WO2005123181A2 - Implantable pulse generator for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue - Google Patents
Implantable pulse generator for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue Download PDFInfo
- Publication number
- WO2005123181A2 WO2005123181A2 PCT/US2005/020506 US2005020506W WO2005123181A2 WO 2005123181 A2 WO2005123181 A2 WO 2005123181A2 US 2005020506 W US2005020506 W US 2005020506W WO 2005123181 A2 WO2005123181 A2 WO 2005123181A2
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- pulse generator
- implantable pulse
- battery
- circuit
- implantable
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/372—Arrangements in connection with the implantation of stimulators
- A61N1/37211—Means for communicating with stimulators
- A61N1/37235—Aspects of the external programmer
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
- A61B5/0031—Implanted circuitry
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/389—Electromyography [EMG]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/389—Electromyography [EMG]
- A61B5/395—Details of stimulation, e.g. nerve stimulation to elicit EMG response
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/372—Arrangements in connection with the implantation of stimulators
- A61N1/37211—Means for communicating with stimulators
- A61N1/37235—Aspects of the external programmer
- A61N1/37247—User interfaces, e.g. input or presentation means
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
- A61B2560/02—Operational features
- A61B2560/0204—Operational features of power management
- A61B2560/0209—Operational features of power management adapted for power saving
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
- A61B5/7232—Signal processing specially adapted for physiological signals or for diagnostic purposes involving compression of the physiological signal, e.g. to extend the signal recording period
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36003—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of motor muscles, e.g. for walking assistance
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S128/00—Surgery
- Y10S128/903—Radio telemetry
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S128/00—Surgery
- Y10S128/904—Telephone telemetry
Definitions
- Neuromuscular stimulation the electrical excitation of nerves and/or muscle to directly elicit the contraction of muscles
- neuromodulation stimulation the electrical excitation of nerves, often afferent nerves, to indirectly affect the stability or performance of a physiological system
- brain stimulation the stimulation of cerebral or other central nervous system tissue
- neuromodulation stimulation has been used for the treatment of erectile dysfunction.
- Erectile dysfunction is often referred to as "impotency. " When a man has impotency, he cannot get a firm erection or keep his penis erect during intercourse. There are some common diseases such as diabetes, Peyronie ' s disease, heart disease, and prostate cancer that are associated with impotency or have treatments that may cause impotency. And in some cases the cause may be psychological . A wide range of options exist for the treatment of erectile dysfunction. Treatments include everything from medications, simple mechanical devices, psychological counseling, and surgery for both external and implantable devices . Both external and implantable devices are available for the purpose of neuromodulation stimulation for the treatment of erectile dysfunction.
- Implantable devices have provided an improvement in the portability of neuromodulation stimulation devices, but there remains the need for continued improvement .
- Implantable stimulators described in the art have additional limitations in that they are challenging to surgically implant because they are relatively large; they require direct skin contact for programming and for turning on and off. In addition, current implantable stimulators are expensive; owing in part to their limited scope of usage.
- implantable devices are also limited in their ability to provide sufficient power which limits their use in a wide range of neuromuscular stimulation, and limits their acceptance by patients because of the need to surgically replace the device when batteries fail, or the need to frequently recharge a rechargeable power supply.
- implantable microstimulators have been introduced that can be injected into soft tissues through a cannula or needle.
- these small implantable stimulation devices have a reduced physical size, their application to a wide range of neuromuscular stimulation application is limited.
- Their micro size extremely limits their ability to maintain adequate stimulation strength for an extended period without the need for frequent replacement, or for recharging of an internal rechargeable power supply (battery) .
- the invention provides improved assemblies, systems, and methods for providing prosthetic or therapeutic stimulation of central nervous system tissue, muscles, or nerves, or muscles and nerves.
- One aspect of the invention provides a stimulation assembly sized and configured to provide prosthetic or therapeutic stimulation of central nervous system tissue, muscles, or nerves, or muscles and nerves.
- the stimulation assembly includes an implantable pulse generator (IPG) attached to at least one lead and one electrode .
- IPG implantable pulse generator
- the implantable pulse generator is implanted subcutaneously in tissue, preferably in a subcutaneous pocket located remote from the electrode.
- the electrode is implanted in electrical conductive contact (i.e., the electrode proximity to the excitable tissue allows current flow from the electrode to excite the tissue/nerve) with at least one functional grouping of neural tissue, muscle, or at least one nerve, or at least one muscle and nerve .
- the lead is tunneled subcutaneously in order to electrically connect the implantable pulse generator to the electrode.
- Another aspect of the invention provides improved assemblies, systems, and methods for providing a universal device which can be used for many specific clinical indications requiring the application of pulse trains to muscle and/or nervous tissue for therapeutic (treatment) or functional restoration purposes.
- the implantable pulse generator device may include one or more of the following: a primary power source and/or a rechargeable secondary power source for improved service life, wireless telemetry for programming and interrogation, a single or limited number of stimulus output stage (s) for pulse generation that are directed to one or more output channels, a lead connection header to provide reliable and easy connection and replacement of the lead/electrode, a programmable microcontroller for timing and control of the implantable pulse generator device functions, and power management circuitry for efficient recharging of the secondary power source, and the distribution of appropriate voltages and currents to other circuitry, all of which are incorporated within a small composite case for improved quality of life and ease of implantation.
- the power management circuitry (through the use of logic and algorithms implemented by the microcontroller) communicates with an external controller outside the body through the wireless telemetry communications link.
- the power management may include operating modes configured to operate the implantable pulse generator at its most efficient power consumption throughout the storage and operation of the implantable pulse generator. These modes selectively disable or shut down circuit functions that are not needed.
- the modes may include, but are not limited to IPG Active, IPG Dormant, and IPG Active and Charging.
- the power management circuitry may also be generally responsible for recovery of power from a radio-frequency (RF) magnetic field applied externally over the implantable pulse generator, for charging and monitoring the optional rechargeable battery.
- RF radio-frequency
- the efficient recharging of the secondary power source is accomplished by adjusting the strength of the RF magnetic field generated by the externally mounted implantable pulse generator charger in response to the magnitude of the voltage recovered by the implantable pulse generator and the power demands of the implantable pulse generator's battery.
- the wireless telemetry may allowss the implantable pulse generator to wirelessly interact with a clinician programmer, a clinician programmer derivative, a patient controller, and in an alternative embodiment, an implantable pulse generator charger, for example.
- the wireless telemetry allows a clinician to transmit stimulus parameters, regimes, and other setting to the implantable pulse generator before or after it has been implanted.
- the wireless telemetry also allows the clinician to retrieve information stored in the implantable pulse generator about the patient ' s usage of the implantable pulse generator and information about any modifications to the settings of the implantable pulse generator made by the patient .
- the wireless telemetry also allows the patient controller operated by the user to control the implantable pulse generator, both stimulus parameters and settings in the context of a therapeutic application, or the real-time stimulus commands in the case of a neural prosthetic application.
- the wireless telemetry allows the operating program of the implantable pulse generator, i.e., the embedded executable code which incorporates the algorithms and logic for the operation of the implantable pulse generator, to be installed or revised after the implantable pulse generator has been assembled, tested, sterilized, and perhaps implanted.
- the wireless telemetry allows the implantable pulse generator to communicate with the recharger (implantable pulse generator charger) during a battery recharge in order to adjust the recharging parameters if necessary, which provides for an efficient and effective recharge.
- the assemblies, systems and methods may provide a clinician programmer incorporating technology based on industry-standard hand-held computing platforms .
- the clinician programmer allows the clinician or physician to set parameters in the implantable pulse generator (IPG) relating to the treatment of the approved indication.
- the clinician programmer uses the wireless telemetry feature of the implantable pulse generator to bi-directionally communicate to the implantable pulse generator.
- a clinician programmer derivative (or perhaps a feature included in the IPG charger) would connect to the patient's computer in their home through an industry standard network such as the Universal Serial Bus (USB) , where in turn an applet downloaded from the clinician's server would contain the necessary code to establish a reliable transport level connection between the implantable pulse generator and the clinician's client software, using the clinician programmer derivative as a bridge.
- USB Universal Serial Bus
- Such a connection may also be established through separately installed software .
- the clinician or physician could then view relevant diagnostic information, such as the health of the unit or its current efficacy, and then direct the patient to take the appropriate action.
- relevant diagnostic information such as the health of the unit or its current efficacy
- Such a feature would save the clinician, the patient and the health care system substantial time and money by reducing the number of office visits during the life of the implant.
- Other features of the clinician programmer based on an industry standard platform, might include the ability to connect to the clinician's computer system in his or hers office. Such features may take advantage of the Conduit connection employed by Palm OS based devices . Such a connection then would transfer relevant patient data to the host computer or server for electronic processing and archiving.
- the clinician programmer then becomes an integral link in an electronic chain that provides better patient service by reducing the amount of paperwork that the physician's office needs to process on each office visit. It also improves the reliability of the service since it reduces the chance of mis-entered or mis-placed information, such as the record of the parameter setting adjusted during the visit.
- Fig. 1 is a view of a stimulation assembly that provides electrical stimulation to central nervous system tissue, muscles and/or nerves inside the body using a general purpose implantable pulse generator .
- Figs. 2A and 2B are front and side views of the general purpose implantable pulse generator shown in Fig. 1, which is powered by a primary battery.
- Figs. 2C and 2D are front and side views of an alternative embodiment of a general purpose implantable pulse generator shown in Fig. 1, which is powered using a rechargeable battery.
- Fig. 3 is a view showing how the geometry of the implantable pulse generator shown in Figs . 2A and 2B aids in its implantation in a tissue pocket.
- Fig. 1 is a view of a stimulation assembly that provides electrical stimulation to central nervous system tissue, muscles and/or nerves inside the body using a general purpose implantable pulse generator .
- Figs. 2A and 2B are front and side views of the general purpose implantable pulse generator shown in Fig. 1, which is powered by a primary battery
- FIG. 4A is a view showing an alternative embodiment of the implantable pulse generator shown in Figs. 2C and 2D, the alternative embodiment having a rechargeable battery and shown in association with a transcutaneous implantable pulse generator charger (battery recharger) including an integral charging coil which generates the RF magnetic field, and also showing the implantable pulse generator charger using wireless telemetry to communicate with the implantable pulse generator.
- Fig. 4B is an anatomic view showing the transcutaneous implantable pulse generator charger (battery recharger) as shown in Fig. 4A, including a separate, cable coupled charging coil which generates the RF magnetic field, and also showing the implantable pulse generator charger using wireless telemetry to communicate with the implantable pulse generator.
- Fig. 4C is a perspective view of the implantable pulse generator charger of the type shown in Figs. 4A and
- Fig. 5A is an anatomic view showing the implantable pulse generator shown in Figs. 2A and 2B in association with an external programmer that relies upon wireless telemetry, and showing the programmer's capability of communicating with the implantable pulse generator up to an arm's length away from the implantable pulse generator.
- Fig. 5B is a system view of an implantable pulse generator system incorporating a clinician programmer derivative and showing the system's capability of communicating and transferring data over a network, including a remote network.
- Fig. 5C is a perspective graphical view of one possible type of patient controller that may be used with the implantable pulse generator shown in Figs. 2A and 2B.
- Fig. 6 is a block diagram of a circuit that the implantable pulse generator shown in Figs. 2A and 2B can incorporate.
- Fig. 7 is an alternative embodiment of the block diagram shown in Fig. 6, and shows an alternative block circuit diagram that an implantable pulse generator having a rechargeable battery may utilize.
- Fig. 8 is a circuit diagram showing a possible circuit for the wireless telemetry feature used with the implantable pulse generator shown in Figs. 2A and 2B.
- Fig. 9 is a circuit diagram showing a possible circuit for the stimulus output stage and output multiplexing features used with the implantable pulse generator shown in Figs . 2A and 2B .
- Fig. 10 is a graphical view of a desirable biphasic stimulus pulse output of the implantable pulse generator for use with the system shown in Fig. 1.
- Fig. 11 is a circuit diagram showing a possible circuit for the microcontroller used with the implantable pulse generator shown in Figs. 2A and 2B.
- Fig. 12 is a circuit diagram showing one possible option for a power management sub-circuit where the sub- circuit includes MOSFET isolation between the battery and charger circuit, the power management sub-circuit being a part of the implantable pulse generator circuit shown in Fig. 7.
- Fig. 11 is a circuit diagram showing a possible circuit for the microcontroller used with the implantable pulse generator shown in Figs. 2A and 2B.
- Fig. 12 is a circuit diagram showing one possible option for a power management sub-circuit where the sub- circuit includes MOSFET isolation between the battery and charger circuit, the power management sub-circuit being a part of the implantable pulse generator circuit shown in Fig. 7.
- FIG. 13 is a circuit diagram showing a second possible option for a power management sub-circuit where the sub-circuit does not include MOSFET isolation between the battery and charger circuit, the power management sub-circuit being a part of the implantable pulse generator circuit shown in Fig. 7.
- Fig. 14 is a circuit diagram showing a possible circuit for the VHH power supply feature used with the implantable pulse generator shown in Figs. 2A and 2B .
- the invention may be embodied in several forms without departing from its spirit or essential characteristics. The scope of the invention is defined in the appended claims, rather than in the specific description preceding them. All embodiments that fall within the meaning and range of equivalency of the claims are therefore intended to be embraced by the claims .
- FIG. 1 shows an assembly 10 for stimulating a central nervous system tissue, nerve, or a muscle, or a nerve and a muscle for therapeutic (treatment) or functional restoration purposes.
- the assembly includes an implantable lead 12 coupled to an implantable pulse generator or IPG 18.
- the lead 12 and the implantable pulse generator 18 are shown implanted within a tissue region T of a human or animal body.
- the distal end of the lead 12 includes at least one electrically conductive surface, which will in shorthand be called an electrode 16.
- the electrode 16 is implanted in electrical conductive contact with at least one functional grouping of neural tissue, muscle, or at least one nerve, or at least one muscle and nerve.
- the implantable pulse generator 18 includes a connection header 14 that desirably carries a plug-in receptacle for the lead 12. In this way, the lead 12 electrically connects the electrode 16 to the implantable pulse generator 18.
- the implantable pulse generator 18 is sized and configured to be implanted subcutaneously in tissue, desirably in a subcutaneous pocket P, which can be remote from the electrode 16, as Fig. 1 shows.
- the implantable pulse generator 18 is sized and configured to be implanted using a minimally invasive surgical procedure .
- the surgical procedure may be completed in a number of steps. For example, once a local anesthesia is established, the electrode 16 is positioned at the target site. Next, a subcutaneous pocket P is made and sized to accept the implantable pulse generator 18. The pocket P is formed remote from the electrode 16. Having developed the subcutaneous pocket P for the implantable pulse generator 18, a subcutaneous tunnel is formed for connecting the lead 12 and electrode 16 to the implantable pulse generator 18. The lead 12 is routed through the subcutaneous tunnel to the pocket site P where the implantable pulse generator 18 is to be implanted.
- the implantable pulse generator 18 includes a circuit 20 that generates electrical stimulation waveforms.
- An on-board, primary battery 22 desirably provides the power. In an alternative embodiment, the battery may be a rechargeable battery.
- the implantable pulse generator 18 also desirably includes an on-board, programmable microcontroller 24, which carries embedded code. The code expresses pre-programmed rules or algorithms under which the desired electrical stimulation waveforms are generated by the circuit 20.
- the implantable pulse generator 18 desirably includes an electrically conductive case 26, which can also serve as the return electrode for the stimulus current introduced by the lead/electrode when operated in a monopolar configuration. According to its programmed rules, when switched on, the implantable pulse generator 18 generates prescribed stimulation waveforms through the lead 12 and to the electrode 16. These stimulation waveforms stimulate the central nervous system tissue, muscle, nerve, or both nerve and muscle tissue that lay in electrical conductive contact (i.e., within close proximity to the electrode surface where the current densities are high) with the electrode 16, in a manner that achieves the desired therapeutic (treatment) or functional restoration result. As previously discussed, erectile restoration is just one example of a functional restoration result. Additional examples of desirable therapeutic (treatment) or functional restoration indications will be described in greater detail in section II.
- the assembly 10 may also include additional - In ⁇
- the size and configuration of the implantable pulse generator 18 makes possible its use as a general purpose or universal device (i.e., creating a platform technology) , which can be used for many specific clinical indications requiring the application of pulse trains to central nervous system tissue, muscle and/or nervous tissue for therapeutic (treatment) or functional restoration purposes .
- Most of the components of the implantable pulse generator 18 are desirably sized and configured so that they can accommodate several different indications, without major change or modification.
- Examples of components that desirably remain unchanged for different indications include the case 26, the battery 22, the power management circuitry 40, the microcontroller 24, much of the software (firmware) of the embedded code, and the stimulus power supply. Thus, a new indication may require only changes to the programming of the microcontroller 24. Most desirably, the particular code is remotely embedded in the microcontroller 24 after final assembly, packaging, and sterilization of the implantable pulse generator 18. Certain components of the implantable pulse generator 18 may be expected to change as the indication changes; for example, due to differences in leads and electrodes, the connection header 14 and associated receptacle (s) for the lead may be configured differently for different indications.
- the implantable pulse generator 18 is well suited for use for diverse indications.
- the implantable pulse generator 18 thereby accommodates coupling to a lead 12 and an electrode 16 implanted in diverse tissue regions, which are targeted depending upon the therapeutic (treatment) or functional restoration results desired.
- the implantable pulse generator 18 also accommodates coupling to a lead 12 and an electrode 16 having diverse forms and configurations, again depending upon the therapeutic or functional effects desired. For this reason, the implantable pulse generator can be considered to be general purpose or "universal . " 1. Desirable Technical Features
- the implantable pulse generator 18 can incorporate various technical features to enhance its universality. a.
- the implantable pulse generator 18 can be sized small enough to be implanted (or replaced) with only local anesthesia.
- the functional elements of the implantable pulse generator 18 e.g., circuit 20, the microcontroller 24, the battery 22, and the connection header 14
- the implantable pulse generator 18 may comprise a case 26 having a small cross section, e.g., 5mm to 10mm thick x (45mm to 60mm wide) x (45mm to 60mm long) .
- the overall weight of the implantable pulse generator 18 may be approximately twenty to thirty grams .
- Figs . 2C and 2D illustrate an alternative embodiment of an implantable pulse generator 68 utilizing a rechargeable battery 72.
- the rechargeable implantable pulse generator 68 shares many features of the primary cell implantable pulse generator 18.
- Like structural elements are therefore assigned like numerals .
- the case 76 defines a small cross section; e.g., (5mm to 10 mm thick) x (15mm to 25mm wide) x (40mm to 50mm long) . These dimensions make possible implantation of the case 76 with a small incision; i.e., suitable for minimally invasive implantation.
- the case 26 of the implantable pulse generator 18 is desirably shaped with a smaller end 30 and a larger end 32. As Fig. 3 shows, this geometry allows the smaller end 30 of the case 26 to be placed into the skin pocket P first, with the larger end 32 being pushed in last.
- the case 26 for the implantable pulse generator 18 comprises a laser welded titanium material. This construction offers high reliability with a low manufacturing cost.
- the clam shell construction has two stamped or successively drawn titanium case halves that are laser welded around the circuit assembly and battery 22 with feed-thrus. Typically, a molded plastic spacing nest is used to hold the battery 22, the circuit 20, and perhaps a power recovery (receive) coil together and secure them within the titanium case.
- the implantable pulse generator 18 may be implanted at a target implant depth of not less than five millimeters beneath the skin, and not more than fifteen millimeters beneath the skin, although this implant depth may change due to the particular application, or the implant depth may change over time based on physical conditions of the patient .
- the thickness of the titanium for the case is selected to provide adequate mechanical strength while balancing the greater power absorption and shielding effects to the low to medium frequency magnetic field 54 used to transcutaneously recharge the implantable rechargeable battery 72 with thicker case material (the competing factors are poor transformer action at low frequencies - due to the very low transfer impedances at low frequencies - and the high shielding losses at high frequencies) .
- the selection of the thickness ensures that the titanium case allows adequate power coupling to recharge the secondary power source (described below) of the rechargeable pulse generator 68 at the target implant depth using a low frequency radio frequency (RF) magnetic field 52 from an implantable pulse generator charger 34 mounted on the skin (see Figs. 4A and 4B) .
- the implantable pulse generator 18 desirably possesses an internal battery capacity sufficient to allow a service life of greater than three years with the stimulus being a high duty cycle, e.g., virtually continuous, low frequency, low current stimulus pulses, or alternatively, the stimulus being higher frequency and amplitude stimulus pulses that are used only intermittently, e.g., a very low duty cycle .
- the primary battery 22 of the implantable pulse generator 18 desirably comprises a primary power source; most desirably a Lithium Ion battery 22.
- the implantable pulse generator 18 desirably incorporates a primary battery, e.g., a Lithium Ion battery.
- a Lithium Ion battery with a capacity of at least 30mA-hr will operate for over three years. Lithium Ion implant grade batteries are available from a domestic supplier.
- a representative battery provides 35mA-hr in a package configuration that is of appropriate size and shape to fit within the implantable pulse generator 18.
- the implantable pulse generator 18 desirably incorporates circuitry and/or programming to assure that the implantable pulse generator 18 will suspend stimulation, and perhaps fall-back to only very low rate telemetry, and eventually suspends all operations when the primary battery 22 has discharged the majority of its capacity (i.e., only a safety margin charge remains).
- the implantable pulse generator may provide limited communications and is in condition for replacement.
- the rechargeable implantable pulse generator 68 desirably possesses a rechargeable battery capacity sufficient to allow operation with recharging not more frequently than once per week for many or most clinical applications.
- the battery 72 of the rechargeable implantable pulse generator 68 desirably can be recharged in less than approximately six hours with a recharging mechanism that allows the patient to sleep in bed or carry on most normal daily activities while recharging the battery 72 of the rechargeable implantable pulse generator 68.
- the power for recharging the battery 72 of the rechargeable implantable pulse generator 68 is provided through the application of a low frequency (e.g., 30KHz to 300KHz) RF magnetic field 52 applied by a skin or clothing mounted recharger 34 placed over the implantable pulse generator (see Figs. 4A and 4B) .
- the user would wear the recharger 34, including an internal magnetic coupling coil (charging coil) 35, over the rechargeable implantable pulse generator 68 to recharge the rechargeable implantable pulse generator 68 (see Fig. 4A) .
- the recharger 34 might use a separate magnetic coupling coil (charging coil) 35 which is placed and/or secured on the skin or clothing over the rechargeable implantable pulse generator 68 and connected by cable to the recharger 34 (circuitry and battery in a housing) that is worn on a belt or clipped to the clothing (see Fig. 4B) .
- the charging coil 35 preferably includes a predetermined construction, e.g., 200 turns of six strands of #36 enameled magnetic wire, or the like.
- the charging coil mean diameter is preferably about 50 millimeters, although the diameter may vary.
- the thickness of the charging coil 35 as measured perpendicular to the mounting plane is to be significantly less than the di-ameter, e.g., two to five millimeters, so as to allow the coil to be embedded or laminated in a sheet to facilitate placement on or near the skin. Such a construction will allow for efficient power transfer and will allow the charging coil 35 to maintain a temperature below 41 degrees Celsius.
- the recharger 34 preferably includes its own internal batteries which may be recharged from the power mains, for example.
- a charging base 39 may be included to provide for convenient docking and recharging of the system's operative components, including the recharger and the recharger' s internal batteries (see Fig.
- the implantable pulse generator recharger 34 does not need to be plugged into the power mains while in use to recharge the rechargeable implantable pulse generator 68.
- the rechargeable implantable pulse generator 68 may be recharged while it is operating and will not increase in temperature by more than two degrees Celsius above the surrounding tissue during the recharging. It is desirable that the recharging of the battery 72 requires not more than six hours, and a recharging would be required between once per month to once per week depending upon the power requirements of the stimulus regime used. c.
- the system or assembly 10 includes an implantable pulse generator 18, which desirably incorporates wireless telemetry (rather that an inductively coupled telemetry) for a variety of functions to be performed within arm's reach of the patient, the functions including receipt of programming and clinical parameters and settings from the clinician programmer 36, communicating usage history to the clinician programmer, providing user control of the implantable pulse generator 18, and alternatively for controlling the RF magnetic field 52 generated by the rechargeable implantable pulse generator charger 34.
- Each implantable pulse generator may also have a unique signature that limits communication to only the dedicated controllers (e.g., the matched Patient Controller, implantable pulse generator Charger, or a clinician programmer configured for the implantable pulse generator in question) .
- the implantable pulse generator 18 desirably incorporates wireless telemetry as an element of the implantable pulse generator circuit 20 shown in Fig. 6.
- a circuit diagram showing a desired configuration for the wireless telemetry feature is shown in Fig. 8. It is to be appreciated that modifications to this circuit diagram configuration which produce the same or similar functions as described are within the scope of the invention.
- the assembly 10 desirably includes a clinician programmer 36 that, through a wireless telemetry 38, transfers commands, data, and programs into the implantable pulse generator 18 and retrieves data out of the implantable pulse generator 18.
- the clinician programmer may communicate with more than one implantable pulse generator implanted in the same user .
- the clinician programmer 36 may incorporate a custom programmed general purpose digital device, e.g., a custom program, industry standard handheld computing platform or other personal digital assistant (PDA) .
- the clinician programmer 36 can include an on-board microcontroller powered by a rechargeable battery.
- the rechargeable battery of the clinician programmer 36 may be recharged in the same or similar manner as described and shown for the recharger 34, i.e., docked on a charging base 39 (see Fig. 4C) ; or the custom electronics of the clinician programmer may receive power from the connected PDA.
- the microcontroller carries embedded code which may include pre-programmed rules or algorithms that allow a clinician to remotely download program stimulus parameters and stimulus sequences parameters into the implantable pulse generator 18.
- the microcontroller of the clinician programmer 36 is also desirably able to interrogate the implantable pulse generator and upload usage data from the implantable pulse generator.
- Fig. 5A shows one possible application where the clinician is using the programmer 36 to interrogate the implantable pulse generator.
- Fig. 5B shows an alternative application where the clinician programmer, or a clinician programmer derivative 33 intended for remote programming applications and having the same or similar functionality as the clinician programmer, is used to interrogate the implantable pulse generator.
- the clinician programmer derivative 33 is connected to a local computer, allowing for remote interrogation via a local area network, wide area network, or Internet connection, for example.
- features of the clinician programmer 36 or clinician programmer derivative 33 might include the ability of the clinician or physician to remotely monitor and adjust parameters using the Internet or other known or future developed networking schemes.
- a clinician programmer derivative 33 (perhaps a feature included in the implantable pulse generator charger) would desirably connect to the patient's computer in their home through an industry standard network such as the Universal Serial
- USB Universal Serial Bus
- an applet downloaded from the clinician's server would contain the necessary code to establish a reliable transport level connection between the implantable pulse generator 18 and the clinician' s client software, using the clinician programmer derivative 33 as a bridge.
- Such a connection may also be established through separately installed software.
- the clinician or physician could then view relevant diagnostic information, such as the health of the unit or its current settings, and then modify the stimulus settings in the IPG or direct the patient to take the appropriate action.
- Such a feature would save the clinician, the patient and the health care system substantial time and money by reducing the number of office visits during the life of the implant.
- Other features of the clinician programmer based on an industry standard platform, might include the ability to connect to the clinician's computer system in his or hers office.
- Such features may take advantage of the Conduit connection employed by Palm OS based devices . Such a connection then would transfer relevant patient data to the host computer or server for electronic processing and archiving. With a feature as described here, the clinician programmer then becomes an integral link in an electronic chain that provides better patient service by reducing the amount of paperwork that the physician's office needs to process on each office visit. It also improves the reliability of the service since it reduces the chance of mis-entered or mis-placed information, such as the record of the parameter setting adjusted during the visit. With the use of a patient controller 37 (see Fig. 5C) , the wireless link 38 allows a patient to control certain parameters of the implantable pulse generator within a predefined limited range.
- the parameters may include the operating modes/states, increasing/decreasing or optimizing stimulus patterns, or providing open or closed loop feedback from an external sensor or control source.
- the wireless telemetry 38 also desirably allows the user to interrogate the implantable pulse generator 18 as to the status of its internal battery 22.
- the full ranges within these parameters may be controlled, adjusted, and limited by a clinician, so the user may not be allowed the full range of possible adjustments.
- the patient controller 37 is sized and configured to couple to a key chain, as seen in Fig 5C. It is to be appreciated that the patient controller 37 may take on any convenient shape, such as a ring on a finger, or a watch on a wrist, or an attachment to a belt, for example.
- the wireless telemetry may incorporate a suitable, low power wireless telemetry transceiver (radio) chip set that can operate in the MICS (Medical Implant Communications Service) band (402MHz to 405MHz) or other V ⁇ F/UHF low power, unlicensed bands.
- MICS Medical Implant Communications Service
- a wireless telemetry link not only makes the task of communicating with the implantable pulse generator 18 easier, but it also makes the link suitable for use in motor control applications where the user issues a command to the implantable pulse generator to produce muscle contractions to achieve a functional goal (e.g., to stimulate ankle flexion to aid in the gait of an individual after a stroke) without requiring a coil or other component taped or placed on the skin over the implanted implantable pulse generator.
- a functional goal e.g., to stimulate ankle flexion to aid in the gait of an individual after a stroke
- the implantable pulse generator is exclusively the communications slave, with all communications initiated by the external controller (the communications master) .
- the receiver chip of the implantable pulse generator is OFF more than 99% of the time and is pulsed on periodically to search for a command from an external controller, including but not limited to the clinician programmer 36, the patient controller 37, and alternatively the implantable pulse generator charger 34.
- Communications protocols include appropriate check and message acknowledgment handshaking to assure the necessary accuracy and completeness of every message. Some operations (such as reprogramming or changing stimulus parameters) require rigorous message accuracy testing and acknowledgement. Other operations, such as a single user command value in a string of many consecutive values, might require less rigorous checking and a more loosely coupled acknowledgement .
- the timing with which the implantable pulse generator enables its transceiver to search for RF telemetry from an external controller is precisely controlled (using a time base established by a quartz crystal) at a relatively low rate, e.g., the implantable pulse generator may look for commands from the external controller at a rate of less than one (1) Hz. This equates to a monitoring interval of several seconds. It is to be appreciated that the monitoring rate may vary faster or slower depending on the application, (e.g., twice per second; i.e., every 500 milliseconds). This allows the external controller to time when the implantable pulse generator responds to a command and then to synchronize its commands with when the implantable pulse generator will be listening for commands.
- the communications sequence is configured to have the external controller issue commands in synchronization with when the implantable pulse generator will be listening for a command.
- the command set implemented is selected to minimize the number of messages necessary and the length of each message consistent with the appropriate level of error detection and message integrity monitoring. It is to be appreciated that the monitoring rate may vary faster or slower depending on the application; and may vary over time within a given application.
- a suitable radio chip is used for the half duplex wireless communications, e.g., the AMIS-52100 (AMI Semiconductor; Pocatello, Idaho) .
- This transceiver chip is designed specifically for the MICS and its European counter-part the ULP-AMI (Ultra Low Power-Active Medical Implant) band.
- This chip set is optimized by micro-power operation with rapid start-up, and RF 'sniffing' circuitry.
- the implantable pulse generator 18 desirably uses a single stimulus output stage (generator) that is directed to one or more output channels (electrode surfaces) by analog switch(es) or analog multiplexer (s) .
- the implantable pulse generator 18 will deliver at least one channel of stimulation via a lead/electrode.
- several channels can be generated by a single output stage.
- two or more output stages could be used, each with separate multiplexing to multiple channels, to allow an implantable pulse generator with eight or more stimulus channels.
- the stimulation desirably has a biphasic waveform (net DC current less than lO ⁇ A) , amplitude of at least 8mA, for neuromodulation applications, or 16mA to 20mA for muscle stimulation applications, and pulse durations up to 500 microseconds.
- the stimulus current (amplitude) and pulse duration being programmable on a channel to channel basis and adjustable over time based on a clinically programmed sequence or regime or based on user (patient) commands received via the wireless communications link.
- a circuit diagram showing a desired configuration for the stimulus output stage feature is shown in Fig. 9. It is to be appreciated that modifications to this circuit diagram configuration which produce the same or similar functions as described are within the scope of the invention.
- the implantable pulse generator 18 may have the capability of applying stimulation twenty-four hours per day.
- a typical stimulus regime for such applications might have a constant stimulus phase, a no stimulus phase, and ramping of stimulus levels between these phases .
- the implantable pulse generator 18 includes a single stimulus generator (with its associated DC current blocking output capacitor) which is multiplexed to a number of output channels; or a small number of such stimulus generators each being multiplexed to a number of output channels.
- This circuit architecture allows multiple output channels with very little additional circuitry.
- a typical, biphasic stimulus pulse is shown in Fig. 10. Note that the stimulus output stage circuitry 46 may incorporate a mechanism to limit the recovery phase current to a small value (perhaps 0.5mA) .
- the stimulus generator (and the associated timing of control signals generated by the microcontroller) may provide a delay (typically of the order of 100 microseconds) between the cathodic phase and the recovery phase to limit the recovery phase diminution of the cathodic phase effective at eliciting a neural excitation.
- the charge recovery phase for any electrode must be long enough to assure that all of the charge delivered in the cathodic phase has been returned in the recovery phase; i.e., greater than or equal to five time constants are allowed for the recovery phase. This will allow the stimulus stage to be used for the next electrode while assuring there is no net DC current transfer to any electrode.
- the single stimulus generator having this characteristic would be limited to four channels (electrodes) , each with a maximum frequency of 30 Hz to 50 Hz. This operating frequency exceeds the needs of many indications for which the implantable pulse generator is well suited. For applications requiring more channels (or higher composite operating frequencies) , two or more separate output stages might each be multiplexed to multiple (e.g., four) electrodes. e.
- the Lead Connection Header According to one desirable technical feature, the implantable pulse generator 18 desirably includes a lead connection header 14 for connecting the lead(s) 12 that will enable reliable and easy replacement of the lead/electrode (see Figs. 2A and 2B) , and includes a small antenna 54 for use with the wireless telemetry feature .
- the implantable pulse generator desirably incorporates a connection header (top header) 14 that is easy to use, reliable, and robust enough to allow multiple replacements of the implantable pulse generator after many years (e.g., more than ten years) of use.
- the surgical complexity of replacing an implantable pulse generator is usually low compared to the surgical complexity of correctly placing the implantable lead 12/electrode 16 in proximity to the target nerve/tissue and routing the lead 12 to the implantable pulse generator.
- the lead 12 and electrode 16 desirably has a service life of at least ten years with a probable service life of fifteen years or more. Based on the clinical application, the implantable pulse generator may not have this long a service life.
- the implantable pulse generator service life is largely determined by the power capacity of the Lithium Ion battery 22, and is likely to be three to ten years, based on the usage of the device. Desirably, the implantable pulse generator 18 has a service life of at least three years.
- the implantable pulse generator preferably will use a laser welded titanium case.
- the implantable lead(s) 12 connect to the implantable pulse generator through a molded or cast polymeric connection header 14 (top header) .
- Metal- ceramic or metal-glass feed-thrus maintain the hermetic seal of the titanium capsule while providing electrical contact to the electrical contacts of the lead 12/electrode 16.
- the standard implantable connectors may be similar in design and construction to the low-profile IS-1 connector system (per ISO 5841-3).
- the IS-1 connectors have been in use since the late 1980s and have been shown to be reliable and provide easy release and re-connection over several implantable pulse generator replacements during the service life of a single pacing lead.
- Full compatibility with the IS-1 standard, and mating with pacemaker leads, is not a requirement for the implantable pulse generator.
- the implantable pulse generator connection system may include a modification of the IS-1 connector system, which shrinks the axial length dimensions while keeping the format and radial dimensions of the IS-1.
- the top header 14 may incorporate one or more connection receptacles each of which accommodate leads with typically four conductors.
- connection header When two or more leads are accommodated by the header, these lead may exit the connection header in opposite directions (i.e., from opposite sides of the header) .
- These connectors can be similar to the banded axial connectors used by other multi-polar implantable pulse generators or may follow the guidance of the draft IS-4 implantable connector standard.
- the design of the implantable pulse generator housing and header 14 preferably includes provisions for adding the additional feed-thrus and larger headers for such indications.
- the inclusion of the UHF antenna 54 for the wireless telemetry inside the connection header (top header) 14 is necessary as the shielding offered by the titanium case will severely limit (effectively eliminate) radio wave propagation through the case.
- the antenna 54 connection will be made through a feed-thru similar to that used for the electrode connections.
- the wireless telemetry signal may be coupled inside the implantable pulse generator onto a stimulus output channel and coupled to the antenna 54 with passive filtering/coupling elements/methods in the connection header 14.
- the implantable pulse generator 18 desirably uses a standard, commercially available micro-power, flash programmable microcontroller 24 or processor core in an application specific integrated circuit (ASIC) .
- ASIC application specific integrated circuit
- This device or possibly more than one such device for a computationally complex application with sensor input processing
- other large semiconductor components may have custom packaging such as chip-on-board, solder flip chip, or adhesive flip chip to reduce circuit board real estate needs .
- a circuit diagram showing a desired configuration for the microcontroller 24 is shown in Fig. 11.
- the implantable pulse generator 18 desirably includes efficient power management circuitry as an element of the implantable pulse generator circuitry 20 shown in Fig. 6.
- the power management circuitry is generally responsible for the efficient distribution of power and monitoring the battery 22, and alternatively for the recovery of power from the RF magnetic field 52 and for charging and monitoring the rechargeable battery 72.
- the operation of the implantable pulse generator 18 can be described in terms of having operating modes as relating to the function of the power management circuitry. These modes may include, but are not limited to IPG Active, IPG Dormant, and alternatively, IPG Active and Charging.
- Fig. 12 shows one possible power management sub-circuit having MOSFET isolation between the battery 22 and the charger circuit.
- Fig. 13 shows another possible power management sub-circuit diagram without having MOSFET isolation between the battery 22 and the charger circuit.
- the leakage current of the disabled charge control integrated circuit chip (UI) must be very low to prevent this leakage current from discharging the battery 22 in all modes (including the Dormant Mode) .
- the description of these modes applies to both circuits . i .
- IPG Active Mode occurs when the implantable pulse generator 18 is operating normally. In this mode, the implantable pulse generator may be generating stimulus outputs or it may be waiting for the next request to generate stimulus in response to a timed neuromodulation sequence or a telemetry command from an external controller. In this mode, the implantable pulse generator is active (microcontroller 24 is powered and coordinating wireless communications and may be timing & controlling the generation and delivery of stimulus pulses) .
- IPG Active Mode In the IPG Active mode, as can be seen in Fig. 12, the lack of DC current from VRAW means that Q5 is held off. This, in turn, holds Q3 off and a portion of the power management circuitry is isolated from the battery 22. In Fig.
- IPG Dormant Mode occurs when the implantable pulse generator 18 is completely disabled (powered down) . In this mode, power is not being supplied to the microcontroller 24 or other enabled circuitry. This is the mode for the long-term storage of the implantable pulse generator before or after implantation.
- the dormant mode may only be exited by placing a pacemaker magnet (or comparable device) over the implantable pulse generator 18 for a predetermined amount of time, e.g., five seconds.
- the dormant mode may be exited by placing the rechargeable implantable pulse generator 68 into the Active and Charging mode by placing the implantable pulse generator charging coil 35 of a functional implantable pulse generator charger 34 in close proximity to the rechargeable implantable pulse generator 68.
- IPG Dormant Mode In the IPG Dormant mode, VBAT is not delivered to the remainder of the implantable pulse generator circuitry because Q4 is turned off. The Dormant mode is stable because the lack of VBAT means that VCC is also not present, and thus Q6 is not held on through R8 and RIO. Thus the battery 22 is completely isolated from all load circuitry (the VCC power supply and the VHH power supply) .
- the Dormant mode is entered through the application of a long magnet placement over SI (magnetic reed switch) or through the reception of a command by the wireless telemetry.
- the PortD4 which is normally configured as a microcontroller input, is configured as a logic output with a logic low (0) value.
- This discharges C8 through R12 and turns off Q6; which, in turn, turns off Q4 and forces the implantable pulse generator into the Dormant mode.
- R12 is much smaller in value than R10, thus the microcontroller 24 can force C8 to discharge even though VCC is still present.
- the lack of DC current from VRAW means that Q5 is held off.
- the IPG Active and Charging mode occurs when the rechargeable implantable pulse generator 68 is being charged. In this mode, the rechargeable implantable pulse generator 68 is active, i.e., the microcontroller 24 is powered and coordinating wireless communications and may be timing and controlling the generation and delivery of stimulus pulses.
- the rechargeable implantable pulse generator 68 may be communicating with the implantable pulse generator charger 34 concerning the magnitude of the battery voltage and the DC voltage recovered from the RF magnetic field 52.
- the charger 34 uses this data for two purposes : to provide feedback to the user about the proximity of the charging coil 35 to the implanted pulse generator, and to increase or decrease the strength of the RF magnetic field 52. This, in turn, minimizes the power losses and undesirable heating of the implantable pulse generator.
- the power management circuitry 40 serves the following primary functions : (1) provides battery power to the rest of the rechargeable implantable pulse generator circuitry 70, (2) recovers power from the RF magnetic field 52 generated by the implantable pulse generator charger 34, (3) provides controlled charging current (from the recovered power) to the rechargeable battery 72, and (4) communicates with the implantable pulse generator charger 34 via the wireless telemetry link 38 to provide feedback to the user positioning the charging coil 35 over the rechargeable implantable pulse generator 68, and to cause the implantable pulse generator charger 34 to increase or decrease the strength of its RF magnetic field 52 for optimal charging of the rechargeable implantable pulse generator battery 72 (Lithium Ion battery) .
- iii (a) Principles of Operation, IPG Active and Charging Mode iii (a) (1) RF voltage is induced in the Receive Coil by the RF magnetic field 52 of the implantable pulse generator charger 34 iii (a) (2) Capacitor Cl is in series with the Receive Coil and is selected to introduce a capacitive reactance that compensates (subtracts) the inductive reactance of the Receive Coil iii (a) (3) Dl - D2 form a full wave rectifier that converts the AC voltage recovered by the Receive Coil into a pulsating DC current flow iii (a) (4) This pulsating DC current is smoothed (filtered) by C3 (this filtered DC voltage is labeled VRAW) iii (a) (5) D4 is a zener diode that acts as a voltage limiting device (in normal operation, D4 is not conducting significant current) iii (a) (6) D3 prevents the flow of current from the rechargeable battery 72 from
- UI is a micropower, Lithium Ion Charge Management Controller chip implementing a constant current phase and constant voltage phase charge regime. This chip desirably incorporates an internal voltage reference of high accuracy (+/- 0.5%) to establish the constant voltage charge level .
- UI performs the following functions : monitors the voltage drop across a series resistor R2 (effectively the current charging the rechargeable battery 72) to control the current delivered to the battery through the external pass transistor Q2.
- UI uses this voltage across R2 to establish the current of the constant current phase (typically the battery capacity divided by five hours) and decreases the current charging the battery as required to limit the battery voltage and effectively transition from constant current phase to constant voltage phase as the battery voltage approaches the terminal voltage, iii (a)
- UI also includes provisions for timing the duration of the constant current and constant voltage phases and suspends the application of current to the rechargeable battery 72 if too much time is spent in the phase. These fault timing features of UI are not used in normal operation.
- the constant voltage phase of the battery charging sequence is timed by the microcontroller 24 and not by UI .
- the microcontroller monitors the battery 5 voltage and terminates the charging sequence (i.e., tells the implantable pulse generator charger 34 that the rechargeable implantable pulse generator battery 72 is fully charged) after the battery voltage has been in the
- the rechargeable battery 72, and the disabled current of this chip is a load on the rechargeable battery 72 in all modes (including the dormant mode) . This, in turn, is a more demanding requirement on the current
- FI is a fuse that protects against long- duration, high current component failures. In all anticipated transient high current failures, (i.e., soft failures that cause the
- the VBAT circuitry will disconnect the rechargeable battery 72 from the temporary high load without blowing the fuse.
- the specific sequence is: • High current flows into a component (s) powered by VBAT (most likely the VHH power supply or an element powered by the VCC power supply) .
- the rechargeable implantable pulse generator 68 is now stable in the Dormant Mode, i.e., VBAT is disconnected from the rechargeable battery 72 by a turned OFF Q4.
- the only load remaining on the battery is presented by the charging circuit and by the analog multiplexer (switches) U3 that are used to direct an analog voltage to the microcontroller 24 for monitoring the battery voltage and (by subtracting the voltage after the resistance of FI) an estimate of the current consumption of the entire circuit.
- a failure of these voltage monitoring circuits is not protected by the fuse, but resistance values limit the current flow to safe levels even in the event of component failures.
- a possible source of a transient high-current circuit failure is the SCR latchup or supply-to- ground short failure of a semiconductor device directly connected to VBAT or VCC.
- R9 & Rll form a voltage divider to convert VRAW (OV to 8V) into the voltage range of the microcontroller's A-D inputs (used for closed loop control of the RF magnetic field strength)
- iii (a) (14)
- R8 and C9 form the usual R-C reset input circuit for the microcontroller 24; this circuit causes a hardware reset when the magnetic reed switch (SI) is closed by the application of a suitable static magnetic field for a short duration
- iii (a) (15) RIO and C8 form a much slower time constant that allows the closure of the reed switch by the application of the static magnetic field for a long duration to force the rechargeable implantable pulse generator 68 into the Dormant mode by turning OFF Q6 and thus turning OFF Q4.
- Fig . 6 shows an embodiment of a block diagram circuit 20 for the primary cell implantable pulse generator 18 that takes into account the desirable technical features discussed above.
- Fig. 7 shows an embodiment of a block diagram circuit 70 for the rechargeable implantable pulse generator 68 that also takes into account the desirable technical features discussed above. Both the circuit 20 and the circuit 70 can be grouped into functional blocks, which generally correspond to the association and interconnection of the electronic components.
- Figs. 6 and 7 show alternative embodiments of a block diagram that provides an overview of a representative desirable implantable pulse generator design.
- circuit 20 there may be re-use of the circuit 20, or alternatively, portions of the circuit 20 of the primary cell implantable pulse generator 18, with minimal modifications, e.g., a predetermined selection of components may be included or may be exchanged for other components, and minimal changes to the operating firmware.
- Re-use of a majority of the circuitry from the primary cell implantable pulse generator 18 and much of the firmware from the primary cell implantable pulse generator 18 allows for a low development cost for the rechargeable implantable pulse generator 68 having a secondary cell 72.
- the Microcontroller 24 is responsible for the following functions: (1) The timing and sequencing of the stimulator stage and the VHH power supply used by the stimulator stage, (2) The sequencing and timing of power management functions, (3) The monitoring of the battery voltage, the stimulator voltages produced during the generation of stimulus pulses, and the total circuit current consumption, VHH, and VCC, (4) The timing, control, and interpretation of commands to and from the wireless telemetry circuit, (5) The logging (recording) of patient usage data as well as clinician programmed stimulus parameters and configuration data, and (6) The processing of commands (data) received from the user (patient) via the wireless link to modify the characteristics of the stimulus being delivered.
- a microcontroller incorporating flash programmable memory allows the operating program of the implantable pulse generator as well as the stimulus parameters and settings to be stored in non-volatile memory (data remains safely stored even if the battery 22 becomes fully discharged; or if the implantable pulse generator is placed in the Dormant Mode) . Yet, the data (operating program, stimulus parameters, usage history log, etc.) can be erased and reprogrammed thousands of times during the life of the implantable pulse generator.
- the software (firmware) of the implantable pulse generator must be segmented to support the operation of the wireless telemetry routines while the flash memory of the microcontroller 24 is being erased and reprogrammed.
- the VCC power supply 42 must support the power requirements of the microcontroller 24 during the flash memory erase and program operations .
- the microcontroller 24 may be a single component, the firmware is developed as a number of separate modules that deal with specific needs and hardware peripherals. The functions and routines of these software modules are executed sequentially; but the execution of these modules are timed and coordinated so as to effectively function simultaneously. The microcontroller operations that are associated directly with a given hardware functional block are described with that block.
- the Components of the Microcontroller Circuit may include : (1) A single chip microcontroller 24. This component may be a member of the Texas Instruments MSP430 family of flash programmable, micro-power, highly integrated mixed signal microcontroller.
- MSP430F1610 Likely family members to be used include the MSP430F1610, MSP430F1611, MSP430F1612, MSP430F168, and the MSP430F169.
- Each of these parts has numerous internal peripherals, and a micropower internal organization that allows unused peripherals to be configured by minimal power dissipation, and an instruction set that supports bursts of operation separated by intervals of sleep where the microcontroller suspends most functions.
- a miniature, quartz crystal (XI) for establishing precise timing of the microcontroller. This may be a 32.768KHz quartz crystal.
- Miscellaneous power decoupling and analog signal filtering capacitors b.
- the Power Management Circuit 40 (including associated microcontroller actions) is responsible for the following functions: (1) monitor the battery voltage, (2) suspend stimulation when the battery voltage becomes very low, and/or suspend all operation (go into the Dormant Mode) when the battery voltage becomes critically low, (3) communicate (through the wireless telemetry link 38) with the external equipment the charge status of the battery 22, (4) prevent (with single fault tolerance) the delivery of excessive current from the battery 22, (5) provide battery power to the rest of the circuitry of the implantable pulse generator, i.e., VCC and VHH power supplies, (6) provide isolation of the Lithium Ion battery 22 from other circuitry while in the Dormant Mode, (7) provide a hard microprocessor reset and force entry into the Dormant Mode in the presence of a pacemaker magnet (or comparable device) , and (8) provide the microcontroller 24 with analog voltages with which to measure the magnitude of the battery voltage and the appropriate battery current flow
- Alternative responsibilities for the Power Management Circuitry may include: (1) recover power from the Receive Coil, (2) control delivery of the Receive Coil power to recharge the Lithium Ion secondary battery 72, (3) monitor the battery voltage during charge and discharge conditions, (4) communicate (through the wireless telemetry link 38) with the externally mounted implantable pulse generator charger 34 to increase or decrease the strength of the RF magnetic field 52 for optimal charging of the rechargeable battery 72, (5) disable (with single fault tolerance) the delivery of charging current to the rechargeable battery 72 in overcharge conditions, and (6) provide the microcontroller 24 with analog voltages with which to measure the magnitude of the recovered power from the RF magnetic field 52.
- the Components of the Power Management Circuit may include : (1) Low on resistance, low threshold P channel MOSFETs with very low off state leakage current (Q2, Q3 , and Q4) . (2) Analog switches (or an analog multiplexer) U3. (3) Logic translation N-channel MOSFETs (Q5 & Q6) with very low off state leakage current.
- Alternative components of the Power Management Circuit may include: (1) The Receive Coil, which desirably is a multi- turn, fine copper wire coil near the inside perimeter of the rechargeable implantable pulse generator 68.
- the receive coil includes a predetermined construction, e.g., 300 turns of four strands of #40 enameled magnetic wire, or the like.
- the VCC Power Supply 42 is generally responsible for the following functions: (1) Some of the time, the VCC power supply passes the battery voltage to the circuitry powered by VCC, such as the microcontroller 24, stimulator output stage 46, wireless telemetry circuitry 50, etc.
- the VCC power supply fractionally steps up the voltage to about 3.3V; (other useable voltages include 3.0V, 2.7V, etc.) despite changes in the Lithium Ion battery 22 voltage. This higher voltage is required for some operations such as programming or erasing the flash memory in the microcontroller 24, (i.e., in circuit programming).
- the voltage converter / switch part at the center of the VCC power supply may be a charge pump DC to DC converter. Typical choices for this part may include the Maxim MAX1759, the Texas Instruments TPS60204, or the Texas Instruments REG710, among others.
- the VCC power supply may include a micropower, low drop out, linear voltage regulator; e.g., Microchip NCP1700T-3302 , Maxim Semiconductor MAX1725, or Texas Instruments TPS79730.
- the characteristics of the VCC Power Supply might include: (1) high efficiency and low quiescent current, i.e., the current wasted by the power supply in its normal operation. This value should be less than a few microamperes; and (2) drop-out voltage, i.e., the minimal difference between the VBAT supplied to the VCC power supply and its output voltage. This voltage may be less than about lOOmV even at the current loads presented by the transmitter of the wireless telemetry circuitry 50.
- VCC power supply 42 may allows in-circuit reprogramming of the implantable pulse generator firmware, or optionally, the implantable pulse generator 18 may not use a VCC power supply, which may not allow in-circuit reprogramming of the implantable pulse generator firmware.
- VHH Power Supply A circuit diagram showing a desired configuration for the VHH power supply 44 is shown in Fig. 14. It is to be appreciated that modifications to this circuit diagram configuration which produce the same or similar functions as described are within the scope of the invention.
- the VHH Power Supply 44 is generally responsible for the following functions: (1) Provide the Stimulus Output Stage 46 and the Output Multiplexer 48 with a programmable DC voltage between the battery voltage and a voltage high enough to drive the required cathodic phase current through the electrode circuit plus the voltage drops across the stimulator stage, the output multiplexer stage, and the output coupling capacitor.
- VHH is typically 12VDC or less for neuromodulation applications; and 25V or less for muscle stimulation applications.
- the Components of the VHH Power Supply might include: (1) Micropower, inductor based (fly-back topology) switch mode power supply (U10) ; e.g., Texas Instruments TPS61045, Texas Instruments TPS61041, or Linear Technology LT3464 with external voltage adjustment components.
- L6 is the flyback energy storage inductor.
- C42 & C43 form the output capacitor.
- R27, R28, and R29 establish the operating voltage range for VHH given the internal DAC which is programmed via the SETVHH logic command from the microcontroller 24.
- Diode D9 serves no purpose in normal operation and is added to offer protection from over-voltage in the event of a VHH circuit failure .
- the microcontroller 24 monitors VHH for detection of a VHH power supply failure, system failures, and optimizing VHH for the exhibited electrode circuit impedance . e.
- the Stimulus Output Stage (s) 46 is responsible for the following functions: (1) Generate the identified biphasic stimulus current with programmable (dynamically adjustable during use) cathodic phase amplitude, pulse width, and frequency.
- the recovery phase may incorporate a maximum current limit; and there may be a delay time (most likely a fixed delay) between the cathodic phase and the recovery phase (see Fig. 10) .
- Typical currents (cathodic phase) for neuromodulation applications are 1mA to 10mA; and 2mA to 20mA for muscle stimulation applications. .
- stimulus amplitudes of less than 1mA might be necessary.
- Electrode circuit impedances can vary with the electrode and the application, but are likely to be less than 2,000 ohms and greater than 100 ohms across a range of electrode types.
- the Components of the Stimulus Output Stage may include : (1) The cathodic phase current through the electrode circuit is established by a high gain (HFE) NPN transistor (Q7) with emitter degeneration. In this configuration, the collector current of the transistor (Q7) is defined by the base drive voltage and the value of the emitter resistor (R24) . Two separate configurations are possible: In the first configuration (as shown in Fig.
- the base drive voltage is provided by a DAC peripheral inside the microcontroller 24 and is switched on and off by a timer peripheral inside the microcontroller. This switching function is performed by an analog switch (U8) .
- the emitter resistor (R24) is fixed in value and fixed to ground.
- the base drive voltage is a fixed voltage pulse (e.g., a logic level pulse) and the emitter resistor is manipulated under microcontroller control .
- Typical options may include resistor (s) terminated by microcontroller 10 port pins that are held or pulsed low, high, or floating; or an external MOSFET that pulls one or more resistors from the emitter to ground under program control .
- the pulse timing need only be applied to the base drive logic; the timing of the emitter resistor manipulation is not critical.
- the transistor (Q7) desirably is suitable for operation with VHH on the collector.
- the cathodic phase current through the electrode circuit is established by the voltage drop across the emitter resistor. Diode D7, if used, provides a degree of temperature compensation to this circuit.
- the microcontroller 24 (preferably including a programmable counter/timer peripheral) generates stimulus pulse timing to generate the cathodic and recovery phases and the interphase delay.
- the microcontroller 24 also monitors the cathode voltage to confirm the correct operation of the output coupling capacitor, to detect system failures, and to optimize VHH for the exhibited electrode circuit impedance; i.e., to measure the electrode circuit impedance. Additionally, the microcontroller 24 can also monitor the pulsing voltage on the emitter resistor; this allows the fine adjustment of low stimulus currents (cathodic phase amplitude) through changes to the DAC value . f.
- the Output Multiplexer 48 is responsible for the following functions : (1) Route the Anode and Cathode connections of the Stimulus Output Stage 46 to the appropriate electrode based on addressing data provided by the microcontroller 24.
- the circuit shown in Fig. 9 may be configured to provide monopolar stimulation (using the case 26 as the return electrode) to Electrode 1, to Electrode 2, or to both through time multiplexing.
- This circuit could also be configured as a single bipolar output channel by changing the hardwire connection between the circuit board and the electrode; i.e., by routing the CASE connection to Electrode 1 or Electrode 2.
- the use of four or more channels per multiplexer stage (i.e., per output coupling capacitor) is possible.
- the Components of the Output Multiplexer might include : (1) An output coupling capacitor in series with the electrode circuit. This capacitor is desirably located such that there is no DC across the capacitor in steady state. This capacitor is typically charged by the current flow during the cathodic phase to a voltage range of about l/4th to 1/lOth of the voltage across the electrode circuit during the cathodic phase. Similarly, this capacitor is desirably located in the circuit such that the analog switches do not experience voltages beyond their ground of power supply (VHH) . (2) The analog switches (U7) must have a suitably high operating voltage, low ON resistance, and very low quiescent current consumption while being driven from the specified logic levels .
- Suitable analog switches include the Vishay/Siliconix DG412HS, for example.
- Microcontroller 24 selects the electrode connections to carry the stimulus current (and time the interphase delay) via address lines.
- Other analog switches U9 may be used to sample the voltage of VHH, the CASE, and the selected
- the Wireless Telemetry circuit 50 is responsible for the following functions : (1) Provide reliable, bidirectional communications (half duplex) with an external controller, programmer, or an optional charger 34, for example, via a VHF-UHF RF link (likely in the 403MHZ to 406MHz MICS band per FCC 47 CFR Part 95 and the Ultra Low Power - Active Medical Implant (AMI) regulations of the European Union) .
- This circuit will look for RF commands at precisely timed intervals (e.g., twice a second), and this function must consume very little power. Much less frequently this circuit will transmit to the external controller.
- the RF carrier is amplitude modulated (on-off keyed) with the digital data.
- Serial data is generated by the microcontroller 24 already formatted and timed.
- the wireless telemetry circuit 50 converts the serial data stream into a pulsing carrier signal during the transit process; and it converts a varying RF signal strength into a serial data stream during the receive process .
- the Components of the Wireless Telemetry Circuit might include: (1) a crystal controlled, micropower transceiver chip such as the AMI Semiconductor AMIS-52100 (U6) .
- This chip is responsible for generating the RF carrier during transmissions and for amplifying, receiving, and detecting (converting to a logic level) the received RF signals.
- the transceiver chip must also be capable of quickly starting and stopping operation to minimize power consumption by keeping the chip disabled (and consuming very little power) the majority of the time; and powering up for only as long as required for the transmitting or receiving purpose.
- the transceiver chip has separate transmit and receive ports that must be switched to a single antenna/feedthru. This function is performed by the transmit/receive switch (U5) under microcontroller control via the logic line XMIT.
- the microcontroller 24 controls the operation of the transceiver chip via an I 2 C serial communications link.
- the serial data to and from the transceiver chip may be handled by a UART or a SPI peripheral of the microcontroller.
- the message encoding/decoding and error detection may be performed by a separate, dedicated microcontroller; else this processing will be time shared with the other tasks of the only microcontroller.
- the various inductor and capacitor components (U6) surrounding the transceiver chip and the transmit/receive switch (U5) are impedance matching components and harmonic filtering components, except as follows: (1) X2, C33 and C34 are used to generate the crystal controlled carrier, desirably tuned to the carrier frequency divided by thirty-two, (2) L4 and C27 form the tuned elements of a VCO (voltage controlled oscillator) operating at twice the carrier frequency, and (3) R20, C29, and C30 are filter components of the
- PLL phase locked loop
- the implantable pulse generator 18 and the alternative embodiment rechargeable implantable pulse generator 68 as described in section I can be used to provide beneficial results in diverse therapeutic and functional restorations indications .
- possible indications for use of the implantable pulse generators 18 and 68 include the treatment of (i) urinary and fecal incontinence; (ii) micturition/retention; (iii) restoration of sexual function; (iv) defecation/constipation; (v) pelvic floor muscle activity; and/or (vi) pelvic pain.
- the implantable pulse generators 18 and 68 can be used for deep brain stimulation in the treatment of (i) Parkinson's disease; (ii) multiple sclerosis; (iii) essential tremor; (iv) depression; (v) eating disorders; (vi) epilepsy; and/or (vii) minimally conscious state.
- the implantable pulse generators 18 and 68 can be used for pain management by interfering with or blocking pain signals from reaching the brain, in the treatment of, e.g., (i) peripheral neuropathy; and/or (ii) cancer.
- the implantable pulse generators 18 and 68 can be used for vagal nerve stimulation for control of epilepsy, depression, or other mood/psychiatric disorders.
- the implantable pulse generators 18 and 68 can be used for the treatment of obstructive sleep apnea.
- the implantable pulse generators 18 and 68 can be used for gastric stimulation to prevent reflux or to reduce appetite or food consumption.
- the implantable pulse generators 18 and 68 can be used in functional restorations indications such as the restoration of motor control, to restore (i) impaired gait after stroke or spinal cord injury (SCI) ; (ii) impaired hand and arm function after stroke or SCI; (iii) respiratory disorders; (iv) swallowing disorders; (v) sleep apnea; and/or (vi) neurotherapeutics, allowing individuals with neurological deficits, such as stroke survivors or those with multiple sclerosis, to recover functionally.
Abstract
Description
Claims
Applications Claiming Priority (8)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US57874204P | 2004-06-10 | 2004-06-10 | |
US60/578,742 | 2004-06-10 | ||
US59919304P | 2004-08-05 | 2004-08-05 | |
US60/599,193 | 2004-08-05 | ||
US68059805P | 2005-05-13 | 2005-05-13 | |
US60/680,598 | 2005-05-13 | ||
US11/150,535 US7813809B2 (en) | 2004-06-10 | 2005-06-10 | Implantable pulse generator for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue |
US11/150,418 US7239918B2 (en) | 2004-06-10 | 2005-06-10 | Implantable pulse generator for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue |
Publications (2)
Publication Number | Publication Date |
---|---|
WO2005123181A2 true WO2005123181A2 (en) | 2005-12-29 |
WO2005123181A3 WO2005123181A3 (en) | 2006-11-16 |
Family
ID=36941828
Family Applications (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2005/020480 WO2006022993A2 (en) | 2004-06-10 | 2005-06-10 | Implantable generator for muscle and nerve stimulation |
PCT/US2005/020474 WO2005123185A1 (en) | 2004-06-10 | 2005-06-10 | Implantable system for processing myoelectric signals |
PCT/US2005/020506 WO2005123181A2 (en) | 2004-06-10 | 2005-06-10 | Implantable pulse generator for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue |
Family Applications Before (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2005/020480 WO2006022993A2 (en) | 2004-06-10 | 2005-06-10 | Implantable generator for muscle and nerve stimulation |
PCT/US2005/020474 WO2005123185A1 (en) | 2004-06-10 | 2005-06-10 | Implantable system for processing myoelectric signals |
Country Status (2)
Country | Link |
---|---|
US (4) | US7283867B2 (en) |
WO (3) | WO2006022993A2 (en) |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8131377B2 (en) | 2007-07-11 | 2012-03-06 | Boston Scientific Neuromodulation Corporation | Telemetry listening window management for an implantable medical device |
Families Citing this family (568)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9320900B2 (en) | 1998-08-05 | 2016-04-26 | Cyberonics, Inc. | Methods and systems for determining subject-specific parameters for a neuromodulation therapy |
US7747325B2 (en) | 1998-08-05 | 2010-06-29 | Neurovista Corporation | Systems and methods for monitoring a patient's neurological disease state |
US9375573B2 (en) | 1998-08-05 | 2016-06-28 | Cyberonics, Inc. | Systems and methods for monitoring a patient's neurological disease state |
US9042988B2 (en) | 1998-08-05 | 2015-05-26 | Cyberonics, Inc. | Closed-loop vagus nerve stimulation |
US9415222B2 (en) | 1998-08-05 | 2016-08-16 | Cyberonics, Inc. | Monitoring an epilepsy disease state with a supervisory module |
US8762065B2 (en) | 1998-08-05 | 2014-06-24 | Cyberonics, Inc. | Closed-loop feedback-driven neuromodulation |
US20080077192A1 (en) | 2002-05-03 | 2008-03-27 | Afferent Corporation | System and method for neuro-stimulation |
WO2003095018A2 (en) | 2002-05-09 | 2003-11-20 | Daemen College | Electrical stimulation unit and waterbath system |
US7993108B2 (en) | 2002-10-09 | 2011-08-09 | Abbott Diabetes Care Inc. | Variable volume, shape memory actuated insulin dispensing pump |
US7727181B2 (en) | 2002-10-09 | 2010-06-01 | Abbott Diabetes Care Inc. | Fluid delivery device with autocalibration |
EP2322798A1 (en) | 2002-10-09 | 2011-05-18 | Abbott Diabetes Care Inc. | Device and method for delivering medical fluids using a shape memory alloy |
US7373206B2 (en) * | 2002-10-31 | 2008-05-13 | Medtronic, Inc. | Failsafe programming of implantable medical devices |
US7811231B2 (en) | 2002-12-31 | 2010-10-12 | Abbott Diabetes Care Inc. | Continuous glucose monitoring system and methods of use |
US8771183B2 (en) | 2004-02-17 | 2014-07-08 | Abbott Diabetes Care Inc. | Method and system for providing data communication in continuous glucose monitoring and management system |
US7587287B2 (en) | 2003-04-04 | 2009-09-08 | Abbott Diabetes Care Inc. | Method and system for transferring analyte test data |
US7679407B2 (en) | 2003-04-28 | 2010-03-16 | Abbott Diabetes Care Inc. | Method and apparatus for providing peak detection circuitry for data communication systems |
US8066639B2 (en) * | 2003-06-10 | 2011-11-29 | Abbott Diabetes Care Inc. | Glucose measuring device for use in personal area network |
US7797058B2 (en) * | 2004-08-04 | 2010-09-14 | Ndi Medical, Llc | Devices, systems, and methods employing a molded nerve cuff electrode |
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 |
US8467875B2 (en) | 2004-02-12 | 2013-06-18 | Medtronic, Inc. | Stimulation of dorsal genital nerves to treat urologic dysfunctions |
US8086318B2 (en) * | 2004-02-12 | 2011-12-27 | Ndi Medical, Llc | Portable assemblies, systems, and methods for providing functional or therapeutic neurostimulation |
US8165692B2 (en) | 2004-06-10 | 2012-04-24 | Medtronic Urinary Solutions, Inc. | Implantable pulse generator power management |
US7761167B2 (en) | 2004-06-10 | 2010-07-20 | Medtronic Urinary Solutions, Inc. | Systems and methods for clinician control of stimulation systems |
US9308382B2 (en) | 2004-06-10 | 2016-04-12 | Medtronic Urinary Solutions, Inc. | Implantable pulse generator systems and methods for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue |
US9205255B2 (en) | 2004-06-10 | 2015-12-08 | Medtronic Urinary Solutions, Inc. | Implantable pulse generator systems and methods for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue |
US7283867B2 (en) * | 2004-06-10 | 2007-10-16 | Ndi Medical, Llc | Implantable system and methods for acquisition and processing of electrical signals from muscles and/or nerves and/or central nervous system tissue |
US8195304B2 (en) | 2004-06-10 | 2012-06-05 | Medtronic Urinary Solutions, Inc. | Implantable systems and methods for acquisition and processing of electrical signals |
US7648441B2 (en) * | 2004-11-10 | 2010-01-19 | Silk Jeffrey E | Self-contained real-time gait therapy device |
US9636450B2 (en) | 2007-02-19 | 2017-05-02 | Udo Hoss | Pump system modular components for delivering medication and analyte sensing at seperate insertion sites |
US7697967B2 (en) | 2005-12-28 | 2010-04-13 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor insertion |
WO2006102412A2 (en) | 2005-03-21 | 2006-09-28 | Abbott Diabetes Care, Inc. | Method and system for providing integrated medication infusion and analyte monitoring system |
US20070007285A1 (en) * | 2005-03-31 | 2007-01-11 | Mingui Sun | Energy delivery method and apparatus using volume conduction for medical applications |
US8912908B2 (en) | 2005-04-28 | 2014-12-16 | Proteus Digital Health, Inc. | Communication system with remote activation |
US9198608B2 (en) | 2005-04-28 | 2015-12-01 | Proteus Digital Health, Inc. | Communication system incorporated in a container |
US8836513B2 (en) | 2006-04-28 | 2014-09-16 | Proteus Digital Health, Inc. | Communication system incorporated in an ingestible product |
EP3827747A1 (en) | 2005-04-28 | 2021-06-02 | Otsuka Pharmaceutical Co., Ltd. | Pharma-informatics system |
US8730031B2 (en) | 2005-04-28 | 2014-05-20 | Proteus Digital Health, Inc. | Communication system using an implantable device |
US8802183B2 (en) | 2005-04-28 | 2014-08-12 | Proteus Digital Health, Inc. | Communication system with enhanced partial power source and method of manufacturing same |
US8112240B2 (en) | 2005-04-29 | 2012-02-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing leak detection in data monitoring and management systems |
CA2966418A1 (en) * | 2005-05-03 | 2006-11-09 | The University Of Western Ontario | An oral device and kit for use in association therewith |
US7768408B2 (en) | 2005-05-17 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US7644714B2 (en) | 2005-05-27 | 2010-01-12 | Apnex Medical, Inc. | Devices and methods for treating sleep disorders |
US7620437B2 (en) * | 2005-06-03 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and apparatus for providing rechargeable power in data monitoring and management systems |
US7813803B2 (en) * | 2005-06-09 | 2010-10-12 | Medtronic, Inc. | Regional therapies for treatment of pain |
US20070299483A1 (en) * | 2005-06-10 | 2007-12-27 | Ndi Medical, Inc. | Implantable pulse generator for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue |
US8639329B2 (en) | 2005-08-30 | 2014-01-28 | Georgia Tech Research Corporation | Circuits and methods for artifact elimination |
US8547248B2 (en) | 2005-09-01 | 2013-10-01 | Proteus Digital Health, Inc. | Implantable zero-wire communications system |
US8951190B2 (en) | 2005-09-28 | 2015-02-10 | Zin Technologies, Inc. | Transfer function control for biometric monitoring system |
US8764654B2 (en) | 2008-03-19 | 2014-07-01 | Zin Technologies, Inc. | Data acquisition for modular biometric monitoring system |
US8880138B2 (en) | 2005-09-30 | 2014-11-04 | Abbott Diabetes Care Inc. | Device for channeling fluid and methods of use |
US7756561B2 (en) | 2005-09-30 | 2010-07-13 | Abbott Diabetes Care Inc. | Method and apparatus for providing rechargeable power in data monitoring and management systems |
WO2007044540A2 (en) * | 2005-10-05 | 2007-04-19 | Tolli William D | Electronic communication devices and methods |
US9014798B2 (en) * | 2005-10-20 | 2015-04-21 | Neurometrix, Inc. | Automated stimulus artifact removal for nerve conduction studies |
US7583190B2 (en) | 2005-10-31 | 2009-09-01 | Abbott Diabetes Care Inc. | Method and apparatus for providing data communication in data monitoring and management systems |
US7766829B2 (en) | 2005-11-04 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and system for providing basal profile modification in analyte monitoring and management systems |
US7423496B2 (en) | 2005-11-09 | 2008-09-09 | Boston Scientific Scimed, Inc. | Resonator with adjustable capacitance for medical device |
US8725243B2 (en) | 2005-12-28 | 2014-05-13 | Cyberonics, Inc. | Methods and systems for recommending an appropriate pharmacological treatment to a patient for managing epilepsy and other neurological disorders |
US11298058B2 (en) | 2005-12-28 | 2022-04-12 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor insertion |
US8868172B2 (en) | 2005-12-28 | 2014-10-21 | Cyberonics, Inc. | Methods and systems for recommending an appropriate action to a patient for managing epilepsy and other neurological disorders |
EP1979042A4 (en) * | 2006-01-16 | 2009-12-30 | Continence Control Systems Int | A stimulator for the control of a bodily function |
US20100191306A1 (en) * | 2006-01-25 | 2010-07-29 | Greatbatch Ltd. | Transient voltage suppression circuit for an implanted rfid chip |
US7736310B2 (en) | 2006-01-30 | 2010-06-15 | Abbott Diabetes Care Inc. | On-body medical device securement |
US8344966B2 (en) | 2006-01-31 | 2013-01-01 | Abbott Diabetes Care Inc. | Method and system for providing a fault tolerant display unit in an electronic device |
EP1815784A1 (en) * | 2006-02-06 | 2007-08-08 | Mashhour Mustafa Moh'd Bani Amer | System with intelligent cable-less transducers for monitoring and analysing biosignals |
WO2007098200A2 (en) * | 2006-02-16 | 2007-08-30 | Imthera Medical, Inc. | An rfid-based apparatus, system, and method for therapeutic treatment of obstructive sleep apnea |
US7981034B2 (en) | 2006-02-28 | 2011-07-19 | Abbott Diabetes Care Inc. | Smart messages and alerts for an infusion delivery and management system |
US7826879B2 (en) | 2006-02-28 | 2010-11-02 | Abbott Diabetes Care Inc. | Analyte sensors and methods of use |
US7653425B2 (en) | 2006-08-09 | 2010-01-26 | Abbott Diabetes Care Inc. | Method and system for providing calibration of an analyte sensor in an analyte monitoring system |
US9392969B2 (en) | 2008-08-31 | 2016-07-19 | Abbott Diabetes Care Inc. | Closed loop control and signal attenuation detection |
US8226891B2 (en) | 2006-03-31 | 2012-07-24 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods therefor |
US20090171178A1 (en) * | 2006-03-31 | 2009-07-02 | Abbott Diabetes Care, Inc. | Method and System for Powering an Electronic Device |
US7620438B2 (en) | 2006-03-31 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and system for powering an electronic device |
US7618369B2 (en) | 2006-10-02 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and system for dynamically updating calibration parameters for an analyte sensor |
US8374668B1 (en) | 2007-10-23 | 2013-02-12 | Abbott Diabetes Care Inc. | Analyte sensor with lag compensation |
US8140312B2 (en) | 2007-05-14 | 2012-03-20 | Abbott Diabetes Care Inc. | Method and system for determining analyte levels |
US8346335B2 (en) | 2008-03-28 | 2013-01-01 | Abbott Diabetes Care Inc. | Analyte sensor calibration management |
US8473022B2 (en) | 2008-01-31 | 2013-06-25 | Abbott Diabetes Care Inc. | Analyte sensor with time lag compensation |
JP2009544338A (en) | 2006-05-02 | 2009-12-17 | プロテウス バイオメディカル インコーポレイテッド | Treatment regimen customized to the patient |
US9480846B2 (en) * | 2006-05-17 | 2016-11-01 | Medtronic Urinary Solutions, Inc. | Systems and methods for patient control of stimulation systems |
JP2009537226A (en) * | 2006-05-18 | 2009-10-29 | エヌディーアイ メディカル, エルエルシー | Portable assembly, system, and method for providing functional or therapeutic neural stimulation |
US9020597B2 (en) | 2008-11-12 | 2015-04-28 | Endostim, Inc. | Device and implantation system for electrical stimulation of biological systems |
US7385498B2 (en) * | 2006-05-19 | 2008-06-10 | Delphi Technologies, Inc. | Wristband reader apparatus for human-implanted radio frequency identification device |
US8463393B2 (en) * | 2006-06-22 | 2013-06-11 | Medtronic, Inc. | Implantable medical devices having a liquid crystal polymer housing |
EP2034885A4 (en) | 2006-06-23 | 2010-12-01 | Neurovista Corp | Minimally invasive monitoring systems and methods |
US8206296B2 (en) | 2006-08-07 | 2012-06-26 | Abbott Diabetes Care Inc. | Method and system for providing integrated analyte monitoring and infusion system therapy management |
US20080082144A1 (en) * | 2006-09-29 | 2008-04-03 | James Marcotte | Universal usb-based telemetry rf head |
US9345879B2 (en) | 2006-10-09 | 2016-05-24 | Endostim, Inc. | Device and implantation system for electrical stimulation of biological systems |
US20150224310A1 (en) | 2006-10-09 | 2015-08-13 | Endostim, Inc. | Device and Implantation System for Electrical Stimulation of Biological Systems |
US9724510B2 (en) | 2006-10-09 | 2017-08-08 | Endostim, Inc. | System and methods for electrical stimulation of biological systems |
US11577077B2 (en) | 2006-10-09 | 2023-02-14 | Endostim, Inc. | Systems and methods for electrical stimulation of biological systems |
US7797041B2 (en) * | 2006-10-11 | 2010-09-14 | Cardiac Pacemakers, Inc. | Transcutaneous neurostimulator for modulating cardiovascular function |
US7797046B2 (en) * | 2006-10-11 | 2010-09-14 | Cardiac Pacemakers, Inc. | Percutaneous neurostimulator for modulating cardiovascular function |
US9186511B2 (en) | 2006-10-13 | 2015-11-17 | Cyberonics, Inc. | Obstructive sleep apnea treatment devices, systems and methods |
US8855771B2 (en) | 2011-01-28 | 2014-10-07 | Cyberonics, Inc. | Screening devices and methods for obstructive sleep apnea therapy |
US9205262B2 (en) | 2011-05-12 | 2015-12-08 | Cyberonics, Inc. | Devices and methods for sleep apnea treatment |
US9744354B2 (en) | 2008-12-31 | 2017-08-29 | Cyberonics, Inc. | Obstructive sleep apnea treatment devices, systems and methods |
US8417343B2 (en) | 2006-10-13 | 2013-04-09 | Apnex Medical, Inc. | Obstructive sleep apnea treatment devices, systems and methods |
US9913982B2 (en) | 2011-01-28 | 2018-03-13 | Cyberonics, Inc. | Obstructive sleep apnea treatment devices, systems and methods |
US8054140B2 (en) | 2006-10-17 | 2011-11-08 | Proteus Biomedical, Inc. | Low voltage oscillator for medical devices |
WO2008048321A1 (en) * | 2006-10-18 | 2008-04-24 | Boston Scientific Neuromodulation Corporation | Multi-electrode implantable stimulator device with a single current path decoupling capacitor |
US7881803B2 (en) | 2006-10-18 | 2011-02-01 | Boston Scientific Neuromodulation Corporation | Multi-electrode implantable stimulator device with a single current path decoupling capacitor |
US7979126B2 (en) * | 2006-10-18 | 2011-07-12 | Boston Scientific Neuromodulation Corporation | Orientation-independent implantable pulse generator |
KR101611240B1 (en) | 2006-10-25 | 2016-04-11 | 프로테우스 디지털 헬스, 인코포레이티드 | Controlled activation ingestible identifier |
US20080103572A1 (en) | 2006-10-31 | 2008-05-01 | Medtronic, Inc. | Implantable medical lead with threaded fixation |
US8579853B2 (en) | 2006-10-31 | 2013-11-12 | Abbott Diabetes Care Inc. | Infusion devices and methods |
US8295934B2 (en) | 2006-11-14 | 2012-10-23 | Neurovista Corporation | Systems and methods of reducing artifact in neurological stimulation systems |
WO2008063626A2 (en) | 2006-11-20 | 2008-05-29 | Proteus Biomedical, Inc. | Active signal processing personal health signal receivers |
WO2008069896A2 (en) * | 2006-12-06 | 2008-06-12 | Medtronic, Inc. | Telemetry device for a medical device programmer |
US20080154146A1 (en) * | 2006-12-21 | 2008-06-26 | Dellon A L | System and method for managing neurosensory test information |
US7996092B2 (en) * | 2007-01-16 | 2011-08-09 | Ndi Medical, Inc. | Devices, systems, and methods employing a molded nerve cuff electrode |
EP2124734A2 (en) | 2007-01-25 | 2009-12-02 | NeuroVista Corporation | Methods and systems for measuring a subject's susceptibility to a seizure |
WO2008092119A2 (en) | 2007-01-25 | 2008-07-31 | Neurovista Corporation | Systems and methods for identifying a contra-ictal condition in a subject |
MY165532A (en) | 2007-02-01 | 2018-04-02 | Proteus Digital Health Inc | Ingestible event marker systems |
EP2111661B1 (en) | 2007-02-14 | 2017-04-12 | Proteus Digital Health, Inc. | In-body power source having high surface area electrode |
US20080199894A1 (en) | 2007-02-15 | 2008-08-21 | Abbott Diabetes Care, Inc. | Device and method for automatic data acquisition and/or detection |
US8123686B2 (en) | 2007-03-01 | 2012-02-28 | Abbott Diabetes Care Inc. | Method and apparatus for providing rolling data in communication systems |
US11331488B2 (en) | 2007-03-09 | 2022-05-17 | Mainstay Medical Limited | Systems and methods for enhancing function of spine stabilization muscles associated with a spine surgery intervention |
US8068918B2 (en) | 2007-03-09 | 2011-11-29 | Enteromedics Inc. | Remote monitoring and control of implantable devices |
US11679262B2 (en) | 2007-03-09 | 2023-06-20 | Mainstay Medical Limited | Systems and methods for restoring muscle function to the lumbar spine |
US10925637B2 (en) * | 2010-03-11 | 2021-02-23 | Mainstay Medical Limited | Methods of implanting electrode leads for use with implantable neuromuscular electrical stimulator |
WO2008112577A1 (en) | 2007-03-09 | 2008-09-18 | Proteus Biomedical, Inc. | In-body device having a multi-directional transmitter |
US11679261B2 (en) | 2007-03-09 | 2023-06-20 | Mainstay Medical Limited | Systems and methods for enhancing function of spine stabilization muscles associated with a spine surgery intervention |
US9072897B2 (en) | 2007-03-09 | 2015-07-07 | Mainstay Medical Limited | Systems and methods for restoring muscle function to the lumbar spine |
EP2063771A1 (en) | 2007-03-09 | 2009-06-03 | Proteus Biomedical, Inc. | In-body device having a deployable antenna |
US8428728B2 (en) * | 2007-03-09 | 2013-04-23 | Mainstay Medical Limited | Muscle stimulator |
US8036736B2 (en) | 2007-03-21 | 2011-10-11 | Neuro Vista Corporation | Implantable systems and methods for identifying a contra-ictal condition in a subject |
WO2008120129A2 (en) * | 2007-03-30 | 2008-10-09 | Koninklijke Philips Electronics N.V. | Personal accessory for use with a pill |
EP2146625B1 (en) | 2007-04-14 | 2019-08-14 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in medical communication system |
ES2817503T3 (en) | 2007-04-14 | 2021-04-07 | Abbott Diabetes Care Inc | Procedure and apparatus for providing data processing and control in a medical communication system |
CA2683959C (en) | 2007-04-14 | 2017-08-29 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in medical communication system |
CA2683953C (en) | 2007-04-14 | 2016-08-02 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in medical communication system |
US8386025B2 (en) * | 2007-04-30 | 2013-02-26 | IctalCare A/S, Delta | Device and method for monitoring muscular activity |
US8665091B2 (en) | 2007-05-08 | 2014-03-04 | Abbott Diabetes Care Inc. | Method and device for determining elapsed sensor life |
US8461985B2 (en) | 2007-05-08 | 2013-06-11 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US8456301B2 (en) | 2007-05-08 | 2013-06-04 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US7928850B2 (en) | 2007-05-08 | 2011-04-19 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US7957813B1 (en) * | 2007-05-08 | 2011-06-07 | Pacesetter, Inc. | Adaptive staged wake-up for implantable medical device communication |
US10002233B2 (en) | 2007-05-14 | 2018-06-19 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8239166B2 (en) | 2007-05-14 | 2012-08-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US9125548B2 (en) | 2007-05-14 | 2015-09-08 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8103471B2 (en) | 2007-05-14 | 2012-01-24 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8444560B2 (en) | 2007-05-14 | 2013-05-21 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8260558B2 (en) | 2007-05-14 | 2012-09-04 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8560038B2 (en) | 2007-05-14 | 2013-10-15 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8600681B2 (en) | 2007-05-14 | 2013-12-03 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8540632B2 (en) | 2007-05-24 | 2013-09-24 | Proteus Digital Health, Inc. | Low profile antenna for in body device |
US8140167B2 (en) * | 2007-05-31 | 2012-03-20 | Enteromedics, Inc. | Implantable therapy system with external component having multiple operating modes |
US9421388B2 (en) | 2007-06-01 | 2016-08-23 | Witricity Corporation | Power generation for implantable devices |
US8805530B2 (en) | 2007-06-01 | 2014-08-12 | Witricity Corporation | Power generation for implantable devices |
JP5680960B2 (en) | 2007-06-21 | 2015-03-04 | アボット ダイアベティス ケア インコーポレイテッドAbbott Diabetes Care Inc. | Health care device and method |
US8617069B2 (en) | 2007-06-21 | 2013-12-31 | Abbott Diabetes Care Inc. | Health monitor |
US8160900B2 (en) | 2007-06-29 | 2012-04-17 | Abbott Diabetes Care Inc. | Analyte monitoring and management device and method to analyze the frequency of user interaction with the device |
US9788744B2 (en) | 2007-07-27 | 2017-10-17 | Cyberonics, Inc. | Systems for monitoring brain activity and patient advisory device |
US8834366B2 (en) | 2007-07-31 | 2014-09-16 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor calibration |
WO2009026382A1 (en) * | 2007-08-20 | 2009-02-26 | Kopell, Brian, H. | Systems and methods for treating neurological disorders by light stimulation |
EP4011289A1 (en) | 2007-09-25 | 2022-06-15 | Otsuka Pharmaceutical Co., Ltd. | In-body device with virtual dipole signal amplification |
WO2009048580A1 (en) | 2007-10-09 | 2009-04-16 | Imthera Medical, Inc. | Apparatus, system, and method for selective stimulation |
US8409093B2 (en) | 2007-10-23 | 2013-04-02 | Abbott Diabetes Care Inc. | Assessing measures of glycemic variability |
US8377031B2 (en) | 2007-10-23 | 2013-02-19 | Abbott Diabetes Care Inc. | Closed loop control system with safety parameters and methods |
US8244367B2 (en) * | 2007-10-26 | 2012-08-14 | Medtronic, Inc. | Closed loop long range recharging |
ATE509661T1 (en) * | 2007-10-26 | 2011-06-15 | Medtronic Inc | METHOD AND DEVICE FOR DYNAMIC ADJUSTMENT OF RECHARGE PARAMETERS |
WO2009065101A1 (en) * | 2007-11-16 | 2009-05-22 | Mclean Hospital Corporation | Intracranial electrical seizure therapy (icest) |
US20090135886A1 (en) | 2007-11-27 | 2009-05-28 | Proteus Biomedical, Inc. | Transbody communication systems employing communication channels |
US20090164239A1 (en) | 2007-12-19 | 2009-06-25 | Abbott Diabetes Care, Inc. | Dynamic Display Of Glucose Information |
US9259591B2 (en) | 2007-12-28 | 2016-02-16 | Cyberonics, Inc. | Housing for an implantable medical device |
US20090171168A1 (en) | 2007-12-28 | 2009-07-02 | Leyde Kent W | Systems and Method for Recording Clinical Manifestations of a Seizure |
US10004657B2 (en) * | 2008-02-08 | 2018-06-26 | The University Of Western Ontario | Method of brain activation |
JP2011513865A (en) | 2008-03-05 | 2011-04-28 | プロテウス バイオメディカル インコーポレイテッド | Multi-mode communication ingestible event marker and system and method of using the same |
AU2009237353B2 (en) * | 2008-04-15 | 2014-10-23 | Trudell Medical International | Swallowing air pulse therapy mouthpiece and method for the use thereof |
DE102008023352B4 (en) * | 2008-05-13 | 2014-02-06 | Siemens Medical Instruments Pte. Ltd. | hearing Aid |
JP5188880B2 (en) * | 2008-05-26 | 2013-04-24 | オリンパスメディカルシステムズ株式会社 | Capsule type medical device and method for charging capsule type medical device |
US7826382B2 (en) | 2008-05-30 | 2010-11-02 | Abbott Diabetes Care Inc. | Close proximity communication device and methods |
US8591410B2 (en) | 2008-05-30 | 2013-11-26 | Abbott Diabetes Care Inc. | Method and apparatus for providing glycemic control |
US8924159B2 (en) | 2008-05-30 | 2014-12-30 | Abbott Diabetes Care Inc. | Method and apparatus for providing glycemic control |
WO2010005877A2 (en) | 2008-07-08 | 2010-01-14 | Proteus Biomedical, Inc. | Ingestible event marker data framework |
WO2010006218A2 (en) * | 2008-07-11 | 2010-01-14 | Don Headley | Sleep apnea device and method |
WO2010009172A1 (en) | 2008-07-14 | 2010-01-21 | Abbott Diabetes Care Inc. | Closed loop control system interface and methods |
CA2732732C (en) * | 2008-08-01 | 2016-04-12 | Jonathan L. Sakai | Portable assemblies, systems, and methods for providing functional or therapeutic neurostimulation |
US8700177B2 (en) | 2008-08-01 | 2014-04-15 | Ndi Medical, Llc | Systems and methods for providing percutaneous electrical stimulation |
KR101214453B1 (en) | 2008-08-13 | 2012-12-24 | 프로테우스 디지털 헬스, 인코포레이티드 | Ingestible circuitry |
US8622988B2 (en) | 2008-08-31 | 2014-01-07 | Abbott Diabetes Care Inc. | Variable rate closed loop control and methods |
US20100057040A1 (en) | 2008-08-31 | 2010-03-04 | Abbott Diabetes Care, Inc. | Robust Closed Loop Control And Methods |
US8734422B2 (en) | 2008-08-31 | 2014-05-27 | Abbott Diabetes Care Inc. | Closed loop control with improved alarm functions |
US9943644B2 (en) | 2008-08-31 | 2018-04-17 | Abbott Diabetes Care Inc. | Closed loop control with reference measurement and methods thereof |
US20100057167A1 (en) * | 2008-09-02 | 2010-03-04 | Xander Evers | System and Method for the Interrogation of Implantable Medical Devices |
US8957549B2 (en) | 2008-09-27 | 2015-02-17 | Witricity Corporation | Tunable wireless energy transfer for in-vehicle applications |
US8692412B2 (en) | 2008-09-27 | 2014-04-08 | Witricity Corporation | Temperature compensation in a wireless transfer system |
US8569914B2 (en) | 2008-09-27 | 2013-10-29 | Witricity Corporation | Wireless energy transfer using object positioning for improved k |
US8963488B2 (en) | 2008-09-27 | 2015-02-24 | Witricity Corporation | Position insensitive wireless charging |
US8400017B2 (en) | 2008-09-27 | 2013-03-19 | Witricity Corporation | Wireless energy transfer for computer peripheral applications |
US9093853B2 (en) | 2008-09-27 | 2015-07-28 | Witricity Corporation | Flexible resonator attachment |
US8907531B2 (en) | 2008-09-27 | 2014-12-09 | Witricity Corporation | Wireless energy transfer with variable size resonators for medical applications |
US9318922B2 (en) | 2008-09-27 | 2016-04-19 | Witricity Corporation | Mechanically removable wireless power vehicle seat assembly |
US8947186B2 (en) | 2008-09-27 | 2015-02-03 | Witricity Corporation | Wireless energy transfer resonator thermal management |
US8912687B2 (en) | 2008-09-27 | 2014-12-16 | Witricity Corporation | Secure wireless energy transfer for vehicle applications |
US8723366B2 (en) | 2008-09-27 | 2014-05-13 | Witricity Corporation | Wireless energy transfer resonator enclosures |
US9160203B2 (en) | 2008-09-27 | 2015-10-13 | Witricity Corporation | Wireless powered television |
US8466583B2 (en) | 2008-09-27 | 2013-06-18 | Witricity Corporation | Tunable wireless energy transfer for outdoor lighting applications |
US20110074346A1 (en) * | 2009-09-25 | 2011-03-31 | Hall Katherine L | Vehicle charger safety system and method |
US8643326B2 (en) | 2008-09-27 | 2014-02-04 | Witricity Corporation | Tunable wireless energy transfer systems |
US8461722B2 (en) | 2008-09-27 | 2013-06-11 | Witricity Corporation | Wireless energy transfer using conducting surfaces to shape field and improve K |
US9601270B2 (en) | 2008-09-27 | 2017-03-21 | Witricity Corporation | Low AC resistance conductor designs |
US8901778B2 (en) | 2008-09-27 | 2014-12-02 | Witricity Corporation | Wireless energy transfer with variable size resonators for implanted medical devices |
US8471410B2 (en) | 2008-09-27 | 2013-06-25 | Witricity Corporation | Wireless energy transfer over distance using field shaping to improve the coupling factor |
US9515494B2 (en) | 2008-09-27 | 2016-12-06 | Witricity Corporation | Wireless power system including impedance matching network |
US8933594B2 (en) | 2008-09-27 | 2015-01-13 | Witricity Corporation | Wireless energy transfer for vehicles |
US8497601B2 (en) | 2008-09-27 | 2013-07-30 | Witricity Corporation | Wireless energy transfer converters |
US9544683B2 (en) | 2008-09-27 | 2017-01-10 | Witricity Corporation | Wirelessly powered audio devices |
US9601261B2 (en) | 2008-09-27 | 2017-03-21 | Witricity Corporation | Wireless energy transfer using repeater resonators |
US8692410B2 (en) | 2008-09-27 | 2014-04-08 | Witricity Corporation | Wireless energy transfer with frequency hopping |
US8552592B2 (en) | 2008-09-27 | 2013-10-08 | Witricity Corporation | Wireless energy transfer with feedback control for lighting applications |
US8487480B1 (en) | 2008-09-27 | 2013-07-16 | Witricity Corporation | Wireless energy transfer resonator kit |
US8461721B2 (en) | 2008-09-27 | 2013-06-11 | Witricity Corporation | Wireless energy transfer using object positioning for low loss |
US8304935B2 (en) | 2008-09-27 | 2012-11-06 | Witricity Corporation | Wireless energy transfer using field shaping to reduce loss |
US8441154B2 (en) | 2008-09-27 | 2013-05-14 | Witricity Corporation | Multi-resonator wireless energy transfer for exterior lighting |
US8922066B2 (en) | 2008-09-27 | 2014-12-30 | Witricity Corporation | Wireless energy transfer with multi resonator arrays for vehicle applications |
US8324759B2 (en) | 2008-09-27 | 2012-12-04 | Witricity Corporation | Wireless energy transfer using magnetic materials to shape field and reduce loss |
US8937408B2 (en) | 2008-09-27 | 2015-01-20 | Witricity Corporation | Wireless energy transfer for medical applications |
US8669676B2 (en) | 2008-09-27 | 2014-03-11 | Witricity Corporation | Wireless energy transfer across variable distances using field shaping with magnetic materials to improve the coupling factor |
US8410636B2 (en) | 2008-09-27 | 2013-04-02 | Witricity Corporation | Low AC resistance conductor designs |
US8587155B2 (en) | 2008-09-27 | 2013-11-19 | Witricity Corporation | Wireless energy transfer using repeater resonators |
US8461720B2 (en) | 2008-09-27 | 2013-06-11 | Witricity Corporation | Wireless energy transfer using conducting surfaces to shape fields and reduce loss |
US8587153B2 (en) | 2008-09-27 | 2013-11-19 | Witricity Corporation | Wireless energy transfer using high Q resonators for lighting applications |
US9396867B2 (en) | 2008-09-27 | 2016-07-19 | Witricity Corporation | Integrated resonator-shield structures |
US9601266B2 (en) | 2008-09-27 | 2017-03-21 | Witricity Corporation | Multiple connected resonators with a single electronic circuit |
US9184595B2 (en) | 2008-09-27 | 2015-11-10 | Witricity Corporation | Wireless energy transfer in lossy environments |
US9246336B2 (en) | 2008-09-27 | 2016-01-26 | Witricity Corporation | Resonator optimizations for wireless energy transfer |
US8946938B2 (en) | 2008-09-27 | 2015-02-03 | Witricity Corporation | Safety systems for wireless energy transfer in vehicle applications |
US8686598B2 (en) | 2008-09-27 | 2014-04-01 | Witricity Corporation | Wireless energy transfer for supplying power and heat to a device |
US8598743B2 (en) | 2008-09-27 | 2013-12-03 | Witricity Corporation | Resonator arrays for wireless energy transfer |
US8772973B2 (en) | 2008-09-27 | 2014-07-08 | Witricity Corporation | Integrated resonator-shield structures |
US8482158B2 (en) | 2008-09-27 | 2013-07-09 | Witricity Corporation | Wireless energy transfer using variable size resonators and system monitoring |
US9744858B2 (en) | 2008-09-27 | 2017-08-29 | Witricity Corporation | System for wireless energy distribution in a vehicle |
US9065423B2 (en) | 2008-09-27 | 2015-06-23 | Witricity Corporation | Wireless energy distribution system |
US8928276B2 (en) | 2008-09-27 | 2015-01-06 | Witricity Corporation | Integrated repeaters for cell phone applications |
US8476788B2 (en) | 2008-09-27 | 2013-07-02 | Witricity Corporation | Wireless energy transfer with high-Q resonators using field shaping to improve K |
US9577436B2 (en) | 2008-09-27 | 2017-02-21 | Witricity Corporation | Wireless energy transfer for implantable devices |
US9106203B2 (en) | 2008-09-27 | 2015-08-11 | Witricity Corporation | Secure wireless energy transfer in medical applications |
US8901779B2 (en) | 2008-09-27 | 2014-12-02 | Witricity Corporation | Wireless energy transfer with resonator arrays for medical applications |
US8629578B2 (en) | 2008-09-27 | 2014-01-14 | Witricity Corporation | Wireless energy transfer systems |
JP2012504387A (en) | 2008-09-27 | 2012-02-16 | ウィトリシティ コーポレーション | Wireless energy transfer system |
US9105959B2 (en) | 2008-09-27 | 2015-08-11 | Witricity Corporation | Resonator enclosure |
US9035499B2 (en) | 2008-09-27 | 2015-05-19 | Witricity Corporation | Wireless energy transfer for photovoltaic panels |
US8986208B2 (en) | 2008-09-30 | 2015-03-24 | Abbott Diabetes Care Inc. | Analyte sensor sensitivity attenuation mitigation |
EP3714771A1 (en) | 2008-10-01 | 2020-09-30 | Inspire Medical Systems, Inc. | System for treating sleep apnea transvenously |
BRPI0920548B8 (en) | 2008-10-09 | 2021-06-22 | Imthera Medical Inc | device to control the position of a patient's tongue |
US9327121B2 (en) | 2011-09-08 | 2016-05-03 | Nevro Corporation | Selective high frequency spinal cord modulation for inhibiting pain, including cephalic and/or total body pain with reduced side effects, and associated systems and methods |
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 |
DE102008043451A1 (en) * | 2008-11-04 | 2010-05-06 | Biotronik Crm Patent Ag | Modular universal programming device |
EP2346567A4 (en) | 2008-11-13 | 2012-04-25 | Proteus Biomedical Inc | Multiplexed multi-electrode neurostimulation devices |
EP2349466A4 (en) | 2008-11-13 | 2013-03-20 | Proteus Digital Health Inc | Shielded stimulation and sensing system and method |
KR101192690B1 (en) | 2008-11-13 | 2012-10-19 | 프로테우스 디지털 헬스, 인코포레이티드 | Ingestible therapy activator system, therapeutic device and method |
EP3184045B1 (en) | 2008-11-19 | 2023-12-06 | Inspire Medical Systems, Inc. | System treating sleep disordered breathing |
DE102008043973B4 (en) | 2008-11-21 | 2011-12-01 | Burkhard Brocke | Device for transcranial neurostimulation |
WO2010064206A1 (en) * | 2008-12-05 | 2010-06-10 | Koninklijke Philips Electronics N.V. | Electrical stimulation device for locating an electrical stimulation point and method |
SG172077A1 (en) | 2008-12-11 | 2011-07-28 | Proteus Biomedical Inc | Evaluation of gastrointestinal function using portable electroviscerography systems and methods of using the same |
US9659423B2 (en) | 2008-12-15 | 2017-05-23 | Proteus Digital Health, Inc. | Personal authentication apparatus system and method |
WO2013012869A1 (en) | 2011-07-21 | 2013-01-24 | Proteus Digital Health, Inc. | Mobile communication device, system, and method |
US9439566B2 (en) | 2008-12-15 | 2016-09-13 | Proteus Digital Health, Inc. | Re-wearable wireless device |
TWI503101B (en) | 2008-12-15 | 2015-10-11 | Proteus Digital Health Inc | Body-associated receiver and method |
US8281875B2 (en) * | 2008-12-19 | 2012-10-09 | Halliburton Energy Services, Inc. | Pressure and flow control in drilling operations |
US8849390B2 (en) | 2008-12-29 | 2014-09-30 | Cyberonics, Inc. | Processing for multi-channel signals |
EP3395333A1 (en) | 2009-01-06 | 2018-10-31 | Proteus Digital Health, Inc. | Pharmaceutical dosages delivery system |
CN102341031A (en) | 2009-01-06 | 2012-02-01 | 普罗秋斯生物医学公司 | Ingestion-related biofeedback and personalized medical therapy method and system |
US8588933B2 (en) | 2009-01-09 | 2013-11-19 | Cyberonics, Inc. | Medical lead termination sleeve for implantable medical devices |
US8560082B2 (en) | 2009-01-30 | 2013-10-15 | Abbott Diabetes Care Inc. | Computerized determination of insulin pump therapy parameters using real time and retrospective data processing |
US9402544B2 (en) | 2009-02-03 | 2016-08-02 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
US8335569B2 (en) | 2009-02-10 | 2012-12-18 | Boston Scientific Neuromodulation Corporation | External device for communicating with an implantable medical device having data telemetry and charging integrated in a single housing |
US8627705B2 (en) * | 2009-02-26 | 2014-01-14 | Belvac Production Machinery, Inc. | Self compensating sliding air valve mechanism |
US9375571B2 (en) * | 2013-01-15 | 2016-06-28 | ElectroCore, LLC | Mobile phone using non-invasive nerve stimulation |
GB2480965B (en) | 2009-03-25 | 2014-10-08 | Proteus Digital Health Inc | Probablistic pharmacokinetic and pharmacodynamic modeling |
WO2010117810A1 (en) | 2009-03-31 | 2010-10-14 | Inspire Medical Systems, Inc. | Percutaneous access for systems of treating sleep-related disordered breathing |
US8497777B2 (en) | 2009-04-15 | 2013-07-30 | Abbott Diabetes Care Inc. | Analyte monitoring system having an alert |
ES2624748T3 (en) | 2009-04-22 | 2017-07-17 | Nevro Corporation | Selective high frequency modulation of the spinal cord for pain inhibition with reduced side effects, and associated systems and methods |
EP2421600B1 (en) | 2009-04-22 | 2014-03-05 | Nevro Corporation | Spinal cord modulation systems for inducing paresthetic and anesthetic effects |
MX2011011506A (en) | 2009-04-28 | 2012-05-08 | Proteus Biomedical Inc | Highly reliable ingestible event markers and methods for using the same. |
US9226701B2 (en) | 2009-04-28 | 2016-01-05 | Abbott Diabetes Care Inc. | Error detection in critical repeating data in a wireless sensor system |
WO2010129375A1 (en) | 2009-04-28 | 2010-11-11 | Abbott Diabetes Care Inc. | Closed loop blood glucose control algorithm analysis |
EP2424426B1 (en) | 2009-04-29 | 2020-01-08 | Abbott Diabetes Care, Inc. | Method and system for providing data communication in continuous glucose monitoring and management system |
US8483967B2 (en) | 2009-04-29 | 2013-07-09 | Abbott Diabetes Care Inc. | Method and system for providing real time analyte sensor calibration with retrospective backfill |
US9149423B2 (en) | 2009-05-12 | 2015-10-06 | Proteus Digital Health, Inc. | Ingestible event markers comprising an ingestible component |
US9184490B2 (en) | 2009-05-29 | 2015-11-10 | Abbott Diabetes Care Inc. | Medical device antenna systems having external antenna configurations |
US8786624B2 (en) | 2009-06-02 | 2014-07-22 | Cyberonics, Inc. | Processing for multi-channel signals |
US8746062B2 (en) | 2010-06-29 | 2014-06-10 | Orthosensor Inc. | Medical measurement system and method |
US8826733B2 (en) | 2009-06-30 | 2014-09-09 | Orthosensor Inc | Sensored prosthetic component and method |
US9839390B2 (en) | 2009-06-30 | 2017-12-12 | Orthosensor Inc. | Prosthetic component having a compliant surface |
US8516884B2 (en) | 2010-06-29 | 2013-08-27 | Orthosensor Inc. | Shielded prosthetic component |
US9462964B2 (en) | 2011-09-23 | 2016-10-11 | Orthosensor Inc | Small form factor muscular-skeletal parameter measurement system |
US8701484B2 (en) | 2010-06-29 | 2014-04-22 | Orthosensor Inc. | Small form factor medical sensor structure and method therefor |
US8714009B2 (en) | 2010-06-29 | 2014-05-06 | Orthosensor Inc. | Shielded capacitor sensor system for medical applications and method |
US8661893B2 (en) | 2010-06-29 | 2014-03-04 | Orthosensor Inc. | Prosthetic component having a compliant surface |
US8696756B2 (en) | 2010-06-29 | 2014-04-15 | Orthosensor Inc. | Muscular-skeletal force, pressure, and load measurement system and method |
US8707782B2 (en) | 2009-06-30 | 2014-04-29 | Orthosensor Inc | Prosthetic component for monitoring synovial fluid and method |
US8720270B2 (en) | 2010-06-29 | 2014-05-13 | Ortho Sensor Inc. | Prosthetic component for monitoring joint health |
US8679186B2 (en) | 2010-06-29 | 2014-03-25 | Ortho Sensor Inc. | Hermetically sealed prosthetic component and method therefor |
US9259179B2 (en) | 2012-02-27 | 2016-02-16 | Orthosensor Inc. | Prosthetic knee joint measurement system including energy harvesting and method therefor |
US20100331733A1 (en) * | 2009-06-30 | 2010-12-30 | Orthosensor | Sensing device and method for an orthopedic joint |
DK3689237T3 (en) | 2009-07-23 | 2021-08-16 | Abbott Diabetes Care Inc | Method of preparation and system for continuous analyte measurement |
EP3936032A1 (en) | 2009-07-23 | 2022-01-12 | Abbott Diabetes Care, Inc. | Real time management of data relating to physiological control of glucose levels |
US8498710B2 (en) | 2009-07-28 | 2013-07-30 | Nevro Corporation | Linked area parameter adjustment for spinal cord stimulation and associated systems and methods |
WO2011014851A1 (en) | 2009-07-31 | 2011-02-03 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte monitoring system calibration accuracy |
US8738122B2 (en) * | 2009-08-21 | 2014-05-27 | The Chinese University Of Hong Kong | Systems and methods for reproducing body motions via networks |
US8558563B2 (en) | 2009-08-21 | 2013-10-15 | Proteus Digital Health, Inc. | Apparatus and method for measuring biochemical parameters |
EP3923295A1 (en) | 2009-08-31 | 2021-12-15 | Abbott Diabetes Care, Inc. | Medical devices and methods |
US9314195B2 (en) | 2009-08-31 | 2016-04-19 | Abbott Diabetes Care Inc. | Analyte signal processing device and methods |
WO2011026148A1 (en) | 2009-08-31 | 2011-03-03 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods for managing power and noise |
ES2912584T3 (en) | 2009-08-31 | 2022-05-26 | Abbott Diabetes Care Inc | A glucose monitoring system and method |
TWI517050B (en) | 2009-11-04 | 2016-01-11 | 普羅托斯數位健康公司 | System for supply chain management |
US20110112601A1 (en) | 2009-11-10 | 2011-05-12 | Imthera Medical, Inc. | System for stimulating a hypoglossal nerve for controlling the position of a patient's tongue |
UA109424C2 (en) | 2009-12-02 | 2015-08-25 | PHARMACEUTICAL PRODUCT, PHARMACEUTICAL TABLE WITH ELECTRONIC MARKER AND METHOD OF MANUFACTURING PHARMACEUTICAL TABLETS | |
AU2011210648B2 (en) | 2010-02-01 | 2014-10-16 | Otsuka Pharmaceutical Co., Ltd. | Data gathering system |
US9643019B2 (en) | 2010-02-12 | 2017-05-09 | Cyberonics, Inc. | Neurological monitoring and alerts |
US20110282248A1 (en) | 2010-03-04 | 2011-11-17 | Martin Ruth E | Portable high frequency air pulse delivery device |
US8447404B2 (en) | 2010-03-05 | 2013-05-21 | Endostim, Inc. | Device and implantation system for electrical stimulation of biological systems |
US11717681B2 (en) | 2010-03-05 | 2023-08-08 | Endostim, Inc. | Systems and methods for treating gastroesophageal reflux disease |
US9950159B2 (en) | 2013-10-23 | 2018-04-24 | Mainstay Medical Limited | Systems and methods for restoring muscle function to the lumbar spine and kits for implanting the same |
US11786725B2 (en) | 2012-06-13 | 2023-10-17 | Mainstay Medical Limited | Systems and methods for restoring muscle function to the lumbar spine and kits for implanting the same |
CN103079633B (en) | 2010-03-11 | 2016-05-04 | 梅恩斯塔伊医疗公司 | Be used for the treatment of modular stimulator, implanted RF ablation system and the using method of backache |
US9999763B2 (en) | 2012-06-13 | 2018-06-19 | Mainstay Medical Limited | Apparatus and methods for anchoring electrode leads adjacent to nervous tissue |
US11684774B2 (en) | 2010-03-11 | 2023-06-27 | Mainstay Medical Limited | Electrical stimulator for treatment of back pain and methods of use |
US9332943B2 (en) | 2011-09-23 | 2016-05-10 | Orthosensor Inc | Flexible surface parameter measurement system for the muscular-skeletal system |
US8926530B2 (en) * | 2011-09-23 | 2015-01-06 | Orthosensor Inc | Orthopedic insert measuring system for having a sterilized cavity |
WO2011127252A2 (en) | 2010-04-07 | 2011-10-13 | Proteus Biomedical, Inc. | Miniature ingestible device |
US9814885B2 (en) | 2010-04-27 | 2017-11-14 | Medtronic, Inc. | Stimulation electrode selection |
US9265422B2 (en) | 2010-04-27 | 2016-02-23 | Apollo Endosurgery, Inc. | System and method for determining an adjustment to a gastric band based on satiety state data and weight loss data |
US8594806B2 (en) | 2010-04-30 | 2013-11-26 | Cyberonics, Inc. | Recharging and communication lead for an implantable device |
TWI557672B (en) | 2010-05-19 | 2016-11-11 | 波提亞斯數位康健公司 | Computer system and computer-implemented method to track medication from manufacturer to a patient, apparatus and method for confirming delivery of medication to a patient, patient interface device |
US8939030B2 (en) | 2010-06-29 | 2015-01-27 | Orthosensor Inc | Edge-detect receiver for orthopedic parameter sensing |
US9602168B2 (en) | 2010-08-31 | 2017-03-21 | Witricity Corporation | Communication in wireless energy transfer systems |
US11213226B2 (en) | 2010-10-07 | 2022-01-04 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods |
US10226209B2 (en) | 2010-10-15 | 2019-03-12 | Brain Sentinel, Inc. | Method and apparatus for classification of seizure type and severity using electromyography |
WO2012051628A1 (en) | 2010-10-15 | 2012-04-19 | Lgch, Inc. | Method and apparatus for detecting seizures |
US8788048B2 (en) | 2010-11-11 | 2014-07-22 | Spr Therapeutics, Llc | Systems and methods for the treatment of pain through neural fiber stimulation |
US8788046B2 (en) | 2010-11-11 | 2014-07-22 | Spr Therapeutics, Llc | Systems and methods for the treatment of pain through neural fiber stimulation |
US8788047B2 (en) | 2010-11-11 | 2014-07-22 | Spr Therapeutics, Llc | Systems and methods for the treatment of pain through neural fiber stimulation |
EP2642983A4 (en) | 2010-11-22 | 2014-03-12 | Proteus Digital Health Inc | Ingestible device with pharmaceutical product |
US8649874B2 (en) | 2010-11-30 | 2014-02-11 | Nevro Corporation | Extended pain relief via high frequency spinal cord modulation, and associated systems and methods |
US8386051B2 (en) | 2010-12-30 | 2013-02-26 | Medtronic, Inc. | Disabling an implantable medical device |
EP2476370A1 (en) * | 2011-01-17 | 2012-07-18 | Catsanis, Nicholas | Electronic device and platform for collecting and transmitting electrical signals |
WO2012112178A1 (en) | 2011-02-18 | 2012-08-23 | Medtronic,Inc | Modular medical device programmer |
US8352034B2 (en) | 2011-02-18 | 2013-01-08 | Medtronic, Inc. | Medical device programmer with adjustable kickstand |
CN103619255B (en) | 2011-02-28 | 2016-11-02 | 雅培糖尿病护理公司 | The device that associates with analyte monitoring device, system and method and combine their device |
US10136845B2 (en) | 2011-02-28 | 2018-11-27 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
US9439599B2 (en) | 2011-03-11 | 2016-09-13 | Proteus Digital Health, Inc. | Wearable personal body associated device with various physical configurations |
US9166321B2 (en) | 2011-03-22 | 2015-10-20 | Greatbatch Ltd. | Thin profile stacked layer contact |
US8874219B2 (en) | 2011-04-07 | 2014-10-28 | Greatbatch, Ltd. | Arbitrary waveform generator and neural stimulation application |
US9656076B2 (en) | 2011-04-07 | 2017-05-23 | Nuvectra Corporation | Arbitrary waveform generator and neural stimulation application with scalable waveform feature and charge balancing |
US8996115B2 (en) | 2011-04-07 | 2015-03-31 | Greatbatch, Ltd. | Charge balancing for arbitrary waveform generator and neural stimulation application |
US8996117B2 (en) | 2011-04-07 | 2015-03-31 | Greatbatch, Ltd. | Arbitrary waveform generator and neural stimulation application with scalable waveform feature |
AU2012242533B2 (en) | 2011-04-14 | 2016-10-20 | Endostim, Inc. | Systems and methods for treating gastroesophageal reflux disease |
US8406890B2 (en) | 2011-04-14 | 2013-03-26 | Medtronic, Inc. | Implantable medical devices storing graphics processing data |
US8430320B2 (en) | 2011-06-01 | 2013-04-30 | Branko Prpa | Sterile implant tracking device and method |
US9355289B2 (en) | 2011-06-01 | 2016-05-31 | Matrix It Medical Tracking Systems, Inc. | Sterile implant tracking device and method |
CA2839532A1 (en) | 2011-06-16 | 2012-12-20 | Advanced Uro-Solutions, Llc | Percutaneous tibial nerve stimulator |
US9076187B1 (en) | 2011-06-16 | 2015-07-07 | Advanced Uro-Solutions, Llc | Medical device payment system |
AU2012278966B2 (en) | 2011-07-05 | 2015-09-03 | Brain Sentinel, Inc. | Method and apparatus for detecting seizures |
US9948145B2 (en) | 2011-07-08 | 2018-04-17 | Witricity Corporation | Wireless power transfer for a seat-vest-helmet system |
WO2015112603A1 (en) | 2014-01-21 | 2015-07-30 | Proteus Digital Health, Inc. | Masticable ingestible product and communication system therefor |
US9756874B2 (en) | 2011-07-11 | 2017-09-12 | Proteus Digital Health, Inc. | Masticable ingestible product and communication system therefor |
EP2739344B1 (en) | 2011-08-02 | 2019-03-20 | Mainstay Medical Limited | Apparatus for anchoring electrode leads for use with implantable neuromuscular electrical stimulator |
CN108110907B (en) | 2011-08-04 | 2022-08-02 | 韦特里西提公司 | Tunable wireless power supply architecture |
US20150039045A1 (en) | 2011-08-11 | 2015-02-05 | Inspire Medical Systems, Inc. | Method and system for applying stimulation in treating sleep disordered breathing |
US8934992B2 (en) | 2011-09-01 | 2015-01-13 | Inspire Medical Systems, Inc. | Nerve cuff |
US9925367B2 (en) | 2011-09-02 | 2018-03-27 | Endostim, Inc. | Laparoscopic lead implantation method |
ES2558182T3 (en) | 2011-09-09 | 2016-02-02 | Witricity Corporation | Detection of foreign objects in wireless energy transfer systems |
US20130062966A1 (en) | 2011-09-12 | 2013-03-14 | Witricity Corporation | Reconfigurable control architectures and algorithms for electric vehicle wireless energy transfer systems |
US9839374B2 (en) | 2011-09-23 | 2017-12-12 | Orthosensor Inc. | System and method for vertebral load and location sensing |
US8945133B2 (en) | 2011-09-23 | 2015-02-03 | Orthosensor Inc | Spinal distraction tool for load and position measurement |
US8784339B2 (en) | 2011-09-23 | 2014-07-22 | Orthosensor Inc | Spinal instrument for measuring load and position of load |
US9414940B2 (en) | 2011-09-23 | 2016-08-16 | Orthosensor Inc. | Sensored head for a measurement tool for the muscular-skeletal system |
AU2012312050B2 (en) * | 2011-09-23 | 2017-08-17 | Howmedica Osteonics Corp. | Device and method for enabling an orthopedic tool for parameter measurement |
US8911448B2 (en) | 2011-09-23 | 2014-12-16 | Orthosensor, Inc | Device and method for enabling an orthopedic tool for parameter measurement |
US9318257B2 (en) | 2011-10-18 | 2016-04-19 | Witricity Corporation | Wireless energy transfer for packaging |
WO2013066873A1 (en) | 2011-10-31 | 2013-05-10 | Abbott Diabetes Care Inc. | Electronic devices having integrated reset systems and methods thereof |
KR20140085591A (en) | 2011-11-04 | 2014-07-07 | 위트리시티 코포레이션 | Wireless energy transfer modeling tool |
AU2012332102B2 (en) | 2011-11-04 | 2017-05-04 | Nevro Corporation | Medical device communication and charding assemblies for use with implantable signal generators |
USD736383S1 (en) | 2012-11-05 | 2015-08-11 | Nevro Corporation | Implantable signal generator |
US9980669B2 (en) | 2011-11-07 | 2018-05-29 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods |
US9235683B2 (en) | 2011-11-09 | 2016-01-12 | Proteus Digital Health, Inc. | Apparatus, system, and method for managing adherence to a regimen |
AU2012334926B2 (en) | 2011-11-11 | 2017-07-13 | The Regents Of The University Of California | Transcutaneous spinal cord stimulation: noninvasive tool for activation of locomotor circuitry |
US8710993B2 (en) | 2011-11-23 | 2014-04-29 | Abbott Diabetes Care Inc. | Mitigating single point failure of devices in an analyte monitoring system and methods thereof |
US9317656B2 (en) | 2011-11-23 | 2016-04-19 | Abbott Diabetes Care Inc. | Compatibility mechanisms for devices in a continuous analyte monitoring system and methods thereof |
WO2013078426A2 (en) | 2011-11-25 | 2013-05-30 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods of use |
US8668344B2 (en) | 2011-11-30 | 2014-03-11 | Izi Medical Products | Marker sphere including edged opening to aid in molding |
DE112012005241T5 (en) * | 2011-12-15 | 2014-08-28 | Autodesk, Inc. | Implanted devices and relevant user interfaces |
EP2794000B1 (en) | 2011-12-19 | 2016-03-30 | Mainstay Medical Limited | Apparatus for rehabilitating a muscle and assessing progress of rehabilitation |
US9306635B2 (en) | 2012-01-26 | 2016-04-05 | Witricity Corporation | Wireless energy transfer with reduced fields |
US9844335B2 (en) | 2012-02-27 | 2017-12-19 | Orthosensor Inc | Measurement device for the muscular-skeletal system having load distribution plates |
US9622701B2 (en) | 2012-02-27 | 2017-04-18 | Orthosensor Inc | Muscular-skeletal joint stability detection and method therefor |
US9271675B2 (en) | 2012-02-27 | 2016-03-01 | Orthosensor Inc. | Muscular-skeletal joint stability detection and method therefor |
US8661573B2 (en) | 2012-02-29 | 2014-03-04 | Izi Medical Products | Protective cover for medical device having adhesive mechanism |
US20140114385A1 (en) * | 2012-04-09 | 2014-04-24 | Spinal Modulation, Inc. | Devices, systems and methods for modulation of the nervous system |
US9186501B2 (en) | 2012-06-13 | 2015-11-17 | Mainstay Medical Limited | Systems and methods for implanting electrode leads for use with implantable neuromuscular electrical stimulator |
US10195419B2 (en) | 2012-06-13 | 2019-02-05 | Mainstay Medical Limited | Electrode leads for use with implantable neuromuscular electrical stimulator |
US9833614B1 (en) | 2012-06-22 | 2017-12-05 | Nevro Corp. | Autonomic nervous system control via high frequency spinal cord modulation, and associated systems and methods |
US9343922B2 (en) | 2012-06-27 | 2016-05-17 | Witricity Corporation | Wireless energy transfer for rechargeable batteries |
US9623253B2 (en) | 2012-07-17 | 2017-04-18 | Micron Devices, LLC | Devices and methods for treating urological disorders |
WO2014153219A1 (en) * | 2013-03-14 | 2014-09-25 | Perryman Laura Tyler | Devices and methods for treating urological disorders |
TW201424689A (en) | 2012-07-23 | 2014-07-01 | Proteus Digital Health Inc | Techniques for manufacturing ingestible event markers comprising an ingestible component |
US9287607B2 (en) | 2012-07-31 | 2016-03-15 | Witricity Corporation | Resonator fine tuning |
US9343923B2 (en) | 2012-08-23 | 2016-05-17 | Cyberonics, Inc. | Implantable medical device with backscatter signal based communication |
US9623238B2 (en) | 2012-08-23 | 2017-04-18 | Endostim, Inc. | Device and implantation system for electrical stimulation of biological systems |
EP3395252A1 (en) | 2012-08-30 | 2018-10-31 | Abbott Diabetes Care, Inc. | Dropout detection in continuous analyte monitoring data during data excursions |
CA2882974C (en) | 2012-08-31 | 2018-10-23 | Alfred E. Mann Foundation For Scientific Research | Feedback controlled coil driver for inductive power transfer |
US9968306B2 (en) | 2012-09-17 | 2018-05-15 | Abbott Diabetes Care Inc. | Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems |
US9595378B2 (en) | 2012-09-19 | 2017-03-14 | Witricity Corporation | Resonator enclosure |
US9935498B2 (en) | 2012-09-25 | 2018-04-03 | Cyberonics, Inc. | Communication efficiency with an implantable medical device using a circulator and a backscatter signal |
WO2014052985A1 (en) * | 2012-09-28 | 2014-04-03 | Pare Mike | Systems. devices, and methods for selectively locating implantable devices |
US9782587B2 (en) | 2012-10-01 | 2017-10-10 | Nuvectra Corporation | Digital control for pulse generators |
US9268909B2 (en) | 2012-10-18 | 2016-02-23 | Proteus Digital Health, Inc. | Apparatus, system, and method to adaptively optimize power dissipation and broadcast power in a power source for a communication device |
CN109969007A (en) | 2012-10-19 | 2019-07-05 | 韦特里西提公司 | External analyte detection in wireless energy transfer system |
US20140135744A1 (en) | 2012-11-09 | 2014-05-15 | Orthosensor Inc | Motion and orientation sensing module or device for positioning of implants |
US9842684B2 (en) | 2012-11-16 | 2017-12-12 | Witricity Corporation | Systems and methods for wireless power system with improved performance and/or ease of use |
AU2014207685B2 (en) * | 2013-01-15 | 2018-04-19 | Transient Electronics, Inc. | Implantable transient nerve stimulation device |
US11149123B2 (en) | 2013-01-29 | 2021-10-19 | Otsuka Pharmaceutical Co., Ltd. | Highly-swellable polymeric films and compositions comprising the same |
US20170112409A1 (en) * | 2013-02-06 | 2017-04-27 | BTS S.p.A. | Wireless probe for dental electromyography |
US9498619B2 (en) | 2013-02-26 | 2016-11-22 | Endostim, Inc. | Implantable electrical stimulation leads |
AU2014236294B2 (en) * | 2013-03-14 | 2018-07-12 | Curonix Llc | Wireless implantable power receiver system and methods |
US10080896B2 (en) | 2013-03-15 | 2018-09-25 | Cirtec Medical Corp. | Implantable pulse generator that generates spinal cord stimulation signals for a human body |
JP6498177B2 (en) | 2013-03-15 | 2019-04-10 | プロテウス デジタル ヘルス, インコーポレイテッド | Identity authentication system and method |
US10413730B2 (en) | 2013-03-15 | 2019-09-17 | Cirtec Medical Corp. | Implantable pulse generator that generates spinal cord stimulation signals for a human body |
US9440076B2 (en) | 2013-03-15 | 2016-09-13 | Globus Medical, Inc. | Spinal cord stimulator system |
US9872997B2 (en) | 2013-03-15 | 2018-01-23 | Globus Medical, Inc. | Spinal cord stimulator system |
US10016604B2 (en) | 2013-03-15 | 2018-07-10 | Globus Medical, Inc. | Implantable pulse generator that generates spinal cord stimulation signals for a human body |
AU2014229693A1 (en) | 2013-03-15 | 2015-10-15 | The University Of Western Ontario | Oral mouthpiece and method for the use thereof |
US9887574B2 (en) | 2013-03-15 | 2018-02-06 | Globus Medical, Inc. | Spinal cord stimulator system |
US10226628B2 (en) | 2013-03-15 | 2019-03-12 | Cirtec Medical Corp. | Implantable pulse generator that generates spinal cord stimulation signals for a human body |
CN104769847B (en) | 2013-03-15 | 2018-02-13 | 艾尔弗雷德·E·曼科学研究基金会 | High pressure monitors gradual approaching A/D converter |
EP2968940B1 (en) | 2013-03-15 | 2021-04-07 | The Regents Of The University Of California | Multi-site transcutaneous electrical stimulation of the spinal cord for facilitation of locomotion |
US10175376B2 (en) | 2013-03-15 | 2019-01-08 | Proteus Digital Health, Inc. | Metal detector apparatus, system, and method |
EP2968924B1 (en) * | 2013-03-15 | 2022-07-27 | Fast Track Technologies, Inc. | Electro-stimulation device for systematically compounded modulation of current intensity with other output parameters for affecting biological tissues |
CN105164920B (en) | 2013-03-15 | 2018-02-06 | 艾尔弗雷德·E·曼科学研究基金会 | Current sense multi-output current stimulator with fast on-times |
US9878170B2 (en) | 2013-03-15 | 2018-01-30 | Globus Medical, Inc. | Spinal cord stimulator system |
US11793424B2 (en) | 2013-03-18 | 2023-10-24 | Orthosensor, Inc. | Kinetic assessment and alignment of the muscular-skeletal system and method therefor |
US9259172B2 (en) | 2013-03-18 | 2016-02-16 | Orthosensor Inc. | Method of providing feedback to an orthopedic alignment system |
JP6513638B2 (en) | 2013-05-03 | 2019-05-15 | アルフレッド イー. マン ファウンデーション フォー サイエンティフィック リサーチ | Multi-branch stimulation electrode for subcutaneous area stimulation |
US9221119B2 (en) | 2013-05-03 | 2015-12-29 | Alfred E. Mann Foundation For Scientific Research | High reliability wire welding for implantable devices |
US9308378B2 (en) | 2013-05-03 | 2016-04-12 | Alfred E. Mann Foundation For Scientific Research | Implant recharger handshaking system and method |
US11229789B2 (en) | 2013-05-30 | 2022-01-25 | Neurostim Oab, Inc. | Neuro activator with controller |
JP2016523125A (en) | 2013-05-30 | 2016-08-08 | グラハム エイチ. クリーシー | Local nervous stimulation |
JP6511439B2 (en) | 2013-06-04 | 2019-05-15 | プロテウス デジタル ヘルス, インコーポレイテッド | Systems, devices, and methods for data collection and outcome assessment |
US9895539B1 (en) | 2013-06-10 | 2018-02-20 | Nevro Corp. | Methods and systems for disease treatment using electrical stimulation |
US9155899B2 (en) | 2013-06-17 | 2015-10-13 | Nyxoah SA | Antenna buffer layer for an electromagnetic control unit |
CA3075310C (en) | 2013-07-29 | 2022-04-05 | Alfred E. Mann Foundation For Scientific Research | Microprocessor controlled class e driver |
AU2014296322B2 (en) * | 2013-07-29 | 2020-01-16 | Alfred E. Mann Foundation For Scientific Research | High efficiency magnetic link for implantable devices |
AU2014296320B2 (en) | 2013-07-29 | 2018-07-26 | Alfred E. Mann Foundation For Scientific Research | Implant charging field control through radio link |
US9857821B2 (en) | 2013-08-14 | 2018-01-02 | Witricity Corporation | Wireless power transfer frequency adjustment |
US9796576B2 (en) | 2013-08-30 | 2017-10-24 | Proteus Digital Health, Inc. | Container with electronically controlled interlock |
CN105848708A (en) | 2013-09-03 | 2016-08-10 | 恩多斯蒂姆股份有限公司 | Methods and systems of electrode polarity switching in electrical stimulation therapy |
MX356850B (en) | 2013-09-20 | 2018-06-15 | Proteus Digital Health Inc | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping. |
US9577864B2 (en) | 2013-09-24 | 2017-02-21 | Proteus Digital Health, Inc. | Method and apparatus for use with received electromagnetic signal at a frequency not known exactly in advance |
CA2925754C (en) | 2013-09-27 | 2023-02-21 | The Regents Of The University Of California | Engaging the cervical spinal cord circuitry to re-enable volitional control of hand function in tetraplegic subjects |
US10084880B2 (en) | 2013-11-04 | 2018-09-25 | Proteus Digital Health, Inc. | Social media networking based on physiologic information |
US10149978B1 (en) | 2013-11-07 | 2018-12-11 | Nevro Corp. | Spinal cord modulation for inhibiting pain via short pulse width waveforms, and associated systems and methods |
US9780573B2 (en) | 2014-02-03 | 2017-10-03 | Witricity Corporation | Wirelessly charged battery system |
US11383083B2 (en) | 2014-02-11 | 2022-07-12 | Livanova Usa, Inc. | Systems and methods of detecting and treating obstructive sleep apnea |
US9952266B2 (en) | 2014-02-14 | 2018-04-24 | Witricity Corporation | Object detection for wireless energy transfer systems |
WO2015161035A1 (en) | 2014-04-17 | 2015-10-22 | Witricity Corporation | Wireless power transfer systems with shield openings |
US9842687B2 (en) | 2014-04-17 | 2017-12-12 | Witricity Corporation | Wireless power transfer systems with shaped magnetic components |
US9837860B2 (en) | 2014-05-05 | 2017-12-05 | Witricity Corporation | Wireless power transmission systems for elevators |
EP3140680B1 (en) | 2014-05-07 | 2021-04-21 | WiTricity Corporation | Foreign object detection in wireless energy transfer systems |
EP3157621B1 (en) * | 2014-06-18 | 2019-08-07 | Vanderbilt University | Multichannel biphasic signal generator circuit |
US9452293B2 (en) * | 2014-06-19 | 2016-09-27 | Inspire Medical Systems, Inc. | Hybrid communication channel for communicating with an implantable medical device |
WO2015196123A2 (en) | 2014-06-20 | 2015-12-23 | Witricity Corporation | Wireless power transfer systems for surfaces |
US9842688B2 (en) | 2014-07-08 | 2017-12-12 | Witricity Corporation | Resonator balancing in wireless power transfer systems |
US10574091B2 (en) | 2014-07-08 | 2020-02-25 | Witricity Corporation | Enclosures for high power wireless power transfer systems |
EP3180071B1 (en) | 2014-08-15 | 2021-09-22 | Axonics, Inc. | External pulse generator device and associated system for trial nerve stimulation |
WO2016025910A1 (en) | 2014-08-15 | 2016-02-18 | Axonics Modulation Technologies, Inc. | Implantable lead affixation structure for nerve stimulation to alleviate bladder dysfunction and other indications |
US10682521B2 (en) | 2014-08-15 | 2020-06-16 | Axonics Modulation Technologies, Inc. | Attachment devices and associated methods of use with a nerve stimulation charging device |
EP3180073B1 (en) | 2014-08-15 | 2020-03-11 | Axonics Modulation Technologies, Inc. | System for neurostimulation electrode configurations based on neural localization |
JP6779860B2 (en) | 2014-08-15 | 2020-11-04 | アクソニクス モジュレーション テクノロジーズ インコーポレイテッド | Integrated EMG clinician programming device for use with implantable neurostimulators |
CA2958199C (en) | 2014-08-15 | 2023-03-07 | Axonics Modulation Technologies, Inc. | Electromyographic lead positioning and stimulation titration in a nerve stimulation system for treatment of overactive bladder |
EP3180069B1 (en) | 2014-08-17 | 2020-05-13 | Nine Continents Medical, Inc. | Miniature implatable neurostimulator system for sciatic nerves and their branches |
US20210275808A1 (en) * | 2014-08-17 | 2021-09-09 | Coloplast A/S | Implantable Pulse Generator with Automatic Jump-Start |
EP3183028A4 (en) | 2014-08-21 | 2018-05-02 | The Regents of the University of California | Regulation of autonomic control of bladder voiding after a complete spinal cord injury |
WO2016033369A1 (en) | 2014-08-27 | 2016-03-03 | The Regents Of The University Of California | Multi-electrode array for spinal cord epidural stimulation |
US10471268B2 (en) | 2014-10-16 | 2019-11-12 | Mainstay Medical Limited | Systems and methods for monitoring muscle rehabilitation |
US9682234B2 (en) | 2014-11-17 | 2017-06-20 | Endostim, Inc. | Implantable electro-medical device programmable for improved operational life |
US9843217B2 (en) | 2015-01-05 | 2017-12-12 | Witricity Corporation | Wireless energy transfer for wearables |
CN107427683B (en) | 2015-01-09 | 2019-06-21 | 艾克索尼克斯调制技术股份有限公司 | For can plant the improvement antenna and application method of nerve stimulator |
JP6805153B2 (en) | 2015-01-09 | 2020-12-23 | アクソニクス モジュレーション テクノロジーズ インコーポレイテッド | How to use with patient remote devices and associated neurostimulation systems |
EP3242721B1 (en) | 2015-01-09 | 2019-09-18 | Axonics Modulation Technologies, Inc. | Attachment devices and associated methods of use with a nerve stimulation charging device |
WO2016118954A1 (en) * | 2015-01-23 | 2016-07-28 | Juan Parodi | Sensors for detecting acute stroke and method of using same |
US9294802B1 (en) | 2015-01-30 | 2016-03-22 | Rovi Guides, Inc. | Gesture control based on prosthetic nerve signal detection |
US11077301B2 (en) | 2015-02-21 | 2021-08-03 | NeurostimOAB, Inc. | Topical nerve stimulator and sensor for bladder control |
CN113908438A (en) | 2015-03-19 | 2022-01-11 | 启迪医疗仪器公司 | Stimulation for treating sleep disordered breathing |
US10052486B2 (en) | 2015-04-06 | 2018-08-21 | Medtronic, Inc. | Timed delivery of electrical stimulation therapy |
WO2017011346A1 (en) | 2015-07-10 | 2017-01-19 | Abbott Diabetes Care Inc. | System, device and method of dynamic glucose profile response to physiological parameters |
JP6946261B2 (en) | 2015-07-10 | 2021-10-06 | アクソニクス インコーポレイテッド | Implantable nerve stimulators and methods with internal electronics without ASICs |
US11051543B2 (en) | 2015-07-21 | 2021-07-06 | Otsuka Pharmaceutical Co. Ltd. | Alginate on adhesive bilayer laminate film |
WO2017035512A1 (en) | 2015-08-26 | 2017-03-02 | The Regents Of The University Of California | Concerted use of noninvasive neuromodulation device with exoskeleton to enable voluntary movement and greater muscle activation when stepping in a chronically paralyzed subject |
WO2017044904A1 (en) * | 2015-09-11 | 2017-03-16 | Nalu Medical, Inc. | Apparatus for peripheral or spinal stimulation |
US10248899B2 (en) | 2015-10-06 | 2019-04-02 | Witricity Corporation | RFID tag and transponder detection in wireless energy transfer systems |
US9929721B2 (en) | 2015-10-14 | 2018-03-27 | Witricity Corporation | Phase and amplitude detection in wireless energy transfer systems |
US10063110B2 (en) | 2015-10-19 | 2018-08-28 | Witricity Corporation | Foreign object detection in wireless energy transfer systems |
EP3365958B1 (en) | 2015-10-22 | 2020-05-27 | WiTricity Corporation | Dynamic tuning in wireless energy transfer systems |
US11318310B1 (en) | 2015-10-26 | 2022-05-03 | Nevro Corp. | Neuromodulation for altering autonomic functions, and associated systems and methods |
US11097122B2 (en) * | 2015-11-04 | 2021-08-24 | The Regents Of The University Of California | Magnetic stimulation of the spinal cord to restore control of bladder and/or bowel |
US10075019B2 (en) | 2015-11-20 | 2018-09-11 | Witricity Corporation | Voltage source isolation in wireless power transfer systems |
US10195423B2 (en) | 2016-01-19 | 2019-02-05 | Axonics Modulation Technologies, Inc. | Multichannel clip device and methods of use |
US9517338B1 (en) | 2016-01-19 | 2016-12-13 | Axonics Modulation Technologies, Inc. | Multichannel clip device and methods of use |
AU2017211121B2 (en) | 2016-01-25 | 2022-02-24 | Nevro Corp. | Treatment of congestive heart failure with electrical stimulation, and associated systems and methods |
EP3407965B1 (en) | 2016-01-29 | 2021-03-03 | Axonics Modulation Technologies, Inc. | Systems for frequency adjustment to optimize charging of implantable neurostimulator |
US10263473B2 (en) | 2016-02-02 | 2019-04-16 | Witricity Corporation | Controlling wireless power transfer systems |
WO2017139406A1 (en) | 2016-02-08 | 2017-08-17 | Witricity Corporation | Pwm capacitor control |
JP7072510B2 (en) | 2016-02-12 | 2022-05-20 | アクソニクス インコーポレイテッド | External pulse generator devices and related methods for experimental nerve stimulation |
EP3432975B1 (en) | 2016-03-21 | 2024-02-14 | Nalu Medical, Inc. | Devices for positioning external devices in relation to implanted devices |
CA3021522A1 (en) | 2016-04-19 | 2017-10-26 | Brain Sentinel, Inc. | Systems and methods for characterization of seizures |
US10327810B2 (en) | 2016-07-05 | 2019-06-25 | Mainstay Medical Limited | Systems and methods for enhanced implantation of electrode leads between tissue layers |
EP3995175A1 (en) | 2016-07-15 | 2022-05-11 | ONWARD Medical B.V. | Pulse generating system |
WO2018017463A1 (en) | 2016-07-18 | 2018-01-25 | Nalu Medical, Inc. | Methods and systems for treating pelvic disorders and pain conditions |
CN109843149B (en) | 2016-07-22 | 2020-07-07 | 普罗秋斯数字健康公司 | Electromagnetic sensing and detection of ingestible event markers |
US11540973B2 (en) | 2016-10-21 | 2023-01-03 | Spr Therapeutics, Llc | Method and system of mechanical nerve stimulation for pain relief |
JP2019535377A (en) | 2016-10-26 | 2019-12-12 | プロテウス デジタル ヘルス, インコーポレイテッド | Method for producing capsules with ingestible event markers |
EP3323466B1 (en) * | 2016-11-16 | 2024-04-03 | ONWARD Medical N.V. | An active closed-loop medical system |
WO2018094207A1 (en) | 2016-11-17 | 2018-05-24 | Endostim, Inc. | Modular stimulation system for the treatment of gastrointestinal disorders |
US11241297B2 (en) | 2016-12-12 | 2022-02-08 | Cadwell Laboratories, Inc. | System and method for high density electrode management |
EP3585475B1 (en) | 2017-02-24 | 2024-04-03 | Nalu Medical, Inc. | Apparatus with sequentially implanted stimulators |
US11596330B2 (en) | 2017-03-21 | 2023-03-07 | Abbott Diabetes Care Inc. | Methods, devices and system for providing diabetic condition diagnosis and therapy |
WO2018217791A1 (en) * | 2017-05-23 | 2018-11-29 | The Regents Of The University Of California | Accessing spinal networks to address sexual dysfunction |
CN108209912B (en) * | 2017-05-25 | 2020-06-05 | 深圳市前海未来无限投资管理有限公司 | Electromyographic signal acquisition method and device |
WO2019006376A1 (en) | 2017-06-29 | 2019-01-03 | Witricity Corporation | Protection and control of wireless power systems |
EP3421081B1 (en) | 2017-06-30 | 2020-04-15 | GTX medical B.V. | A system for neuromodulation |
AU2018316277B2 (en) | 2017-08-11 | 2023-12-07 | Inspire Medical Systems, Inc. | Cuff electrode |
EP3681381A1 (en) | 2017-09-14 | 2020-07-22 | Orthosensor Inc. | Non-symmetrical insert sensing system and method therefor |
EP3459449B1 (en) * | 2017-09-26 | 2023-04-26 | Nokia Technologies Oy | Apparatus for sensing biosignals |
US20200324108A1 (en) * | 2017-10-10 | 2020-10-15 | Cochlear Limited | Neural stimulator with flying lead electrode |
EP3700617A4 (en) | 2017-10-25 | 2021-08-04 | Epineuron Technologies Inc. | Systems and methods for delivering neuroregenerative therapy |
US10589089B2 (en) | 2017-10-25 | 2020-03-17 | Epineuron Technologies Inc. | Systems and methods for delivering neuroregenerative therapy |
JP2021510608A (en) | 2017-11-07 | 2021-04-30 | ニューロスティム オーエービー インコーポレイテッド | Non-invasive nerve activator with adaptive circuit |
CA3083143C (en) * | 2017-11-20 | 2021-06-08 | University Of Central Florida Research Foundation, Inc. | Monolithic neural interface system |
EP3755418B1 (en) | 2018-02-22 | 2023-06-21 | Axonics, Inc. | Neurostimulation leads for trial nerve stimulation |
US11517239B2 (en) * | 2018-04-05 | 2022-12-06 | Cadwell Laboratories, Inc. | Systems and methods for processing and displaying electromyographic signals |
US11596337B2 (en) | 2018-04-24 | 2023-03-07 | Cadwell Laboratories, Inc | Methods and systems for operating an intraoperative neurophysiological monitoring system in conjunction with electrocautery procedures |
US11115074B1 (en) * | 2018-07-05 | 2021-09-07 | Snap Inc. | Wearable device antenna |
US10471251B1 (en) | 2018-07-31 | 2019-11-12 | Manicka Institute Llc | Subcutaneous device for monitoring and/or providing therapies |
US11717674B2 (en) | 2018-07-31 | 2023-08-08 | Manicka Institute Llc | Subcutaneous device for use with remote device |
US10576291B2 (en) | 2018-07-31 | 2020-03-03 | Manicka Institute Llc | Subcutaneous device |
US11433233B2 (en) | 2020-11-25 | 2022-09-06 | Calyan Technologies, Inc. | Electrode contact for a subcutaneous device |
US10716511B2 (en) | 2018-07-31 | 2020-07-21 | Manicka Institute Llc | Subcutaneous device for monitoring and/or providing therapies |
US11179571B2 (en) | 2018-07-31 | 2021-11-23 | Manicka Institute Llc | Subcutaneous device for monitoring and/or providing therapies |
US11660444B2 (en) | 2018-07-31 | 2023-05-30 | Manicka Institute Llc | Resilient body component contact for a subcutaneous device |
US10646721B2 (en) | 2018-07-31 | 2020-05-12 | Manicka Institute Llc | Injectable subcutaneous device |
US11185684B2 (en) | 2018-09-18 | 2021-11-30 | Cadwell Laboratories, Inc. | Minimally invasive two-dimensional grid electrode |
US11517245B2 (en) | 2018-10-30 | 2022-12-06 | Cadwell Laboratories, Inc. | Method and system for data synchronization |
US11471087B2 (en) | 2018-11-09 | 2022-10-18 | Cadwell Laboratories, Inc. | Integrity verification system for testing high channel count neuromonitoring recording equipment |
DE18205817T1 (en) | 2018-11-13 | 2020-12-24 | Gtx Medical B.V. | SENSOR IN CLOTHING OF LIMBS OR FOOTWEAR |
ES2911465T3 (en) | 2018-11-13 | 2022-05-19 | Onward Medical N V | Control system for the reconstruction and/or restoration of a patient's movement |
US11529107B2 (en) | 2018-11-27 | 2022-12-20 | Cadwell Laboratories, Inc. | Methods for automatic generation of EEG montages |
US11128076B2 (en) | 2019-01-21 | 2021-09-21 | Cadwell Laboratories, Inc. | Connector receptacle |
US11590352B2 (en) | 2019-01-29 | 2023-02-28 | Nevro Corp. | Ramped therapeutic signals for modulating inhibitory interneurons, and associated systems and methods |
EP3917611A4 (en) * | 2019-01-31 | 2022-10-12 | The University of Chicago | Bionic breast |
EP3693055B1 (en) | 2019-02-09 | 2022-05-11 | ONWARD Medical N.V. | Wireless power transfer for medical devices |
EP3695878B1 (en) | 2019-02-12 | 2023-04-19 | ONWARD Medical N.V. | A system for neuromodulation |
WO2020185902A1 (en) | 2019-03-11 | 2020-09-17 | Axonics Modulation Technologies, Inc. | Charging device with off-center coil |
US11478137B2 (en) * | 2019-04-08 | 2022-10-25 | Electronics And Telecommunications Research Institute | Capsule endoscope image receiver and capsule endoscope device having the same |
US11848090B2 (en) | 2019-05-24 | 2023-12-19 | Axonics, Inc. | Trainer for a neurostimulator programmer and associated methods of use with a neurostimulation system |
US11439829B2 (en) | 2019-05-24 | 2022-09-13 | Axonics, Inc. | Clinician programmer methods and systems for maintaining target operating temperatures |
EP3747504A1 (en) | 2019-06-05 | 2020-12-09 | GTX medical B.V. | Antenna for an implantable pulse generator |
JP2022538419A (en) | 2019-06-26 | 2022-09-02 | ニューロスティム テクノロジーズ エルエルシー | Noninvasive neuroactivation device with adaptive circuitry |
US11364381B2 (en) | 2019-10-01 | 2022-06-21 | Epineuron Technologies Inc. | Methods for delivering neuroregenerative therapy and reducing post-operative and chronic pain |
US11812978B2 (en) | 2019-10-15 | 2023-11-14 | Orthosensor Inc. | Knee balancing system using patient specific instruments |
DE19211698T1 (en) | 2019-11-27 | 2021-09-02 | Onward Medical B.V. | Neuromodulation system |
EP4017580A4 (en) | 2019-12-16 | 2023-09-06 | Neurostim Technologies LLC | Non-invasive nerve activator with boosted charge delivery |
US10987060B1 (en) | 2020-09-14 | 2021-04-27 | Calyan Technologies, Inc. | Clip design for a subcutaneous device |
US11583682B2 (en) | 2020-12-07 | 2023-02-21 | Onward Medical N.V. | Antenna for an implantable pulse generator |
CN114272523B (en) * | 2021-12-27 | 2023-05-26 | 燕山大学 | Portable animal transcranial ultrasonic stimulation and brain myoelectricity wireless acquisition system |
US20240113534A1 (en) * | 2022-09-30 | 2024-04-04 | The Alfred E. Mann Foundation For Scientific Research | Wake-able electronic device and methods for waking thereof |
Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4232679A (en) * | 1977-01-26 | 1980-11-11 | Pacesetter Systems, Inc. | Programmable human tissue stimulator |
US5354320A (en) * | 1991-09-12 | 1994-10-11 | Biotronik Mess- Und Therapiegerate Gmbh & Co., Ingenieurburo Berlin | Neurostimulator for production of periodic stimulation pulses |
US5370663A (en) * | 1993-08-12 | 1994-12-06 | Intermedics, Inc. | Implantable cardiac-stimulator with flat capacitor |
US6163725A (en) * | 1994-09-06 | 2000-12-19 | Case Western Reserve University | Functional neuromuscular stimulation system |
US6453198B1 (en) * | 2000-04-28 | 2002-09-17 | Medtronic, Inc. | Power management for an implantable medical device |
US6690974B2 (en) * | 2000-04-05 | 2004-02-10 | Neuropace, Inc. | Stimulation signal generator for an implantable device |
Family Cites Families (279)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3421511A (en) * | 1965-12-10 | 1969-01-14 | Medtronic Inc | Implantable electrode for nerve stimulation |
US3654933A (en) * | 1968-11-18 | 1972-04-11 | Medtronic Inc | Implatable electrode |
US3727616A (en) * | 1971-06-15 | 1973-04-17 | Gen Dynamics Corp | Electronic system for the stimulation of biological systems |
GB1434524A (en) * | 1972-04-27 | 1976-05-05 | Nat Res Dev | Urinary control apparatus |
US3774618A (en) | 1972-07-03 | 1973-11-27 | Avery Labor Inc | Implantable nerve stimulation electrode |
US3902501A (en) | 1973-06-21 | 1975-09-02 | Medtronic Inc | Endocardial electrode |
US3941136A (en) * | 1973-11-21 | 1976-03-02 | Neuronyx Corporation | Method for artificially inducing urination, defecation, or sexual excitation |
US3943938A (en) * | 1974-02-27 | 1976-03-16 | Paul Wexler | Anal sphincter device and barium enema plug |
US3939843A (en) * | 1974-03-04 | 1976-02-24 | Medtronic, Inc. | Transvenous electrode |
US3939841A (en) * | 1974-03-06 | 1976-02-24 | Dohring Albert A | Acupuncture needle guide and restraint |
US3926198A (en) * | 1974-06-10 | 1975-12-16 | Arco Med Prod Co | Cardiac pacer |
US3943932A (en) * | 1975-01-17 | 1976-03-16 | Yen Kong Woo | Acupuncture needles and holder |
US4257423A (en) * | 1978-11-06 | 1981-03-24 | Medtronic, Inc. | Medical device |
US4262678A (en) * | 1979-06-28 | 1981-04-21 | Medtronic, Inc. | Pacing lead with tine protector |
US4254775A (en) * | 1979-07-02 | 1981-03-10 | Mieczyslaw Mirowski | Implantable defibrillator and package therefor |
BR8008859A (en) | 1979-10-10 | 1981-08-25 | Cyclotech Med Ind | PAIN BLOCKING BANDAGE |
DE3015260A1 (en) | 1980-04-21 | 1981-10-22 | Siemens AG, 1000 Berlin und 8000 München | ENDOCARD ELECTRODE ARRANGEMENT |
US4424812A (en) | 1980-10-09 | 1984-01-10 | Cordis Corporation | Implantable externally programmable microprocessor-controlled tissue stimulator |
US4406288A (en) | 1981-04-06 | 1983-09-27 | Hugh P. Cash | Bladder control device and method |
US4721118A (en) * | 1981-04-20 | 1988-01-26 | Cordis Leads, Inc. | Pervenous electrical pacing lead with foldable fins |
US4585013A (en) * | 1981-04-20 | 1986-04-29 | Cordis Corporation | Lumenless pervenous electrical lead and method of implantation |
US4793353A (en) | 1981-06-30 | 1988-12-27 | Borkan William N | Non-invasive multiprogrammable tissue stimulator and method |
US4512351A (en) * | 1982-11-19 | 1985-04-23 | Cordis Corporation | Percutaneous lead introducing system and method |
US4519404A (en) | 1983-09-28 | 1985-05-28 | Fleischhacker John J | Endocardial electrode lead with conical fixation mechanism |
US4585005A (en) * | 1984-04-06 | 1986-04-29 | Regents Of University Of California | Method and pacemaker for stimulating penile erection |
US4607639A (en) | 1984-05-18 | 1986-08-26 | Regents Of The University Of California | Method and system for controlling bladder evacuation |
US4739764A (en) * | 1984-05-18 | 1988-04-26 | The Regents Of The University Of California | Method for stimulating pelvic floor muscles for regulating pelvic viscera |
US4703755A (en) | 1984-05-18 | 1987-11-03 | The Regents Of The University Of California | Control system for the stimulation of two bodily functions |
US4771779A (en) | 1984-05-18 | 1988-09-20 | The Regents Of The University Of California | System for controlling bladder evacuation |
US4590946A (en) | 1984-06-14 | 1986-05-27 | Biomed Concepts, Inc. | Surgically implantable electrode for nerve bundles |
US4573481A (en) * | 1984-06-25 | 1986-03-04 | Huntington Institute Of Applied Research | Implantable electrode array |
US4590689A (en) | 1984-08-30 | 1986-05-27 | Vynalam, Ltd. | Air-trapping insoles |
US4602624A (en) | 1984-10-11 | 1986-07-29 | Case Western Reserve University | Implantable cuff, method of manufacture, and method of installation |
US4649936A (en) * | 1984-10-11 | 1987-03-17 | Case Western Reserve University | Asymmetric single electrode cuff for generation of unidirectionally propagating action potentials for collision blocking |
US4628942A (en) | 1984-10-11 | 1986-12-16 | Case Western Reserve University | Asymmetric shielded two electrode cuff |
US4569351A (en) * | 1984-12-20 | 1986-02-11 | University Of Health Sciences/The Chicago Medical School | Apparatus and method for stimulating micturition and certain muscles in paraplegic mammals |
US4658515A (en) * | 1985-02-05 | 1987-04-21 | Oatman Donald S | Heat insulating insert for footwear |
US4716888A (en) * | 1985-06-17 | 1988-01-05 | Cordis Corporation | Tined leads |
US4835372A (en) | 1985-07-19 | 1989-05-30 | Clincom Incorporated | Patient care system |
US4741341A (en) * | 1986-03-12 | 1988-05-03 | Siemens-Pacesetter, Inc. | Protection circuit and method for implanted ECG telemetry circuits |
US5167229A (en) * | 1986-03-24 | 1992-12-01 | Case Western Reserve University | Functional neuromuscular stimulation system |
US4750499A (en) | 1986-08-20 | 1988-06-14 | Hoffer Joaquin A | Closed-loop, implanted-sensor, functional electrical stimulation system for partial restoration of motor functions |
US4934368A (en) | 1988-01-21 | 1990-06-19 | Myo/Kinetics Systems, Inc. | Multi-electrode neurological stimulation apparatus |
US4926875A (en) | 1988-01-25 | 1990-05-22 | Baylor College Of Medicine | Implantable and extractable biological sensor probe |
US4920979A (en) | 1988-10-12 | 1990-05-01 | Huntington Medical Research Institute | Bidirectional helical electrode for nerve stimulation |
US4940065A (en) | 1989-01-23 | 1990-07-10 | Regents Of The University Of California | Surgically implantable peripheral nerve electrode |
US4989617A (en) * | 1989-07-14 | 1991-02-05 | Case Western Reserve University | Intramuscular electrode for neuromuscular stimulation system |
US5154172A (en) | 1989-11-13 | 1992-10-13 | Cyberonics, Inc. | Constant current sources with programmable voltage source |
US5235980A (en) | 1989-11-13 | 1993-08-17 | Cyberonics, Inc. | Implanted apparatus disabling switching regulator operation to allow radio frequency signal reception |
US5265608A (en) | 1990-02-22 | 1993-11-30 | Medtronic, Inc. | Steroid eluting electrode for peripheral nerve stimulation |
US5669161A (en) | 1990-02-26 | 1997-09-23 | Huang; Ing-Jing | Shock-absorbing cushion |
US5095905A (en) * | 1990-06-07 | 1992-03-17 | Medtronic, Inc. | Implantable neural electrode |
US5113869A (en) | 1990-08-21 | 1992-05-19 | Telectronics Pacing Systems, Inc. | Implantable ambulatory electrocardiogram monitor |
US5282845A (en) * | 1990-10-01 | 1994-02-01 | Ventritex, Inc. | Multiple electrode deployable lead |
US5370671A (en) | 1991-03-26 | 1994-12-06 | Empi, Inc. | Incontinence electrode apparatus |
US5215086A (en) | 1991-05-03 | 1993-06-01 | Cyberonics, Inc. | Therapeutic treatment of migraine symptoms by stimulation |
US5222494A (en) | 1991-07-31 | 1993-06-29 | Cyberonics, Inc. | Implantable tissue stimulator output stabilization system |
US5335664A (en) | 1991-09-17 | 1994-08-09 | Casio Computer Co., Ltd. | Monitor system and biological signal transmitter therefor |
US5324322A (en) | 1992-04-20 | 1994-06-28 | Case Western Reserve University | Thin film implantable electrode and method of manufacture |
SE9201453L (en) | 1992-05-08 | 1993-07-12 | Jens Schouenborg | MEDICAL DEVICE FOR RELIEFING THE PAIN CONDITION INCLUDING AN ELECTRIC PLATE |
GB9211085D0 (en) | 1992-05-23 | 1992-07-08 | Tippey Keith E | Electrical stimulation |
US5330515A (en) | 1992-06-17 | 1994-07-19 | Cyberonics, Inc. | Treatment of pain by vagal afferent stimulation |
US6319599B1 (en) | 1992-07-14 | 2001-11-20 | Theresa M. Buckley | Phase change thermal control materials, method and apparatus |
US6004662A (en) | 1992-07-14 | 1999-12-21 | Buckley; Theresa M. | Flexible composite material with phase change thermal storage |
US5257634A (en) | 1992-07-16 | 1993-11-02 | Angeion Corporation | Low impedence defibrillation catheter electrode |
US5300107A (en) * | 1992-10-22 | 1994-04-05 | Medtronic, Inc. | Universal tined myocardial pacing lead |
US5344439A (en) | 1992-10-30 | 1994-09-06 | Medtronic, Inc. | Catheter with retractable anchor mechanism |
JP3142398B2 (en) | 1992-11-06 | 2001-03-07 | 三菱電機株式会社 | Portable semiconductor device and manufacturing method thereof |
US5397338A (en) * | 1993-03-29 | 1995-03-14 | Maven Labs, Inc. | Electrotherapy device |
US5289821A (en) * | 1993-06-30 | 1994-03-01 | Swartz William M | Method of ultrasonic Doppler monitoring of blood flow in a blood vessel |
US5369257A (en) | 1993-07-08 | 1994-11-29 | Jmk International, Inc. | Windshield de-icing and defrosting mitt using microwave energy heating and method |
US5400784A (en) * | 1993-10-15 | 1995-03-28 | Case Western Reserve University | Slowly penetrating inter-fascicular nerve cuff electrode and method of using |
US5411537A (en) | 1993-10-29 | 1995-05-02 | Intermedics, Inc. | Rechargeable biomedical battery powered devices with recharging and control system therefor |
US5486202A (en) * | 1993-12-17 | 1996-01-23 | Intermedics, Inc. | Cardiac stimulator lead connector |
US5476500A (en) | 1993-12-20 | 1995-12-19 | Ventritex, Inc. | Endocardial lead system with defibrillation electrode fixation |
US5454840A (en) | 1994-04-05 | 1995-10-03 | Krakovsky; Alexander A. | Potency package |
CA2121219A1 (en) | 1994-04-11 | 1995-10-12 | Robert L. Erickson | Methods using repositionable instructions and kits containing same |
US5505201A (en) * | 1994-04-20 | 1996-04-09 | Case Western Reserve University | Implantable helical spiral cuff electrode |
US5645586A (en) | 1994-07-08 | 1997-07-08 | Ventritex, Inc. | Conforming implantable defibrillator |
US6249703B1 (en) | 1994-07-08 | 2001-06-19 | Medtronic, Inc. | Handheld patient programmer for implantable human tissue stimulator |
DE4433111A1 (en) | 1994-09-16 | 1996-03-21 | Fraunhofer Ges Forschung | Cuff electrode |
US5531778A (en) | 1994-09-20 | 1996-07-02 | Cyberonics, Inc. | Circumneural electrode assembly |
US5480416A (en) * | 1994-09-22 | 1996-01-02 | Intermedics, Inc. | Cardiac pacemaker with universal coating |
US5588960A (en) | 1994-12-01 | 1996-12-31 | Vidamed, Inc. | Transurethral needle delivery device with cystoscope and method for treatment of urinary incontinence |
US5487756A (en) * | 1994-12-23 | 1996-01-30 | Simon Fraser University | Implantable cuff having improved closure |
US5591217A (en) * | 1995-01-04 | 1997-01-07 | Plexus, Inc. | Implantable stimulator with replenishable, high value capacitive power source and method therefor |
US5741319A (en) * | 1995-01-27 | 1998-04-21 | Medtronic, Inc. | Biocompatible medical lead |
US5733322A (en) * | 1995-05-23 | 1998-03-31 | Medtronic, Inc. | Positive fixation percutaneous epidural neurostimulation lead |
US5540730A (en) * | 1995-06-06 | 1996-07-30 | Cyberonics, Inc. | Treatment of motility disorders by nerve stimulation |
US5690693A (en) | 1995-06-07 | 1997-11-25 | Sulzer Intermedics Inc. | Transcutaneous energy transmission circuit for implantable medical device |
US5702431A (en) | 1995-06-07 | 1997-12-30 | Sulzer Intermedics Inc. | Enhanced transcutaneous recharging system for battery powered implantable medical device |
US5722999A (en) * | 1995-08-02 | 1998-03-03 | Pacesetter, Inc. | System and method for storing and displaying historical medical data measured by an implantable medical device |
US5759199A (en) | 1995-08-02 | 1998-06-02 | Pacesetter, Inc. | System and method for ambulatory monitoring and programming of an implantable medical device |
US5607461A (en) * | 1995-10-20 | 1997-03-04 | Nexmed, Inc. | Apparatus and method for delivering electrical stimulus to tissue |
WO1997018857A1 (en) | 1995-11-24 | 1997-05-29 | Advanced Bionics Corporation | System and method for conditioning pelvic musculature using an implanted microstimulator |
US5683447A (en) | 1995-12-19 | 1997-11-04 | Ventritex, Inc. | Lead with septal defibrillation and pacing electrodes |
US5683432A (en) | 1996-01-11 | 1997-11-04 | Medtronic, Inc. | Adaptive, performance-optimizing communication system for communicating with an implanted medical device |
EP0788813B1 (en) | 1996-02-15 | 2003-10-15 | Nihon Kohden Corporation | An apparatus for treating urinary incontinence |
US6051017A (en) | 1996-02-20 | 2000-04-18 | Advanced Bionics Corporation | Implantable microstimulator and systems employing the same |
CA2171067A1 (en) | 1996-03-05 | 1997-09-06 | Brian J. Andrews | Neural prosthesis |
DE19611777C2 (en) | 1996-03-14 | 2001-09-27 | Biotronik Mess & Therapieg | Arrangement for electrical contacting |
US7269457B2 (en) | 1996-04-30 | 2007-09-11 | Medtronic, Inc. | Method and system for vagal nerve stimulation with multi-site cardiac pacing |
US5716384A (en) * | 1996-07-08 | 1998-02-10 | Pacesetter, Inc. | Method and system for organizing, viewing and manipulating information in implantable device programmer |
US5733313A (en) * | 1996-08-01 | 1998-03-31 | Exonix Corporation | RF coupled, implantable medical device with rechargeable back-up power source |
US5755767A (en) | 1996-08-02 | 1998-05-26 | Pacesetter, Inc. | Anti-dislodgment and anti-perforation distal tip design for transvenous lead |
US5741313A (en) * | 1996-09-09 | 1998-04-21 | Pacesetter, Inc. | Implantable medical device with a reduced volumetric configuration and improved shock stabilization |
US5713939A (en) * | 1996-09-16 | 1998-02-03 | Sulzer Intermedics Inc. | Data communication system for control of transcutaneous energy transmission to an implantable medical device |
US6091995A (en) | 1996-11-08 | 2000-07-18 | Surx, Inc. | Devices, methods, and systems for shrinking tissues |
AU6667698A (en) | 1997-02-26 | 1998-09-18 | Alfred E. Mann Foundation For Scientific Research | Battery-powered patient implantable device |
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 |
US5938596A (en) | 1997-03-17 | 1999-08-17 | Medtronic, Inc. | Medical electrical lead |
US5752977A (en) * | 1997-04-15 | 1998-05-19 | Medtronic, Inc. | Efficient high data rate telemetry format for implanted medical device |
US5843141A (en) | 1997-04-25 | 1998-12-01 | Medronic, Inc. | Medical lead connector system |
US5861015A (en) * | 1997-05-05 | 1999-01-19 | Benja-Athon; Anuthep | Modulation of the nervous system for treatment of pain and related disorders |
US6321124B1 (en) | 1997-05-28 | 2001-11-20 | Transneuronix, Inc. | Implant device for electrostimulation and/or monitoring of endo-abdominal cavity tissue |
US5861016A (en) * | 1997-05-28 | 1999-01-19 | Swing; Fred P. | Method of wound healing using electrical stimulation and acupuncture needles |
US6125645A (en) | 1997-06-12 | 2000-10-03 | Horn; Stephen T. | Moisture removal phase shift personal cooling Garment |
US5899933A (en) | 1997-06-16 | 1999-05-04 | Axon Engineering, Inc. | Nerve cuff electrode carrier |
US5824027A (en) | 1997-08-14 | 1998-10-20 | Simon Fraser University | Nerve cuff having one or more isolated chambers |
US6597954B1 (en) * | 1997-10-27 | 2003-07-22 | Neuropace, Inc. | System and method for controlling epileptic seizures with spatially separated detection and stimulation electrodes |
US6149636A (en) | 1998-06-29 | 2000-11-21 | The Procter & Gamble Company | Disposable article having proactive sensors |
US5857968A (en) * | 1997-11-24 | 1999-01-12 | Benja-Athon; Anuthep | Coupling device in electroacupuncture |
GB9802382D0 (en) * | 1998-02-04 | 1998-04-01 | Medtronic Inc | Apparatus for management of sleep apnea |
FR2775592B1 (en) | 1998-03-06 | 2000-06-16 | Patrick Cazaux | PORTABLE ACUPUNCTURE APPARATUS |
US6055457A (en) * | 1998-03-13 | 2000-04-25 | Medtronic, Inc. | Single pass A-V lead with active fixation device |
US6836685B1 (en) | 1998-04-07 | 2004-12-28 | William R. Fitz | Nerve stimulation method and apparatus for pain relief |
US6216038B1 (en) | 1998-04-29 | 2001-04-10 | Medtronic, Inc. | Broadcast audible sound communication of programming change in an implantable medical device |
US6370433B1 (en) * | 1998-04-29 | 2002-04-09 | Medtronic, Inc. | Interrogation of an implantable medical device using broadcast audible sound communication |
US6450172B1 (en) | 1998-04-29 | 2002-09-17 | Medtronic, Inc. | Broadcast audible sound communication from an implantable medical device |
US6845271B2 (en) * | 1998-06-03 | 2005-01-18 | Neurocontrol Corporation | Treatment of shoulder dysfunction using a percutaneous intramuscular stimulation system |
ATE311927T1 (en) | 1998-06-03 | 2005-12-15 | Neurocontrol Corp | PERCUTANE INTRAMUSCULAR STIMULATION SYSTEM |
US6016451A (en) * | 1998-06-24 | 2000-01-18 | Sanchez-Rodarte; Salvador | Neurological stabilizer device |
US6941171B2 (en) | 1998-07-06 | 2005-09-06 | Advanced Bionics Corporation | Implantable stimulator methods for treatment of incontinence and pain |
US6735474B1 (en) | 1998-07-06 | 2004-05-11 | Advanced Bionics Corporation | Implantable stimulator system and method for treatment of incontinence and pain |
US6282082B1 (en) | 1998-07-31 | 2001-08-28 | Qubit, Llc | Case for a modular tablet computer system |
US6308101B1 (en) | 1998-07-31 | 2001-10-23 | Advanced Bionics Corporation | Fully implantable cochlear implant system |
US6240316B1 (en) | 1998-08-14 | 2001-05-29 | Advanced Bionics Corporation | Implantable microstimulation system for treatment of sleep apnea |
US6558320B1 (en) | 2000-01-20 | 2003-05-06 | Medtronic Minimed, Inc. | Handheld personal data assistant (PDA) with a medical device and method of using the same |
PT1115454E (en) | 1998-08-31 | 2007-01-31 | Travanti Pharma Inc | Controlled dosage drug delivery system |
US6212431B1 (en) | 1998-09-08 | 2001-04-03 | Advanced Bionics Corporation | Power transfer circuit for implanted devices |
AU6118799A (en) | 1998-10-06 | 2000-04-26 | Bio Control Medical, Ltd. | Incontinence treatment device |
DE19847446B4 (en) | 1998-10-08 | 2010-04-22 | Biotronik Gmbh & Co. Kg | Nerve electrode assembly |
US5948006A (en) | 1998-10-14 | 1999-09-07 | Advanced Bionics Corporation | Transcutaneous transmission patch |
US6275737B1 (en) | 1998-10-14 | 2001-08-14 | Advanced Bionics Corporation | Transcutaneous transmission pouch |
US6505074B2 (en) | 1998-10-26 | 2003-01-07 | Birinder R. Boveja | Method and apparatus for electrical stimulation adjunct (add-on) treatment of urinary incontinence and urological disorders using an external stimulator |
US20060122660A1 (en) * | 1998-10-26 | 2006-06-08 | Boveja Birinder R | Method and system for modulating sacral nerves and/or its branches in a patient to provide therapy for urological disorders and/or fecal incontinence, using rectangular and/or complex electrical pulses |
US7076307B2 (en) | 2002-05-09 | 2006-07-11 | Boveja Birinder R | Method and system for modulating the vagus nerve (10th cranial nerve) with electrical pulses using implanted and external components, to provide therapy neurological and neuropsychiatric disorders |
US6836684B1 (en) | 1998-10-30 | 2004-12-28 | Neurocon Aps | Method to control an overactive bladder |
EP1135060A1 (en) | 1998-12-04 | 2001-09-26 | The Johns Hopkins University | Telemetric in vivo bladder monitoring system |
US6257906B1 (en) | 1999-02-08 | 2001-07-10 | 3Com Corporation | Functionally illuminated electronic connector with improved light dispersion |
ES2230826T3 (en) * | 1999-04-02 | 2005-05-01 | Sorin Biomedica Crm S.R.L. | ANCHORAGE STRUCTURE FOR IMPLANTABLE ELECTRODES. |
US6542776B1 (en) | 1999-04-14 | 2003-04-01 | Transneuronix Inc. | Gastric stimulator apparatus and method for installing |
US6200265B1 (en) * | 1999-04-16 | 2001-03-13 | Medtronic, Inc. | Peripheral memory patch and access method for use with an implantable medical device |
US6166518A (en) | 1999-04-26 | 2000-12-26 | Exonix Corporation | Implantable power management system |
US6055456A (en) | 1999-04-29 | 2000-04-25 | Medtronic, Inc. | Single and multi-polar implantable lead for sacral nerve electrical stimulation |
US6169925B1 (en) | 1999-04-30 | 2001-01-02 | Medtronic, Inc. | Telemetry system for implantable medical devices |
US6240317B1 (en) * | 1999-04-30 | 2001-05-29 | Medtronic, Inc. | Telemetry system for implantable medical devices |
DE19930263A1 (en) * | 1999-06-25 | 2000-12-28 | Biotronik Mess & Therapieg | Method and device for data transmission between an electromedical implant and an external device |
US6804558B2 (en) | 1999-07-07 | 2004-10-12 | Medtronic, Inc. | System and method of communicating between an implantable medical device and a remote computer system or health care provider |
US6445955B1 (en) | 1999-07-08 | 2002-09-03 | Stephen A. Michelson | Miniature wireless transcutaneous electrical neuro or muscular-stimulation unit |
US20020019652A1 (en) * | 1999-07-08 | 2002-02-14 | Cyclotec Advanced Medical Technologies | Two part tens bandage |
US6607500B2 (en) | 1999-07-08 | 2003-08-19 | Cyclotec Advanced Medical Technologies, Inc. | Integrated cast and muscle stimulation system |
US6308105B1 (en) | 1999-07-15 | 2001-10-23 | Medtronic Inc. | Medical electrical stimulation system using an electrode assembly having opposing semi-circular arms |
US6516227B1 (en) | 1999-07-27 | 2003-02-04 | Advanced Bionics Corporation | Rechargeable spinal cord stimulator system |
US7177690B2 (en) * | 1999-07-27 | 2007-02-13 | Advanced Bionics Corporation | Implantable system having rechargeable battery indicator |
US6553263B1 (en) * | 1999-07-30 | 2003-04-22 | Advanced Bionics Corporation | Implantable pulse generators using rechargeable zero-volt technology lithium-ion batteries |
US6456866B1 (en) | 1999-09-28 | 2002-09-24 | Dustin Tyler | Flat interface nerve electrode and a method for use |
US6381496B1 (en) | 1999-10-01 | 2002-04-30 | Advanced Bionics Corporation | Parameter context switching for an implanted device |
US7949395B2 (en) | 1999-10-01 | 2011-05-24 | Boston Scientific Neuromodulation Corporation | Implantable microdevice with extended lead and remote electrode |
US6660265B1 (en) | 1999-10-15 | 2003-12-09 | The Brigham & Women's Hospital, Inc. | Fresh, cryopreserved, or minimally cardiac valvular xenografts |
US6442433B1 (en) | 1999-10-26 | 2002-08-27 | Medtronic, Inc. | Apparatus and method for remote troubleshooting, maintenance and upgrade of implantable device systems |
DE10053118A1 (en) | 1999-10-29 | 2001-05-31 | Medtronic Inc | Remote self-identification apparatus and method for components in medical device systems |
US6409675B1 (en) | 1999-11-10 | 2002-06-25 | Pacesetter, Inc. | Extravascular hemodynamic monitor |
US6904324B2 (en) | 1999-12-01 | 2005-06-07 | Meagan Medical, Inc. | Method and apparatus for deploying a percutaneous probe |
WO2001039831A1 (en) * | 1999-12-06 | 2001-06-07 | Advanced Bionics Corporation | Implantable device programmer |
US6442432B2 (en) | 1999-12-21 | 2002-08-27 | Medtronic, Inc. | Instrumentation and software for remote monitoring and programming of implantable medical devices (IMDs) |
DE19962915A1 (en) | 1999-12-23 | 2001-09-06 | Intelligent Implants Gmbh | Device for the protected operation of neuroprostheses and method therefor |
US6920359B2 (en) | 2000-02-15 | 2005-07-19 | Advanced Bionics Corporation | Deep brain stimulation system for the treatment of Parkinson's Disease or other disorders |
US6580947B1 (en) * | 2000-03-10 | 2003-06-17 | Medtronic, Inc. | Magnetic field sensor for an implantable medical device |
US6974411B2 (en) | 2000-04-03 | 2005-12-13 | Neoguide Systems, Inc. | Endoscope with single step guiding apparatus |
US6338347B1 (en) * | 2000-04-04 | 2002-01-15 | Yun-Yin Chung | Blood circulation stimulator |
JP2001286569A (en) | 2000-04-05 | 2001-10-16 | Polytronics Ltd | Endermism device |
US6650943B1 (en) | 2000-04-07 | 2003-11-18 | Advanced Bionics Corporation | Fully implantable neurostimulator for cavernous nerve stimulation as a therapy for erectile dysfunction and other sexual dysfunction |
US6441747B1 (en) * | 2000-04-18 | 2002-08-27 | Motorola, Inc. | Wireless system protocol for telemetry monitoring |
US6580948B2 (en) * | 2000-04-25 | 2003-06-17 | Medtronic, Inc. | Interface devices for instruments in communication with implantable medical devices |
US7167756B1 (en) * | 2000-04-28 | 2007-01-23 | Medtronic, Inc. | Battery recharge management for an implantable medical device |
US6859364B2 (en) * | 2000-06-06 | 2005-02-22 | Matsushita Refrigeration Company | Portable information appliance |
US6505077B1 (en) * | 2000-06-19 | 2003-01-07 | Medtronic, Inc. | Implantable medical device with external recharging coil electrical connection |
US6738670B1 (en) | 2000-06-19 | 2004-05-18 | Medtronic, Inc. | Implantable medical device telemetry processor |
US7672730B2 (en) | 2001-03-08 | 2010-03-02 | Advanced Neuromodulation Systems, Inc. | Methods and apparatus for effectuating a lasting change in a neural-function of a patient |
US6482154B1 (en) * | 2000-08-02 | 2002-11-19 | Medtronic, Inc | Long range implantable medical device telemetry system with positive patient identification |
US6510347B2 (en) * | 2000-08-17 | 2003-01-21 | William N. Borkan | Spinal cord stimulation leads |
US6868288B2 (en) | 2000-08-26 | 2005-03-15 | Medtronic, Inc. | Implanted medical device telemetry using integrated thin film bulk acoustic resonator filtering |
US6535766B1 (en) | 2000-08-26 | 2003-03-18 | Medtronic, Inc. | Implanted medical device telemetry using integrated microelectromechanical filtering |
US6432037B1 (en) | 2000-08-31 | 2002-08-13 | Flexiprobe Ltd. | Intravaginal device for electrically stimulating and/or for sensing electrical activity of muscles and/or nerves defining and surrounding the intravaginal cavity |
US6684109B1 (en) * | 2000-09-13 | 2004-01-27 | Oscor Inc. | Endocardial lead |
US7198603B2 (en) | 2003-04-14 | 2007-04-03 | Remon Medical Technologies, Inc. | Apparatus and methods using acoustic telemetry for intrabody communications |
US6530914B1 (en) | 2000-10-24 | 2003-03-11 | Scimed Life Systems, Inc. | Deflectable tip guide in guide system |
US6738671B2 (en) * | 2000-10-26 | 2004-05-18 | Medtronic, Inc. | Externally worn transceiver for use with an implantable medical device |
US6567703B1 (en) * | 2000-11-08 | 2003-05-20 | Medtronic, Inc. | Implantable medical device incorporating miniaturized circuit module |
US6591137B1 (en) * | 2000-11-09 | 2003-07-08 | Neuropace, Inc. | Implantable neuromuscular stimulator for the treatment of gastrointestinal disorders |
US6574510B2 (en) * | 2000-11-30 | 2003-06-03 | Cardiac Pacemakers, Inc. | Telemetry apparatus and method for an implantable medical device |
US6658300B2 (en) | 2000-12-18 | 2003-12-02 | Biosense, Inc. | Telemetric reader/charger device for medical sensor |
SE0004765D0 (en) * | 2000-12-20 | 2000-12-20 | St Jude Medical | An electrode head fixation arrangement |
IL155922A0 (en) | 2000-12-22 | 2003-12-23 | Aspen Aerogels Inc | Aerogel composite with fibrous batting |
US6735475B1 (en) | 2001-01-30 | 2004-05-11 | Advanced Bionics Corporation | Fully implantable miniature neurostimulator for stimulation as a therapy for headache and/or facial pain |
US6445088B1 (en) | 2001-03-20 | 2002-09-03 | American Power Conversion | Multipurpose data port |
US7047078B2 (en) | 2001-03-30 | 2006-05-16 | Case Western Reserve University | Methods for stimulating components in, on, or near the pudendal nerve or its branches to achieve selective physiologic responses |
JP2004526510A (en) * | 2001-03-30 | 2004-09-02 | ケース ウエスタン リザーブ ユニバーシティ | Systems and methods for selectively stimulating components in, on, or near pudendal nerves or pudendal nerve branches to achieve selective physiological responses |
US7369897B2 (en) | 2001-04-19 | 2008-05-06 | Neuro And Cardiac Technologies, Llc | Method and system of remotely controlling electrical pulses provided to nerve tissue(s) by an implanted stimulator system for neuromodulation therapies |
US6907295B2 (en) | 2001-08-31 | 2005-06-14 | Biocontrol Medical Ltd. | Electrode assembly for nerve control |
US6928320B2 (en) | 2001-05-17 | 2005-08-09 | Medtronic, Inc. | Apparatus for blocking activation of tissue or conduction of action potentials while other tissue is being therapeutically activated |
US6643552B2 (en) | 2001-05-30 | 2003-11-04 | Foster-Miller, Inc. | Implantable devices having a liquid crystal polymer substrate |
US6687543B1 (en) * | 2001-06-06 | 2004-02-03 | Pacesetter, Inc. | Implantable cardiac stimulation device having reduced shelf current consumption and method |
US20050055063A1 (en) * | 2001-07-20 | 2005-03-10 | Loeb Gerald E. | Method and apparatus for the treatment of urinary tract dysfunction |
EP1416903A2 (en) | 2001-07-20 | 2004-05-12 | Alfred E. Mann Institute for Biomedical Engineering at the University of Southern California | Method and apparatus for the treatment of urinary tract dysfunction |
US7103923B2 (en) | 2001-08-07 | 2006-09-12 | Brooke Picotte | Head protector for infants, small children, senior citizens, adults or physically disabled individuals |
US6493881B1 (en) | 2001-08-07 | 2002-12-17 | Brooke Picotte | Head protector for infants and small children |
DE20200685U1 (en) | 2001-08-17 | 2002-03-28 | Hoeven Martin V D | Muscle electrostimulation device |
US6721602B2 (en) | 2001-08-21 | 2004-04-13 | Medtronic, Inc. | Implantable medical device assembly and manufacturing method |
US6600956B2 (en) | 2001-08-21 | 2003-07-29 | Cyberonics, Inc. | Circumneural electrode assembly |
US6449512B1 (en) | 2001-08-29 | 2002-09-10 | Birinder R. Boveja | Apparatus and method for treatment of urological disorders using programmerless implantable pulse generator system |
US6999819B2 (en) | 2001-08-31 | 2006-02-14 | Medtronic, Inc. | Implantable medical electrical stimulation lead fixation method and apparatus |
US6701188B2 (en) * | 2001-09-06 | 2004-03-02 | Medtronic, Inc. | Controlling noise sources during telemetry |
WO2003026736A2 (en) | 2001-09-28 | 2003-04-03 | Northstar Neuroscience, Inc. | Methods and implantable apparatus for electrical therapy |
CN1694746A (en) | 2001-09-28 | 2005-11-09 | 密根医药公司 | Method and apparatus for controlling percutaneous electrical signals |
US7136695B2 (en) * | 2001-10-12 | 2006-11-14 | Pless Benjamin D | Patient-specific template development for neurological event detection |
US7260436B2 (en) * | 2001-10-16 | 2007-08-21 | Case Western Reserve University | Implantable networked neural system |
US6763269B2 (en) * | 2001-11-02 | 2004-07-13 | Pacesetter, Inc. | Frequency agile telemetry system for implantable medical device |
US6891353B2 (en) | 2001-11-07 | 2005-05-10 | Quallion Llc | Safety method, device and system for an energy storage device |
US6937894B1 (en) | 2001-11-08 | 2005-08-30 | Pacesetter, Inc. | Method of recharging battery for an implantable medical device |
US6672895B2 (en) * | 2001-11-26 | 2004-01-06 | Cardiac Pacemakers, Inc. | Marking system for lead connector and header |
US6862480B2 (en) * | 2001-11-29 | 2005-03-01 | Biocontrol Medical Ltd. | Pelvic disorder treatment device |
US6993393B2 (en) * | 2001-12-19 | 2006-01-31 | Cardiac Pacemakers, Inc. | Telemetry duty cycle management system for an implantable medical device |
US7729776B2 (en) | 2001-12-19 | 2010-06-01 | Cardiac Pacemakers, Inc. | Implantable medical device with two or more telemetry systems |
US6963780B2 (en) | 2002-01-31 | 2005-11-08 | Medtronic, Inc. | Implantable medical device including a surface-mount terminal array |
US6985773B2 (en) * | 2002-02-07 | 2006-01-10 | Cardiac Pacemakers, Inc. | Methods and apparatuses for implantable medical device telemetry power management |
US6613953B1 (en) | 2002-03-22 | 2003-09-02 | Dan Altura | Insulator-conductor device for maintaining a wound near normal body temperature |
AU2003221744A1 (en) | 2002-04-19 | 2003-11-03 | Broncus Technologies, Inc. | Devices for maintaining surgically created openings |
JP4000895B2 (en) | 2002-04-23 | 2007-10-31 | 日本電気株式会社 | Bit rate control method and apparatus for real-time communication |
US7191012B2 (en) * | 2003-05-11 | 2007-03-13 | Boveja Birinder R | Method and system for providing pulsed electrical stimulation to a craniel nerve of a patient to provide therapy for neurological and neuropsychiatric disorders |
US20030220673A1 (en) | 2002-05-24 | 2003-11-27 | Snell Jeffrey D. | Multi-device telemetry architecture |
US6856506B2 (en) * | 2002-06-19 | 2005-02-15 | Motion Computing | Tablet computing device with three-dimensional docking support |
EP1517725B1 (en) * | 2002-06-28 | 2015-09-09 | Boston Scientific Neuromodulation Corporation | Microstimulator having self-contained power source and bi-directional telemetry system |
US6925330B2 (en) | 2002-07-10 | 2005-08-02 | Pacesetter, Inc. | Implantable medical device and method for detecting cardiac events without using of refractory or blanking periods |
US20040018336A1 (en) | 2002-07-29 | 2004-01-29 | Brian Farnworth | Thermally insulating products for footwear and other apparel |
US7101607B2 (en) | 2002-08-21 | 2006-09-05 | The Research Foundation Of State University Of New York | Process for enhancing material properties and materials so enhanced |
DE20213613U1 (en) | 2002-08-29 | 2002-10-31 | Biotronik Mess & Therapieg | Removable "Operation Module" |
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 |
US7608067B2 (en) | 2002-11-06 | 2009-10-27 | Aram Bonni | Patient-adjustable incontinence device (AID) |
US6990376B2 (en) * | 2002-12-06 | 2006-01-24 | The Regents Of The University Of California | Methods and systems for selective control of bladder function |
US7591786B2 (en) | 2003-01-31 | 2009-09-22 | Sonosite, Inc. | Dock for connecting peripheral devices to a modular diagnostic ultrasound apparatus |
US7499758B2 (en) * | 2003-04-11 | 2009-03-03 | Cardiac Pacemakers, Inc. | Helical fixation elements for subcutaneous electrodes |
US7317947B2 (en) * | 2003-05-16 | 2008-01-08 | Medtronic, Inc. | Headset recharger for cranially implantable medical devices |
US20080097564A1 (en) | 2003-07-18 | 2008-04-24 | Peter Lathrop | Electrotherapeutic Device |
US20050038491A1 (en) * | 2003-08-11 | 2005-02-17 | Haack Scott Graham | Cardiac pacing lead having dual fixation and method of using the same |
US7616988B2 (en) | 2003-09-18 | 2009-11-10 | Cardiac Pacemakers, Inc. | System and method for detecting an involuntary muscle movement disorder |
US7343202B2 (en) * | 2004-02-12 | 2008-03-11 | Ndi Medical, Llc. | Method for affecting urinary function with electrode implantation in adipose tissue |
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 |
US7280872B1 (en) | 2003-10-16 | 2007-10-09 | Transoma Medical, Inc. | Wireless communication with implantable medical device |
US7187968B2 (en) * | 2003-10-23 | 2007-03-06 | Duke University | Apparatus for acquiring and transmitting neural signals and related methods |
US7118801B2 (en) * | 2003-11-10 | 2006-10-10 | Gore Enterprise Holdings, Inc. | Aerogel/PTFE composite insulating material |
US20060035054A1 (en) * | 2004-01-05 | 2006-02-16 | Aspen Aerogels, Inc. | High performance vacuum-sealed insulations |
US20080132969A1 (en) | 2004-02-12 | 2008-06-05 | Ndi Medical, Inc. | Systems and methods for bilateral stimulation of left and right branches of the dorsal genital nerves to treat urologic dysfunctions |
WO2005079295A2 (en) | 2004-02-12 | 2005-09-01 | Ndi Medical, Llc | Portable assemblies, systems and methods for providing functional or therapeutic neuromuscular stimulation |
US8467875B2 (en) | 2004-02-12 | 2013-06-18 | Medtronic, Inc. | Stimulation of dorsal genital nerves to treat urologic dysfunctions |
US8086318B2 (en) | 2004-02-12 | 2011-12-27 | Ndi Medical, Llc | Portable assemblies, systems, and methods for providing functional or therapeutic neurostimulation |
US20080161874A1 (en) | 2004-02-12 | 2008-07-03 | Ndi Medical, Inc. | Systems and methods for a trial stage and/or long-term treatment of disorders of the body using neurostimulation |
US7475245B1 (en) * | 2004-03-15 | 2009-01-06 | Cardiac Pacemakers, Inc. | System and method for providing secure exchange of sensitive information with an implantable medical device |
US20060033720A1 (en) * | 2004-06-04 | 2006-02-16 | Robbins Michael S | Control interface bezel |
US7865250B2 (en) * | 2004-06-10 | 2011-01-04 | Medtronic Urinary Solutions, Inc. | Methods for electrical stimulation of nerves in adipose tissue regions |
US7283867B2 (en) * | 2004-06-10 | 2007-10-16 | Ndi Medical, Llc | Implantable system and methods for acquisition and processing of electrical signals from muscles and/or nerves and/or central nervous system tissue |
US9308382B2 (en) * | 2004-06-10 | 2016-04-12 | Medtronic Urinary Solutions, Inc. | Implantable pulse generator systems and methods for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue |
ATE523221T1 (en) * | 2004-06-10 | 2011-09-15 | Medtronic Urinary Solutions Inc | SYSTEMS AND METHODS FOR THE BILATERAL STIMULATION OF LEFT AND RIGHT BRANCHES OF THE DORSAL GENITAL NERVES FOR THE TREATMENT OF FUNCTIONAL DISORDERS SUCH AS URINARY INCONTINENCE |
US7751891B2 (en) | 2004-07-28 | 2010-07-06 | Cyberonics, Inc. | Power supply monitoring for an implantable device |
US7532933B2 (en) * | 2004-10-20 | 2009-05-12 | Boston Scientific Scimed, Inc. | Leadless cardiac stimulation systems |
WO2006055547A2 (en) | 2004-11-15 | 2006-05-26 | Izex Technologies, Inc. | Instrumented orthopedic and other medical implants |
US7443057B2 (en) | 2004-11-29 | 2008-10-28 | Patrick Nunally | Remote power charging of electronic devices |
US20070100411A1 (en) | 2005-10-27 | 2007-05-03 | Medtronic, Inc. | Implantable medical electrical stimulation lead fixation method and apparatus |
-
2005
- 2005-06-10 US US11/150,734 patent/US7283867B2/en active Active
- 2005-06-10 WO PCT/US2005/020480 patent/WO2006022993A2/en active Application Filing
- 2005-06-10 WO PCT/US2005/020474 patent/WO2005123185A1/en active Application Filing
- 2005-06-10 US US11/150,535 patent/US7813809B2/en active Active
- 2005-06-10 US US11/150,418 patent/US7239918B2/en active Active
- 2005-06-10 WO PCT/US2005/020506 patent/WO2005123181A2/en active Application Filing
-
2010
- 2010-06-28 US US12/825,089 patent/US20110004269A1/en not_active Abandoned
Patent Citations (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4232679A (en) * | 1977-01-26 | 1980-11-11 | Pacesetter Systems, Inc. | Programmable human tissue stimulator |
US4232679B1 (en) * | 1977-01-26 | 1988-05-31 | ||
US5354320A (en) * | 1991-09-12 | 1994-10-11 | Biotronik Mess- Und Therapiegerate Gmbh & Co., Ingenieurburo Berlin | Neurostimulator for production of periodic stimulation pulses |
US5370663A (en) * | 1993-08-12 | 1994-12-06 | Intermedics, Inc. | Implantable cardiac-stimulator with flat capacitor |
US6163725A (en) * | 1994-09-06 | 2000-12-19 | Case Western Reserve University | Functional neuromuscular stimulation system |
US6690974B2 (en) * | 2000-04-05 | 2004-02-10 | Neuropace, Inc. | Stimulation signal generator for an implantable device |
US6453198B1 (en) * | 2000-04-28 | 2002-09-17 | Medtronic, Inc. | Power management for an implantable medical device |
Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8131377B2 (en) | 2007-07-11 | 2012-03-06 | Boston Scientific Neuromodulation Corporation | Telemetry listening window management for an implantable medical device |
Also Published As
Publication number | Publication date |
---|---|
US20050277999A1 (en) | 2005-12-15 |
WO2005123185A1 (en) | 2005-12-29 |
US20050278000A1 (en) | 2005-12-15 |
WO2006022993A2 (en) | 2006-03-02 |
WO2005123181A3 (en) | 2006-11-16 |
US20050277844A1 (en) | 2005-12-15 |
WO2006022993A3 (en) | 2006-12-21 |
US7813809B2 (en) | 2010-10-12 |
US7239918B2 (en) | 2007-07-03 |
US7283867B2 (en) | 2007-10-16 |
US20110004269A1 (en) | 2011-01-06 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7813809B2 (en) | Implantable pulse generator for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue | |
US8165692B2 (en) | Implantable pulse generator power management | |
US10434320B2 (en) | Implantable pulse generator systems and methods for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue | |
US20070299483A1 (en) | Implantable pulse generator for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue | |
US11679257B2 (en) | Method of treating an overactive bladder condition | |
US9205255B2 (en) | Implantable pulse generator systems and methods for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue | |
EP2029219B1 (en) | Implantable pulse generator systems | |
US8195304B2 (en) | Implantable systems and methods for acquisition and processing of electrical signals | |
US20070060967A1 (en) | Implantable pulse generator systems and methods for providing functional and /or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue | |
US20070067000A1 (en) | Implantable pulse generator systems and methods for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue | |
US20070060979A1 (en) | Implantable pulse generator systems and methods for providing functional and / or therapeutic stimulation of muscles and / or nerves and / or central nervous system tissue | |
US20070060955A1 (en) | Implantable pulse generator systems and methods for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue | |
US20070066995A1 (en) | Implantable pulse generator systems and methods for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue | |
EP3636314B1 (en) | Neural stimulation devices and systems for treatment of chronic inflammation | |
WO2006124068A1 (en) | Systems for electrical stimulation of nerves in adipose tissue regions | |
EP1786511A2 (en) | Implantable pulse generator for providing functional and/or therapeutic stimulation of muscles and/or nerves and/or central nervous system tissue |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AK | Designated states |
Kind code of ref document: A2 Designated state(s): AE AG AL AM AT AU AZ BA BB BG BR BW BY BZ CA CH CN CO CR CU CZ DE DK DM DZ EC EE EG ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KM KP KR KZ LC LK LR LS LT LU LV MA MD MG MK MN MW MX MZ NA NG NI NO NZ OM PG PH PL PT RO RU SC SD SE SG SK SL SM SY TJ TM TN TR TT TZ UA UG US UZ VC VN YU ZA ZM ZW |
|
AL | Designated countries for regional patents |
Kind code of ref document: A2 Designated state(s): BW GH GM KE LS MW MZ NA SD SL SZ TZ UG ZM ZW AM AZ BY KG KZ MD RU TJ TM AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HU IE IS IT LT LU MC NL PL PT RO SE SI SK TR BF BJ CF CG CI CM GA GN GQ GW ML MR NE SN TD TG |
|
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
NENP | Non-entry into the national phase |
Ref country code: DE |
|
WWW | Wipo information: withdrawn in national office |
Country of ref document: DE |
|
122 | Ep: pct application non-entry in european phase |