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WO2025014843A2 - Système de surveillance et de distribution continue d'énergie pour dispositifs implantables - Google Patents

Système de surveillance et de distribution continue d'énergie pour dispositifs implantables Download PDF

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Publication number
WO2025014843A2
WO2025014843A2 PCT/US2024/036984 US2024036984W WO2025014843A2 WO 2025014843 A2 WO2025014843 A2 WO 2025014843A2 US 2024036984 W US2024036984 W US 2024036984W WO 2025014843 A2 WO2025014843 A2 WO 2025014843A2
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WO
WIPO (PCT)
Prior art keywords
wearable device
implant
power signal
power
protocol
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Pending
Application number
PCT/US2024/036984
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WO2025014843A3 (fr
Inventor
Philipp Gutruf
Tucker STUART
Kevin Kasper
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University of Arizona
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University of Arizona
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Publication of WO2025014843A3 publication Critical patent/WO2025014843A3/fr
Pending legal-status Critical Current
Anticipated expiration legal-status Critical

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    • 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
    • A61N1/378—Electrical supply
    • A61N1/3787—Electrical supply from an external energy source
    • 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
    • A61N1/37217—Means for communicating with stimulators characterised by the communication link, e.g. acoustic or tactile
    • A61N1/37223—Circuits for electromagnetic coupling
    • A61N1/37229—Shape or location of the implanted or external antenna
    • 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
    • A61N1/37252—Details of algorithms or data aspects of communication system, e.g. handshaking, transmitting specific data or segmenting data
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J7/00—Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries
    • H02J7/00032—Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries characterised by data exchange
    • H02J7/00034—Charger exchanging data with an electronic device, i.e. telephone, whose internal battery is under charge
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J2310/00—The network for supplying or distributing electric power characterised by its spatial reach or by the load
    • H02J2310/10—The network having a local or delimited stationary reach
    • H02J2310/20—The network being internal to a load
    • H02J2310/23—The load being a medical device, a medical implant, or a life supporting device
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J50/00—Circuit arrangements or systems for wireless supply or distribution of electric power
    • H02J50/80—Circuit arrangements or systems for wireless supply or distribution of electric power involving the exchange of data, concerning supply or distribution of electric power, between transmitting devices and receiving devices

Definitions

  • the present disclosure is generally directed to a continuous power delivery system for implantable devices, and more particularly, to a continuous power delivery and data a monitoring system for subcutaneously implantable devices.
  • FIG. 1 illustrates an example continuous power delivery and data monitoring system for subcutaneously implantable devices according to several embodiments of the present disclosure
  • FIGS.3A-3D illustrate various views of a continuous power delivery and data monitoring system according to one embodiment of the present disclosure
  • FIGS.4A-4C illustrate various aspects of long-term human trials of the continuous power delivery and data monitoring system according to embodiments described herein
  • FIGS.5A-5F illustrate a continuous power delivery and data monitoring system according to one embodiment
  • FIGS.7A-7F illustrate long-term results of the large animal study of the continuous power delivery and data monitoring system of FIGS.5 and 6.
  • WPT wireless power transfer
  • the present disclosure provides a system that includes a continuously operating, wireless, wearable biosymbiotic device for powering and communicating with, for example, Near Field Communication (NFC)-capable implantable devices.
  • This wearable device contains a small power storage which is recharged through far-field wireless power transfer, enabling continuous operation without the need to remove or connect the device for charging.
  • NFC Near Field Communication
  • the wearable device can energize and establish bidirectional communication with any NFC-capable device implanted up to several centimeters deep.
  • the teachings of the present disclosure demonstrate continuous seven-day operation without any changes in habit or routines of the wearers.
  • the teachings of the present disclosure show the feasibility of long-term bone health monitoring when paired with a fully-implantable, wireless, battery-free bone strain sensor.
  • the system has broad applications for patient monitoring, from post-surgical recovery monitoring to assessment of therapeutic interventions, and as a sensing and stimulation interface for long-term disease management.
  • the present disclosure provides a continuous power delivery and data monitoring system for subcutaneously implantable devices.
  • the system includes an implant device that includes communications circuitry for implantation into a patient.
  • the system also includes a wearable device configured with power management circuitry, a rechargeable battery, and communications circuitry to wirelessly transmit power to the implant device.
  • the system also includes power transmitter circuitry to communicate with the wearable device to wirelessly deliver power to the wearable device to charge the rechargeable battery of the wearable device.
  • Communication between the implant and the wearable device may comply with, for example, known and/or proprietary near-field communications protocols.
  • Communication between the wearable device and the power transmitter circuitry may comply with, for example, known and/or proprietary far-field communications protocols.
  • the wearable device may include memory to store data associated with the implant device, and may also include additional Docket No.: UA22-173PCT communications circuitry to exchange commands and data with, for example, a patient monitoring database for long-term collection of patient data.
  • FIG. 1 illustrates an example continuous power delivery and data monitoring system 100 for subcutaneously implantable devices, according to several embodiments of the present disclosure.
  • the system 100 includes power transmitter circuitry 102 configured to wirelessly transmit power to a wearable device 104, and the wearable device 104 is generally configured to wirelessly transmit power to a subdermal implant device 106.
  • the power transmitter circuitry 102 is configured to generate power and to transmit power, via far- field control circuitry 103, using a known and/or proprietary far-field power communications protocol, for example, Wireless Power Transfer (WPT), Wireless Energy Harvesting (WEH), etc.
  • the power transmitter circuitry 102 may include a far-field antenna 108 to transmit power.
  • the antenna 108 may include, for example, known and/or proprietary antenna designs, for example, known and/or proprietary antenna designs such as a dipole antenna, trace antenna, monopole antenna, etc., and power may be transmitted, via antenna 108 at a selected frequency to optimize power transfer, for example, 915 MHz, etc.
  • the power transmitter circuitry 102 is configured to transmit power at a range of, for example, several meters.
  • the power transmitter circuitry 102 may be embodied as a desktop device, bed side device, automobile device, etc., such that when a patient is within range, power can be transmitted to the wearable device 104, as described below.
  • the wearable device 104 includes a far-field antenna 110 to communicate with and receive power from the power transmitter 102.
  • the antenna 110 may be matched or tuned to antenna 108, and may include, for example, known and/or proprietary antenna designs, for example, known and/or proprietary antenna designs such as a dipole antenna, trace antenna, monopole antenna, etc., and power may be transmitted, via antenna 108 at a selected frequency to optimize power transfer, for example, 915 MHz, etc.
  • the wearable device 104 also includes battery management circuitry 112 generally configured to provide controllable charging and discharging of a rechargeable battery 114.
  • the battery 114 may include, for example, lithium ion (LiIon) type rechargeable battery configured to be recharged by transmitted power from the power transmitter 102.
  • the wearable device 104 also includes near field communications (NFC) control and powering circuitry 118 generally configured to exchange commands and data with the implant device 106, and to provide power delivery to the implant device 106.
  • NFC near field communications
  • the wearable device 104 Docket No.: UA22-173PCT also includes an NFC antenna 120.
  • the antenna 120 may include, for example, known and/or proprietary antenna designs, for example, known and/or proprietary antenna designs such as a 3D printed antenna with ferrite core antenna, trace antenna, coil antenna, etc., and power may be transmitted, via antenna 108 at a selected frequency to optimize power transfer, for example, 13.56 MHz, etc.
  • the wearable device 104 is configured to transmit power at a range of, for example, several centimeters.
  • the implant device 106 includes an NFC antenna 122 to communicate with and receive power from the wearable device 104.
  • the antenna 122 may be matched or tuned to antenna 120, and may include, for example, known and/or proprietary antenna designs, for example, known and/or proprietary antenna designs such as 3D printable antenna with ferrite core antenna, trace antenna, coil antenna, etc., and the implant device 106 may exchange commands and data with the wearable device 104 and receive power transmitted by the wearable device 104, via antenna 122 at a selected frequency to optimize power transfer, for example, 13.56 MHz, etc.
  • the implant device 106 also includes near field communications (NFC) control circuitry 118 generally configured to exchange commands and data with the implant device 106, and to control power delivery to the implant device 106 by coordinating with NFC control circuitry 118 of the wearable device 104.
  • NFC near field communications
  • the implant device 106 also includes one or more implant component(s) 126 generally configured to provide a desired operability of the implant device 106 when subdermally implanted in a patient.
  • the one or more implant component(s) 126 may include, for example, one or more sensors (e.g., temperature sensors, strain sensors, fluid sensors, etc.), one or more light activation devices (e.g., optegenetic stimulation circuitry, light emitting diode (LED) circuitry, etc.), etc., and/or other implant devices that provide for continuous data monitoring and/or therapeutic functionality.
  • the implant component(s) 126 may be continuously powered by the NFC power delivery from the wearable device 104, and may also deliver data from the implant component(s) 126 (e.g., temperature data, strain data, fluid flow data, activation data, etc.) to the wearable device 104 for continuous patient monitoring.
  • the wearable device 106 may also include communications circuitry 116 to exchange commands and data between the wearable device 104 and a patient database 134, via network 130.
  • the communications circuitry 116 may comply or be compatible with, for example, Bluetooth short-range wireless communication, WiFi, and/or other know and/or proprietary communications protocols.
  • the wearable device 104 may also include memory Docket No.: UA22-173PCT circuitry 128 to store data parameters generated by the implant component(s) 126.
  • the patient database 134 may provide remote access to patient data (generated by the implant device 106) by a doctor or clinician.
  • the patient database 134 may include wearable control circuitry 136 to provide administrative and operational control of the wearable device 104.
  • the wearable control circuitry 136 may communicate with the wearable device 104, via network 130, to control power delivery levels provided by the battery management circuitry 112, retrieve patent data stored in memory 128, and/or control other aspects of the functional parameters of the wearable device 104.
  • the patient database 134 may also include implant control circuitry 138 to control various functional parameters of the implant device, via network 130 and wearable device 104.
  • the implant control circuitry 138 may control the implant component(s) 126 to define data collection intervals, intensity levels, etc.
  • the patient database 134 may incorporated with the power transmitter circuitry 102.
  • FIG.2 illustrates an example use-based embodiments of the continuous power delivery and data monitoring systems described herein.
  • FIG.2 illustrates continuous power delivery and data collection at various stages of a patient’s health protocol, for example, in-hospital recovery (top left image), continuous power delivery and data collection during rehabilitation activities (Middle image), and post-surgical rehabilitation, e.g., continuous power delivery and data collection during at-home care activities (bottom right image).
  • the continuous power delivery and data monitoring systems described herein have broad applications for patient monitoring, from post-surgical recovery monitoring to assessment of therapeutic interventions, and as a sensing and stimulation interface for long-term disease management.
  • FIGS. 3A-3D illustrate various features of a continuous power delivery and data monitoring system according to one embodiment of the present disclosure.
  • FIG. 3A illustrates a continuous power delivery and data monitoring system 300 according to one embodiment of the present disclosure.
  • the far-field power transmitter circuitry 102’ is embodied as 915MHz power caster circuitry 302 that can be placed in areas where subjects spend most of their time, which can be discerned subjectively or through neural-network driven behavioral analysis.
  • the wearable device 104’ of this embodiment includes Bluetooth Low Energy communication circuitry 304 and NFC transceiver control circuitry 118’, which may be embodied as an ultra-low-power microcontroller, for example, an STM32WB55, with the capacity for mesh Docket No.: UA22-173PCT networking using, for example, Thread and Zigbee communication protocols.
  • FIG. 3B is a photograph of the wearable device 104’ on a subject’s upper arm. As illustrated in the bottom image, the wearable device 104’ is separated into functional “islands” joined via serpentine interconnects.
  • the serpentine structures between islands improve overall system robustness and conformality, as they minimize strain on the copper traces and deform more readily than linear traces.
  • Battery management circuitry on the wearable enables high efficiency recharge and battery maintenance through a far field antenna and has advanced low power features that can isolate the electrochemical energy storage and charging circuitry from the digital circuitry, to reduce idle state power usage.
  • Embedding the electronics into a 3D printed flexible thermoplastic polyurethane (TPU) mesh offers improved conformality, ensures fixation over the implant site during continuous operation, and avoids issues with skin turnover inherent to devices that use adhesive-based fixation.
  • all electronics are coated in flexible UV-cure TPU resin for improved environmental resistance and physical protection.
  • Fig.3A (bottom) an exploded model shows the layers that comprise the wearable electronics.
  • the NFC antenna 120’ and far field power harvesting antenna 110’ are illustrated.
  • FIG. 3C is a photograph of an NFC-capable implant device 106’ located within the NFC coil antenna 120’ of the wearable device 104’ demonstrating the concept of readout and powering.
  • the wearable antenna is larger than many currently available fully implantable, wireless, battery- free devices, allowing for continued interfacing even through location mismatch and translational movement in highly mobile areas of the body.
  • FIGS.4A-4C illustrate various aspects of long-term human trials of the continuous power delivery and data monitoring system 400 according to embodiments described herein.
  • FIG. 4A is a photograph of the wearable device 104’ on a subject’s upper arm.
  • the device fits comfortably under various types of clothing (FIG. 4B) with no significant losses in power harvesting nor impairment to NFC communication.
  • FIG. 4B To demonstrate long-term, continuous data collection, a 7- day experiment is performed with two subjects.
  • Plots in FIG. 4C show data rate (top portion of plot 400) and battery life (bottom portion of plot 400) of the wearable device 104’ over a continuous one-week period.
  • FIGS. 5A-5F illustrate a continuous power delivery and data monitoring system 500 according to one embodiment.
  • the implant device 106’ is an osseosurface device.
  • FIG.5A is a photograph of implantable osseosurface device 106’ and exploded 3D model showing device composition.
  • FIG.5B is a functional block diagram for implantable device.
  • the 13.56MHz antenna shown in energy harvesting block is also capable of transmitting data.
  • FIG. 5C is a graph of load sweeps for proprietary STMicroelectronics NFC tag power harvesting using ISO 15693. Full wave rectifier results show enhanced power harvesting over original osseosurface devices published previously.
  • FIG.5D illustrates strain data collected from slowly rocking sheep to shift weight onto leg. Strain is relative.
  • FIG.5E is a graph of internal tibia surface temperature recorded during a data collection session.
  • FIG.5F is a graph of data rate in kilobits per second vs days since implantation, showing no degradation in data transmission over monthslong operation.
  • FIGS.6A-6E illustrate various aspects of a large animal model 600 of the continuous power delivery and data monitoring system according to one embodiment.
  • FIG.6A is a photograph of wearable device fixed above target implant on sheep left posterior leg.
  • FIG. 6B is an X-ray showing location of wearable relative to implant.
  • FIG. 6C is a photo during explantation of Docket No.: UA22-173PCT implantable device showing minimal tissue response and fibrous capsule.
  • FIG.6D are time lapse photos of sheep a walking with data makers for hoof, ankle, tibia implant/wearable, and stifle. Video data was analyzed using a deep neural network to best match data from implant.
  • FIG.6E is a graph and photos of time synchronized strain recording and corresponding video frames of the sheep gait cycle.
  • FIGS. 7A-7F illustrate long-term results 700 of the large animal study of the continuous power delivery and data monitoring system of FIGS.5 and 6.
  • FIG.7A is a diagram showing gait data recorded over days since implantation. Accurate strain data was recorded four months post- implantation with no loss in data quality over study duration.
  • FIG. 7B is a graph of strain data extracted from single femur implant over chronic time period. Data show loading of femur during rocking of sheep and demonstrate consistency of device operation over time.
  • FIG.7C is a graph of temperature data from sheep tibia showing circadian rhythm.
  • FIG. 7D is a graph of strain profiles of experimental vs contralateral bone showing minimal changes in bone integrity.
  • FIG. 7E is a fluorescent microscopy image showing osteogenesis at 93 days post implantation. Calcein was administered 10 and 3 days before sacrifice.
  • FIG. 7F is an SEM image (left) and CT scan (right) of implanted bone showing osseointegration and bone overgrowth.
  • Wireless, battery-free implantable electronics enable data collection over long time scales (months to years), as they are not limited by electrochemical power supplies. Through wireless power transfer methods, such as inductive coupling, enough power is provided for implants to operate continuously with complex sensing and stimulation modalities, although the power casting devices are often tethered or, when wearable, have large battery supplies.
  • the teachings herein provide a wireless, wearable device capable of transferring power and exchanging data with wireless, battery-free implantable devices.
  • Far-field power harvesting enables wireless charging of the wearable’s power bank with no modification to daily routines and no interaction required from the wearer.
  • the wearable mesh has a small, personalized form factor and may be manufactured using a basic FDM 3D printer with minor off-the-shelf modifications.
  • Using standardized RF communication protocols and commercially electronic components allows for an accessible, easily produced wearable power casting and data transfer device that is readily adapted to any NFC-capable implant, including already existing devices.
  • the present disclosure demonstrates the ability of this device to energize and communicate with a fully implanted, battery-free bone strain sensor and send collected data over BLE.
  • Continuous data links with implants were maintained through several centimeters of highly mobile muscle tissue in live, freely moving sheep during several fifteen-minute data recording sessions.
  • the gait profile of the sheep was accurately reconstructed using the strain data collected and correlated to video recordings, as shown in FIG. 6D.
  • Collected data is stored locally on a BLE- capable laptop, although can also be stored on an Amazon Web Services (AWS) for immediately storing recorded data securely in the cloud.
  • AWS Amazon Web Services
  • the device was worn on the arm and powered an epidermal NFC-capable sensor for a week of continuous wear, demonstrating the feasibility of chronic vitals monitoring without any input from a patient. This experiment also showcases the ability to wirelessly charge the wearable without tethering or removal of the device.
  • the present disclosure illustrates enhanced capabilities of osseosurface electronics, specifically post-implantation non-surgical adjustment of sensor gain and biasing. Long-term animal studies involving osseosurface devices demonstrate continuous operation in vivo for over six months, sufficient lifetime for monitoring post-fracture bone healing and evaluating bone strength in humans. Additionally, four-point bending of implanted bones revealed minimal differences in strain profiles relative to non-implanted contralaterals (see Fig.
  • Implantable device fabrication Wearable and implantable electronics were fabricated on a flexible panel structure and sent for external manufacturing.
  • the flexible PCB stackup consists of a polyimide substrate (25 ⁇ m) between two layers of ENIG-finished copper (18 ⁇ m/layer). Additional polyimide layers Docket No.: UA22-173PCT (27.5 ⁇ m/layer) were used on both sides as solder mask. Devices were depaneled using UV (355 nm) laser ablation (LPKF; Protolaser U4) and cleaned via sonication (Vevor; TS391LT) in isopropanol (IPA). Surface mount components were placed and reflowed manually with low temperature solder paste (Chip Quick; TS391LT).
  • Wearable mesh fabrication [0041] High-resolution 3D scans of subject arms and legs were collected using a handheld 3D scanner (Shining 3D, EinScan Pro HD) and unfolded into 2D maps using open-source 3D creation software (Blender Foundation, Blender). Flexible mesh drawings referenced these 2D maps to ensure accurate wearable fit and placement.2D mesh drawings were exported from AutoCAD and imported into a 3D modeling software (Dassault Systèmes, Solidworks) for extrusion. Stereolithography (STL) files were generated from the 3D model and imported into 3D slicing software (Prusa3D, PrusaSlicer) to generate machine code for a 3D printer.
  • STL Stereolithography
  • a fusion deposition modeling printer (Creality, CR-10s) was outfitted with a custom x-axis carriage that housed a direct drive extruder (Creality, Sprite Extruder Pro), hotend, and automatic bed leveling unit (Antclabs, BLTouch).
  • a TPU filament (NinjaTek, NinjaFlex) was printed at 30 mm/s and 225°C with a bed temperature of 45°C. After printing, segmented sections of the mesh structure were joined by melting TPU material together at junctions to form the completed linear structures.
  • Wearable device electronics were fabricated in the same manner as implantable device electronics, cleaned with IPA post-assembly, and embedded into the 3D-printed TPU mesh.
  • Implant wireless power-harvesting capability RF power at 2W was provided by a High Frequency (HF) Long Range RFID Reader (Feig Electronic GmbH, ID LR2500).
  • HF High Frequency
  • ID LR2500 The primary Docket No.: UA22-173PCT antenna was connected to a tuning/matching circuit board and tuned at 13.56 MHz with a voltage standing wave ratio (VSWR) below 1.5.
  • VSWR voltage standing wave ratio
  • a 2-turn circular primary antenna with diameter of 20 cm was used to power devices implanted onto sheep femurs and tibias.
  • Experimental bone strength characterization [0046] Mechanical characterization of experimental bone strength was performed using a servo- hydraulic MTS (MTS Systems Corporation, Series 810).
  • Animal Studies [0048] All animal studies were performed following an IACUC approved protocol. Six adult sheep in total were used (3 male, 3 female) for long-term in vivo data collection. Implanted devices were sterilized using ethylene oxide and aerated for 24 hours prior to placement. Sheep were anesthetized using isoflurane prior to surgery. An 8cm incision was made over the left posterior leg.
  • the lateral surface of the femur was exposed subperiosteally, and two devices were placed at the midpoint of the bone, spaced approximately 5cm apart with strain gauges oriented axially along the femur. TGF- ⁇ and CPC-coated gauges were fastened in place using vicryl sutures tied around the circumference of the femur before the incision was closed. Next, a 6cm incision was made anteriorly along the left posterior tibia. The medial and lateral surfaces of the tibia were exposed subperiosteally through this anterior approach. Two devices total were placed on the medial and lateral surfaces of the tibia with TGF- ⁇ /CPC-coated gauges oriented axially.
  • HF High Frequency Long Range RFID Reader
  • ID LR2500 2-turn circular antenna with diameter 20cm and adjustable antenna tuning circuit.
  • the coil antenna was embedded into a 3D printed PLA (OVERTURE, 1.75mm PLA) housing to provide rigidity and maintain structural integrity.
  • the tuning circuit was adjusted to match to 50 Ohms at 13.56 MHz.
  • the strain sensing circuit was implemented using a Wheatstone bridge configuration, with two 1k ⁇ 0.1% resistors (Vishay / Dale, TNPW02011K00BEED) forming one half of the bridge, and a high precision 1k ⁇ metal-foil strain gauge (Micro Measurements; ED-DY-125BZ-10C/E) and 5k ⁇ digital potentiometer (Microchip Technology, MCP4561) in parallel with a 2.2k ⁇ 5% resistor forming the other half.
  • HF Reader control software Feig Electronic GmbH, ID ISOStart+ V11
  • values stored in the NFC tag are read upon boot by the microcontroller and loaded into the digital potentiometer via I2C communication.
  • the low-power, high-precision instrumentation amplifier (Maxim Integrated, MAX41400) uses two digital input pins to adjust gain. These pins are connected to GPIOs on the microcontroller, which are set upon boot using values retrieved from the NFC tag.
  • Gain of individual implants was adjusted as necessary to maintain significant strain signal amplitude without voltage clipping. Wheatstone bridge biasing was adjusted to account for pre- strain of the strain gauge introduced during surgical implantation and subsequent wound healing process.
  • Deep Neural Net Analysis Markerless pose estimation software, DeepLabCut (version 2.2.b6), was used to perform deep neural network analysis. The neural net was trained with several 5-minute long clips, where 20 frames from each were labeled and used as training material. The training session was performed with 50,000 iterations on Puma, a High-Performance Computer at the University of Arizona’s High Performance Computing Lab. After training, a 12-second video clip with consistent gait was tracked and analyzed to extract and plot the coordinates for hoof, ankle, wearable device, and stifle joint. The data were then used to sync data acquired from the wearable device.
  • a list of items joined by the term “and/or” can mean any combination of the listed items.
  • the phrase “A, B and/or C” can mean Docket No.: UA22-173PCT A; B; C; A and B; A and C; B and C; or A, B and C.
  • a list of items joined by the term “at least one of” can mean any combination of the listed terms.
  • the phrases “at least one of A, B or C” can mean A; B; C; A and B; A and C; B and C; or A, B and C.
  • circuitry may comprise, for example, singly or in any combination, hardwired circuitry, programmable circuitry such as processors comprising one or more individual instruction processing cores, state machine circuitry, and/or firmware that stores instructions executed by programmable circuitry and/or future computing circuitry including, for example, massive parallelism, analog or quantum computing, hardware embodiments of accelerators such as neural net processors and non-silicon implementations of the above.
  • the circuitry may, collectively or individually, be embodied as circuitry that forms part of a larger system, for example, an integrated circuit (IC), system on-chip (SoC), application-specific integrated circuit (ASIC), programmable logic devices (PLD), digital signal processors (DSP), field programmable gate array (FPGA), logic gates, registers, semiconductor device, chips, microchips, chip sets, etc.
  • IC integrated circuit
  • SoC system on-chip
  • ASIC application-specific integrated circuit
  • PLD programmable logic devices
  • DSP digital signal processors
  • FPGA field programmable gate array
  • the storage device includes any type of tangible medium, for example, any type of disk including hard disks, floppy disks, optical disks, compact disk read-only memories (CD-ROMs), compact disk rewritables (CD-RWs), and magneto-optical disks, semiconductor devices such as read-only memories (ROMs), random access memories (RAMs) such as dynamic and static RAMs, erasable programmable read-only memories (EPROMs), electrically erasable programmable read-only memories (EEPROMs), flash memories, Solid State Disks (SSDs), embedded multimedia cards (eMMCs), secure digital input/output (SDIO) cards, magnetic or optical cards, or any type of media suitable for storing electronic instructions.
  • ROMs read-only memories
  • RAMs random access memories
  • EPROMs erasable programmable read-only memories
  • EEPROMs electrically erasable programmable read-only memories
  • flash memories Solid State Disks (SSDs), embedded multimedia cards (eMMCs

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  • Measuring And Recording Apparatus For Diagnosis (AREA)
  • Electrotherapy Devices (AREA)

Abstract

La présente invention concerne un système de distribution continue d'énergie pour dispositifs implantables, comprenant : un dispositif portable conçu pour être porté sur le corps d'un patient, le dispositif portable étant configuré pour communiquer avec un émetteur d'énergie et recevoir un premier signal d'énergie par l'intermédiaire d'un premier protocole de communication, le dispositif portable comprenant un circuit de gestion de batterie pour commander la charge d'une batterie à l'aide du premier signal d'énergie et pour commander la décharge de la batterie de manière à générer un second signal d'énergie ; le dispositif portable étant en outre configuré pour communiquer le second signal d'énergie par l'intermédiaire d'un second protocole de communication et d'alimentation en énergie ; et un dispositif d'implant conçu pour être implanté dans le corps du patient, le dispositif d'implant étant configuré pour communiquer avec le dispositif portable et recevoir le second signal d'énergie par l'intermédiaire du second protocole de communication et d'alimentation en énergie, le dispositif d'implant comprenant un ou plusieurs composants d'implant configurés pour être alimentés par le second signal d'énergie.
PCT/US2024/036984 2023-07-07 2024-07-07 Système de surveillance et de distribution continue d'énergie pour dispositifs implantables Pending WO2025014843A2 (fr)

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US202363525625P 2023-07-07 2023-07-07
US63/525,625 2023-07-07

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Publication number Priority date Publication date Assignee Title
CN107003984A (zh) * 2014-09-17 2017-08-01 卡纳里医疗公司 用于使用和监测医疗设备的设备、系统和方法
EP4395124A3 (fr) * 2016-03-21 2024-07-31 Nalu Medical, Inc. Dispositifs et procédés de positionnement de dispositifs externes par rapport à des dispositifs implantés
US12334750B2 (en) * 2021-01-04 2025-06-17 Medtronic Minimed, Inc. Far-field wireless charging of medical devices
WO2022261492A1 (fr) * 2021-06-10 2022-12-15 Northwestern University Systèmes et procédés de surveillance de l'état physiologique d'un sujet vivant et d'administration de substances à cet effet

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