprise an elongate member, and can specifically comprise an elongate rectangular member that can have first end 354 and a second end 356. As seem in FIG. 7, an axis 357, which can be a longitudinal axis, can extend along the centerline of the core 352 between the first end 354 and the second end 356, and the length of the core 352 can be measured and/or defined with respect to this axis 357.
  • The core 352 can comprise a first foot 358 and/or a second foot 360. In some embodiments, the first foot 358 can be located at and/or proximate to the first end 354 and the second foot 360 can be located at and/or proximate to the second end 356. In some embodiments, the first and second feet 358, 360 extend away from the axis 357, and in some embodiments, the first and second feet 358, 360 extend in the same direction and to the same extent away from the axis 357. In some embodiments, the first and second feet 358, 360 can be configured for sliding engagement with other components of the charger 116, and specifically with other components of the charge head 144. The first and second feet 358, 360 can, in some embodiments, be made of the same material as the core 352, and in some embodiments, the feet 358, 360 can be made of a different material than the core 352.
  • The charging coil 350 can further include a plurality of windings 362 around the core 352. The windings 362 can, together with the core 352 allow charging coil 350 to magnetically couple with implantable pulse generator 104 to recharge the energy storage features of the implantable pulse generator 104. In some embodiments, the windings 362 can be made by looping wire 364, which wire 364 can be any type of wire including, for example, a litz wire, and which can be any material having desired properties, and specifically can be a metal wire, one or more times around core 352. In some embodiments, the windings 362 can comprise any desired number of loops of wire, and can, for example, comprise 2 loops, 5 loops, 10 loops, 15 loops, 20 loops, 25 loops, 29 loops, 30 loops, 35 loops, 40 loops, 50 loops 100 loops, 200 loops, 1,000 loops, and/or any other or intermediate number of loops. In some embodiments, the windings 362 can be exposed, and in some embodiments, the windings 362 can be covered by, for example, tape such as a mylar tape.
  • In some embodiments, although not depicted in FIG. 7, the wire 364 can be looped around core 352 so as to create a plurality of layers of loops at different radial distances from axis 357. Specifically a first layer of loops can be positioned so as to contact core 352 and to be a first radial distance from axis 357, and a second layer of loops can be positioned so as to contact the first layer of loops and be a second radial distance from axis 357. In such an embodiment, the first radial distance can be less than the second radial distance, and thus the volume encompassed by the loops of the first layer of loops can be less than the volume encompassed by the loops of the second layer of loops.
  • The charging coil 350 can include a first lead 366 and a second lead 368. The first and second leads 366, 368 can be used to electrically connect the charging coil 350 to other features and/or components of the charger 116. In some embodiments, the leads 366, 368 can be the ends of wire 364, and in some embodiments, the leads 366, 368 can be connected to the ends of wire 364.
  • With reference now to FIG. 8, a flowchart illustrating one embodiment of a process 500 for providing an alignment indicator for a charger 116 is shown. The process 500 can be performed by one or several of the components of the implantable neurostimulation system 100, and in some embodiments, can be performed by the charger 116. In some embodiments, the process 500 can be performed by some or all of the components of the charger 116 including, for example, the network interface 350, the indicator control module 352, and/or the charging module 354. The process 500 can be performed as part of recharging, and can be specifically performed to facilitate in the positioning and/or orienting of the charger 116 with respect to the implantable pulse generator 104. The process 500 can facilitate in positioning and/or orienting of the charger 116 through the control of one or several indicators which can provide information to the user regarding the effectiveness of a charging field at the implantable pulse generator 104, which effectiveness can vary, at least in part, based on the positioning and/or orienting of the charger 116 with respect to the implantable pulse generator 104.
  • The process 500 begins at block 502 wherein the charging coil of the charger 116 is operated at a first power level. In some embodiments, this first power level can describe the power of the charging field generated by the charging coil of the charger 116. This first power level can be obtained by controlling, for example, one or both of the voltage of the charging coil of the charger 116 and the current of the charging coil of the charger 116. In some embodiments, this first power level can be a zero power level, in which no charging field is generated, and in some embodiments, this first power level can be a non-zero power level, in which a charging field is generated. In some embodiments, the charging coil can be operated at the first level based on controls received from, for example, the charging module 354 of the charger 116.
  • After the charging coil is set to the first level, the process 500 proceeds to block 504, wherein a signal is received from a charged device. In some embodiments, the signal can be received via the network interface 350 of the charger 116. The signal can be received from the charged device, which can be the implantable pulse generator 104 via network 110, and specifically, can be received from the network interface 300 of the implantable pulse generator 104. In some embodiments, the signal can be analyzed by the processor of the charger 116. In some embodiments, the signal can be received at a discrete time, and in some embodiments, the signal can be repeatedly and/or continuously received during the performing of steps 506-514. In some such embodiments, process 500 can become a dynamic process in that many of steps 506-514 are simultaneously performed as the signal is repeatedly and/or continuously received.
  • The signal can include information relating to a parameter of the implantable pulse generator 104, and specifically to a parameter identifying the effect of the charging field on the implantable pulse generator 104. This parameter can, for example, identify the voltage induced by the charging field at the charging coil of the implantable pulse generator 104, identify the current induced by the charging field at the charging coil of the implantable pulse generator 104, identify a temperature of the implantable pulse generator 104, of a component of the implantable pulse generator 104, or of surrounding tissue, identify a charge state of the energy storage features of the implantable pulse generator 104, or the like.
  • After the signal received from the charged device has been received, the process 500 proceeds to block 506, wherein the signal is compared to one or several charging criteria. In some embodiments, these criteria can relate to whether and to what degree the charging field is charging the energy storage feature of the implantable pulse generator 104. These criteria can relate to, for example, whether the charging field is detectable at the implantable pulse generator 104, the voltage induced by the charging field in the charging coil of the implantable pulse generator 104, the current induced by the charging field in the charging coil of the implantable pulse generator 104, the charge state of the energy storage features of the implantable pulse generator 104, the temperature of the implantable pulse generator 104 or components thereof, or the like. In some embodiments, the comparison of the signal to the criteria can include a determination of whether the charging field allows safe charging of the implantable pulse generator 104 and the degree to which the charging field allows effective charging of the implantable pulse generator 104 such as, for example, whether the measured parameter (induced voltage, induced current, temperature, temp delta, etc. . . . falls within an acceptable range).
  • After the signal has been compared to the charging criteria, the process 500 proceeds to decision state 508, wherein it is determined if the charge coil level should be adjusted. In some embodiments, this can include, for example, increasing the level of the charging field if the charging field strength is inadequate, decreasing the level of the charging field if the charging field strength is too high, or the like. In some embodiments, this can further include determining that adjustment to the position and/or orientation of the charger 116 with respect to the implantable pulse generator 104 is desirable to increase the effectiveness of the charging field.
  • If it is determined that the coil level is to be adjusted, then the process 500 proceeds to block 510, wherein the coil level is adjusted. In some embodiments, this can include, for example, incrementing or decrementing the coil level to the next one of several discrete levels, or increasing the coil level by a predetermined value.
  • Returning again to decision state 508, if it is determined that the coil level should not be adjusted, then the process 500 proceeds to block 512, wherein the indicator, which can be an alignment indicator is activated. In some embodiments, in which the signal is repeatedly and/or continuously received, the indicator can be controlled to reflect the change of charging field effectiveness as represented by the signal over a period of time. Thus, in such an embodiment, if the effectiveness of the charging field increases, which can be due to, for example, the repositioning and/or reorienting of the charger 116, the indicator can be controlled to reflect this increased effectiveness. Similarly, if the effectiveness of the charging field decreases, which can be due to, for example, the repositioning and/or reorienting of the charger 116, the indicator can be controlled to reflect this decreased effectiveness.
  • With reference now to FIG. 9, a flowchart illustrating one embodiment of a process 600 for providing an alignment indicator for a charger based on detected variations in measured voltage and current is shown. The process 600 can be performed by one or several of the components of the implantable neurostimulation system 100, and in some embodiments, can be performed by the charger 116. In some embodiments, the process 600 can be performed by some or all of the components of the charger 116 including, for example, the network interface 350, the indicator control module 352, and/or the charging module 354. The process 600 can be performed as part of recharging, and can be specifically performed to facilitate in the positioning of the charger 116 with respect to the implantable pulse generator 104. The process 600 can facilitate in positioning of the charger 116 through the control of one or several indicators which can provide information to the user regarding the effectiveness of a charging field at the implantable pulse generator 104, which effectiveness can vary, at least in part, based on the positioning of the charger 116 with respect to the implantable pulse generator 104.
  • The process 600 begins at block 602 wherein the charger 116 is powered. In some embodiments, the powering of the charger 116 can correspond to a user turning the charger 116 on, or to selecting a charging mode of operation. After the charger is powered, the process 600 proceeds to block 604, wherein the charging coil is set to and/or operated at an initial level. In some embodiments, this initial level can describe the power of the charging field generated by the charging coil of the charger 116. This initial level can be obtained by controlling, for example, one or both of the voltage of the charging coil of the charger 116 and the current of the charging coil of the charger 116. In some embodiments, this initial level can be a zero power level, in which no charging field is generated, and in some embodiments, this initial level can be a non-zero power level, in which a charging field is generated. In some embodiments, the charging coil can be operated at the initial level based on controls received from, for example, the charging module 354 of the charger 116.
  • After the charging coil is set to an initial level, the process 600 proceeds to block 606, wherein communication between the implantable pulse generator 104 and the charger 116 is established. In some embodiments, this can include, for example, the charger 116 initiating communication by sending a query to the implantable pulse generator 104, and the implantable pulse generator 104 responding to the query of the charger 116.
  • After communication between the implantable pulse generator 104 and the charger 116 has been established, process 600 proceeds to decision state 608, wherein the communication link between the implantable pulse generator 104 and the charger is confirmed. If it is determined that communication has not been established, then the process 600 proceeds to block 610, wherein the event is logged in, for example, the memory of the charger, and the process 600 then proceeds to block 612, wherein the failure is indicated. In some embodiments, this indication can identify a specific failure, in this case, for example, a failure to establish communication between the implantable pulse generator 104 and the charger 116 is indicated, and in some embodiments, the indication of the failure can be generic.
  • Returning again to decision state 608, if it is determined that communication has been established, then the process 600 proceeds to block 614, wherein the indicators are activated. In some embodiments, this can include powering the indicators. After the indicators have been activated, the process 600 proceeds to block 616 wherein the coil level of the charging coil of the charger 116 is increased. After the coil level of the charging coil of the charger 116 has been increased, the process 600 proceeds to decision state 618, wherein it is determined if the charging coil is operating at its maximum level, and specifically if a preset upper limit has been reached. This determination can be made by identifying the present level of the charging coil and comparing the present level of the charging coil to the maximum possible level of the charging coil. If the present level of the charging coil is less than the maximum level of the charging coil, then the charging coil is not operating at its maximum level. Alternatively, if the present level of the charging coil is equal to the maximum level, then the charging coil is operating at the maximum level.
  • If it is determined that the charging coil is not operating at its maximum level, then the process 600 proceeds to decision state 620, wherein it is determined if the charging field is detected at the charged device, and specifically, if the charging field is detectable at the implantable pulse generator 104. In some embodiments, this determination can be made based on information that can be received, via a signal or via a communication from the implantable pulse generator 104. In some embodiments, this information can include data relating to one or several parameters, identifying the effect of the charging field on the implantable pulse generator 104. If it is determined, based on this data, that the charging field is not detectable at the charged device, then the process 600 returns to block 616, and proceeds as outlined above.
  • If it is determined that the charging field is detected at the charged device, then the process 600 proceeds to decision state 622, wherein it is determined if the charging field, as measured at the implantable pulse generator, is too strong, or alternatively, if the charging field is at an acceptable strength level. In some embodiments, an acceptable strength level can be a level at which the implantable pulse generator is capable of recharging the energy storage features. In some embodiments, this can be determined by comparing a current property of the energy storage features, such as, for example, the voltage of the energy storage features with a parameter of the charging field, such as, for example, the voltage induced by the charging field at the charging coil of the implantable pulse generator 104. In some embodiments, an acceptable strength level can be a level at which the implantable pulse generator is capable or recharging the energy storage features and an acceptable rate or within an acceptable time range.
  • In some embodiments, the acceptability of the strength level of the charging field can be determined by determining whether the charging field is causing excessive heating of the implantable pulse generator 104 or one or several components thereof, or if the strength of the charging field is resulting in the induction of undesirable current levels at the charging coil of the implantable pulse generator 104. In one embodiment, for example, this can be determined by measuring the current passing through the shunt circuit. In some embodiments, the shunt circuit can be any circuit that can dispose of or channel excess current generated by the charging field. If this current exceeds a threshold value, then the strength of the charging field may be too high. Similarly, if the temperature of the implantable pulse generator, or one or several components thereof exceeds a threshold temperature, then the strength of the charging field may be too high.
  • If it is determined that the charging field is too strong, then the process 600 proceeds to block 624, wherein the coil level is decreased. After the coil level has been decreased, the process 600 returns to decision state 622 and proceeds as outlined above.
  • Returning again to decision state 618, if it is determined that the charging coil has reached its maximum level, or returning again to decision state 622, if it is determined that the charging field is not too strong, then process 600 proceeds to decision state 626, wherein it is determined if the charging field is detected at the charged device, and specifically, if the charging field is detectable at the implantable pulse generator 104. In some embodiments, this decision state can replicate the determination of decision state 620. In such an embodiment, this determination can be made based on information that can be received, via a signal or via a communication from the implantable pulse generator 104. In some embodiments, this information can include data relating to one or several parameters, identifying the effect of the charging field on the implantable pulse generator 104. If it is determined, based on this data, that the charging field is not detected, then the process 600 proceeds to block 610 wherein the event is logged in, for example, the memory of the charger, and the process 600 then proceeds to block 612, wherein the failure is indicated. In some embodiments, this indication can identify a specific failure, in this case, for example, a failure create a charging field detectable at the implantable pulse generator 104 is indicated, and in some embodiments, the indication of the failure can be generic.
  • Returning again to decision state 626, if it is determined that the charging field is detected, then the process 600 proceeds to decision state 628 wherein it is determined if there is a change in the voltage induced by the charging field at the charging coil of the implantable pulse generator 104 The determination of decision state 628 can be based on data contained in one or several signals received from the implantable pulse generator 104 during the performance of the process 600.
  • In some embodiments, decision state 628 can, in connection with decision state 630 be used to determine whether the effectiveness of the charging field at the charging coil of the implantable pulse generator 104 is increasing or decreasing. In some embodiments, these changes to the effectiveness of the charge coil can be caused by the movement and/or repositioning and/or reorienting of the charger 116 with respect to the implantable pulse generator 104. In some embodiments the advancement of process 600 to decision state 628 can be delayed until a predetermined time interval has passed, and can be preceded by the activation of an indicator directing the user to reposition the charger 116. In such an embodiment, this can result in comparing the effectiveness of the charging field at a first time to the effectiveness of the charging field at a second time. In some embodiments, this can result in determining an effectiveness of the charging field at a first time based on a first signal, and determining the effectiveness of the charging field at a second time based on a second signal. In some embodiments, this can be repeated until a desired and/or maximum effectiveness level is identified, and in some embodiments, this can be repeated until a pre-determined amount of time has passed.
  • If it is determined that there is no change in the voltage induced by the charging field at the charging coil of the implantable pulse generator 104, then the process 600 proceeds to decisions state 630, wherein it is determined if there is a change in the current induced by the charging field at the charging coil of the implantable pulse generator 104. In some embodiments, this change in current induced by the charging field at the charging coil of the implantable pulse generator 104 can be based on data received at the charger 116 from the implantable pulse generator 104, which data can identify, for example, changes to the current flowing through the shunt circuit of the implantable pulse generator 104.
  • If it is determined that the current induced by the charging field at the charging coil of the implantable pulse generator 104 is higher at decisions state 630, as compared to the previous current induced by the charging field at the charging coil of the implantable pulse generator, or if it is determined that the voltage induced by the charging field at the charging coil of the implantable pulse generator 104 is higher at decision state 628, as compared to the previous voltage induced by the charging field at the charging coil of the implantable pulse generator, then the process 600 proceeds to block 632, wherein the indicators are controlled to indicate the increased voltage or current. In some embodiments, this can likewise indicate an increased effectiveness of the charging field at the charging coil of the implantable pulse generator 104.
  • Returning again to decision state 630, if it is determined that the current induced by the charging field at the charging coil of the implantable pulse generator 104 is lower at decisions state 530, as compared to the previous current induced by the charging field at the charging coil of the implantable pulse generator, or if it is determined that the voltage induced by the charging field at the charging coil of the implantable pulse generator 104 is lower at decision state 628, as compared to the previous voltage induced by the charging field at the charging coil of the implantable pulse generator, then the process 600 proceeds to block 634, wherein the indicators are controlled to indicate the decreased voltage or current. In some embodiments, this can likewise indicate an decreased effectiveness of the charging field at the charging coil of the implantable pulse generator 104.
  • After the indicators have been adjusted as in either block 632 or block 634, or returning again to decision state 630, if it is determined that there has been no change in the current induced by the charging field, the process 600 proceeds to decision state 636, wherein it is determined whether to continue process 600. In some embodiments, this can include, for example, determining whether a predetermined amount of time has passed, after which the process 600 should be terminated. In some embodiments, decision state 636 can include determining whether the effectiveness of the charging field has reached a maximum value, or exceeded an effectiveness threshold. If it is determined that process 600 should not be continued, then process 600 proceeds to block 638 and terminates. If it is determined that process 600 should continue, process 600 returns to decision state 628 and proceeds as outlined above. In some embodiments, the process 600 can be performed and/or repeated at any desired rate. In some embodiments, for example, process 600 can be performed and/or repeated 1,000 times per second, 500 times per second, 200 times per second, 100 times per second, 50 times per second, 25 times per second, 10 times per second, 5 times per second, 2 times per second, 1 times per second, 30 times per minutes, 20 times per minute, 10 times per minute, 5 times per minute, 1 time per minute, 30 times per hour, 20 times per hour, 10 times per hour, 5 times per hour, 1 time per hour, and/or any other or intermediate rate.
  • With reference now to FIG. 10, a flowchart illustrating one embodiment of a process 700 in which movement of a charger is detected during the charging is shown. In some embodiments, the process 700 can be performed during the charging of the implantable pulse generator 104 to detect movement of the charger 116 with respect to the implantable pulse generator 104. The process can be performed by the implantable pulse generator 104, the charger 116, and/or any other components of the implantable neurostimulation system 100. The process 700 can be performed during the charging of the implantable pulse generator 104. In some embodiments, the process 700 can be continuously performed during the charging of the implantable pulse generator 104, and in some embodiments, the process 700 can be periodically performed during the charging of the implantable pulse generator.
  • The process 700 begins at block 702, wherein charge data is received by the charger 116 from a charged device, which can be, for example, the implantable pulse generator 104. In some embodiments, this charge data can include information identifying the charge state of the energy storage features of the implantable pulse generator 104, and in some embodiments, this information can identify whether the charging of the implantable pulse generator 104 is complete. This information can be received by the network interface 350 of the implantable pulse generator 104 from the network interface 300 of the implantable pulse generator 104.
  • After the charge data has been received, the process 700 proceeds to decision state 704, wherein it is determined if the charging of the implantable pulse generator 104 is complete. In some embodiments, this determination can be made based on the charge data received in block 702, which data can include information identifying the charge state of the energy storage features of the implantable pulse generator 104, and/or whether the charging of the implantable pulse generator 104 is complete. If it is determined that the charging is complete, then process 700 proceeds to bock 706, wherein the charging coil of the charger 116 is turned off.
  • Returning again to decision state 704, if it is determined that charging is not complete, process 700 proceeds to decision state 708, wherein temperature data contained in the received charge data is evaluated to determine if the temperature of the implantable pulse generator 104 or component thereof is too high. In some embodiments, the temperature data can identify the temperature of the implantable pulse generator 104 and/or of one or several components of the implantable pulse generator 104. The temperature data can be evaluated to determine whether the temperature of the implantable pulse generator 104, or of one or several components thereof, is too high. In some embodiments, this can include determining if the temperature of the implantable pulse generator 104 or of one or several components thereof is higher than a threshold value, which threshold value can be stored in memory of the implantable neurostimulation system 100. In some embodiments, the process 700 can, in decision state 708, determine if the temperature of the implantable pulse generator 104 or a component thereof is above a first threshold, which can be indicative of a temperature that is too high, but is at dangerous levels.
  • If it is determined that the temperature is too high, then the process 700 proceeds to decision state 710, wherein it is determined if the temperature of the implantable pulse generator 104 or component thereof is an extreme temperature. This determination can be based on temperature data received as part of the charge data in block 702.
  • In some embodiments, an extreme temperature can be a temperature at a dangerous level. In some embodiments, the difference between a temperature that is too high and an extreme temperature can be found in how each temperature is resolved. Thus, in some embodiments, a temperature that is too high may be resolved by decreasing the level of the charging field, whereas an extreme temperature is resolved by stopping charging.
  • If it is determined that the implantable pulse generator 104 or component thereof has reached an extreme temperature, then the process 700 proceeds to block 712, wherein the charging coil of the charger 116 is turned off. If it is determined that the implantable pulse generator 104 or component thereof has not reached an extreme temperature, then the process proceeds to decision state 714, wherein it is determined if the charging coil of the charger 116 is operating at its minimum level, which can be, for example, a preset lower limit. This determination can be made by identifying the present level of the charging coil and comparing the present level of the charging coil to the minimum possible level of the charging coil. If the present level of the charging coil is greater than the minimum level of the charging coil, then the charging coil is not operating at its minimum level. Alternatively, if the present level of the charging coil is equal to the minimum level, then the charging coil is operating at the minimum level.
  • If it is determined that the charging coil of the charger 116 is operating at its minimum level, then the process 700 proceeds to block 712, wherein the charging coil of the charger 116 is turned off. If it is determined that the charging coil of the charger 116 is not operating at its minimum level, then the process 700 proceeds to decision state 716, wherein it is determined if the implantable pulse generator 104 is charging. In some embodiments, this determination can comprise a binary determination of whether charging is occurring or not, and in some embodiments, this determination can comprise a qualification of the degree to which charging is occurring. In one specific embodiment, decision state 716 can include determining if charging is occurring and qualifying the degree to which charging is occurring. In this embodiment, decision state 716 can further include estimating the degree to which the coil level of the charging coil of the charger 116 can be decreased without ending charging and/or the degree to which a decrease in the coil level of the charging coil of the charger will impact the effectiveness of the charging field. If it is determined that the implantable pulse generator 104 is not charging, then the process 700 proceeds to block 712, wherein the charging coil of the charger 116 is turned off.
  • If it is determined that the implantable pulse generator 104 is charging, then the process 700 proceeds to block 718, wherein the level of the charging coil of the charger 116 is decreased. After the level of the charging coil of the charger 116 has been decreased, the process 700 proceeds to block 712, wherein the charging coil of the charger 116 is turned off.
  • Returning again to decision state 708, if it is determined that the temperature of the implantable pulse generator 104 or component thereof is not too high, then the process 700 proceeds to decision state 720, wherein it is determined if the implantable pulse generator 104 is charging. In some embodiments, this determination can comprise a binary determination of whether charging is occurring or not, and in some embodiments, this determination can comprise a qualification of the degree to which charging is occurring.
  • In some embodiments, the determination of decision state 720 can comprise a binary determination of whether charging is occurring or not, and in some embodiments, this determination can comprise a qualification of the degree to which charging is occurring. In one specific embodiment, decision state 716 can include determining if charging is occurring and qualifying the degree to which charging is occurring. In this embodiment, decision state 716 can further include estimating the degree to which the coil level of the charging coil of the charger 116 can be decreased without ending charging and/or the degree to which a decrease in the coil level of the charging coil of the charger will impact the effectiveness of the charging field.
  • If it is determined that the implantable pulse generator 104 is charging, then the process 700 returns to block 702 and proceeds as outlined above. In some embodiments, the return to block 702 can further include waiting a predetermined period of time before additional charge data is received, or before received charge data is analyzed.
  • If it is determined that the implantable pulse generator 104 is not charging, then the process 700 proceeds to decision state 722, wherein it is determined if the charging coil of the charger 116 is operating at its maximum level, which can be, for example, a preset upper limit. This determination can be made by identifying the present level of the charging coil and comparing the present level of the charging coil to the maximum possible level of the charging coil. If the present level of the charging coil is less than the maximum level of the charging coil, then the charging coil is not operating at its maximum level. Alternatively, if the present level of the charging coil is equal to the maximum level, then the charging coil is operating at the maximum level.
  • If it is determined that the charger 116 is operating at the maximum coil level, then process 700 proceeds to block 724, wherein the indicators are controlled to direct the user to reposition the charger 116 and/or to indicate the charger 116 has moved from its original position. After the indicators have been controlled, the process 700 can return to block 702 and proceed as outlined above. In some embodiments, and before returning to block 702, the process 700 proceeds to decision state 628 of process 600 in FIG. 9, and proceeds as outlined therein. In such an embodiment, after termination is indicated in block 638, process 700 would then return to block 702 and proceed as outlined above.
  • Returning now to decision state 722, if it is determined that the charge level of the charging coil of the charger 116 is not operating at a maximum level, the process 700 proceeds to block 726, wherein the coil level of the charging coil of the charger 116 is increased. After the coil level of the charging coil of the charger 116 has been increased, the process 700 proceeds to block 724 and continues as outlined above.
  • In the foregoing specification, the invention is described with reference to specific embodiments thereof, but those skilled in the art will recognize that the invention is not limited thereto. Various features and aspects of the above-described invention can be used individually or jointly. Further, the invention can be utilized in any number of environments and applications beyond those described herein without departing from the broader spirit and scope of the specification. The specification and drawings are, accordingly, to be regarded as illustrative rather than restrictive. It will be recognized that the terms “comprising,” “including,” and “having,” as used herein, are specifically intended to be read as open-ended terms of art.

Claims (27)

    What is claimed is:
  1. 1. A charger comprising:
    a charging coil configured to magnetically couple with a corresponding charging coil of an implantable device,
    an indicator configured to identify the effectiveness of a charging field created between the charging coil of the charger and the corresponding charging coil of the implantable device; and
    a processor configured to:
    receive a signal from the implantable device at a first time;
    direct the indicator to identify a first effectiveness level based on a determined effectiveness of the charging field at the first time;
    receive a signal from the implantable device at a second time; and
    direct the indicator to identify a second effectiveness level based on a determined effectiveness of the charging field at the second time.
  2. 2. The charger of claim 1, wherein the indicator comprises one of a visual and an audible indicator.
  3. 3. The charger of claim 2, wherein the visual indicator comprises one of a light and a display.
  4. 4. The charger of claim 1, wherein the processor determines the effectiveness of the charging field based on at least one of a voltage induced by the charging field at the charging coil of the implantable device and a current induced by the charging field at the charging coil of the implantable device.
  5. 5. The charger of claim 1, wherein the processor is further configured to direct the charging coil of the charger to generate a charging field.
  6. 6. The charger of claim 5, wherein the processor is configured to optimize the charging field before the first time.
  7. 7. The charger of claim 6, wherein the optimizing of the charging field comprises:
    determining if the charging field is inducing a voltage at the charging coil of the implantable device that is greater than the voltage of an energy storage device of the implantable device.
  8. 8. The charger of claim 7, wherein optimizing the charging field further comprises:
    increasing the voltage on the charging coil of the charger if the charge filed is inducing a voltage at the charging coil of the implantable device that is less than the voltage of an energy storage device of the implantable device.
  9. 9. The charger of claim 1, wherein the effectiveness of the charging field at the second time is greater than the effectiveness of the charging field at the first time.
  10. 10. The charger of claim 1, wherein the effectiveness of the charging field at the second time is less than the effectiveness of the charging field at the first time.
  11. 11. A method of directing alignment of a charger with an implantable device, the method comprising:
    applying a first voltage to a charging coil of a charger, wherein the application of the first voltage to the charging coil of the charger generates a charging field;
    receiving a first signal from the implantable device at a first time, wherein the first signal includes information identifying a parameter of an effect of the charging field on the implantable device at the first time;
    directing an indicator to identify a first effectiveness level;
    receiving a second signal from the implantable device at a second time, wherein the second signal includes information identifying the parameter of the effect of the charging field on the implantable device at the second time; and
    directing the indicator to identify a second effectiveness level.
  12. 12. The method of claim 11, wherein directing the indicator to identify the second effectiveness level comprises directing the identifier to identify an increased effectiveness when the second effectiveness level is greater than the first effectiveness level.
  13. 13. The method of claim 11, wherein directing the indicator to identify the second effectiveness level comprises directing the identifier to identify a decreased effectiveness when the second effectiveness level is less than the first effectiveness level.
  14. 14. The method of claim 11, further comprising:
    receiving a third signal from the implantable device at a third time, wherein the third signal includes information identifying a parameter of an effect of the charging field on the implantable device at the third time; and
    optimizing the voltage applied to the charging coil of the charger based on the third signal.
  15. 15. The method of claim 14, wherein the receipt of the third signal at the third time precedes the receipt of the first signal at the first time.
  16. 16. The method of claim 11, further comprising:
    determining the effectiveness of the charging field at the first time; and
    determining the effectiveness of the charging field at the second time.
  17. 17. The method of claim 16, wherein determining the effectiveness of the charging field is based on at least one of a voltage induced by the charging field at the charging coil of the implantable device and a current induced by the charging field at the charging coil of the implantable device.
  18. 18. The method of claim 16, wherein the effectiveness of the charging field is determined by comparing the parameter of the effect of the charging field on the implantable device with a threshold value.
  19. 19. The method of claim 18, wherein the charging field is effective if the parameter of the effect of the charging field on the implantable device is greater than the threshold value.
  20. 20. A system for delivering power to an implantable device, the system comprising:
    an implantable device, wherein the implantable device comprises:
    a network interface; and
    a charging module comprising a first charging coil, wherein the charging module is configured to monitor at least one charge parameter; and
    a charger comprising:
    a network interface configured to receive the at least one charge parameter from the implantable device;
    a charging module comprising a second charging coil, wherein the charging module is configured to control the voltage of the second charging coil according to the received at least one charge parameter; and
    an indicator control module configured to control an indicator to identify the effectiveness of the magnetic coupling between the implantable device and the charger.
  21. 21. The system of claim 20, wherein the indicator is configured to identify the effectiveness of the magnetic coupling between the implantable device and the charger by identifying a change in the least one charge parameter over a period of time.
  22. 22. The system of claim 21, wherein the at least one charge parameter comprises a voltage induced at the first charging coil.
  23. 23. The system of claim 21, wherein the at least one charge parameter comprises a current induced at the charging coil of the implantable device.
  24. 24. A charger comprising:
    a charging coil configured to magnetically couple with a corresponding charging coil of a peripherally implanted pulse generator, wherein the peripherally implanted pulse generator comprises a plurality of electrodes,
    an indicator configured to identify the effectiveness of a charging field created between the charging coil of the charger and the corresponding charging coil of the implantable device; and
    a processor configured to:
    receive a signal from the peripherally implanted pulse generator at a first time, wherein the signal indicates the effectiveness of the charging field at the first time;
    direct the indicator to identify a first effectiveness level;
    receive a signal from the peripherally implanted pulse generator at a second time, wherein the signal indicates the effectiveness of the charging field at the second time; and
    direct the indicator to identify a second effectiveness level.
  25. 25. A charger comprising:
    a charging coil configured to magnetically couple with a corresponding charging coil of recharging device,
    an indicator configured to identify the effectiveness of a charging field created between the charging coil of the charger and the corresponding charging coil of the recharging device; and
    a processor configured to:
    receive a signal from the recharging device at a first time;
    direct the indicator to identify a first effectiveness level based on a determined effectiveness of the charging field at the first time;
    receive a signal from the recharging device at a second time; and
    direct the indicator to identify a second effectiveness level based on a determined effectiveness of the charging field at the second time.
  26. 26. The charger of claim 25, wherein the recharging device is an implantable device.
  27. 27. The charger of claim 26, wherein the implantable device comprises a peripherally implanted pulse generator comprising a plurality of electrodes.
US14446280 2013-07-29 2014-07-29 Implant charging field control through radio link Pending US20150028805A1 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
US201361859484 true 2013-07-29 2013-07-29
US14446280 US20150028805A1 (en) 2013-07-29 2014-07-29 Implant charging field control through radio link

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US14446280 US20150028805A1 (en) 2013-07-29 2014-07-29 Implant charging field control through radio link
US14593807 US9155901B2 (en) 2013-07-29 2015-01-09 Implant charging field control through radio link

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US14593807 Continuation US9155901B2 (en) 2013-07-29 2015-01-09 Implant charging field control through radio link

Publications (1)

Publication Number Publication Date
US20150028805A1 true true US20150028805A1 (en) 2015-01-29

Family

ID=51358075

Family Applications (2)

Application Number Title Priority Date Filing Date
US14446280 Pending US20150028805A1 (en) 2013-07-29 2014-07-29 Implant charging field control through radio link
US14593807 Active US9155901B2 (en) 2013-07-29 2015-01-09 Implant charging field control through radio link

Family Applications After (1)

Application Number Title Priority Date Filing Date
US14593807 Active US9155901B2 (en) 2013-07-29 2015-01-09 Implant charging field control through radio link

Country Status (6)

Country Link
US (2) US20150028805A1 (en)
EP (1) EP3028365A1 (en)
JP (1) JP2016531662A (en)
CN (1) CN105264736B (en)
CA (1) CA2919462C (en)
WO (1) WO2015017472A1 (en)

Citations (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6447448B1 (en) * 1998-12-31 2002-09-10 Ball Semiconductor, Inc. Miniature implanted orthopedic sensors
US6473652B1 (en) * 2000-03-22 2002-10-29 Nac Technologies Inc. Method and apparatus for locating implanted receiver and feedback regulation between subcutaneous and external coils
US6609032B1 (en) * 1999-01-07 2003-08-19 Advanced Bionics Corporation Fitting process for a neural stimulation system
US20050068019A1 (en) * 2003-09-30 2005-03-31 Sharp Kabushiki Kaisha Power supply system
US7289761B2 (en) * 2003-06-23 2007-10-30 Cardiac Pacemakers, Inc. Systems, devices, and methods for selectively preventing data transfer from a medical device
US20110004278A1 (en) * 2009-07-06 2011-01-06 Boston Scientific Neuromodulation Corporation External Charger for a Medical Implantable Device Using Field Sensing Coils to Improve Coupling
US20110121777A1 (en) * 2009-11-23 2011-05-26 Rafael Carbunaru Efficient External Charger for Charging a Plurality of Implantable Medical Devices
US20120119699A1 (en) * 2010-11-17 2012-05-17 Boston Scientific Neuromodulation Corporation External Charger for an Implantable Medical Device Having at Least One Moveable Charging Coil
US20120214418A1 (en) * 2011-02-23 2012-08-23 Jungseok Lee Wireless charging of mobile device
US20130033117A1 (en) * 2011-08-05 2013-02-07 Samsung Electronics Co., Ltd. Wireless power transmission system, and method and apparatus for controlling power in wireless power transmission system
US20130096651A1 (en) * 2011-10-13 2013-04-18 Boston Scientific Neuromodulation Corporation Charger Alignment in an Implantable Medical Device System Employing Reflected Impedance Modulation

Family Cites Families (159)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3942535A (en) * 1973-09-27 1976-03-09 G. D. Searle & Co. Rechargeable tissue stimulating system
US4082097A (en) * 1976-05-20 1978-04-04 Pacesetter Systems Inc. Multimode recharging system for living tissue stimulators
US4468723A (en) 1981-04-24 1984-08-28 Hewlett-Packard Company Magnetically regulated power supply
US4673867A (en) 1986-06-30 1987-06-16 Motorola, Inc. Current mirror circuit and method for providing zero temperature coefficient trimmable current ratios
DE3914662C2 (en) 1989-05-03 1993-04-22 Eckhard Dr. 8012 Ottobrunn De Alt
US6035237A (en) 1995-05-23 2000-03-07 Alfred E. Mann Foundation Implantable stimulator that prevents DC current flow without the use of discrete output coupling capacitors
US5702431A (en) 1995-06-07 1997-12-30 Sulzer Intermedics Inc. Enhanced transcutaneous recharging system for battery powered implantable medical device
US5690693A (en) 1995-06-07 1997-11-25 Sulzer Intermedics Inc. Transcutaneous energy transmission circuit for implantable medical device
US5877472A (en) 1996-02-22 1999-03-02 Pacesetter, Inc. System for laser-welding components of an implantable device
DE19623788A1 (en) 1996-06-04 1997-12-11 Biotronik Mess & Therapieg An implantable stimulation device
US6191365B1 (en) 1997-05-02 2001-02-20 General Science And Technology Corp Medical devices incorporating at least one element made from a plurality of twisted and drawn wires
US5741316A (en) 1996-12-02 1998-04-21 Light Sciences Limited Partnership Electromagnetic coil configurations for power transmission through tissue
US5735887A (en) 1996-12-10 1998-04-07 Exonix Corporation Closed-loop, RF-coupled implanted medical device
JP3954177B2 (en) 1997-01-29 2007-08-08 日本碍子株式会社 Joint structure and a method of manufacturing the metal member and the ceramic member
US8684009B2 (en) 1997-02-26 2014-04-01 Alfred E. Mann Foundation For Scientific Research System for determining relative distance(s) and/or angle(s) between at least two points
US7114502B2 (en) 1997-02-26 2006-10-03 Alfred E. Mann Foundation For Scientific Research Battery-powered patient implantable device
US8555894B2 (en) 1997-02-26 2013-10-15 Alfred E. Mann Foundation For Scientific Research System for monitoring temperature
US7460911B2 (en) 1997-02-26 2008-12-02 Alfred E. Mann Foundation For Scientific Research System and method suitable for treatment of a patient with a neurological deficit by sequentially stimulating neural pathways using a system of discrete implantable medical devices
US6164284A (en) 1997-02-26 2000-12-26 Schulman; Joseph H. System of implantable devices for monitoring and/or affecting body parameters
US6208894B1 (en) 1997-02-26 2001-03-27 Alfred E. Mann Foundation For Scientific Research And Advanced Bionics System of implantable devices for monitoring and/or affecting body parameters
WO1998037926A1 (en) 1997-02-26 1998-09-03 Alfred E. Mann Foundation For Scientific Research Battery-powered patient implantable device
US5871513A (en) 1997-04-30 1999-02-16 Medtronic Inc. Centerless ground feedthrough pin for an electrical power source in an implantable medical device
DE69840306D1 (en) 1997-08-01 2009-01-15 Mann Alfred E Found Scient Res The implantable device having an improved arrangement for charging the battery and for supplying energy
US6427086B1 (en) 1997-10-27 2002-07-30 Neuropace, Inc. Means and method for the intracranial placement of a neurostimulator
US6265789B1 (en) 1997-11-20 2001-07-24 Seiko Epson Corporation Electronic apparatus
US6402793B1 (en) 1998-04-03 2002-06-11 Medtronic, Inc. Implantable medical device having flat electrolytic capacitor with cathode/case electrical connections
US6221513B1 (en) 1998-05-12 2001-04-24 Pacific Coast Technologies, Inc. Methods for hermetically sealing ceramic to metallic surfaces and assemblies incorporating such seals
US6735474B1 (en) 1998-07-06 2004-05-11 Advanced Bionics Corporation Implantable stimulator system and method for treatment of incontinence and pain
US6178353B1 (en) 1998-07-27 2001-01-23 Advanced Bionics Corporation Laminated magnet keeper for implant device
US6212431B1 (en) 1998-09-08 2001-04-03 Advanced Bionics Corporation Power transfer circuit for implanted devices
US7142925B1 (en) 1998-09-16 2006-11-28 Axon Engineering, Inc. Combined stimulation of ventral and dorsal sacral roots for control of bladder function
US6836684B1 (en) 1998-10-30 2004-12-28 Neurocon Aps Method to control an overactive bladder
US7555346B1 (en) 1999-01-07 2009-06-30 Boston Scientific Neuromodulation Corporation Implantable pulse generator having current steering means
US6246911B1 (en) 1999-02-08 2001-06-12 Peter Seligman Cochlear implants with offset coils for transmission of radio frequency links
US8666495B2 (en) 1999-03-05 2014-03-04 Metacure Limited Gastrointestinal methods and apparatus for use in treating disorders and controlling blood sugar
EP1171188B1 (en) 1999-03-24 2009-05-06 Second Sight Medical Products, Inc. Retinal color prosthesis for color sight restoration
US6055456A (en) 1999-04-29 2000-04-25 Medtronic, Inc. Single and multi-polar implantable lead for sacral nerve electrical stimulation
US6212430B1 (en) 1999-05-03 2001-04-03 Abiomed, Inc. Electromagnetic field source with detection of position of secondary coil in relation to multiple primary coils
US6505075B1 (en) 1999-05-29 2003-01-07 Richard L. Weiner Peripheral nerve stimulation method
US7177690B2 (en) 1999-07-27 2007-02-13 Advanced Bionics Corporation Implantable system having rechargeable battery indicator
US6516227B1 (en) 1999-07-27 2003-02-04 Advanced Bionics Corporation Rechargeable spinal cord stimulator system
US7047082B1 (en) 1999-09-16 2006-05-16 Micronet Medical, Inc. Neurostimulating lead
US6654642B2 (en) 1999-09-29 2003-11-25 Medtronic, Inc. Patient interactive neurostimulation system and method
US6442434B1 (en) 1999-10-19 2002-08-27 Abiomed, Inc. Methods and apparatus for providing a sufficiently stable power to a load in an energy transfer system
US6438423B1 (en) 2000-01-20 2002-08-20 Electrocore Technique, Llc Method of treating complex regional pain syndromes by electrical stimulation of the sympathetic nerve chain
WO2001080795A1 (en) 2000-04-20 2001-11-01 Cochlear Limited Transcutaneous power optimization circuit for cochlear implant
US6456220B1 (en) 2000-06-19 2002-09-24 Cygnal Integrated Products, Inc. Analog-to-digital converter for processing differential and single-ended inputs
DK1307687T3 (en) 2000-08-07 2006-07-03 Luminex S P A A textile product with the illuminated fibers, article or article made thereof and the production method for the same
US7054689B1 (en) 2000-08-18 2006-05-30 Advanced Bionics Corporation Fully implantable neurostimulator for autonomic nerve fiber stimulation as a therapy for urinary and bowel dysfunction
US6864755B2 (en) 2000-10-06 2005-03-08 Alfred E. Mann Institute For Biomedical Engineering At The University Of Southern California Switched reactance modulated E-class oscillator design
US6745077B1 (en) 2000-10-11 2004-06-01 Advanced Bionics Corporation Electronic impedance transformer for inductively-coupled load stabilization
US6600954B2 (en) 2001-01-25 2003-07-29 Biocontrol Medical Bcm Ltd. Method and apparatus for selective control of nerve fibers
US6975906B2 (en) 2001-02-08 2005-12-13 Wilson Greatbatch Ltd. One piece header assembly over molded to an implantable medical device
US6901287B2 (en) 2001-02-09 2005-05-31 Medtronic, Inc. Implantable therapy delivery element adjustable anchor
US6597953B2 (en) 2001-02-20 2003-07-22 Neuropace, Inc. Furcated sensing and stimulation lead
US6708065B2 (en) 2001-03-02 2004-03-16 Cardiac Pacemakers, Inc. Antenna for an implantable medical device
US6584355B2 (en) 2001-04-10 2003-06-24 Cardiac Pacemakers, Inc. System and method for measuring battery current
US6892098B2 (en) 2001-04-26 2005-05-10 Biocontrol Medical Ltd. Nerve stimulation for treating spasticity, tremor, muscle weakness, and other motor disorders
US6521350B2 (en) 2001-06-18 2003-02-18 Alfred E. Mann Foundation For Scientific Research Application and manufacturing method for a ceramic to metal seal
JP2003047179A (en) 2001-07-26 2003-02-14 Matsushita Electric Works Ltd Contactless electric power transmission device
US6456256B1 (en) 2001-08-03 2002-09-24 Cardiac Pacemakers, Inc. Circumferential antenna for an implantable medical device
US6999819B2 (en) 2001-08-31 2006-02-14 Medtronic, Inc. Implantable medical electrical stimulation lead fixation method and apparatus
US7734355B2 (en) 2001-08-31 2010-06-08 Bio Control Medical (B.C.M.) Ltd. Treatment of disorders by unidirectional nerve stimulation
WO2003026736A3 (en) 2001-09-28 2003-11-06 Vertis Neuroscience Inc Methods and implantable apparatus for electrical therapy
US6894456B2 (en) * 2001-11-07 2005-05-17 Quallion Llc Implantable medical power module
US6721603B2 (en) 2002-01-25 2004-04-13 Cyberonics, Inc. Nerve stimulation as a treatment for pain
US7317948B1 (en) 2002-02-12 2008-01-08 Boston Scientific Scimed, Inc. Neural stimulation system providing auto adjustment of stimulus output as a function of sensed impedance
US8386048B2 (en) 2002-06-28 2013-02-26 Boston Scientific Neuromodulation Corporation Systems and methods for communicating with or providing power to an implantable stimulator
US7437193B2 (en) 2002-06-28 2008-10-14 Boston Scientific Neuromodulation Corporation Microstimulator employing improved recharging reporting and telemetry techniques
US7369894B2 (en) 2002-09-06 2008-05-06 Medtronic, Inc. Method, system and device for treating disorders of the pelvic floor by electrical stimulation of the sacral and/or pudendal nerves
US7396265B2 (en) 2002-09-30 2008-07-08 Cochlear Limited Feedthrough for electrical connectors
US7127298B1 (en) 2002-10-18 2006-10-24 Advanced Bionics Corporation Switched-matrix output for multi-channel implantable stimulator
US7933655B2 (en) 2002-10-31 2011-04-26 Medtronic, Inc. Neurostimulation therapy manipulation
US6990376B2 (en) 2002-12-06 2006-01-24 The Regents Of The University Of California Methods and systems for selective control of bladder function
US7952349B2 (en) 2002-12-09 2011-05-31 Ferro Solutions, Inc. Apparatus and method utilizing magnetic field
WO2004052450A1 (en) 2002-12-12 2004-06-24 Metin Tulgar Externally activated neuro-implant which directly transmits therapeutic signals
US7328068B2 (en) 2003-03-31 2008-02-05 Medtronic, Inc. Method, system and device for treating disorders of the pelvic floor by means of electrical stimulation of the pudendal and associated nerves, and the optional delivery of drugs in association therewith
US7463928B2 (en) 2003-04-25 2008-12-09 Medtronic, Inc. Identifying combinations of electrodes for neurostimulation therapy
US7317947B2 (en) 2003-05-16 2008-01-08 Medtronic, Inc. Headset recharger for cranially implantable medical devices
US7742821B1 (en) 2003-06-11 2010-06-22 Boston Scientific Neutomodulation Corporation Remote control for implantable medical device
US20050075696A1 (en) 2003-10-02 2005-04-07 Medtronic, Inc. Inductively rechargeable external energy source, charger, system and method for a transcutaneous inductive charger for an implantable medical device
US7515967B2 (en) 2003-10-02 2009-04-07 Medtronic, Inc. Ambulatory energy transfer system for an implantable medical device and method therefore
US7225032B2 (en) 2003-10-02 2007-05-29 Medtronic Inc. External power source, charger and system for an implantable medical device having thermal characteristics and method therefore
US7286880B2 (en) 2003-10-02 2007-10-23 Medtronic, Inc. System and method for transcutaneous energy transfer achieving high efficiency
US8140168B2 (en) 2003-10-02 2012-03-20 Medtronic, Inc. External power source for an implantable medical device having an adjustable carrier frequency and system and method related therefore
US6989200B2 (en) 2003-10-30 2006-01-24 Alfred E. Mann Foundation For Scientific Research Ceramic to noble metal braze and method of manufacture
US6986453B2 (en) 2003-11-13 2006-01-17 Alfred E. Mann Foundation For Scientific Research Manufacturing method for a ceramic to metal seal
WO2005082453A1 (en) 2004-02-25 2005-09-09 Advanced Neuromodulation Systems, Inc. System and method for neurological stimulation of peripheral nerves to treat low back pain
US7212110B1 (en) 2004-04-19 2007-05-01 Advanced Neuromodulation Systems, Inc. Implantable device and system and method for wireless communication
US7532936B2 (en) 2004-04-20 2009-05-12 Advanced Neuromodulation Systems, Inc. Programmable switching device for implantable device
US7245972B2 (en) 2004-04-29 2007-07-17 Alfred E. Mann Foundation For Scientific Research Electrical treatment to treat shoulder subluxation
US7450991B2 (en) 2004-05-28 2008-11-11 Advanced Neuromodulation Systems, Inc. Systems and methods used to reserve a constant battery capacity
US7539538B2 (en) 2004-05-28 2009-05-26 Boston Science Neuromodulation Corporation Low power loss current digital-to-analog converter used in an implantable pulse generator
WO2006022993A3 (en) 2004-06-10 2006-12-21 Ndi Medical Llc Implantable generator for muscle and nerve stimulation
WO2006012426A8 (en) 2004-07-20 2006-05-04 Medtronic Inc Locating an implanted object based on external antenna loading
US7061780B2 (en) 2004-09-09 2006-06-13 System General Corp. Switching control circuit with variable switching frequency for primary-side-controlled power converters
US7771838B1 (en) 2004-10-12 2010-08-10 Boston Scientific Neuromodulation Corporation Hermetically bonding ceramic and titanium with a Ti-Pd braze interface
US7979119B2 (en) 2005-04-26 2011-07-12 Boston Scientific Neuromodulation Corporation Display graphics for use in stimulation therapies
US7774069B2 (en) 2005-04-29 2010-08-10 Medtronic, Inc. Alignment indication for transcutaneous energy transfer
US8644941B2 (en) 2005-06-09 2014-02-04 Medtronic, Inc. Peripheral nerve field stimulation and spinal cord stimulation
US7890166B2 (en) 2005-06-09 2011-02-15 Medtronic, Inc. Regional therapies for treatment of pain
KR100792311B1 (en) 2005-07-30 2008-01-07 엘에스전선 주식회사 Rechargeable power supply, rechargeable device, battery device, contactless recharger system and method for charging rechargeable battery cell
US8175717B2 (en) 2005-09-06 2012-05-08 Boston Scientific Neuromodulation Corporation Ultracapacitor powered implantable pulse generator with dedicated power supply
US7444181B2 (en) 2005-12-14 2008-10-28 Boston Scientific Neuromodulation Corporation Techniques for sensing and adjusting a compliance voltage in an implantable stimulator device
US7720547B2 (en) 2006-01-04 2010-05-18 Kenergy, Inc. Extracorporeal power supply with a wireless feedback system for an implanted medical device
US7809443B2 (en) 2006-01-31 2010-10-05 Medtronic, Inc. Electrical stimulation to alleviate chronic pelvic pain
US8019423B2 (en) 2006-02-17 2011-09-13 Marc Possover Laparoscopic implantation of neurostimulators
US8447402B1 (en) 2006-03-31 2013-05-21 Alfred E. Mann Foundation For Scientific Research Zirconia to platinum assembly using a titanium connector
US7761166B2 (en) 2006-04-28 2010-07-20 Medtronic, Inc. Electrical stimulation of iliohypogastric nerve to alleviate chronic pelvic pain
US7738965B2 (en) 2006-04-28 2010-06-15 Medtronic, Inc. Holster for charging pectorally implanted medical devices
US8219202B2 (en) 2006-04-28 2012-07-10 Medtronic, Inc. Electrical stimulation of ilioinguinal nerve to alleviate chronic pelvic pain
US20070282376A1 (en) 2006-06-06 2007-12-06 Shuros Allan C Method and apparatus for neural stimulation via the lymphatic system
EP2422842B1 (en) 2006-08-18 2013-07-17 Second Sight Medical Products, Inc. Package for an implantable neural stimulation device
US7979126B2 (en) 2006-10-18 2011-07-12 Boston Scientific Neuromodulation Corporation Orientation-independent implantable pulse generator
US20100076534A1 (en) 2006-10-25 2010-03-25 William Alan Mock Malleable needle having a plurality of electrodes for facilitating implantation of stimulation lead and method of implanting an electrical stimulation lead
US7857819B2 (en) 2006-11-30 2010-12-28 Boston Scientific Neuromodulation Corporation Implant tool for use with a microstimulator
US8010205B2 (en) 2007-01-11 2011-08-30 Boston Scientific Neuromodulation Corporation Multiple telemetry and/or charging coil configurations for an implantable medical device system
US8549015B2 (en) 2007-05-01 2013-10-01 Giancarlo Barolat Method and system for distinguishing nociceptive pain from neuropathic pain
US7932696B2 (en) 2007-05-14 2011-04-26 Boston Scientific Neuromodulation Corporation Charger alignment indicator with adjustable threshold
US20090076580A1 (en) 2007-09-13 2009-03-19 Medtronic, Inc. Medical electrical lead
EP2207590A1 (en) 2007-09-26 2010-07-21 Medtronic, INC. Therapy program selection
US9452296B2 (en) 2007-10-16 2016-09-27 Peter Forsell Method and system for controlling supply of energy to an implantable medical device
WO2009050647A3 (en) * 2007-10-18 2009-07-02 Koninkl Philips Electronics Nv Biomedical electro-stimulator
WO2009055203A1 (en) 2007-10-26 2009-04-30 Medtronic, Inc. Method and apparatus for dynamic adjustment of recharge parameters
US8244367B2 (en) 2007-10-26 2012-08-14 Medtronic, Inc. Closed loop long range recharging
KR101437975B1 (en) * 2007-12-06 2014-09-05 엘지전자 주식회사 Contactless charging apparatus having charging state display function and charging method using the same
WO2009091267A3 (en) 2008-01-18 2009-11-05 Telemetry Research Limited Selectable resonant frequency transcutaneous energy transfer system
US8332040B1 (en) 2008-03-10 2012-12-11 Advanced Neuromodulation Systems, Inc. External charging device for charging an implantable medical device and methods of regulating duty of cycle of an external charging device
US8509909B2 (en) * 2008-04-10 2013-08-13 Medtronic, Inc. Using telemetry coupling as a surrogate for recharger coupling
US8314594B2 (en) 2008-04-30 2012-11-20 Medtronic, Inc. Capacity fade adjusted charge level or recharge interval of a rechargeable power source of an implantable medical device, system and method
US8103360B2 (en) 2008-05-09 2012-01-24 Foster Arthur J Medical lead coil conductor with spacer element
US7957818B2 (en) 2008-06-26 2011-06-07 Greatbatch Ltd. Stimulation lead design and method of manufacture
WO2010011721A1 (en) 2008-07-24 2010-01-28 Boston Scientific Neuromodulation Corporation System and method for maintaining a distribution of currents in an electrode array using independent voltage sources
US20120119698A1 (en) 2008-09-27 2012-05-17 Aristeidis Karalis Wireless energy transfer for vehicles
WO2010042056A1 (en) * 2008-10-10 2010-04-15 Milux Holding S.A. Charger for implant with means for indicating alignment between charger and implant
WO2010042057A1 (en) 2008-10-10 2010-04-15 Milux Holding S.A. Charger for implant
CN101385890B (en) * 2008-10-17 2011-03-30 清华大学 Patient controller for implantation medical instrument
US8219196B2 (en) 2008-10-31 2012-07-10 Medtronic, Inc. Determination of stimulation output capabilities throughout power source voltage range
US8538530B1 (en) 2008-11-19 2013-09-17 Advanced Bionics Hermetically sealed feedthrough case
US20110278948A1 (en) * 2008-11-21 2011-11-17 Milux Holdings SA System for supplying energy
US8255057B2 (en) 2009-01-29 2012-08-28 Nevro Corporation Systems and methods for producing asynchronous neural responses to treat pain and/or other patient conditions
US8214042B2 (en) 2009-05-26 2012-07-03 Boston Scientific Neuromodulation Corporation Techniques for controlling charging of batteries in an external charger and an implantable medical device
US8577474B2 (en) 2009-11-11 2013-11-05 Boston Scientific Neuromodulation Corporation Minimizing interference between charging and telemetry coils in an implantable medical device
US8457756B2 (en) 2009-11-11 2013-06-04 Boston Scientific Neuromodulation Corporation Using the case of an implantable medical device to broaden communication bandwidth
US9123470B2 (en) 2009-12-18 2015-09-01 Cardiac Pacemakers, Inc. Implantable energy storage device including a connection post to connect multiple electrodes
EP2528193A4 (en) * 2010-01-18 2015-09-23 Toyota Motor Co Ltd Noncontact power-receiving device, noncontact power-transmitting device, noncontact power-feeding system, and vehicle
DE102010006837B4 (en) 2010-02-03 2013-01-17 Heraeus Precious Metals Gmbh & Co. Kg (Meth) acrylates having electrical feedthrough
US8700165B2 (en) 2010-07-16 2014-04-15 Boston Scientific Neuromodulation Corporation System and method for estimating lead configuration from neighboring relationship between electrodes
US9155891B2 (en) 2010-09-20 2015-10-13 Neuropace, Inc. Current management system for a stimulation output stage of an implantable neurostimulation system
US8738141B2 (en) 2011-04-07 2014-05-27 Greatbatch, Ltd. Contact assembly for implantable pulse generator and method of use
US9623257B2 (en) 2011-04-18 2017-04-18 Medtronic, Inc. Recharge tuning techniques for an implantable device
US9136728B2 (en) * 2011-04-28 2015-09-15 Medtronic, Inc. Implantable medical devices and systems having inductive telemetry and recharge on a single coil
US8515545B2 (en) 2011-04-29 2013-08-20 Greatbatch Ltd. Current steering neurostimulator device with unidirectional current sources
US9265958B2 (en) 2011-04-29 2016-02-23 Cyberonics, Inc. Implantable medical device antenna
US8700175B2 (en) 2011-07-19 2014-04-15 Greatbatch Ltd. Devices and methods for visually indicating the alignment of a transcutaneous energy transfer device over an implanted medical device
EP2846680A2 (en) 2012-05-08 2015-03-18 The Cleveland Clinic Foundation Implantable pressure sensor
CN102724017B (en) * 2012-05-30 2015-04-15 北京品驰医疗设备有限公司 Wireless communication device for implantable medical instruments
US9184620B2 (en) * 2012-06-28 2015-11-10 Nokia Technologies Oy Method and apparatus for improved wireless charging efficiency
US9142989B2 (en) * 2012-09-07 2015-09-22 Greatbatch Ltd. Method of minimizing interruptions to implantable medical device recharging

Patent Citations (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6447448B1 (en) * 1998-12-31 2002-09-10 Ball Semiconductor, Inc. Miniature implanted orthopedic sensors
US6609032B1 (en) * 1999-01-07 2003-08-19 Advanced Bionics Corporation Fitting process for a neural stimulation system
US6473652B1 (en) * 2000-03-22 2002-10-29 Nac Technologies Inc. Method and apparatus for locating implanted receiver and feedback regulation between subcutaneous and external coils
US7289761B2 (en) * 2003-06-23 2007-10-30 Cardiac Pacemakers, Inc. Systems, devices, and methods for selectively preventing data transfer from a medical device
US20050068019A1 (en) * 2003-09-30 2005-03-31 Sharp Kabushiki Kaisha Power supply system
US20110004278A1 (en) * 2009-07-06 2011-01-06 Boston Scientific Neuromodulation Corporation External Charger for a Medical Implantable Device Using Field Sensing Coils to Improve Coupling
US20110121777A1 (en) * 2009-11-23 2011-05-26 Rafael Carbunaru Efficient External Charger for Charging a Plurality of Implantable Medical Devices
US20120119699A1 (en) * 2010-11-17 2012-05-17 Boston Scientific Neuromodulation Corporation External Charger for an Implantable Medical Device Having at Least One Moveable Charging Coil
US20120214418A1 (en) * 2011-02-23 2012-08-23 Jungseok Lee Wireless charging of mobile device
US20130033117A1 (en) * 2011-08-05 2013-02-07 Samsung Electronics Co., Ltd. Wireless power transmission system, and method and apparatus for controlling power in wireless power transmission system
US20130096651A1 (en) * 2011-10-13 2013-04-18 Boston Scientific Neuromodulation Corporation Charger Alignment in an Implantable Medical Device System Employing Reflected Impedance Modulation

Also Published As

Publication number Publication date Type
US20150142081A1 (en) 2015-05-21 application
CA2919462C (en) 2018-03-06 grant
WO2015017472A1 (en) 2015-02-05 application
JP2016531662A (en) 2016-10-13 application
US9155901B2 (en) 2015-10-13 grant
EP3028365A1 (en) 2016-06-08 application
CN105264736A (en) 2016-01-20 application
CA2919462A1 (en) 2015-02-05 application
CN105264736B (en) 2017-05-10 grant

Similar Documents

Publication Publication Date Title
US6658301B2 (en) Method and apparatus for conditioning muscles during sleep
US7865245B2 (en) Battery recharge management for implantable medical device
US20090157145A1 (en) Transfer Coil Architecture
US20060195159A1 (en) System and method for choosing electrodes in an implanted stimulator device
US20070021814A1 (en) Safe-mode operation of an implantable medical device
US7062330B1 (en) Electrical stimulation adjunct (Add-ON) therapy for urinary incontinence and urological disorders using implanted lead stimulus-receiver and an external pulse generator
US20060173493A1 (en) Multi-phasic signal for stimulation by an implantable device
US7444184B2 (en) Method and system for providing therapy for bulimia/eating disorders by providing electrical pulses to vagus nerve(s)
US20080172109A1 (en) Multiple Telemetry and/or Charging Coil Configurations for an Implantable Medical Device System
US20110009923A1 (en) System and method for reducing excitability of dorsal root fiber by introducing stochastic background noise
US20110071593A1 (en) Couplings for implanted leads and external stimulators, and associated systems and methods
US20050187590A1 (en) Method and system for providing therapy for autism by providing electrical pulses to the vagus nerve(s)
US20110190849A1 (en) Neural stimulation devices and systems for treatment of chronic inflammation
US20120330384A1 (en) Remote control of power or polarity selection for a neural stimulator
US20050154426A1 (en) Method and system for providing therapy for neuropsychiatric and neurological disorders utilizing transcranical magnetic stimulation and pulsed electrical vagus nerve(s) stimulation
US20050216070A1 (en) Method and system for providing therapy for migraine/chronic headache by providing electrical pulses to vagus nerve(s)
US20130310901A1 (en) Methods and devices for modulating excitable tissue of the exiting spinal nerves
US20130096651A1 (en) Charger Alignment in an Implantable Medical Device System Employing Reflected Impedance Modulation
US20070173890A1 (en) Stimulation mode adjustment for an implantable medical device
US20060009815A1 (en) Method and system to provide therapy or alleviate symptoms of involuntary movement disorders by providing complex and/or rectangular electrical pulses to vagus nerve(s)
US20130066400A1 (en) Microwave field stimulator
US8260426B2 (en) Method, apparatus and system for bipolar charge utilization during stimulation by an implantable medical device
US20090306738A1 (en) Elongated implant having an external energy coupling
WO2002009808A1 (en) Rechargeable spinal cord stimulator system
US8044635B2 (en) Charger alignment indicator with adjustable threshold

Legal Events

Date Code Title Description
AS Assignment

Owner name: ALFRED E. MANN FOUNDATION FOR SCIENTIFIC RESEARCH,

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:DEARDEN, BRIAN R;SHELTON, BRIAN M;WOLFE, JAMES H;SIGNINGDATES FROM 20150106 TO 20150120;REEL/FRAME:034772/0357