USRE45030E1 - Hermetically sealed RFID microelectronic chip connected to a biocompatible RFID antenna - Google Patents
Hermetically sealed RFID microelectronic chip connected to a biocompatible RFID antenna Download PDFInfo
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- USRE45030E1 USRE45030E1 US14/087,734 US201314087734A USRE45030E US RE45030 E1 USRE45030 E1 US RE45030E1 US 201314087734 A US201314087734 A US 201314087734A US RE45030 E USRE45030 E US RE45030E
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
- A61B90/90—Identification means for patients or instruments, e.g. tags
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- A61B19/44—
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- 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
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
- A61B90/90—Identification means for patients or instruments, e.g. tags
- A61B90/98—Identification means for patients or instruments, e.g. tags using electromagnetic means, e.g. transponders
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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
- A61N1/362—Heart stimulators
- A61N1/37—Monitoring; Protecting
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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
- A61N1/37211—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
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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
- A61N1/37211—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
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- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06K—GRAPHICAL DATA READING; PRESENTATION OF DATA; RECORD CARRIERS; HANDLING RECORD CARRIERS
- G06K19/00—Record carriers for use with machines and with at least a part designed to carry digital markings
- G06K19/06—Record carriers for use with machines and with at least a part designed to carry digital markings characterised by the kind of the digital marking, e.g. shape, nature, code
- G06K19/067—Record carriers with conductive marks, printed circuits or semiconductor circuit elements, e.g. credit or identity cards also with resonating or responding marks without active components
- G06K19/07—Record carriers with conductive marks, printed circuits or semiconductor circuit elements, e.g. credit or identity cards also with resonating or responding marks without active components with integrated circuit chips
- G06K19/077—Constructional details, e.g. mounting of circuits in the carrier
- G06K19/07749—Constructional details, e.g. mounting of circuits in the carrier the record carrier being capable of non-contact communication, e.g. constructional details of the antenna of a non-contact smart card
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- A61B2019/448—
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/08—Sensors provided with means for identification, e.g. barcodes or memory chips
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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
- A61N1/362—Heart stimulators
- A61N1/37—Monitoring; Protecting
- A61N1/3718—Monitoring of or protection against external electromagnetic fields or currents
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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
- A61N1/375—Constructional arrangements, e.g. casings
- A61N1/3752—Details of casing-lead connections
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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
- A61N1/375—Constructional arrangements, e.g. casings
- A61N1/3752—Details of casing-lead connections
- A61N1/3754—Feedthroughs
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- 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
Abstract
An implantable radio frequency identification (RFID) tag includes a hermetically sealed biocompatible housing for an active implantable medical device (AIMD), an RFID microelectronics chip is disposed within the housing, and a biocompatible antenna extends from the RFID microelectronic chip and exteriorly of the housing. In a preferred form of the invention, the antenna is disposed within a header block of the AIMD, and the RFID chip is disposed within the AIMD housing.
Description
The present application is a reissue application of U.S. patent application Ser. No. 12/728,538, filed on Mar. 22, 2010, now U.S. Pat. No. 8,248,232, which is a continuation-in-part of application Ser. No. 12/566,223, filed on Sep. 24, 2009, now U.S. Pat. No. 8,253,555, which is a continuation-in-part of application Ser. No. 11/307,145, filed on Jan. 25, 2006, now U.S. Pat. No. 7,916,013.
This invention relates generally to methods of identifying implanted medical devices. More specifically, this invention relates to implantable and biocompatible radio frequency identification (RFID) tags and associated antennas which may be used with medical devices or for general personal identification purposes.
There are known in the art various methods for identifying implanted medical devices. One such method is the use of X-ray identification tags encapsulated within header blocks of pacemakers or implantable cardioverter defibrillators (ICD). Such X-ray identification tags can be read on an X-ray of the implanted device and provide information to the physician. The information so provided is limited due to space and typically includes only the manufacturer and model number of the implanted device.
It would be beneficial if physicians were able to obtain additional information about an implanted device and/or a patient from an implanted identification tag. Such beneficial information includes, in addition to the manufacturer and model number of the device, the serial number of the device, the treating physician's name and contact information and, if authorized by the patient, the patient's name, contact information, medical condition and treatment, and other relevant information.
Currently, most active implantable medical device (AIMD) patients carry some sort of identification. This could be in the form of a card carried in the wallet or an ID bracelet indicating, for example, that they are a pacemaker wearer of a certain model and serial number. However, such forms of identification are often not reliable. It is quite common for an elderly patient to be presented at the emergency room (ER) of a hospital without their wallet and without wearing any type of a bracelet. In addition, there have been a number of situations where the patient (due to dementia or Alzheimer's, etc.) cannot clearly state that he or she even has a pacemaker.
Oftentimes the ER physician will palpitate the patient's chest and feel that there is an implanted device present. If the patient is comatose, has low blood pressure, or is in another form of cardiac distress, this presents a serious dilemma for the ER. At this moment in time, all that the ER knows is that the patient has some sort of an AIMD implant in his or her chest. It could be a pacemaker, a cardioverter defibrillator, or even a vagus nerve stimulator or deep brain stimulator.
What happens next is both laborious and time consuming. The ER physician will have various manufacturers' internal programmers transported from the hospital cardiology laboratory down to the ER. ER personnel will then try to interrogate the implantable medical device to see if they can determine what it is. For example, they might first try to use a Medtronic programmer to see if it is a Medtronic pacemaker. Then they might try a St. Jude, a Guidant, an ELA, a Biotronik or one of a number of other programmers that are present. If none of those programmers work, then the ER physician has to consider that it may be a neurostimulator and perhaps go get a Cyberonics or Neuropace programmer.
It would be a great advantage and potentially lifesaving if the ER physician could very quickly identify the type of implant and model number. In certain cases, for example, with a pacemaker patient who is in cardiac distress, with an external programmer they could boost the pacemaker output voltage to properly recapture the heart, obtain a regular sinus rhythm and stabilize blood pressure. All of the lost time running around to find the right programmer, however, generally precludes this. Accordingly, there is a need for a way to rapidly identify the type and model number of an active implantable medical device so that the proper external programmer for it can be rapidly identified and obtained.
It is also important to note that lead wire systems generally remain in the human body much longer than the active implantable medical device itself. For example, in the case of a cardiac pacemaker, the cardiac pacemaker batteries tend to last for 5 to 7 years. It is a very difficult surgical procedure to actually remove leads from the heart once they are implanted. This is because the distal TIP and other areas of the leads tend to become embedded and overgrown (encapsulated) by tissues. It often takes very complex surgical procedures, including lasers or even open heart surgery, to remove such lead wire systems. When a pacemaker is replaced, the pectoral pocket is simply reopened and a new pacemaker is plugged into the existing leads. However, it is also quite common for leads to fail for various reasons. They could fail due to breakdown of electrical insulation or they could migrate to an improper position within the heart. In this case, the physician normally snips the leads off and abandons them and then installs new leads in parallel with the old abandoned leads.
Abandoned leads can be quite a problem during certain medical diagnostic procedures, such as MRI. It has been demonstrated in the literature that such leads can greatly overheat due to the powerful magnetic fields induced during MRI. Accordingly, it is important that there be a way of identifying abandoned leads and the lead type. Also, there is a need to identify such abandoned leads to an Emergency Room physician or other medical practitioner who may contemplate performing a medical diagnostic procedure on the patient such as MRI. This is in addition to the need to also identify the make and model number of the active implantable medical device.
It is also important to note that certain lead systems are evolving to be compatible with a specific type of medical diagnostic procedure. For example, MRI systems vary in static field strength from 0.5 Tesla all the way above 10 Tesla. A very popular MRI system, for example, operates at 3 Tesla and has a pulse RF frequency of 128 MHz. There are specific certain lead systems that are evolving in the marketplace that would be compatible with only this type of MRI system. In other words, it would be dangerous for a patient with a lead wire designed for 3 Tesla to be exposed to a 1.5 Tesla system. Thus, there is also a need to identify such lead systems to Emergency Room and other medical personnel when necessary. For example, a patient that has a lead system that has been specifically designed for use with a 3 Tesla MRI system may have several pacemaker replacements over the years.
It is already well known in the prior art that RFID tag implants can be used for animals, for example, for pet tracking. They are also used in the livestock industry. For example, RFID tags can be placed in or on cattle to identify them and track certain information. An injectable RFID tag for humans has also been developed. However, none of the current RFID tags have been designed to have long term reliability, hermeticity, and biocompatibility within the body fluid environment.
In the prior art, RFID tags have been encapsulated in plastic or placed in a plastic or glass tube with an epoxy infill. However, as will be discussed more fully below, none of these materials provide a truly hermetic seal against body fluids.
With reference now to FIGS. 1 and 2 , prior art RFID tags 12 typically involve a small substrate 14 on which a microelectronic chip 16 is placed along with an embedded or printed antenna 18. These antennas can be Wheeler spirals, rectangles, dipoles, solenoids or other shapes. The read range of such antennas, particularly for low frequency (LF) and high frequency (HF) readers tends to be very short. That is, the RFID reader has to be in very close proximity to the RFID chip. In order to extend the read range, a larger loop style antenna 18 involving multiple turns, as illustrated in FIG. 2 , is typically used. These involve very fine wire, multiple turns of copper, which are then soldered to the RFID chip. Obviously, neither copper nor solder joints are biocompatible or even reliable for human body implants. When exposed to body fluids, copper causes corrosion problems as well the tin and lead that is typically used in solders. These materials, when leached out can even become toxic to the human body.
One approach would be to hermetically seal the RFID chip and its complete loop antenna. However, when one fully contemplates hermetically sealing an RFID chip with a very large multi-turn loop antenna, one realizes that such an approach becomes entirely impractical. The hermetic seal package would simply be too large to be effectively associated with a medical implant.
Accordingly, there is a need for an improved medical identification tag that can store additional information about an implanted device and/or a patient, without unduly increasing the size of the identification tag or jeopardizing the operation of the implanted device or the health of the patient. The present invention meets these needs by providing an RFID tag whose electronic chip is enclosed within an AIMD hermetic housing, and a biocompatible antenna that is disposed outside of the AIMD housing. The RFID tag of the present invention is capable of storing information about the medical device, the physician, and the patient, as described above.
In general, the present invention is directed to a system for identifying implants within a patient, comprising an implantable medical device, a radio frequency identification (RFID) tag having a hermetically sealed chip and biocompatible antenna and being associated with the implantable medical device, the RFID tag containing information relating to the patient and/or the implantable medical device, and an interrogator capable of communicating with the RFID tag.
Such implantable medical devices may include active implantable medical devices (AIMD) such as a cardiac pacemaker, an implantable defibrillator, a congestive heart failure device, a hearing implant, a cochlear implant, a neurostimulator, a drug pump, a ventricular assist device, an insulin pump, a spinal cord stimulator, an implantable sensing system, a deep brain stimulator, an artificial heart, an incontinence device, a vagus nerve stimulator, a bone growth stimulator, a gastric pacemaker, a Bion, or a prosthetic device and component parts thereof, including lead wires or abandoned lead wires.
More particularly, the present invention relates to an implantable radio frequency identification (RFID) tag, comprising: (1) a hermetically sealed biocompatible housing for an active implantable medical device (AIMD); (2) an RFID microelectronics chip disposed within the housing; and (3) a biocompatible antenna extending from the RFID microelectronics chip and exteriorly of the housing. The antenna may be disposed within a non-hermetically sealed portion of the AIMD, such as the AIMD header block.
With the biocompatible antenna disposed within the AIMD header block, at least one lead extends through a hermetic terminal associated with the AIMD housing to connect the antenna to the RFID tip which is disposed within the AIMD housing. The RFID chip may be disposed either adjacent to the hermetic terminal or remotely within the housing relative to the hermetic terminal. Moreover, at least one lead may comprise a unitary extension of the antenna and/or an active lead which extends through the hermetic terminal in non-conductive relation with the AIMD housing, and a ground lead extending through the AIMD housing in conductive relation.
The AIMD housing preferably has a leak rate of no more than 10−7 cubic centimeters per second. Preferably, the housing is taken from the group including biocompatible metals and alloys such as titanium and/or stainless steel, ceramic, glass, porcelain, sapphire and composites thereof, and specialty polymer composites, where the housing is of a non-conductive material, such as ceramic, glass or the like, then a metal coating would typically be used to provide an overall electromagnetic shield. A desiccant may further be disposed within the housing.
The RFID chip may be read-only or readable/writable, and may comprise a portion of a system which includes an interrogator for electromagnetically communicating with the RFID chip. The interrogator may be a read-only or a reader/writer device and, in turn, may be placed in communication with a computer or a computer network.
The RFID chip may include information pertaining to the AIMD and/or to a patient in which the RFID tag is implanted.
The antenna may be wound around a ferrite-based core comprising a high temperature sintered ferrite-based material having a biocompatible dielectric material at least partially coating the ferrite-based material. Such biocompatible dielectric material may comprise parylene, ETFE, PTFE, polyimide, polyurethane, or silicone. Preferably, the ferrite-based core is comprised of a ferrite material that will not exhibit permanent remanence after exposure to MRI fields.
A sensor may be conductively coupled to the RFID microelectronics chip. The sensor may be disposed either exteriorly of the AIMD housing or within the AIMD housing. The sensor may measure and the RFID tag may transmit measured properties in real time.
The RFID tag's biocompatible antenna may comprise at least one biocompatible conductive material taken from the group of: titanium, platinum and platinum/iridium alloys, tantalum, niobium, zirconium, hafnium, nitinol, Co—Cr—Ni alloys such as MP35N, Havar®, Elgiloy®, stainless steel, gold and its various alloys, palladium, pyrolytic carbon, or any other noble metal.
The RFID tag's biocompatible antenna may also comprise a conductive metal compound taken from any of the following: ZrC, ZrN, TiN, NbO, TiC and TaC, or a substrate and a conductive polymer taken from the group of: Polyethylene, oxide with ionic addition such as NaCl, Polyurethane, Silicone, Polyesters, Polycarbonate, polyethylene, Polyvinyl Chloride, Polypropylene, Methylacrylate, or Para-xylylene.
Other features and advantages of the present invention will become apparent from the following more detailed description, taken in conjunction with the accompanying drawings which illustrate, by way of example, the principles of the invention.
The accompanying drawings illustrate the invention. In such drawings:
The present invention is directed to a radio frequency identification (RFID) system for use with active implantable medical devices (AIMDs) and an associated RFID tag. Specifically, the RFID system comprises an RFID tag implanted in a patient's body and associated with an implanted AIMD, and an interrogator in communication with the RFID tag. The novel tag comprises an electronic RFID chip disposed inside the hermetically sealed housing of an AIMD, and an external biocompatible antenna.
An RFID interrogator 20, also known as a hand held scanner or reader, transmits an electromagnetic field pulse 22 which is intercepted by the antenna 18 that is part of the implanted RFID tag 12. The implanted RFID tag 12 is generally passive, which means that it does not have its own self-contained source of energy such as a battery (although it can). The electromagnetic field pulse 22 that comes from the interrogator 20 resonates with the antenna 18 and the RFID chip 16 providing energy for the RFID chip 16 to generate a signal and the antenna 18 to emit a return pulse 24. There is usually an energy storage and resonant capacitor 158 (FIGS. 21-23 ) that is in parallel with the RFID electronic chip 16 and the antenna 14. This capacitor resonates with the antenna and also stores energy sufficient to power the passive RFID chip 16. The return pulse 24 is picked up by an antenna 26 (FIG. 4 ) in the interrogator 20. The return pulse 24 can be digitally modulated to contain information such as the model number of the patient's AIMD, the serial number of the AIMD, the manufacturer of the lead wire system, the name of the patient's physician, and contact information for the physician. In addition, if the patient authorizes, the digital pulses can also contain the patient's name, the patient's medical condition, the patient's address and telephone number, and other pertinent information.
Ideally, the medical device manufacturer would have a special RFID reader associated with their manufacturing line. For example, a cardiac pacemaker manufacturer, at the point of final sterilization and packaging, would use a production line barcode reader-RFID writer to read a barcode associated with the production lot traveler or packaging, and then the production line RFID writer would write this information to the RFID tag that is embedded in or associated with the pacemaker or other medical device. This would go into an area of permanent memory on the RFID tag. There would also be an area of volatile memory that the doctor could optionally use later to enter information about the patient, the patient's medical condition or even information about the implanting physician all at the time of implant. This would typically be done with informed patient consent. Of course, these principles are applicable to any external or internal medical device.
RFID standards are evolving worldwide at various frequencies generally between 125 kHz and 915 MHz. For example, a 915 MHz protocol is generally evolving to be used for retail goods and inventory control. However, due to the high frequency, the 915 MHz protocols are not very useful for human implants. The reason for this is that humans are largely water and 915 MHz fields are greatly affected by the presence of water. The preferred embodiment is another RFID protocol which operates at 13.56 MHz which is ideal for an implantable RFID tag. The 13.56 MHz lower frequency will readily penetrate and communicate with the tag instead of reflecting off of the skin surface or being absorbed. There are other lower frequency RFID systems, for example, in the 50 to 135 kHz range which would also be ideal.
A non-hermetically sealed RFID tag 12 is encapsulated within the molded header block 38 of the AIMD 10. Such molded header connector blocks are common in the industry and are designated by ISO Standards IS-I, DF-1 or IS-4 or the equivalent. The header block 38 of FIG. 8 is formed of a solid encapsulated material such as an epoxy, thermal setting polymer like Techothane, or the like. In general such materials are not considered truly hermetic and will have leak rates varying from 10−3 to 10−5 cubic centimeters per second. Accordingly, if the AIMD 10 of FIG. 8 were implanted for long periods of time, then body fluids would eventually reach the electronic circuits (microchip 16) of the RFID tag 12 due to the bulk permeability of the header block 38 material. Body fluids are comprised primarily of water and dissolved salts including sodium, chlorine, potassium, calcium and the like. These are ionic and if they reach the surfaces of the RFID tag microchip 16 it will readily short it out. Worse still, the RFID tag 12 itself may contain materials that are not biocompatible and may be toxic to body tissues. For example, when the RFID microchip 16 is viewed under high magnification, one can see that there are hundreds, if not thousands of non-biocompatible electronic circuit connections, which can contain tin, cadmium or even lead.
Prior art RFID tags (like the Verichip) that are used for both animal and sometimes for human implant have a serious deficiency in that they are not truly hermetically sealed. These devices often use a cylindrical glass cup which is filled with epoxy or other types of polymer materials such as silicone or the like. A deficiency with such seals is that over long periods of time moisture will slowly penetrate and reach the sensitive electronic circuits. When moisture reaches electronic circuits under low bias voltage conditions, dendrites and tin whiskers can form thereby shorting out or reducing insulation resistancy to electronic components. Accordingly, the RFID chip should be completely hermetically sealed in a container with a minimum helium leak rate of 1×10−7 cubic centimeters per second. As used herein “hermetically sealed” means a leak rate of 10−7 cubic centimeters per second or slower. This is in sharp contrast to prior art polymer fill systems which achieve at most a helium leak rate of around 1×10−5 cubic centimeters per second. In the most preferred embodiment described herein, the electronic chip portion of the RFID tag 12 is hermetically sealed inside the overall housing of the AIMD.
Since the RFID chip 16 is generally constructed of materials that are not long-term biocompatible and body fluid resistant, it is important to prevent body fluids from reaching the RFID chip 16. Even if the RFID chip 16 is embedded deeply within a molded polymer header block 38 as illustrated in FIG. 8 , when such a device is implanted into body tissue for many years (cochlear implants may last forty years or longer), moisture can slowly penetrate due to the bulk permeability of the polymer material of the header block 38. In the art, this is known as the leak rate or hermeticity of a device. Generally speaking, adjunct sealants, polymers and the like are not considered truly hermetic. A helium leak rate of 10−7 cubic centimeters per second or slower is required to assure that moisture will not penetrate to sensitive electronics over long periods of time. In order to achieve such low leak rates, generally glass seals or gold brazed ceramic seals are required. It is well known that brazed ceramic seals are generally superior to fused or compression glass seals.
In order for the RFID interrogator 20 to be able to read a tag 12 embedded within the human body, it must generate a very powerful yet relatively low frequency field. Such interrogators 20 are most effective when held within ten centimeters of the implant.
In FIGS. 9 and 10 , the RFID tag 40 has been embedded in the header block 38 and is connected to a multiple-turn antenna 42. Read range is important in the present application. The read range should not be too excessive (for example, several meters) because of the possibility of creating electromagnetic interference (picking up stray tags and soon). However, a read range of approximately four to six inches would be optimal. Most implantable medical devices, such as cardiac pacemakers and implantable cardioverter defibrillators (ICDs) are implanted under the skin. In these cases, the implant depth would only be about 12 millimeters. However, for a person who is morbidly obese, this distance could increase significantly, especially if the implant was placed subpectorally or in a pocket down beneath the breast. In this case, a read range closer to 100 millimeters would be desirable. One might be tempted to place the RFID tag 40, closer to one side of the header block than the other. The problem with this is one cannot rely on the implanting physician to always implant the device with one side up. Furthermore, there is the syndrome that has been well documented in the art as Twiddler's Syndrome. Twiddler's Syndrome involves the pacemaker (or other AIMD) patient, either consciously or subconsciously, manipulating their implanted device. There have been documented cases that over a period of months or even years, the pacemakers have been twisted several times in the pocket to the point where the leads are broken or pulled out. Accordingly, the RFID circular antenna 42 would be implanted parallel to the length and height (L, H) plane of the AIMD 10 and midway or halfway in width W. In this case, it would not really matter which side was up when the physician implanted the device as the distance to the RFID antenna would remain constant. This also solves the issue with Twiddler's Syndrome in that it would not matter, again, which way the pacemaker was oriented.
A hermetically sealed package 44 contains the RFID chip therein. There are biocompatible electrical connection terminal pins 46 and 48 between the antenna 42 and the hermetically sealed package 44. These would typically be laser welds or brazes of all biocompatible materials or biocompatible solders or conductive polymers. In other words, no non-biocompatible solder joint or other such non-biocompatible connection would be exposed to body fluids. An alternative would be to use a biocompatible thermally conductive adhesive. Biocompatible metals and alloys that can be used for the electronic network components or component network or the connection materials include all of the metals and alloys of titanium, platinum and platinum iridium alloys, tantalum, niobium, zirconium, Hafnium, nitinol, Co—Cr—Ni alloys such as MP35N, Havar®, Elgiloy®, stainless steel and gold. There are also a number of conductive metal compounds that can be used including ZrC, ZrN, TiN, NbO, TiC, TaC, and Indium Oxide/Indium Tin Oxide (Transparent Conductive Oxides). Commercially available biocompatible electrically conductive epoxies are manufactured by Epoxy Technology, Inc, in Billerica, Mass. For example Epoxy technology EPOTEK H81 features a biocompatible epoxy which is gold filled (www.epotek.com). The conductive connection materials are typically thermal-setting, brazing, welding or special biocompatible soldering materials. So as to be non-migratable, these materials are selected from the group consisting of: gold, gold alloy, platinum, gold-filled-thermal-setting conductive material, platinum-filled-thermal-setting conductive material, gold-bearing glass frit, TiCuSil, CuSil, and gold-based braze.
Referring once again to FIG. 9 , one can see that the RFID tag 40 satisfies all the needs for long term human implant. The header block 38 is not considered by biomedical scientists to be a long term or reliable hermetic seal. Over time, through bulk permeability, body fluids and water will penetrate readily through that entire structure. This is why the AIMD housing 32 is hermetically sealed to make sure that body fluids can never penetrate to the sensitive electronic circuits of the AIMD 10, as further explained by U.S. Patent Publication No. US 2006-0212096 A1, the contents of which are incorporated herein. The same principle applies in the present invention in that the sensitive microelectronic RFID chip 50 (FIG. 11 ) and its associated electrical connections must also be protected over the long term from body fluid intrusion.
Referring once again to FIG. 11 , electrical connections (welds) 64 and 66 can be eliminated by using a suitable biocompatible antenna wire 42, such as platinum or platinum-iridium. One could take a setter, which would be typically of zirconia into which ceramic powder could be placed, which would roughly have the shape of housing 44. The antenna lead wire 42 could be of pure platinum or platinum-iridium, which is a high temperature material. The antenna could be laid through the powder in the same position as the pins 46 and 48 are presently shown. This entire structure could be co-fired (sintered) such that the platinum antenna lead forms its own hermetic seal into the hermetically sealed package 44. All that would be needed then is to attach the lid 54.
The entire non-toxic biocompatible RFID tag 40 of FIGS. 9-11 could be molded or embedded in a thin medical grade plastic disk. This could be a thin silicone disk, a thin epoxy disk or a thin polyimide disk. With a suitable adhesive, this would allow it to be attached to, for example, the housing or header block of the AIMD 10. It could also be implanted through a small incision in various other locations in the body, or it could even be injected with a large needle syringe (if properly configured).
The novel biocompatible antenna 42 and hermetically sealed RFID chip 50 of the present invention does not need to be associated with a pacemaker or other type of AIMD 10. The RFID chip 50 and associated biocompatible and non-toxic antenna 42 could be implanted in the abdominal area, into the arm or even the buttocks. Since these areas are all subject to some movement, flexibility of the antenna 42 is important. The antenna 42 and hermetically sealed RFID chip 50 could be over-molded with silicone or other thin biocompatible but flexible material. Flexibility of the entire structure is important because no matter where you implant this in the human body, it is subject to some motion. The arm would be an extreme example where motion could occur. The novel RFID tag 40 need not be for identification of a medical implant only. It could also be used generally for human identification. This would include applications where lights in a building could be turned on and off automatically as the implanted RFID tag 40 is sensed, doors could be opened and the like. The RFID chip 50 could also contain encrypted information such as Social Security Number, credit card information and the like. This would facilitate automated checkout from retail stores and the like.
Referring to FIGS. 14-16 , it is important in implant applications for humans that the ferrite material of the core 146 be carefully chosen. This has to do with the fact that the human may at some point in his or her life, undergo a medical diagnostic procedure known as magnetic resonance imaging (MRI). MRI equipment embodies three main fields, one of which is known as the Bo main static field. The main static field of an MRI scanner is more than a hundred thousand times more powerful that the earth's magnetic field. This tends to align magnetic domains of a ferromagnetic material. Since it is not important that the RFID tag be read during an actual MRI scan, then it is not particularly important that the ferrite material be saturated during an MRI scan. In the saturated condition, the antenna 142 would become highly inefficient. What this means is it would not be possible to interrogate the RFID tag 140 while the patient was in the presence of a main static field of an MRI scanner. However, this would require that the patient be inside the bore of the MRI scanner at which time there is really no need that the RFID tag 140 be operable. What is important in the present invention is that the magnetic ferrite material that is used be carefully selected such that it not be permanently damaged by exposure to the main static field. Certain ferrite materials, when exposed to a powerful magnetic field, will have their magnetic dipoles aligned. After removal of the powerful magnetic field, those dipoles will remain aligned in a condition known as magnetic remanence. This is a form of magnetic memory which would be very detrimental. If the ferrite material remained in a remanent condition, this would mean that the RFID tag 140 would be ruined and would no longer be capable of being read after the MRI scan. Accordingly, it is a feature of the present invention that the selection of the ferrite be done generally using soft ferrites or other ferrite material that will not exhibit permanent remanence after exposure to MRI.
The structure illustrated in FIG. 21 has a number of very important advantages. First, the antenna 42 is disposed on the outside of the hermetically shielded and hermetic housing 32 of the AIMD. This means that the antenna 42 will not be shielded by the AIMD housing 32 so that it can more effectively capture energy and communicate with an external reader. By disposing the microelectronic RFID chip 50 and its associated capacitor 158 on the inside of the AIMD housing 32, the need to hermetically seal it or construct the RFID chip 50 from biocompatible materials is eliminated. The RFID chip 50 is disposed within the overall hermetically sealed housing 32 of the AIMD and is therefore never exposed to body fluids. Accordingly, the need for a separate hermetically sealed package 44 as shown in FIGS. 10 and 11 is no longer needed. This approach offers a number of very important advantages, including ease of construction and cost reductions. The capacitor 158 may also be disposed on the outside or body fluid side of the hermetic terminal 150. An advantage of this placement is that a higher Q resonance could be obtained between the capacitor 158′ and the antenna structure 42. If the capacitor 158′ was placed on the outside of the AIMD hermetic housing 32, it would be directly exposed to body fluids. Methods of construction for capacitors directly exposed to body fluid are disclosed in U.S. Pat. No. 7,535,693, the contents of which are incorporated herein.
From the foregoing it will be appreciated that a novel aspect of the present invention resides in providing a relatively large non-hermetically sealed biocompatible multi-turn RFID loop antenna 42 which is electrically connected to a miniature RFID chip 50 that is enclosed within its own hermetically sealed miniature package 44. The hermetic package 44 can be very small and the loop antenna 42 can be relatively large wherein the entire RFID tag 40 is both highly reliable, resistant to body fluids and completely biocompatible. In a particularly preferred embodiment, the hermetic seal for the RFID chip 50 is the overall shielded metallic housing 32 of the AIMD 10. The external antenna structure 42 is adaptable for being molded into the header block 38, for example, for a cardiac pacemaker 10 or, alternatively it can be implanted in other locations in the human body.
The hermetically sealed RFID chip with fixation device can be used to attach to one or more abandoned leads in the pectoral pocket. This is very useful whether or not the patient receives a new pacemaker or AIMD, implant or not. That is, if a patient that has reverted to normal sinus rhythm and no longer needs a pacemaker and has abandoned leads, the radiology department can quickly tell through the RFID scan whether or not abandoned lead wires are present. As mentioned, this is extremely important to prevent inadvertent MRI on such a patient. In the past, it has been shown that abandoned leads can heat up so much that ablation of cardiac tissue and even perforation of cardiac walls can occur. It is, therefore, a feature of the present invention that both the lead wire system and the AIMD can be separately identified.
It will also be appreciated that the present invention provides an improved implantable radio frequency identification (RFID) tag that may be used advantageously with an active implantable medical device (AIMD) wherein the RFID microelectronics chip is disposed within the AIMD housing and the biocompatible antenna extends from the RFID microelectronics chip exteriorly of the housing, for example, into the non-hermetically sealed header block for the AIMD. At least one of the leads connecting the antenna to the RFID chip will normally extend through the hermetic terminal associated with the AIMD housing. The RFID chip may be disposed adjacent to the hermetic terminal, or be remotely disposed within the housing relative to the hermetic terminal. The present invention advantageously utilizes the hermetically sealed housing for the AIMD as a hermetically sealed biocompatible container to prevent the RFID microelectronics chip from coming into contact with body fluids or tissue.
Although several embodiments have been described in detail for purposes of illustration, various modifications may be made without departing from the scope and spirit of the invention. Accordingly, the invention is not to be limited, except as by the appended claims.
Claims (41)
1. An implantable medical device, comprising:
a) a hermetically sealed biocompatible housing;
b) an RFID microelectronics chip disposed within the housing;
c) an antenna wire having a first end portion electrically connected to a first end of the RFID chip inside the housing and extending along a length to a second end portion electronically connected to a second end of the RFID chip inside the housing with at least an intermediate portion of the length of the antenna wire between the first and second end portions residing outside the housing; and
d) a sealing material that hermetically seals against an outer surface of the first and second end portions of the antenna wire and against respective perimeter openings in the housing through which the antenna wire extends so that the housing has a helium leak rate of no more than 10−7 cubic centimeters per second, and
e) wherein the intermediate portion of the antenna wire external to the housing serves as an antenna for the RFID microelectronics chip.
2. The implantable medical device of claim 1 wherein the housing has a helium leak rate of no more than 10−7 cubic centimeters per second.
3. The implantable medical device of claim 2 1 wherein the housing is of a material selected from the group consisting of biocompatible metals and alloys, ceramic, glass, porcelain, sapphire and composites thereof, and specialty polymer composites.
4. The implantable medical device of claim 3 including a desiccant within the housing.
5. The implantable medical device of claim 3 including an encapsulant within the housing surrounding at least a portion of the RFID chip.
6. The implantable medical device of claim 5 wherein the encapsulant is comprised of a thermal-setting polymer or a silicone material.
7. The implantable medical device of claim 1 wherein the housing includes a cap hermetically sealed to an open end of a housing container.
8. The implantable medical device of claim 1 wherein the RFID chip is read-only or readable/writable.
9. The implantable medical device of claim 1 wherein the RFID chip is communicable with an external device at a radio frequency of from 125 kHz to 915 MHz.
10. The implantable medical device of claim 9 wherein the RFID chip is communicable with an external device at a radio frequency of approximately 13.56 MHz.
11. The implantable medical device of claim 1 wherein the RFID chip includes information relating to a patient in which the medical device is implanted.
12. The implantable medical device of claim 1 wherein the container, RFID chip, and at least the first and second end portions of the antenna wire are embedded within a non-conductive biocompatible material.
13. The implantable medical device of claim 12 wherein the biocompatible material comprises a disc of a material selected from the group consisting of silicone, epoxy, and a medical grade plastic.
14. The implantable medical device of claim 1 wherein the intermediate portion, of the antenna wire is wound around a ferrite-based core.
15. The implantable medical device of claim 14 wherein the ferrite-based core comprises a high temperature sintered ferrite-based material.
16. The implantable medical device of claim 15 including a biocompatible dielectric material at least partially coating the ferrite-based material.
17. The implantable medical device of claim 16 wherein the biocompatible dielectric material is selected from the group consisting of parylene, ETFE, PTFE, polyimide, polyurethane, and silicone.
18. The implantable medical device of claim 14 wherein the ferrite-based core is comprised of a ferrite material that will not exhibit permanent remanence after exposure to MRI fields.
19. The implantable medical device of claim 1 including a sensor conductively coupled to the RFID microelectronics chip.
20. The implantable medical device of claim 19 wherein the sensor is disposed exterior of the hermetically sealed housing.
21. The implantable medical device of claim 19 wherein the sensor is disposed within the hermetically sealed housing.
22. The implantable medical device of claim 19 wherein the RFID chip is capable of transmitting data measured by the sensor in real time.
23. The implantable medical device of claim 2 1 wherein the measurable data comprises the activity of a human body.
24. The implantable medical device of claim 1 wherein the intermediate portion of the antenna wire is a multi-turn antenna.
25. The implantable medical device of claim 1 wherein the first and second end portions of the antenna wire are first and second feedthrough wires that are hermetically sealed in the respective openings in the housing and opposed end of the intermediate portion of the antenna wire are electrically connected to the first and second feedthrough wires.
26. The implantable medical device of claim 1 wherein the hermetically sealed housing is the housing for the active implantable medical device.
27. The implantable medical device of claim 1 wherein the hermetically sealed housing s of titanium or stainless steel.
28. An implantable medical device, comprising:
a) a hermetically sealed biocompatible housing;
b) an RFID microelectronics chip disposed within the housing;
c) an antenna wire having a first end portion electrically connected to a first end of the RFID chip inside the housing and extending along a length to a second end portion electronically connected to a second end of the RFID chip inside the housing with at least an intermediate portion of the length of the antenna wire between the first and second end portions residing outside the housing; and
d) wherein a wall of the housing hermetically seals against an outer surface of the first and second end portions of the antenna wire so that the housing has a helium leak rate of no more than 10−7 cubic centimeters per second, and
e) wherein the intermediate portion, of the antenna wire external to the housing serves as an antenna for the RFID microelectronics chip.
29. The implantable medical device of claim 28 wherein the housing has a helium leak rate of no more than 10−7 cubic as centimeters per second.
30. An implantable medical device, comprising:
a) a hermetically sealed biocompatible housing;
b) an RFID microelectronics chip disposed within the housing;
c) a first feedthrough, wire comprising a first proximal end electrically connected to the RFID chip and a first distal end residing outside the hermetically sealed housing, wherein a first sealing material hermetically seals against an outer surface of the first feedthrough wire and against a first perimeter opening in the housing through which the first feedthrough wire extends;
d) a second feedthrough wire comprising a second proximal end electrically connected to the RFID chip and a second distal end residing outside the hermetically sealed housing, wherein a second sealing material hermetically seals against an outer surface of the second feedthrough wire and against a second perimeter opening in the housing through which the second feedthrough wire extends so that the housing has a helium leak rate of no more than 10−7 cubic centimeters per second; and
e) an antenna wire having a first end electrically connected to the first distal end of the first feedthrough wire outside the housing and extending along a length to a second end electronically connected to the second distal end of the second feedthrough wire outside the housing.
31. The implantable medical device of claim 30 wherein the housing has a helium leak rate of no more than 10−7 cubic centimeters per second.
32. A medical system comprising:
a) an implantable medical device;
b) hermetically sealed biocompatible housing that is either contained inside the implantable medical device or contacted, to an outer surface thereof;
c) an RFID microelectronics chip disposed within the housing;
d) an antenna wire having a first end portion electrically connected to a first end of the RFID chip inside the housing and extending along a length to a second end portion electronically connected to a second end of the RFID chip inside the housing with at least an intermediate portion of the length of the antenna wire between the first and second end portions residing outside the housing; and
e) a sealing material that hermetically seals against an outer surface of the first and second end portions of the antenna wire and against respective perimeter openings in the housing through which the antenna wire extends so that the housing has a helium leak rate of no more than 10−7 cubic centimeters per second, and
g) wherein the intermediate portion of the antenna wire external to the housing serves as an antenna for the RFID microelectronics chip.
33. The system of claim 32 wherein the housing has a helium leak rate of no more than 10−7 cubic centimeters per second.
34. The system of claim 32 including an interrogator for electromagnetically communicating with the RFID chip.
35. The system of claim 33 32 wherein the interrogator is a read only or a reader/writer device.
36. The system of claim 33 32 wherein the interrogator is capable of communicating with a computer or a computer network.
37. The system of claim 32 wherein the hermetically sealed housing for the RFID chip is disposed within a non-hermetically sealed portion of the medical device.
38. The system of claim 32 wherein the hermetically sealed housing for the RFID chip is disposed within a header block of the medical device.
39. The system of claim 32 wherein the antenna wire and the RFID chip are disposed within the medical device parallel to a length and height plane of the medical device, and midway through the width thereof.
40. The system old aim 32 wherein the RFID chip includes information pertaining to the medical device.
41. The system of claim 32 wherein the implantable medical device is selected from the group consisting of a cardiac pacemaker, an implantable defibrillator, a congestive heart failure device, a hearing implant, a cochlear implant, a neurostimulator, a drug pump, a ventricular assist device, an insulin pump, a spinal cord stimulator, an implantable sensing system, a deep brain stimulator, an artificial heart, an incontinence device, a vagus nerve stimulator, a bone growth stimulator, a gastric pacemaker, a Bion or a prosthetic device, and component parts thereof, including lead wires and abandoned lead wire.
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US14/087,734 USRE45030E1 (en) | 2009-09-24 | 2013-11-22 | Hermetically sealed RFID microelectronic chip connected to a biocompatible RFID antenna |
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Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20140155951A1 (en) * | 2012-12-04 | 2014-06-05 | Biotronik Se & Co. Kg | Implantable Electrostimulation Assembly and Adapter and Electrode Lead of the Same |
US10896300B2 (en) * | 2018-05-31 | 2021-01-19 | STMicroelectronics Austria GmbH | Wireless communication device and method |
US11583682B2 (en) * | 2020-12-07 | 2023-02-21 | Onward Medical N.V. | Antenna for an implantable pulse generator |
US11672983B2 (en) | 2018-11-13 | 2023-06-13 | Onward Medical N.V. | Sensor in clothing of limbs or footwear |
US11969302B2 (en) * | 2018-07-06 | 2024-04-30 | Biotronik Se & Co. Kg | Header having radiographic marker |
Families Citing this family (170)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8244370B2 (en) | 2001-04-13 | 2012-08-14 | Greatbatch Ltd. | Band stop filter employing a capacitor and an inductor tank circuit to enhance MRI compatibility of active medical devices |
US8219208B2 (en) | 2001-04-13 | 2012-07-10 | Greatbatch Ltd. | Frequency selective passive component networks for active implantable medical devices utilizing an energy dissipating surface |
US20070088416A1 (en) * | 2001-04-13 | 2007-04-19 | Surgi-Vision, Inc. | Mri compatible medical leads |
US9060770B2 (en) | 2003-05-20 | 2015-06-23 | Ethicon Endo-Surgery, Inc. | Robotically-driven surgical instrument with E-beam driver |
US20070084897A1 (en) | 2003-05-20 | 2007-04-19 | Shelton Frederick E Iv | Articulating surgical stapling instrument incorporating a two-piece e-beam firing mechanism |
US11896225B2 (en) | 2004-07-28 | 2024-02-13 | Cilag Gmbh International | Staple cartridge comprising a pan |
WO2006119492A2 (en) * | 2005-05-04 | 2006-11-09 | Surgi-Vision, Inc. | Improved electrical lead for an electronic device such as an implantable device |
US7669746B2 (en) | 2005-08-31 | 2010-03-02 | Ethicon Endo-Surgery, Inc. | Staple cartridges for forming staples having differing formed staple heights |
US11246590B2 (en) | 2005-08-31 | 2022-02-15 | Cilag Gmbh International | Staple cartridge including staple drivers having different unfired heights |
US10159482B2 (en) | 2005-08-31 | 2018-12-25 | Ethicon Llc | Fastener cartridge assembly comprising a fixed anvil and different staple heights |
WO2007047966A2 (en) | 2005-10-21 | 2007-04-26 | Surgi-Vision, Inc. | Mri-safe high impedance lead systems |
US8248232B2 (en) * | 2006-01-25 | 2012-08-21 | Greatbatch Ltd. | Hermetically sealed RFID microelectronic chip connected to a biocompatible RFID antenna |
US8186555B2 (en) | 2006-01-31 | 2012-05-29 | Ethicon Endo-Surgery, Inc. | Motor-driven surgical cutting and fastening instrument with mechanical closure system |
US7845537B2 (en) | 2006-01-31 | 2010-12-07 | Ethicon Endo-Surgery, Inc. | Surgical instrument having recording capabilities |
US8708213B2 (en) | 2006-01-31 | 2014-04-29 | Ethicon Endo-Surgery, Inc. | Surgical instrument having a feedback system |
US11793518B2 (en) | 2006-01-31 | 2023-10-24 | Cilag Gmbh International | Powered surgical instruments with firing system lockout arrangements |
US8684253B2 (en) | 2007-01-10 | 2014-04-01 | Ethicon Endo-Surgery, Inc. | Surgical instrument with wireless communication between a control unit of a robotic system and remote sensor |
US8701958B2 (en) | 2007-01-11 | 2014-04-22 | Ethicon Endo-Surgery, Inc. | Curved end effector for a surgical stapling device |
US8600478B2 (en) | 2007-02-19 | 2013-12-03 | Medtronic Navigation, Inc. | Automatic identification of instruments used with a surgical navigation system |
WO2008115426A1 (en) | 2007-03-19 | 2008-09-25 | Boston Scientific Neuromodulation Corporation | Mri and rf compatible leads and related methods of operating and fabricating leads |
CA2679498C (en) | 2007-03-19 | 2016-08-02 | Boston Scientific Neuromodulation Corporation | Methods and apparatus for fabricating leads with conductors and related flexible lead configurations |
US11564682B2 (en) | 2007-06-04 | 2023-01-31 | Cilag Gmbh International | Surgical stapler device |
US8931682B2 (en) | 2007-06-04 | 2015-01-13 | Ethicon Endo-Surgery, Inc. | Robotically-controlled shaft based rotary drive systems for surgical instruments |
US11849941B2 (en) | 2007-06-29 | 2023-12-26 | Cilag Gmbh International | Staple cartridge having staple cavities extending at a transverse angle relative to a longitudinal cartridge axis |
JP5410110B2 (en) | 2008-02-14 | 2014-02-05 | エシコン・エンド−サージェリィ・インコーポレイテッド | Surgical cutting / fixing instrument with RF electrode |
EP2265323B1 (en) * | 2008-03-17 | 2016-09-07 | Surgivision, Inc. | Low profile medical devices with internal drive shafts that cooperate with releasably engageable drive tools |
US9005230B2 (en) | 2008-09-23 | 2015-04-14 | Ethicon Endo-Surgery, Inc. | Motorized surgical instrument |
US8210411B2 (en) | 2008-09-23 | 2012-07-03 | Ethicon Endo-Surgery, Inc. | Motor-driven surgical cutting instrument |
US9386983B2 (en) | 2008-09-23 | 2016-07-12 | Ethicon Endo-Surgery, Llc | Robotically-controlled motorized surgical instrument |
US8608045B2 (en) | 2008-10-10 | 2013-12-17 | Ethicon Endo-Sugery, Inc. | Powered surgical cutting and stapling apparatus with manually retractable firing system |
AU2009302900B2 (en) * | 2008-10-10 | 2016-03-03 | Implantica Patent Ltd. | Charger for implant |
US8551023B2 (en) | 2009-03-31 | 2013-10-08 | Depuy (Ireland) | Device and method for determining force of a knee joint |
US8721568B2 (en) | 2009-03-31 | 2014-05-13 | Depuy (Ireland) | Method for performing an orthopaedic surgical procedure |
US9566061B2 (en) | 2010-09-30 | 2017-02-14 | Ethicon Endo-Surgery, Llc | Fastener cartridge comprising a releasably attached tissue thickness compensator |
US9386988B2 (en) | 2010-09-30 | 2016-07-12 | Ethicon End-Surgery, LLC | Retainer assembly including a tissue thickness compensator |
US9629814B2 (en) | 2010-09-30 | 2017-04-25 | Ethicon Endo-Surgery, Llc | Tissue thickness compensator configured to redistribute compressive forces |
US11849952B2 (en) | 2010-09-30 | 2023-12-26 | Cilag Gmbh International | Staple cartridge comprising staples positioned within a compressible portion thereof |
US10945731B2 (en) | 2010-09-30 | 2021-03-16 | Ethicon Llc | Tissue thickness compensator comprising controlled release and expansion |
US11812965B2 (en) | 2010-09-30 | 2023-11-14 | Cilag Gmbh International | Layer of material for a surgical end effector |
US9317729B2 (en) | 2011-02-09 | 2016-04-19 | West Affum Holdings Corp. | RFID-based sensing of changed condition |
US9237858B2 (en) | 2011-02-09 | 2016-01-19 | West Affum Holdings Corp. | Detecting loss of full skin contact in patient electrodes |
US9265958B2 (en) | 2011-04-29 | 2016-02-23 | Cyberonics, Inc. | Implantable medical device antenna |
US9259582B2 (en) | 2011-04-29 | 2016-02-16 | Cyberonics, Inc. | Slot antenna for an implantable device |
AU2012250197B2 (en) | 2011-04-29 | 2017-08-10 | Ethicon Endo-Surgery, Inc. | Staple cartridge comprising staples positioned within a compressible portion thereof |
US9240630B2 (en) | 2011-04-29 | 2016-01-19 | Cyberonics, Inc. | Antenna shield for an implantable medical device |
US9089712B2 (en) | 2011-04-29 | 2015-07-28 | Cyberonics, Inc. | Implantable medical device without antenna feedthrough |
US8945209B2 (en) | 2011-05-20 | 2015-02-03 | Edwards Lifesciences Corporation | Encapsulated heart valve |
RU2639857C2 (en) | 2012-03-28 | 2017-12-22 | Этикон Эндо-Серджери, Инк. | Tissue thickness compensator containing capsule for medium with low pressure |
MX358135B (en) | 2012-03-28 | 2018-08-06 | Ethicon Endo Surgery Inc | Tissue thickness compensator comprising a plurality of layers. |
US9381011B2 (en) | 2012-03-29 | 2016-07-05 | Depuy (Ireland) | Orthopedic surgical instrument for knee surgery |
US10098761B2 (en) | 2012-03-31 | 2018-10-16 | DePuy Synthes Products, Inc. | System and method for validating an orthopaedic surgical plan |
US10206792B2 (en) | 2012-03-31 | 2019-02-19 | Depuy Ireland Unlimited Company | Orthopaedic surgical system for determining joint forces of a patients knee joint |
US10070973B2 (en) | 2012-03-31 | 2018-09-11 | Depuy Ireland Unlimited Company | Orthopaedic sensor module and system for determining joint forces of a patient's knee joint |
US8690068B2 (en) | 2012-05-21 | 2014-04-08 | Warsaw Orthopedic, Inc. | Miniaturized UHF RFID tag for implantable medical device |
US9101358B2 (en) | 2012-06-15 | 2015-08-11 | Ethicon Endo-Surgery, Inc. | Articulatable surgical instrument comprising a firing drive |
US9289256B2 (en) | 2012-06-28 | 2016-03-22 | Ethicon Endo-Surgery, Llc | Surgical end effectors having angled tissue-contacting surfaces |
US20140001231A1 (en) | 2012-06-28 | 2014-01-02 | Ethicon Endo-Surgery, Inc. | Firing system lockout arrangements for surgical instruments |
US8960546B2 (en) | 2012-10-03 | 2015-02-24 | National Oilwell Varco, L.P. | Extended range EMF antenna |
WO2014076620A2 (en) | 2012-11-14 | 2014-05-22 | Vectorious Medical Technologies Ltd. | Drift compensation for implanted capacitance-based pressure transducer |
US9355242B2 (en) * | 2012-12-17 | 2016-05-31 | Intel Corporation | Method and apparatus for managing and accessing personal data |
WO2014099808A1 (en) * | 2012-12-21 | 2014-06-26 | Cardiac Pacemakers, Inc. | Pre-loaded vibration isolator for implantable device |
US8769986B1 (en) | 2013-01-23 | 2014-07-08 | Jason DiPietro | Tesla energy jewelry |
RU2672520C2 (en) | 2013-03-01 | 2018-11-15 | Этикон Эндо-Серджери, Инк. | Hingedly turnable surgical instruments with conducting ways for signal transfer |
US8909656B2 (en) * | 2013-03-15 | 2014-12-09 | Palantir Technologies Inc. | Filter chains with associated multipath views for exploring large data sets |
US9270011B2 (en) | 2013-03-15 | 2016-02-23 | Cyberonics, Inc. | Antenna coupled to a cover closing an opening in an implantable medical device |
US10205488B2 (en) | 2013-04-18 | 2019-02-12 | Vectorious Medical Technologies Ltd. | Low-power high-accuracy clock harvesting in inductive coupling systems |
WO2014170771A1 (en) | 2013-04-18 | 2014-10-23 | Vectorious Medical Technologies Ltd. | Remotely powered sensory implant |
EP2800021B1 (en) | 2013-04-30 | 2019-09-04 | General Electric Company | Method of imaging an implant placed into a human body, adapted implant, and adapted imaging system |
US9636112B2 (en) * | 2013-08-16 | 2017-05-02 | Covidien Lp | Chip assembly for reusable surgical instruments |
US9775609B2 (en) | 2013-08-23 | 2017-10-03 | Ethicon Llc | Tamper proof circuit for surgical instrument battery pack |
US9724527B2 (en) | 2013-09-27 | 2017-08-08 | Cardiac Pacemakers, Inc. | Color coded header bore identification using multiple images and lens arrangement |
US9387331B2 (en) | 2013-10-08 | 2016-07-12 | Medtronic, Inc. | Implantable medical devices having hollow cap cofire ceramic structures and methods of fabricating the same |
US9502754B2 (en) | 2014-01-24 | 2016-11-22 | Medtronic, Inc. | Implantable medical devices having cofire ceramic modules and methods of fabricating the same |
US9514338B1 (en) * | 2014-04-15 | 2016-12-06 | Anne Bromberg | Implantable identification apparatus and related methods of use |
JP6532889B2 (en) | 2014-04-16 | 2019-06-19 | エシコン エルエルシーEthicon LLC | Fastener cartridge assembly and staple holder cover arrangement |
US20150297223A1 (en) | 2014-04-16 | 2015-10-22 | Ethicon Endo-Surgery, Inc. | Fastener cartridges including extensions having different configurations |
CN106456176B (en) | 2014-04-16 | 2019-06-28 | 伊西康内外科有限责任公司 | Fastener cartridge including the extension with various configuration |
US10452875B2 (en) | 2014-05-22 | 2019-10-22 | Avery Dennison Retail Information Services, Llc | Using RFID devices integrated or included in the packaging of medical devices to facilitate a secure and authorized pairing with a host system |
BR112017004361B1 (en) | 2014-09-05 | 2023-04-11 | Ethicon Llc | ELECTRONIC SYSTEM FOR A SURGICAL INSTRUMENT |
US9924944B2 (en) | 2014-10-16 | 2018-03-27 | Ethicon Llc | Staple cartridge comprising an adjunct material |
US10517594B2 (en) | 2014-10-29 | 2019-12-31 | Ethicon Llc | Cartridge assemblies for surgical staplers |
US9894884B2 (en) * | 2014-11-05 | 2018-02-20 | Allflex Usa, Inc. | Companion animal health monitoring system |
US10085748B2 (en) | 2014-12-18 | 2018-10-02 | Ethicon Llc | Locking arrangements for detachable shaft assemblies with articulatable surgical end effectors |
US11154301B2 (en) | 2015-02-27 | 2021-10-26 | Cilag Gmbh International | Modular stapling assembly |
US10441279B2 (en) | 2015-03-06 | 2019-10-15 | Ethicon Llc | Multiple level thresholds to modify operation of powered surgical instruments |
US10433844B2 (en) | 2015-03-31 | 2019-10-08 | Ethicon Llc | Surgical instrument with selectively disengageable threaded drive systems |
US9965658B2 (en) | 2015-06-16 | 2018-05-08 | Motorola Mobility Llc | Person-centric activation of radio frequency identification (RFID) tag |
US10080653B2 (en) | 2015-09-10 | 2018-09-25 | Edwards Lifesciences Corporation | Limited expansion heart valve |
US10105139B2 (en) | 2015-09-23 | 2018-10-23 | Ethicon Llc | Surgical stapler having downstream current-based motor control |
US10271849B2 (en) | 2015-09-30 | 2019-04-30 | Ethicon Llc | Woven constructs with interlocked standing fibers |
US11890015B2 (en) | 2015-09-30 | 2024-02-06 | Cilag Gmbh International | Compressible adjunct with crossing spacer fibers |
US11206988B2 (en) | 2015-12-30 | 2021-12-28 | Vectorious Medical Technologies Ltd. | Power-efficient pressure-sensor implant |
US10292704B2 (en) | 2015-12-30 | 2019-05-21 | Ethicon Llc | Mechanisms for compensating for battery pack failure in powered surgical instruments |
US11213293B2 (en) | 2016-02-09 | 2022-01-04 | Cilag Gmbh International | Articulatable surgical instruments with single articulation link arrangements |
US10448948B2 (en) | 2016-02-12 | 2019-10-22 | Ethicon Llc | Mechanisms for compensating for drivetrain failure in powered surgical instruments |
US10667904B2 (en) | 2016-03-08 | 2020-06-02 | Edwards Lifesciences Corporation | Valve implant with integrated sensor and transmitter |
US10357247B2 (en) | 2016-04-15 | 2019-07-23 | Ethicon Llc | Surgical instrument with multiple program responses during a firing motion |
US20170296173A1 (en) | 2016-04-18 | 2017-10-19 | Ethicon Endo-Surgery, Llc | Method for operating a surgical instrument |
EP3493732A4 (en) | 2016-08-03 | 2020-04-29 | Geissler Companies, LLC | Passive sensors and related structures for implantable biomedical devices |
JP7010956B2 (en) | 2016-12-21 | 2022-01-26 | エシコン エルエルシー | How to staple tissue |
US11090048B2 (en) | 2016-12-21 | 2021-08-17 | Cilag Gmbh International | Method for resetting a fuse of a surgical instrument shaft |
US20180168625A1 (en) | 2016-12-21 | 2018-06-21 | Ethicon Endo-Surgery, Llc | Surgical stapling instruments with smart staple cartridges |
US10463485B2 (en) | 2017-04-06 | 2019-11-05 | Edwards Lifesciences Corporation | Prosthetic valve holders with automatic deploying mechanisms |
CN110662511B (en) | 2017-04-28 | 2022-03-29 | 爱德华兹生命科学公司 | Prosthetic heart valve with collapsible retainer |
US10307170B2 (en) | 2017-06-20 | 2019-06-04 | Ethicon Llc | Method for closed loop control of motor velocity of a surgical stapling and cutting instrument |
US10779820B2 (en) | 2017-06-20 | 2020-09-22 | Ethicon Llc | Systems and methods for controlling motor speed according to user input for a surgical instrument |
EP3641700A4 (en) | 2017-06-21 | 2020-08-05 | Edwards Lifesciences Corporation | Dual-wireform limited expansion heart valves |
USD906355S1 (en) | 2017-06-28 | 2020-12-29 | Ethicon Llc | Display screen or portion thereof with a graphical user interface for a surgical instrument |
US11678880B2 (en) | 2017-06-28 | 2023-06-20 | Cilag Gmbh International | Surgical instrument comprising a shaft including a housing arrangement |
US10932772B2 (en) | 2017-06-29 | 2021-03-02 | Ethicon Llc | Methods for closed loop velocity control for robotic surgical instrument |
US11944300B2 (en) | 2017-08-03 | 2024-04-02 | Cilag Gmbh International | Method for operating a surgical system bailout |
US10842490B2 (en) | 2017-10-31 | 2020-11-24 | Ethicon Llc | Cartridge body design with force reduction based on firing completion |
US10779826B2 (en) | 2017-12-15 | 2020-09-22 | Ethicon Llc | Methods of operating surgical end effectors |
US11337691B2 (en) | 2017-12-21 | 2022-05-24 | Cilag Gmbh International | Surgical instrument configured to determine firing path |
US11040210B2 (en) * | 2018-04-02 | 2021-06-22 | Pacesetter, Inc. | All metal enclosed implantable medical device with external BLE antenna for RF telemetry |
US11207065B2 (en) | 2018-08-20 | 2021-12-28 | Cilag Gmbh International | Method for fabricating surgical stapler anvils |
EP3616748A1 (en) | 2018-08-27 | 2020-03-04 | National University of Ireland, Galway | Implantable neurostimulator |
US11696761B2 (en) | 2019-03-25 | 2023-07-11 | Cilag Gmbh International | Firing drive arrangements for surgical systems |
KR102212308B1 (en) * | 2019-04-10 | 2021-02-04 | 주식회사 디엔엑스 | Tag apparatus for attachment of things human body communication |
US11903581B2 (en) | 2019-04-30 | 2024-02-20 | Cilag Gmbh International | Methods for stapling tissue using a surgical instrument |
US20200405307A1 (en) * | 2019-06-28 | 2020-12-31 | Ethicon Llc | Control circuit comprising a coating |
US11771419B2 (en) * | 2019-06-28 | 2023-10-03 | Cilag Gmbh International | Packaging for a replaceable component of a surgical stapling system |
US11241235B2 (en) | 2019-06-28 | 2022-02-08 | Cilag Gmbh International | Method of using multiple RFID chips with a surgical assembly |
US11684434B2 (en) | 2019-06-28 | 2023-06-27 | Cilag Gmbh International | Surgical RFID assemblies for instrument operational setting control |
WO2021007571A1 (en) * | 2019-07-11 | 2021-01-14 | Verily Life Sciences Llc | Encapsulation of external components in active implantable medical devices |
US11283161B2 (en) | 2019-07-18 | 2022-03-22 | Medtronic, Inc. | Antenna for implantable medical devices |
EP4076284A1 (en) | 2019-12-16 | 2022-10-26 | Edwards Lifesciences Corporation | Valve holder assembly with suture looping protection |
US11701111B2 (en) | 2019-12-19 | 2023-07-18 | Cilag Gmbh International | Method for operating a surgical stapling instrument |
US11883024B2 (en) | 2020-07-28 | 2024-01-30 | Cilag Gmbh International | Method of operating a surgical instrument |
US11896217B2 (en) | 2020-10-29 | 2024-02-13 | Cilag Gmbh International | Surgical instrument comprising an articulation lock |
US11931025B2 (en) | 2020-10-29 | 2024-03-19 | Cilag Gmbh International | Surgical instrument comprising a releasable closure drive lock |
USD1013170S1 (en) | 2020-10-29 | 2024-01-30 | Cilag Gmbh International | Surgical instrument assembly |
US11779330B2 (en) | 2020-10-29 | 2023-10-10 | Cilag Gmbh International | Surgical instrument comprising a jaw alignment system |
US11849943B2 (en) | 2020-12-02 | 2023-12-26 | Cilag Gmbh International | Surgical instrument with cartridge release mechanisms |
US11744581B2 (en) | 2020-12-02 | 2023-09-05 | Cilag Gmbh International | Powered surgical instruments with multi-phase tissue treatment |
US11737751B2 (en) | 2020-12-02 | 2023-08-29 | Cilag Gmbh International | Devices and methods of managing energy dissipated within sterile barriers of surgical instrument housings |
US11944296B2 (en) | 2020-12-02 | 2024-04-02 | Cilag Gmbh International | Powered surgical instruments with external connectors |
US11890010B2 (en) | 2020-12-02 | 2024-02-06 | Cllag GmbH International | Dual-sided reinforced reload for surgical instruments |
US11950777B2 (en) | 2021-02-26 | 2024-04-09 | Cilag Gmbh International | Staple cartridge comprising an information access control system |
US11751869B2 (en) | 2021-02-26 | 2023-09-12 | Cilag Gmbh International | Monitoring of multiple sensors over time to detect moving characteristics of tissue |
US11793514B2 (en) | 2021-02-26 | 2023-10-24 | Cilag Gmbh International | Staple cartridge comprising sensor array which may be embedded in cartridge body |
US11744583B2 (en) | 2021-02-26 | 2023-09-05 | Cilag Gmbh International | Distal communication array to tune frequency of RF systems |
US11812964B2 (en) | 2021-02-26 | 2023-11-14 | Cilag Gmbh International | Staple cartridge comprising a power management circuit |
US11701113B2 (en) | 2021-02-26 | 2023-07-18 | Cilag Gmbh International | Stapling instrument comprising a separate power antenna and a data transfer antenna |
US11696757B2 (en) | 2021-02-26 | 2023-07-11 | Cilag Gmbh International | Monitoring of internal systems to detect and track cartridge motion status |
US11730473B2 (en) | 2021-02-26 | 2023-08-22 | Cilag Gmbh International | Monitoring of manufacturing life-cycle |
US11749877B2 (en) | 2021-02-26 | 2023-09-05 | Cilag Gmbh International | Stapling instrument comprising a signal antenna |
US11723657B2 (en) | 2021-02-26 | 2023-08-15 | Cilag Gmbh International | Adjustable communication based on available bandwidth and power capacity |
US11723658B2 (en) | 2021-03-22 | 2023-08-15 | Cilag Gmbh International | Staple cartridge comprising a firing lockout |
US11826012B2 (en) | 2021-03-22 | 2023-11-28 | Cilag Gmbh International | Stapling instrument comprising a pulsed motor-driven firing rack |
US11826042B2 (en) | 2021-03-22 | 2023-11-28 | Cilag Gmbh International | Surgical instrument comprising a firing drive including a selectable leverage mechanism |
US11717291B2 (en) | 2021-03-22 | 2023-08-08 | Cilag Gmbh International | Staple cartridge comprising staples configured to apply different tissue compression |
US11737749B2 (en) | 2021-03-22 | 2023-08-29 | Cilag Gmbh International | Surgical stapling instrument comprising a retraction system |
US11806011B2 (en) | 2021-03-22 | 2023-11-07 | Cilag Gmbh International | Stapling instrument comprising tissue compression systems |
US11759202B2 (en) | 2021-03-22 | 2023-09-19 | Cilag Gmbh International | Staple cartridge comprising an implantable layer |
US11786243B2 (en) | 2021-03-24 | 2023-10-17 | Cilag Gmbh International | Firing members having flexible portions for adapting to a load during a surgical firing stroke |
US11793516B2 (en) | 2021-03-24 | 2023-10-24 | Cilag Gmbh International | Surgical staple cartridge comprising longitudinal support beam |
US11786239B2 (en) | 2021-03-24 | 2023-10-17 | Cilag Gmbh International | Surgical instrument articulation joint arrangements comprising multiple moving linkage features |
US11744603B2 (en) | 2021-03-24 | 2023-09-05 | Cilag Gmbh International | Multi-axis pivot joints for surgical instruments and methods for manufacturing same |
US11896219B2 (en) | 2021-03-24 | 2024-02-13 | Cilag Gmbh International | Mating features between drivers and underside of a cartridge deck |
US11849944B2 (en) | 2021-03-24 | 2023-12-26 | Cilag Gmbh International | Drivers for fastener cartridge assemblies having rotary drive screws |
US11903582B2 (en) | 2021-03-24 | 2024-02-20 | Cilag Gmbh International | Leveraging surfaces for cartridge installation |
US11849945B2 (en) | 2021-03-24 | 2023-12-26 | Cilag Gmbh International | Rotary-driven surgical stapling assembly comprising eccentrically driven firing member |
US11896218B2 (en) | 2021-03-24 | 2024-02-13 | Cilag Gmbh International | Method of using a powered stapling device |
US11832816B2 (en) | 2021-03-24 | 2023-12-05 | Cilag Gmbh International | Surgical stapling assembly comprising nonplanar staples and planar staples |
US11857183B2 (en) | 2021-03-24 | 2024-01-02 | Cilag Gmbh International | Stapling assembly components having metal substrates and plastic bodies |
US20220354486A1 (en) * | 2021-05-10 | 2022-11-10 | Cilag Gmbh International | System of surgical staple cartridges comprising absorbable staples |
US11826047B2 (en) | 2021-05-28 | 2023-11-28 | Cilag Gmbh International | Stapling instrument comprising jaw mounts |
US11937816B2 (en) | 2021-10-28 | 2024-03-26 | Cilag Gmbh International | Electrical lead arrangements for surgical instruments |
WO2023119014A1 (en) * | 2021-12-20 | 2023-06-29 | Medtronic, Inc. | Implantable medical device and method of forming same |
Citations (32)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4376441A (en) | 1980-10-14 | 1983-03-15 | Theodore Duncan | Hair treatment applicator |
US4424551A (en) | 1982-01-25 | 1984-01-03 | U.S. Capacitor Corporation | Highly-reliable feed through/filter capacitor and method for making same |
US4846158A (en) | 1986-06-06 | 1989-07-11 | Akihiko Teranishi | Hand type electric massage machine |
EP0534782A1 (en) | 1991-09-26 | 1993-03-31 | Medtronic, Inc. | Implantable medical device enclosure |
US5333095A (en) | 1993-05-03 | 1994-07-26 | Maxwell Laboratories, Inc., Sierra Capacitor Filter Division | Feedthrough filter capacitor assembly for human implant |
US5336158A (en) | 1992-11-12 | 1994-08-09 | Huggins Freddie L | Pneumatic vacuum vibrator apparatus |
US5342408A (en) | 1993-01-07 | 1994-08-30 | Incontrol, Inc. | Telemetry system for an implantable cardiac device |
EP0619101A1 (en) | 1993-02-01 | 1994-10-12 | C.R. Bard, Inc. | Implantable inductively coupled medical identification system |
WO1996011722A1 (en) | 1994-10-12 | 1996-04-25 | Ael Industries, Inc. | Telemetry system for an implanted device |
US5855609A (en) | 1992-08-24 | 1999-01-05 | Lipomatrix, Incorporated (Bvi) | Medical information transponder implant and tracking system |
US5905627A (en) | 1997-09-10 | 1999-05-18 | Maxwell Energy Products, Inc. | Internally grounded feedthrough filter capacitor |
US5963132A (en) | 1996-10-11 | 1999-10-05 | Avid Indentification Systems, Inc. | Encapsulated implantable transponder |
US6216038B1 (en) | 1998-04-29 | 2001-04-10 | Medtronic, Inc. | Broadcast audible sound communication of programming change in an implantable medical device |
US6259937B1 (en) | 1997-09-12 | 2001-07-10 | Alfred E. Mann Foundation | Implantable substrate sensor |
US6275369B1 (en) | 1997-11-13 | 2001-08-14 | Robert A. Stevenson | EMI filter feedthough terminal assembly having a capture flange to facilitate automated assembly |
US6342839B1 (en) | 1998-03-09 | 2002-01-29 | Aginfolink Holdings Inc. | Method and apparatus for a livestock data collection and management system |
US6375780B1 (en) | 1992-06-17 | 2002-04-23 | Micron Technology, Inc. | Method of manufacturing an enclosed transceiver |
US20020049482A1 (en) | 2000-06-14 | 2002-04-25 | Willa Fabian | Lifestyle management system |
US20020151770A1 (en) | 2001-01-04 | 2002-10-17 | Noll Austin F. | Implantable medical device with sensor |
US6566978B2 (en) | 2000-09-07 | 2003-05-20 | Greatbatch-Sierra, Inc. | Feedthrough capacitor filter assemblies with leak detection vents |
US20030181794A1 (en) | 2002-01-29 | 2003-09-25 | Rini Christopher J. | Implantable sensor housing, sensor unit and methods for forming and using the same |
US6765779B2 (en) | 2002-02-28 | 2004-07-20 | Greatbatch-Sierra, Inc. | EMI feedthrough filter terminal assembly for human implant applications utilizing oxide resistant biostable conductive pads for reliable electrical attachments |
US6957107B2 (en) | 2002-03-13 | 2005-10-18 | Cardionet, Inc. | Method and apparatus for monitoring and communicating with an implanted medical device |
US20050247319A1 (en) | 2004-05-07 | 2005-11-10 | Berger J L | Medical implant device with RFID tag and method of identification of device |
US20050258242A1 (en) | 2004-05-20 | 2005-11-24 | Cardiac Pacemakers, Inc. | System and method of managing information for an implantable medical device |
US7017822B2 (en) | 2001-02-15 | 2006-03-28 | Integral Technologies, Inc. | Low cost RFID antenna manufactured from conductive loaded resin-based materials |
US7103413B2 (en) | 2002-07-12 | 2006-09-05 | Cardiac Pacemakers, Inc. | Ferrite core telemetry coil for implantable medical device |
US7174201B2 (en) | 1999-03-11 | 2007-02-06 | Biosense, Inc. | Position sensing system with integral location pad and position display |
US7256695B2 (en) | 2002-09-23 | 2007-08-14 | Microstrain, Inc. | Remotely powered and remotely interrogated wireless digital sensor telemetry system |
US20080065181A1 (en) | 2001-04-13 | 2008-03-13 | Greatbatch, Ltd. | Rfid detection and identification system for implantable medical lead systems |
US7916013B2 (en) | 2005-03-21 | 2011-03-29 | Greatbatch Ltd. | RFID detection and identification system for implantable medical devices |
US8253555B2 (en) * | 2006-01-25 | 2012-08-28 | Greatbatch Ltd. | Miniature hermetically sealed RFID microelectronic chip connected to a biocompatible RFID antenna for use in conjunction with an AIMD |
Family Cites Families (33)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
USRE35565E (en) * | 1990-05-18 | 1997-07-22 | Sumitomo Special Metals Co., Ltd. | Magnetic field generating apparatus for MRI |
US5697958A (en) * | 1995-06-07 | 1997-12-16 | Intermedics, Inc. | Electromagnetic noise detector for implantable medical devices |
US6115634A (en) * | 1997-04-30 | 2000-09-05 | Medtronic, Inc. | Implantable medical device and method of manufacture |
DE19837913C2 (en) | 1998-08-20 | 2000-09-28 | Implex Hear Tech Ag | Implantable device with a charging current feed arrangement having a receiving coil |
US6294997B1 (en) * | 1999-10-04 | 2001-09-25 | Intermec Ip Corp. | RFID tag having timing and environment modules |
US6505072B1 (en) | 2000-11-16 | 2003-01-07 | Cardiac Pacemakers, Inc. | Implantable electronic stimulator having isolation transformer input to telemetry circuits |
US6438408B1 (en) * | 2000-12-28 | 2002-08-20 | Medtronic, Inc. | Implantable medical device for monitoring congestive heart failure |
US6788975B1 (en) * | 2001-01-30 | 2004-09-07 | Advanced Bionics Corporation | Fully implantable miniature neurostimulator for stimulation as a therapy for epilepsy |
JP4433629B2 (en) | 2001-03-13 | 2010-03-17 | 株式会社日立製作所 | Semiconductor device and manufacturing method thereof |
US20070067004A1 (en) | 2002-05-09 | 2007-03-22 | Boveja Birinder R | Methods and systems for modulating the vagus nerve (10th cranial nerve) to provide therapy for neurological, and neuropsychiatric disorders |
US7263401B2 (en) | 2003-05-16 | 2007-08-28 | Medtronic, Inc. | Implantable medical device with a nonhermetic battery |
US7195717B2 (en) * | 2003-07-28 | 2007-03-27 | Kyocera Corporation | Ferrite core for RFID application, method of manufacturing the same, and ferrite coil using the same |
US7112356B2 (en) | 2004-05-11 | 2006-09-26 | Sonoco Development, Inc. | Composite container with RFID device and high-barrier liner |
US7322832B2 (en) | 2004-10-26 | 2008-01-29 | Medtronic, Inc. | Radio frequency antenna flexible circuit interconnect with unique micro connectors |
US8160705B2 (en) * | 2005-02-23 | 2012-04-17 | Greatbatch Ltd | Shielded RF distance telemetry pin wiring for active implantable medical devices |
US7528724B2 (en) | 2005-02-28 | 2009-05-05 | Impinj, Inc. | On die RFID tag antenna |
US7256699B2 (en) | 2005-03-24 | 2007-08-14 | Sdgi Holdings, Inc. | Button-type RFID tag |
US20060224206A1 (en) * | 2005-03-31 | 2006-10-05 | Dublin Garry L | Optional telemetry antenna for implantable medical devices |
US20060241725A1 (en) | 2005-04-25 | 2006-10-26 | Imad Libbus | Method and apparatus for simultaneously presenting cardiac and neural signals |
US20060247711A1 (en) | 2005-04-28 | 2006-11-02 | Verhoef William D | Telemetry antennas for implantable medical devices |
US7643965B2 (en) | 2005-08-10 | 2010-01-05 | Olympus Corporation | EMI management system and method |
JP4289338B2 (en) | 2005-09-29 | 2009-07-01 | 沖電気工業株式会社 | RFID tag communication system, RFID tag and induction antenna device |
US7595723B2 (en) | 2005-11-14 | 2009-09-29 | Edwards Lifesciences Corporation | Wireless communication protocol for a medical sensor system |
US20070120683A1 (en) | 2005-11-25 | 2007-05-31 | Alexis Flippen | Implantable electronically-encoded critical health care instruction aka "the Terry" |
US8248232B2 (en) * | 2006-01-25 | 2012-08-21 | Greatbatch Ltd. | Hermetically sealed RFID microelectronic chip connected to a biocompatible RFID antenna |
US7965180B2 (en) | 2006-09-28 | 2011-06-21 | Semiconductor Energy Laboratory Co., Ltd. | Wireless sensor device |
US7889070B2 (en) | 2006-10-17 | 2011-02-15 | At&T Intellectual Property I, L.P. | Methods, systems, devices and computer program products for transmitting medical information from mobile personal medical devices |
US7865247B2 (en) | 2006-12-18 | 2011-01-04 | Medtronic, Inc. | Medical leads with frequency independent magnetic resonance imaging protection |
US20080180242A1 (en) | 2007-01-29 | 2008-07-31 | Cottingham Hugh V | Micron-scale implantable transponder |
US8231538B2 (en) | 2007-02-20 | 2012-07-31 | University Of Louisville Research Foundation, Inc. | Perivascular pressure sensor and sensing system |
US8480612B2 (en) | 2007-10-31 | 2013-07-09 | DePuy Synthes Products, LLC | Wireless shunts with storage |
US8344889B2 (en) | 2007-12-17 | 2013-01-01 | Solstice Medical, Llc | Side loaded shorted patch RFID tag |
US8207853B2 (en) | 2008-01-14 | 2012-06-26 | Avery Dennison Corporation | Hybrid sensor/communication device, and method |
-
2010
- 2010-03-22 US US12/728,538 patent/US8248232B2/en not_active Ceased
- 2010-03-23 WO PCT/US2010/028243 patent/WO2011037648A1/en active Application Filing
- 2010-09-22 US US12/887,720 patent/US8810405B2/en not_active Expired - Fee Related
-
2013
- 2013-11-22 US US14/087,734 patent/USRE45030E1/en not_active Expired - Fee Related
Patent Citations (39)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4376441A (en) | 1980-10-14 | 1983-03-15 | Theodore Duncan | Hair treatment applicator |
US4424551A (en) | 1982-01-25 | 1984-01-03 | U.S. Capacitor Corporation | Highly-reliable feed through/filter capacitor and method for making same |
US4424551B1 (en) | 1982-01-25 | 1991-06-11 | Highly-reliable feed through/filter capacitor and method for making same | |
US4846158A (en) | 1986-06-06 | 1989-07-11 | Akihiko Teranishi | Hand type electric massage machine |
EP0534782A1 (en) | 1991-09-26 | 1993-03-31 | Medtronic, Inc. | Implantable medical device enclosure |
US6375780B1 (en) | 1992-06-17 | 2002-04-23 | Micron Technology, Inc. | Method of manufacturing an enclosed transceiver |
US5855609A (en) | 1992-08-24 | 1999-01-05 | Lipomatrix, Incorporated (Bvi) | Medical information transponder implant and tracking system |
US5336158A (en) | 1992-11-12 | 1994-08-09 | Huggins Freddie L | Pneumatic vacuum vibrator apparatus |
US5342408A (en) | 1993-01-07 | 1994-08-30 | Incontrol, Inc. | Telemetry system for an implantable cardiac device |
EP0619101A1 (en) | 1993-02-01 | 1994-10-12 | C.R. Bard, Inc. | Implantable inductively coupled medical identification system |
US5333095A (en) | 1993-05-03 | 1994-07-26 | Maxwell Laboratories, Inc., Sierra Capacitor Filter Division | Feedthrough filter capacitor assembly for human implant |
WO1996011722A1 (en) | 1994-10-12 | 1996-04-25 | Ael Industries, Inc. | Telemetry system for an implanted device |
US5963132A (en) | 1996-10-11 | 1999-10-05 | Avid Indentification Systems, Inc. | Encapsulated implantable transponder |
US5905627A (en) | 1997-09-10 | 1999-05-18 | Maxwell Energy Products, Inc. | Internally grounded feedthrough filter capacitor |
US6259937B1 (en) | 1997-09-12 | 2001-07-10 | Alfred E. Mann Foundation | Implantable substrate sensor |
US6275369B1 (en) | 1997-11-13 | 2001-08-14 | Robert A. Stevenson | EMI filter feedthough terminal assembly having a capture flange to facilitate automated assembly |
US6342839B1 (en) | 1998-03-09 | 2002-01-29 | Aginfolink Holdings Inc. | Method and apparatus for a livestock data collection and management system |
US6216038B1 (en) | 1998-04-29 | 2001-04-10 | Medtronic, Inc. | Broadcast audible sound communication of programming change in an implantable medical device |
US7174201B2 (en) | 1999-03-11 | 2007-02-06 | Biosense, Inc. | Position sensing system with integral location pad and position display |
US20020049482A1 (en) | 2000-06-14 | 2002-04-25 | Willa Fabian | Lifestyle management system |
US6735479B2 (en) | 2000-06-14 | 2004-05-11 | Medtronic, Inc. | Lifestyle management system |
US6566978B2 (en) | 2000-09-07 | 2003-05-20 | Greatbatch-Sierra, Inc. | Feedthrough capacitor filter assemblies with leak detection vents |
US20020151770A1 (en) | 2001-01-04 | 2002-10-17 | Noll Austin F. | Implantable medical device with sensor |
US7017822B2 (en) | 2001-02-15 | 2006-03-28 | Integral Technologies, Inc. | Low cost RFID antenna manufactured from conductive loaded resin-based materials |
US20080065181A1 (en) | 2001-04-13 | 2008-03-13 | Greatbatch, Ltd. | Rfid detection and identification system for implantable medical lead systems |
US20030181794A1 (en) | 2002-01-29 | 2003-09-25 | Rini Christopher J. | Implantable sensor housing, sensor unit and methods for forming and using the same |
US7479108B2 (en) | 2002-01-29 | 2009-01-20 | Sicel Technologies, Inc. | Methods for using an implantable sensor unit |
US20060183979A1 (en) | 2002-01-29 | 2006-08-17 | Rini Christopher J | Methods for using an implantable sensor unit |
US6765779B2 (en) | 2002-02-28 | 2004-07-20 | Greatbatch-Sierra, Inc. | EMI feedthrough filter terminal assembly for human implant applications utilizing oxide resistant biostable conductive pads for reliable electrical attachments |
US6957107B2 (en) | 2002-03-13 | 2005-10-18 | Cardionet, Inc. | Method and apparatus for monitoring and communicating with an implanted medical device |
US7103413B2 (en) | 2002-07-12 | 2006-09-05 | Cardiac Pacemakers, Inc. | Ferrite core telemetry coil for implantable medical device |
US7256695B2 (en) | 2002-09-23 | 2007-08-14 | Microstrain, Inc. | Remotely powered and remotely interrogated wireless digital sensor telemetry system |
US7333013B2 (en) | 2004-05-07 | 2008-02-19 | Berger J Lee | Medical implant device with RFID tag and method of identification of device |
US20080048855A1 (en) | 2004-05-07 | 2008-02-28 | Berger J L | Medical implant device with RFID tag and method of identification of device |
US20050247319A1 (en) | 2004-05-07 | 2005-11-10 | Berger J L | Medical implant device with RFID tag and method of identification of device |
US7240833B2 (en) | 2004-05-20 | 2007-07-10 | Cardiac Pacemakers, Inc. | System and method of managing information for an implantable medical device |
US20050258242A1 (en) | 2004-05-20 | 2005-11-24 | Cardiac Pacemakers, Inc. | System and method of managing information for an implantable medical device |
US7916013B2 (en) | 2005-03-21 | 2011-03-29 | Greatbatch Ltd. | RFID detection and identification system for implantable medical devices |
US8253555B2 (en) * | 2006-01-25 | 2012-08-28 | Greatbatch Ltd. | Miniature hermetically sealed RFID microelectronic chip connected to a biocompatible RFID antenna for use in conjunction with an AIMD |
Non-Patent Citations (3)
Title |
---|
U.S. Appl. No. 60/478,717, filed Jun. 16, 2003, Off. |
Wesley J. Clement and Bob Stevenson, Determination of Effective Lead Loop Area for Implantable Pulse Generators and Cardioverter/Defibrillators for Determination of Susceptibility to Radiated Electromagnetic Interference, Heart Rhythm 2005, May 5, 2005, Abstract 05-AB-2928-HRS, New Orleans, LA. |
Wesley J. Clement and Bob Stevenson; Lead Loop Area Measurement of Implantable Pulse Generations and Cardioverter/Defibrillators for Determination of Susceptibility to Radiated Electromagnetic Interference; Heart Rhythm 2005; May 5, 2005; Abstract: 05-AB-2928-HRS, New Orleans, LA. |
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US20140155951A1 (en) * | 2012-12-04 | 2014-06-05 | Biotronik Se & Co. Kg | Implantable Electrostimulation Assembly and Adapter and Electrode Lead of the Same |
US9427590B2 (en) * | 2012-12-04 | 2016-08-30 | Biotronik Se & Co. Kg | Implantable electrostimulation assembly and adapter and electrode lead of the same |
US10896300B2 (en) * | 2018-05-31 | 2021-01-19 | STMicroelectronics Austria GmbH | Wireless communication device and method |
US11969302B2 (en) * | 2018-07-06 | 2024-04-30 | Biotronik Se & Co. Kg | Header having radiographic marker |
US11672983B2 (en) | 2018-11-13 | 2023-06-13 | Onward Medical N.V. | Sensor in clothing of limbs or footwear |
US11583682B2 (en) * | 2020-12-07 | 2023-02-21 | Onward Medical N.V. | Antenna for an implantable pulse generator |
Also Published As
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US8810405B2 (en) | 2014-08-19 |
WO2011037648A1 (en) | 2011-03-31 |
US20100194541A1 (en) | 2010-08-05 |
US8248232B2 (en) | 2012-08-21 |
US20110001610A1 (en) | 2011-01-06 |
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