WO1996011722A1 - Systeme de telemetrie pour dispositif implante - Google Patents

Systeme de telemetrie pour dispositif implante Download PDF

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Publication number
WO1996011722A1
WO1996011722A1 PCT/US1995/013383 US9513383W WO9611722A1 WO 1996011722 A1 WO1996011722 A1 WO 1996011722A1 US 9513383 W US9513383 W US 9513383W WO 9611722 A1 WO9611722 A1 WO 9611722A1
Authority
WO
WIPO (PCT)
Prior art keywords
repeater
signal
telemetry system
transponder
frequency signal
Prior art date
Application number
PCT/US1995/013383
Other languages
English (en)
Other versions
WO1996011722A9 (fr
Inventor
Raymond S. Markowitz
Robert E. Roy
Xiaoguang G. Sun
Original Assignee
Ael Industries, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Ael Industries, Inc. filed Critical Ael Industries, Inc.
Priority to AU41316/96A priority Critical patent/AU4131696A/en
Publication of WO1996011722A1 publication Critical patent/WO1996011722A1/fr
Publication of WO1996011722A9 publication Critical patent/WO1996011722A9/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/37211—Means for communicating with stimulators
    • A61N1/37252—Details of algorithms or data aspects of communication system, e.g. handshaking, transmitting specific data or segmenting data
    • A61N1/37282—Details of algorithms or data aspects of communication system, e.g. handshaking, transmitting specific data or segmenting data characterised by communication with experts in remote locations using a network
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A61B5/0031—Implanted circuitry
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/1112—Global tracking of patients, e.g. by using GPS
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/02—Operational features
    • A61B2560/0204—Operational features of power management
    • A61B2560/0214—Operational features of power management of power generation or supply
    • A61B2560/0219—Operational features of power management of power generation or supply of externally powered implanted units
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/686—Permanently implanted devices, e.g. pacemakers, other stimulators, biochips
    • 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

Definitions

  • This invention relates to a telemetry system for communicating between an electronic implanted device and a remote monitoring station.
  • U.S. Patent No. 4,361,153 discloses an external unit which transmits a carrier signal .
  • the implanted device includes a transponder having a tuned resonant circuit for resonating at the frequency of the carrier signal so as to re-radiate a signal at the carrier frequency.
  • the transponder also includes means for superimposing an information signal on the re-radiated signal by altering the resonance in accordance with the information signal. The re-radiated signal is received by the external device and the information signal is extracted therefrom.
  • the resonant circuit in this patent consumes only the energy required to modulate the transponder's load impedance. Thus, the energy consumption level of this circuit is very low compared to the energy of the total signal reflected by the transponder.
  • Other telemetry systems for implanted devices are described in U.S.
  • Low power passive radio frequency (RF) identification transponder/reader systems are also known in the art.
  • One system is described in Page, Raymond, "A Low Power RF ID Transponder," RF Design, July 1983, 31, 32, 34, 36.
  • the reader transmits an unmodulated RF interrogation signal to a transponder attached to an object such as a rail car.
  • the transponder receives the unmodulated RF signal, and returns a frequency doubled (i.e. , second harmonic) AM modulated RF signal to a receiver placed a short distance away from the transponder.
  • the frequency doubling and modulation are performed in the transponder by a single microwave diode.
  • the return signal is modulated with information identifying the object.
  • a telemetry system which can interrogate an implanted object from a distant monitoring station, which employs a passive-type transponder in the implanted object, which employs an extremely low power transponder that does not require a high power interrogating signal or rectifying circuitry for operation, which employs an antenna design that performs well with extremely low power signals and which can operate at high data rates.
  • the present invention fills that need.
  • the present invention provides a telemetry system for allowing an electronic device implanted in an object to communicate with a remote monitoring station.
  • the telemetry system comprises the remote monitoring station, a passive transponder attached to the implanted device, and a two-way repeater.
  • the electronic device has electronic condition monitoring circuitry associated therewith.
  • the passive transponder is electrically connected to this monitoring circuitry.
  • the transponder automatically transmits signals containing condition information when the transponder receives a proper interrogation signal from the repeater.
  • the repeater is external to the object and in close proximity thereto.
  • the repeater includes a first transceiver for communicating with the transponder and a second transceiver for communicating with the remote monitoring station.
  • the invention also provides a method for interrogating an implanted device from a remote monitoring station by employing a repeater in proximity to the implanted device.
  • Unique aspects of the invention include a novel telemetry arrangement and a transponder which operates on extremely low power requirements, has a very high data rate, and employs a novel antenna design.
  • Fig. 1 is diagram of a telemetry system for an implanted device according to a preferred embodiment of the present invention.
  • Fig. 2 is a diagram of the main components of the telemetry system in Fig. 1 and shows the communications parts of the components.
  • Fig. 3 is a perspective view of the implanted device showing the placement of a novel transponder thereon.
  • Fig. 4 is a sectional view of Fig. 3, taken along lines 4-4 in Fig. 3.
  • Fig. 5 A is a schematic diagram of a transponder circuit associated with the implanted device according to a preferred embodiment of the present invention.
  • Fig. 5B is a schematic diagram of a portion of the transponder circuit for replacing a portion of the circuit shown in Fig. 5 A, according to an alternative embodiment of the present invention.
  • Fig. 6A is a diagrammatic representation of transponder antennas and selected transponder circuitry shown in Fig. 5A.
  • Fig. 6B is an alternative diagrammatic representation of transponder antennas and selected transponder circuitry suitable for use in Fig. 5 A.
  • Fig. 7 is a block diagram of a repeater associated with the telemetry system.
  • Fig. 1 shows an overview of the novel telemetry system.
  • the telemetry system allows a remote monitoring station 10 to communicate with implanted device 12 through repeater 14 and cellular telephone network 16.
  • the cellular telephone network 16 can be a personal communications network (PCN).
  • the device 12 is implanted in patient 13.
  • the repeater 14 is worn externally by the patient 13 in a manner similar to a beeper or pager. Accordingly, the repeater 14 is battery powered, compact in size, and low in weight.
  • the repeater 14 is in wireless communication with the implanted device 12.
  • the communication path in the overall system may be one-way or two-way.
  • the repeater 14 In a one-way communication mode, the repeater 14 initiates an interrogation of the implanted device 12, the implanted device 12 returns an information signal to the repeater 14, and the repeater 14 relays the information to the monitoring station 10.
  • the repeater 14 also provides a carrier signal for powering the return signal from the implanted device 12, as will be further described below.
  • the monitoring station 10 In a two-way communication mode, the monitoring station 10 initiates an information request to the repeater 14. The remaining steps are the same as in the one-way mode.
  • Fig. 2 shows an overview of the communications parts of the invention.
  • the telemetry system employs three different types of communication devices.
  • the first type is a transponder 17 attached to the implanted device 12.
  • the transponder 17 is an extremely low power device (i.e., it consumes very little power, less than 1 nW/baud). It is very small in size and weight so that it can be easily incorporated onto prior art implantable devices. All parts of the transponder 17 which are external to the implantable device, and thus exposed to the patient's tissue, are bio-benign.
  • the second type of communication device is a transceiver 18 associated with the repeater 14.
  • This transceiver 18 is a multi-frequency device because it transmits signals to the implanted device 12 at a first frequency and transmits signals to the monitoring station 10 at a second frequency. In an alternative embodiment of the invention, however, transceiver 18 transmits and receives at the same frequency.
  • the transceiver 18 employs a specialized protocol, as will be described in detail below.
  • the transceiver 18 is connected to a third type of communication device, transceiver 20, through processor/buffer 22.
  • the transceiver 20 and the processor /buffer 22 are also associated with the repeater 14.
  • the transceiver 20 operates on a single standard frequency for receiving and transmitting, and employs a standard protocol and baud rate.
  • the transceiver 20 is a cellular communication device such as a cellular telephone which communicates with cellular networks or a PCN currently in use.
  • the monitoring station 10 also includes a transceiver 20' for communicating with the repeater's transceiver 20.
  • Fig. 3 shows a perspective view of the implanted device 12.
  • the transponder 17 is disposed on a high dielectric substrate 24 attached to one or more outer surfaces of the implanted device 12.
  • the transponder 17 includes transponder circuitry 26 having to a signal receiving antenna 28 for receiving signals transmitted from the repeater 14, a signal transmitting antenna 30 for transmitting information signals back to the repeater 14 and circuitry 32 disposed therebetween.
  • Fig. 3 also shows that the transponder circuitry 26 receives signals from one or more body condition sen- sor(s)/detector(s) 33 disposed inside of the implanted device 12.
  • the sen- sor(s)/detector(s) 33 measure or monitor one or bodily functions.
  • the sen- sor(s)/detector(s) 33 can be any prior art component sensor typically associated with an implanted device, and thus is not further described herein.
  • Fig. 3 depicts one embodiment of the invention wherein the implanted device 12 is a disk-shaped pacemaker. This pacemaker has a thickness w of about 7 mm. Most of the internal area of the pacemaker houses circuitry 34 for performing all of the pacemaker functions, as is well-known in the art. The sensor(s)/detector(s) 33 are included in that circuitry 34. The pacemaker electrode leads are not shown in this view.
  • antennas 28 and 30 are arrays with respect to the implanted device 12 and with respect to each other.
  • the type of antenna employed is the type of antenna employed.
  • the antennas 28 and 30 are microstrip antennas. This type of antenna conforms easily to the outer surface of the implanted device 12, thereby minimizing the amount of thickness added to the implanted device 12. Also, this type of antenna can be attached to a very thin substrate on the device 12 and readily accepts an optional bio-benign protective coating. As described more fully below, the microstrip antennas 28 and 30 may operate at different frequencies. Thus, interference and clutter are potential problems.
  • Fig. 4 is a sectional view of the implanted device 12 shown in Fig. 3, as the device 12 appears when implanted inside the patient. This view shows the device's metal case 36, dielectric substrate 24, transponder circuitry 26 disposed on the substrate 24, and the patient's bio-tissue 38.
  • the transponder circuitry 26 may have an optional bio-benign coating thereon (not shown).
  • the relative width of the substrate 24 with respect to the overall width of the case 36 is substantially exaggerated for illustration purposes.
  • Fig. 4 shows that the metal case 36 is hollow, in fact it is not empty.
  • the case of a prior art implanted device 12 contains body function detection and monitoring circuitry, body function control circuitry and a battery.
  • the case 36 may contain a microproces ⁇ sor-based heart rhythm detection and processing circuitry, heart rhythm control circuitry and an extremely long-life (e.g., 10 years) battery, labelled as pacemaker circuitry 34 in Fig. 3.
  • Fig. 3 also illustrates one such sensor/detector circuit 33 associated with the pacemaker circuitry 34. Since the elements 33 and 34 are well known in the art, they are not described in detail herein.
  • Fig. 5 A shows a schematic diagram of the transponder circuitry 26 of the implanted device 12.
  • the transponder circuitry 26 preferably includes at least the following six main sections:
  • the microprocessor 42 is not necessarily a physical part of the transponder circuitry 26, although it is part of the implanted device 12. For cost- effective implementation, it will be more desirable for the transponder circuitry 26 to time-share with the microprocessor associated with the prior art heart rhythm detection and processing circuitry (which is already disposed in the device's case 36).
  • Such a microprocessor typically includes an interrogation mode which "wakes up" the circuitry . That is, when an appropriate identification signal is received by the microprocessor, it becomes fully functional and sends out information signals related to monitored body conditions (e.g., heart rhythm data, if the implanted device 12 is a pacemaker).
  • signal lines connect the microprocessor disposed in the device's case 36 to the remaining parts of the transponder circuitry 26 attached to an external surface of the case 36.
  • the microprocessor 42 is a dedicated device which is physically part of the transponder circuitry 26.
  • the microprocessor 42 is disposed on the substrate 24 with signal lines extending through the case 36 to sensor circuitry therein.
  • the signal receiving antenna 28 is tuned to receive an RF signal at a frequency f A and pass it into the filtering and rectifying section 40.
  • the output of the antenna 28 is connected to a bandpass filter f A and an RF trap filter f B in the section 40.
  • the bandpass filter f A is desirable because the bandwidth of the antenna 28 will be wide due to the highly lossy tissue surrounding the implanted device 12.
  • frequency f ⁇ is 915 MHz and frequency/,, is the second harmonic of frequency/, or 1830 MHz.
  • the section 40 passes the 915 MHz frequency f A signal and filters out any 1830 MHz frequency/, signals.
  • the filtered, received signal then flows to two different paths.
  • the signal flows through rectifying diode 48 and into a READ terminal of the microprocessor 42.
  • the signal flows directly into a first input of the harmonic generating and modulating section 44.
  • the harmonic generating and modulating section 44 generates harmonics of the frequency of the signal output from the section 40 and modulates the harmonic signals with digital data pulses representing patient information sensed by the implanted device 12.
  • the second harmonic is employed.
  • the harmonic generating and modulating section 44 has two inputs and one output. The first input is connected to section 40, as described above. The second input is connected to a SEND terminal of the microprocessor 42 which is a digital data output source. The output of the section 44 is connected to the signal transmitting filtering section 46 and signal transmitting antenna 30.
  • the section 44 is a circuit comprising a high input impedance data switching transistor 50 (e.g., an N-type field effect transistor) and a harmonic generating diode 52.
  • the positive side of the diode 52 receives the signal from the second path of the section 40 described above and also receives a signal from the drain of the switching transistor 50.
  • the diode 52 may be optionally biased by an extremely low DC current (e.g., 0.1 ⁇ A) to increase the harmonic generation efficiency under very low RF power conditions.
  • the negative side of the diode 52 is the output of the section 44.
  • the source of the switching transistor 50 is connected through a resistor to the SEND terminal of the microprocessor 42 and to ground.
  • the gate of the switching transistor 50 is connected directly to the SEND terminal.
  • Fig. 5B shows an alternative embodiment of the harmonic generating and modulating section 44.
  • the section 44 is a single PNP transistor 54 wherein the transistor emitter is connected to the signal from the second path of the section 40 and the collector is the output of the section 44.
  • the base is connected through a resistor to the SEND terminal of the microprocessor 42 and through a capacitor to ground.
  • the output of the harmonic generating and modulating section 44 is connected to the signal transmitting filtering section 46 and signal transmitting antenna 30.
  • the section 46 is an RF trap filter/,.
  • the antenna 30 thus transmits a pulse code modulated signal at frequency f B , which is 1830 MHz in the described example of the invention .
  • the second harmonic was selected for the frequency f B because it allows for ultra-low power re-radiation.
  • the section 44 generates other harmonics and sub-harmonics of frequency/, which are also suitable for re-radiation.
  • the invention is described as employing a transmitting frequency which is a second harmonic of the receiving frequency, other harmonic frequencies are within the scope of the invention.
  • the antennas 28 and 30 are microstrip antennas.
  • the filters /,, f B and the modulation circuitry can be implemented in the microstrip transmission line on the same substrate as the antennas 28 and 30.
  • the frequency trap filters /, and / ⁇ can be implemented as microstrip stubs.
  • a limiter can be incorporated into the microstrip transmission line associated with the antenna 28 to protect the transponder circuitry 26 against unusually high radiation levels. Either center feeds or offset feeds can be employed for the microstrip antenna design.
  • Fig. 6A shows diagrammatically that the polarization of the antenna 28 is orthogonal to the polarization of the antenna 30.
  • Fig. 6 A also shows filters f A , f B of the filtering and rectifying section 40 implemented in a microstrip transmission line 56.
  • the antenna 30 is shown connected to the diode 52, which in turn, is connected to the switching transistor 50.
  • the microstrip antennas 28 or 30 also function as a DC ground by shorting the center of the antenna (either directly or through an inductive element) to a ground plate such as the implant's case.
  • the symmetrical antenna center can be shorted because the wave impedance at this point is ideally zero. This grounding feature is desirable because many implanted devices use their cases as the DC ground for their circuit functions.
  • Fig. 6B shows an alternative antenna configuration which employs a single dual-frequency rectangular, corner-fed microstrip 82.
  • This microstrip 82 resonates at frequency f A in the long direction and at frequency f B in the orthogonal direction. Again, the two polarizations are orthogonal. The center of the rectangular microstrip is also shorted.
  • the rectangle has a 2: 1 dimensional ratio, reflecting the ratio between the two frequencies.
  • Shunt diode 84 connected at the corner feed performs harmonic generation and detection. This alternative configuration simplifies the circuitry necessary to perform these functions.
  • Element 86 includes the filtering, biasing and switching circuitry.
  • Fig. 7 shows a block diagram of a preferred form of the repeater 14 associated with the telemetry system.
  • the repeater 14 includes transmitting circuitry 58 for transmitting signals at a frequency/,, receiving and demodulating circuitry 60 for receiving and demodulating signals received at a frequency / continent, and communications circuitry 62 for facilitating communication between the repeater 14 and the monitoring station 10 (not shown).
  • the transmitting circuitry 58 includes a carrier frequency generator 64, modulator 66 and signal transmitting antenna 68.
  • the modulator 66 receives its modulation information from processor/buffer 70.
  • the receiving and demodulating circuitry 60 is a high sensitivity heterodyne circuit. Together, the transmitting circuitry 58 and the receiving and demodulating circuitry 60 form a first transceiver in the repeater 14, labelled as the transceiver 18 in Fig. 2.
  • the communications circuitry 62 includes the processor/buffer 70, signal transmitting/receiving antenna 72 and cellular modem 74 connected therebetween.
  • the antenna 72 transmits and receives signals at a cellular frequency f c .
  • the cellular modem 74 includes a built-in auto-dial modem for interfacing with the cellular telephone network 16 shown in Fig. 1.
  • the communications circuitry 62 forms a second transceiver in the repeater 14, labelled as the transceiver 20 in Fig. 2.
  • the repeater 14 optionally includes a global positioning system (GPS) receiver 76 for allowing the repeater 14 to communicate its location to the monitoring station 10.
  • GPS global positioning system
  • the repeater 14 also optionally includes speaker or audio indicator 78 and/or visual indicator 80 for communicating to the patient 13 that an abnormal condition is present, or for communicating sensed condition information or status information to the patient.
  • the transmitting and receiving antennas in the repeater 14 are also orthogonally polarized with respect to each other in same manner as described above with respect to the transponder antennas.
  • the signal received by the antenna in the circuitry 60 may be first downconverted to a common frequency so that a commercially available heterodyne circuit chip can be employed for the remaining parts of the circuitry.
  • the communications protocol of the telemetry system is an important feature of the invention and is best explained with respect to Figs. 1, 5 A, 6, and 7.
  • This protocol allows the monitoring station 10 to interrogate the implanted device 12 at any instance in time and receive back an information signal from the device 12.
  • the monitoring station 10 sends an information request signal to the repeater 14 through the cellular telephone network 16 or an equivalent PCN.
  • the information request signal is received by the repeater's communications circuitry 62 and converted into an interrogation signal.
  • the repeater's transmitting circuitry 58 modulates the carrier frequency /, with the interrogation signal and transmits the modulated signal to the implanted device 12 at time t,.
  • the microprocessor 42 in the transponder circuitry 26 of the implanted device 12 receives the interrogation signal at its READ terminal at time t 2 which will be almost instantaneously after t, when RF carrier signals are employed. In response, the microprocessor 42 sends out a digital data pulse stream (i . e . , a condition information signal) at time t 3 which contains the requested information. Time t 3 is a discrete time period after t 2 .
  • the signal transmitted from the repeater's transmitting circuitry 58 is no longer modulated by the interrogation signal. That is, the interrogation signal only modulates the repeater's carrier signal for a short time interval after time /,.
  • the signal from the second output path of the transponder's filtering and rectifying path 40 which flows directly into the harmonic generating and modulating section 44 is a pure carrier signal at frequency/,. This pure carrier signal is frequency doubled and modulated with the digital data pulse stream to create a modulated signal at frequency f B containing the condition information.
  • the repeater 14 receives this signal, demodulates it and sends it to the repeater's communications circuitry 62 for subsequent communication to the monitoring station 10.
  • the monitoring station 10 requests the optional GPS information and the repeater 14 includes the optional GPS receiver 76, this information is also included in the packet of data sent to the station 10. If the repeater 14 includes one or both of the optional audio or visual indicators 78 and 80, the processor/buffer 70 outputs the responses which are appropriate for the received condition information. In an alternative embodiment, the monitoring station 10 determines the responses which are appropriate for audio or visual display.
  • the transponder circuitry 26 time-shares a microprocessor associated with the implanted device, the interrogation signal sent out by the repeater 14 "wakes up" the microprocessor circuitry.
  • the modulation of the repeater's carrier frequency / is for identification purposes only. This scheme acts as a double check so that the transponder circuitry 26 only returns a modulated information signal when the repeater 14 unequivocally desires to address the implanted device 12 associated with that particular patient.
  • the repeater 14 will perform a first check against causing the implanted device 12 to falsely respond by checking that the information request signal received from the monitoring station 10 is directed to the associated implanted device 12. If the signal is not appropriate for the implanted device 12, the repeater 14 will not transmit any signal from the transmitting circuitry 58.
  • the interrogation routine described above allows the novel system described herein to be retrofitted to existing implanted devices. However, if it is desired to implement more sophisticated interrogation routines, the microprocessor circuitry of the prior art implanted devices must be modified accordingly. Another alternative interrogation routine dispenses with the need for a modulated interrogation signal . Certain microprocessors in implanted devices will "wake up" upon receiving a pure carrier signal. If the implanted device 12 employs such a microprocessor, it is only necessary for the monitoring station 10 to send an information request signal to the repeater 14. In response to this signal, the repeater 14 sends out a pure carrier signal at frequency/,.
  • This pure carrier signal wakes up the microproces ⁇ sor and the interrogation routine continues in the same manner as described above.
  • One disadvantage of this routine is that there is no double check protection against falsely waking up the microprocessor. Thus, the monitoring station 10 could potentially receive a condition information signal from the wrong patient.
  • the novel telemetry system is described as employing a frequency f B which is the second harmonic of frequency /, wherein the frequency/, is 915 MHz
  • the scope of the invention includes any interrogating frequency/, and a responding frequency/,, which is the same, a superharmonic or a subharmonic of the frequency/,.
  • a high carrier frequency such as 915 MHz enables the system to achieve a high communications data rate of about 100 kbps. This rate is over ten times greater than typical prior art telemetry data rates for implanted devices.
  • Other types of modulation schemes are within the scope of the invention .
  • the transponder in the invention operates on extremely low power.
  • a passive miniature transponder built in the manner described above will consume less than 1 nW/baud of energy for signal modulation.
  • the transponder circuitry 26 may include an optional battery charging circuit. This circuit can recharge the device 12 with power collected by rectifying the interrogating signal .
  • the power level output from the repeater's transmitting circuitry 58 would have to be significantly increased from the low levels needed for operating the disclosed transponder circuit.
  • the novel telemetry system described herein can interrogate an implanted object from virtually any part of the world without patient involvement. A patient using the novel system is thus freed from active tasks normally required to communicate interrogated information to a remote source.
  • the transponder circuitry drastically reduces the power requirements of the implanted object transponder to less than 1 nW baud.
  • the transponder antenna design provides a high level of interference suppression and clutter discrimination, even when employing extremely low power signals.
  • the telemetry system allows for very high data rates, in the range of about 100 kbps.
  • the novel telemetry system can be retrofitted to prior art implanted devices for allowing truly remote interrogation of such devices.

Abstract

Un système de télémétrie comprend une station de surveillance éloignée (10), un répéteur (14) porté extérieurement par un patient (13) et un répondeur quasi passif fixé à un dispositif (12) implanté chez le patient (13). La station de surveillance éloignée communique avec le répéteur (14) pour lancer un programme d'interrogation se déroulant entre le répéteur (14) et le répondeur et destiné à extraire des informations sur l'état du patient, à partir du dispositif (12) implanté. Lorsque le répéteur (14) reçoit les informations concernant l'état du patient, il les retransmet à la station de surveillance éloignée (10). Le répondeur est spécialement conçu pour fonctionner à un niveau de puissance extrêmement bas, inférieur à 1 nW/baud, et pour pouvoir être fixé à des dispositifs (12) implantés existants. Le répondeur peut fonctionner à un débit de données très élevé, y compris un débit d'environ 100 kb/s.
PCT/US1995/013383 1994-10-12 1995-10-10 Systeme de telemetrie pour dispositif implante WO1996011722A1 (fr)

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Application Number Priority Date Filing Date Title
AU41316/96A AU4131696A (en) 1994-10-12 1995-10-10 Telemetry system for an implanted device

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US32219294A 1994-10-12 1994-10-12
US322,192 1994-10-12

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WO1996011722A1 true WO1996011722A1 (fr) 1996-04-25
WO1996011722A9 WO1996011722A9 (fr) 1996-11-28

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Cited By (21)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0896828A3 (fr) * 1997-08-13 2000-01-12 SORIN BIOMEDICA S.p.A. Dispositif implantable de surveillance de patient
WO2001043823A1 (fr) * 1999-12-17 2001-06-21 Medtronic, Inc. Surveillance, alarme, diagnostic et programmation virtuels a distance de systemes de dispositifs medicaux implantables
WO2001045793A1 (fr) 1999-12-21 2001-06-28 Medtronic, Inc. Systeme pour la connexion dynamique en reseau a distance avec des dispositifs medicaux implantables
WO2001047600A1 (fr) * 1999-12-24 2001-07-05 Medtronic, Inc. Procede et systeme d'utilisation de donnees d'un dispositif medical implante, dans la mise au point de therapies
WO2001049368A1 (fr) * 1999-12-29 2001-07-12 Medtronic, Inc. Systeme de notification de rappel de composants pour dispositif medical
WO2001051123A1 (fr) * 2000-01-11 2001-07-19 Cedars-Sinai Medical Center Systeme implantable permanent et procede permettant de detecter, de diagnostiquer et de traiter l'insuffisance cardiaque congestive
WO2001080948A1 (fr) * 2000-04-21 2001-11-01 Medtronic, Inc. Systeme de collecte passive de donnees a partir d'un ensemble d'instruments medicaux et de dispositifs implantables
WO2001080731A1 (fr) * 2000-04-19 2001-11-01 Medtronic Inc Procede et appareil de communication avec des systemes de dispositifs medicaux
WO2001097907A3 (fr) * 2000-06-23 2002-06-06 Medtronic Inc Liaison sans fil rf compatible en reseau pour la gestion des donnees d'un dispositif medical
GB2375012B (en) * 2001-04-26 2004-12-01 Re Tech Electronics Ltd Biotelemetry monitoring systems
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DE19758393B4 (de) * 1997-12-23 2006-04-20 Biotronik Meß- und Therapiegeräte GmbH & Co. Ingenieurbüro Berlin Anordnung zur Patientenüberwachung
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EP1704893A1 (fr) * 2005-03-21 2006-09-27 Greatbatch-Sierra, Inc. Système de détection et d'identification radio fréquence (RFID) pour des dispositifs médicaux implantables
US7149587B2 (en) 2002-09-26 2006-12-12 Pacesetter, Inc. Cardiovascular anchoring device and method of deploying same
US7463930B2 (en) 2000-12-20 2008-12-09 Medtronic, Inc. Implantable medical device programmer module for use with existing clinical instrumentation
US7509169B2 (en) 2002-09-26 2009-03-24 Pacesetter, Inc. Implantable pressure transducer system optimized for anchoring and positioning
US7787958B2 (en) 2001-04-13 2010-08-31 Greatbatch Ltd. RFID detection and identification system for implantable medical lead systems
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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
US8761895B2 (en) 2008-03-20 2014-06-24 Greatbatch Ltd. RF activated AIMD telemetry transceiver

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EP0896828A3 (fr) * 1997-08-13 2000-01-12 SORIN BIOMEDICA S.p.A. Dispositif implantable de surveillance de patient
DE19758393B4 (de) * 1997-12-23 2006-04-20 Biotronik Meß- und Therapiegeräte GmbH & Co. Ingenieurbüro Berlin Anordnung zur Patientenüberwachung
WO2001043823A1 (fr) * 1999-12-17 2001-06-21 Medtronic, Inc. Surveillance, alarme, diagnostic et programmation virtuels a distance de systemes de dispositifs medicaux implantables
WO2001045793A1 (fr) 1999-12-21 2001-06-28 Medtronic, Inc. Systeme pour la connexion dynamique en reseau a distance avec des dispositifs medicaux implantables
WO2001047600A1 (fr) * 1999-12-24 2001-07-05 Medtronic, Inc. Procede et systeme d'utilisation de donnees d'un dispositif medical implante, dans la mise au point de therapies
WO2001049368A1 (fr) * 1999-12-29 2001-07-12 Medtronic, Inc. Systeme de notification de rappel de composants pour dispositif medical
WO2001051123A1 (fr) * 2000-01-11 2001-07-19 Cedars-Sinai Medical Center Systeme implantable permanent et procede permettant de detecter, de diagnostiquer et de traiter l'insuffisance cardiaque congestive
US7590449B2 (en) 2000-01-11 2009-09-15 Cedars-Sinai Medical Center Patient signaling method for treating cardiovascular disease
US6328699B1 (en) 2000-01-11 2001-12-11 Cedars-Sinai Medical Center Permanently implantable system and method for detecting, diagnosing and treating congestive heart failure
US7483743B2 (en) 2000-01-11 2009-01-27 Cedars-Sinai Medical Center System for detecting, diagnosing, and treating cardiovascular disease
US7137953B2 (en) 2000-01-11 2006-11-21 Cedars-Sinai Medical Center Implantable system and method for measuring left atrial pressure to detect, diagnose and treating congestive heart failure
US7115095B2 (en) 2000-01-11 2006-10-03 Cedars-Sinai Medical Center Systems and methods for detecting, diagnosing and treating congestive heart failure
US9055917B2 (en) 2000-01-11 2015-06-16 Cedars-Sinai Medical Center Method for detecting, diagnosing, and treating cardiovascular disease
US6970742B2 (en) 2000-01-11 2005-11-29 Savacor, Inc. Method for detecting, diagnosing, and treating cardiovascular disease
WO2001080731A1 (fr) * 2000-04-19 2001-11-01 Medtronic Inc Procede et appareil de communication avec des systemes de dispositifs medicaux
US6561975B1 (en) 2000-04-19 2003-05-13 Medtronic, Inc. Method and apparatus for communicating with medical device systems
WO2001080948A1 (fr) * 2000-04-21 2001-11-01 Medtronic, Inc. Systeme de collecte passive de donnees a partir d'un ensemble d'instruments medicaux et de dispositifs implantables
US6577901B2 (en) 2000-06-23 2003-06-10 Medtronic, Inc. Network compatible RF wireless link for medical device data management
WO2001097907A3 (fr) * 2000-06-23 2002-06-06 Medtronic Inc Liaison sans fil rf compatible en reseau pour la gestion des donnees d'un dispositif medical
US7463930B2 (en) 2000-12-20 2008-12-09 Medtronic, Inc. Implantable medical device programmer module for use with existing clinical instrumentation
US7787958B2 (en) 2001-04-13 2010-08-31 Greatbatch Ltd. RFID detection and identification system for implantable medical lead systems
GB2375012B (en) * 2001-04-26 2004-12-01 Re Tech Electronics Ltd Biotelemetry monitoring systems
US7060030B2 (en) 2002-01-08 2006-06-13 Cardiac Pacemakers, Inc. Two-hop telemetry interface for medical device
US7509169B2 (en) 2002-09-26 2009-03-24 Pacesetter, Inc. Implantable pressure transducer system optimized for anchoring and positioning
US9918677B2 (en) 2002-09-26 2018-03-20 Pacesetter, Inc. Implantable pressure transducer system optimized to correct environmental factors
US7149587B2 (en) 2002-09-26 2006-12-12 Pacesetter, Inc. Cardiovascular anchoring device and method of deploying same
US8303511B2 (en) 2002-09-26 2012-11-06 Pacesetter, Inc. Implantable pressure transducer system optimized for reduced thrombosis effect
US9060696B2 (en) 2002-09-26 2015-06-23 Pacesetter, Inc. Implantable pressure transducer system optimized to correct environmental factors
EP1704893A1 (fr) * 2005-03-21 2006-09-27 Greatbatch-Sierra, Inc. Système de détection et d'identification radio fréquence (RFID) pour des dispositifs médicaux implantables
US7916013B2 (en) 2005-03-21 2011-03-29 Greatbatch Ltd. RFID detection and identification system for implantable medical devices
US8326435B2 (en) 2005-03-21 2012-12-04 Greatbatch Ltd. RFID detection and identification system for implantable medical lead systems
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
US8248232B2 (en) 2006-01-25 2012-08-21 Greatbatch Ltd. Hermetically sealed RFID microelectronic chip connected to a biocompatible RFID antenna
US8761895B2 (en) 2008-03-20 2014-06-24 Greatbatch Ltd. RF activated AIMD telemetry transceiver
USRE45030E1 (en) 2009-09-24 2014-07-22 Greatbatch Ltd. Hermetically sealed RFID microelectronic chip connected to a biocompatible RFID antenna

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