CA2378044C - System and method of interrogating implanted passive resonant-circuit devices - Google Patents
System and method of interrogating implanted passive resonant-circuit devices Download PDFInfo
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- CA2378044C CA2378044C CA002378044A CA2378044A CA2378044C CA 2378044 C CA2378044 C CA 2378044C CA 002378044 A CA002378044 A CA 002378044A CA 2378044 A CA2378044 A CA 2378044A CA 2378044 C CA2378044 C CA 2378044C
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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
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/03—Detecting, measuring or recording fluid pressure within the body other than blood pressure, e.g. cerebral pressure; Measuring pressure in body tissues or organs
- A61B5/031—Intracranial pressure
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Abstract
A system and method for interrogating implanted passive resonant circuits is described. The resonant frequency is detected by transmitting a train of short pulses and then listening between the pulses for output of the resonant circuit. With proper spacing between the pulses, a vastly improved signal-to-noise ratio is obtained.
Description
02-07-2001 CA 02378044 2002-O1-17 US~~188L
SYSTEM AND METHOD OF INTERROGATING
IMPLANTED PASSIVE RESONANT-CIRCUIT DEVICES
s SPECIFICATION
BACKGROUND OF THE INVENTION
This invention relates generally to medical devices and more particularly to to systems for measuring intracranial pressure, and interrogating other implanted passive resonant circuits.
Numerous patents have been issued disclosing various means for monitoring intracranial pressure by means of an implanted, passive, resonant electronic circuit that is interrogated by an external device.
Zs U.S. Patent No. 3,943,915 (Severson) discloses an intracranial pressure monitoring device that incorporates a lumped-constant tuned circuit. The typical Q of such a circuit is on the order of 50. The Q value ("quality factor") basically corresponds to the width of the response curve in the frequency domain for a resonant circuit. The quantity Q can be defined as 2n x maximum energy stored in the resonant circuit 2 o divided by the total energy lost per period from the resonant circuit.
U.S. Patent No. 4,026,276 (Chubbuck) discloses an intracranial pressure monitoring device with a lumped-constant tuned circuit. The typical Q of such a circuit is on the order of 50.
U.S. Patent No. 4,114,606 (Seylar) discloses a monitoring device for 2'~:~ implanted resonant circuits. They are not able to even estimate the signal-to-noise ratio, but use a °grid-dip meter" approach, i.e.; the detector voltage "dips° whenever the interrogating circuit sweeps by the resonant frequency of the implanted resonant frequency circuit.
U.S. Patent No. 4,265,252 (Chubbuck) discloses an intracraniai pressure 3 o monitoring device with a lumped-constant tuned circuit.
U.S. Patent No. 4,354,506 (Sakaguchi) discloses an intracranial pressure monitoring device with a lumped-constant tuned circuit, and purposed using a "grid-dip meter" monitoring system.
U.S. Patent No. 5,873,840 (Neff) discloses an intracranial pressure 35 sensor with a microwave cavity resonator. The preferred embodiment discussed includes a reflected energy measurement approach.
AMENDED SHEET
However, all of these devices suffer from poor signal-to-noise ratios.
Thus, there remains a need for an implanted resonant circuit that provides for a response signal with good signal-to-noise ratio when interrogated.
OBJECTS OF THE INVENTION
s Accordingly, it is the object of this invention to provide a system and method for determining the resonant frequency of a circuit, lumped-constant or other, implanted in a person.
It is further the object of this invention to provide a system and method that can work over a wide range of frequencies, and uses commercially available 1 o components.
It is further the object of this invention to provide a system and method with a high signal-to-noise ratio, which allows it to work without direct contact with the patient.
It is further the object of this invention to provide a system and method 15 that exposes the patient to acceptable levels of irradiation, suitable for continuous monitoring.
It is still yet a further object of this invention to provide a system and method for whose performance is much less sensitive to path loss.
It is even still another object of this invention to provide a system and 2 o method for that it is completely insensitive to dispersion (frequency-dependent reflection, absorption, and transmission characteristics) of the tissue.
SUMMARY OF THE INVENTION
These and other objects of the instant invention are achieved by providing a system for monitoring the pressure within the cranium of a living being. The 25 system comprises: a resonant frequency circuit that is implanted within the cranium;
a remotely-located transmitter (e.g., a voltage-controlled YIG oscillator) and a remotely-located receiver coupled through alternation means (e.g., a pair of MMIC
switches) that operates the transmitter and receiver in alternation such that when the transmitter is transmitting an interrogation signal to the resonant frequency circuit, the 3 o remotely-located receiver is de-activated and when the receiver is listening to a response signal from the resonant frequency circuit the transmitter is de-activated; the interrogation signal comprises high frequency electromagnetic excitation waves (e.g., 3.8 - 3.82 Ghz) wherein one of the excitation waves causes the resonant frequency circuit to resonate at an altered resonance frequency corresponding to the pressure of the cranium; the remotely-located receiver detects the altered resonance frequency in the response signal; and a display, coupled to the remotely-located receiver, displays s the pressure of the cranium corresponding to the detected altered resonance frequency.
These and other objects of the instant invention are also achieved by providing a method for monitoring the pressure within the cranium of a living being.
The method comprises the steps of: implanting a resonant frequency circuit within the 1 o cranium; transmitting high frequency electromagnetic excitation waves (e.g., 3.8 - 3.82 Ghz) from a transmitter (e.g., a voltage-controlled YIG oscillator) to the resonant frequency circuit while precluding a receiver from receiving any response signal from the resonant frequency circuit during the transmitting and wherein one of the excitation waves causes the resonant frequency circuit to resonate at an altered resonance 1s frequency corresponding to the pressure of the cranium; precluding the transmitter from transmitting the high frequency electromagnetic waves while the receiver receives a response signal from the resonant frequency circuit; detecting the altered resonance frequency in the response signal by the receiver; and displaying the pressure of the cranium corresponding to the detected altered resonance frequency.
2 o DESCRIPTION OF THE DRAWINGS
Other objects and many of the attendant advantages of this invention will be readily appreciated as the same becomes better understood by reference to the following detailed description when considered in connection with the accompanying drawings wherein:
2 s Fig. 1 a block diagram of the present invention;
Fig. 2 is a timing diagram of the transmitter and receiver MMIC switches;
Fig. 3A is a circuit schematic of the timing circuit and the voltage sweeper/pressure display; and Fig. 3B is a circuit schematic of the receiver.
SYSTEM AND METHOD OF INTERROGATING
IMPLANTED PASSIVE RESONANT-CIRCUIT DEVICES
s SPECIFICATION
BACKGROUND OF THE INVENTION
This invention relates generally to medical devices and more particularly to to systems for measuring intracranial pressure, and interrogating other implanted passive resonant circuits.
Numerous patents have been issued disclosing various means for monitoring intracranial pressure by means of an implanted, passive, resonant electronic circuit that is interrogated by an external device.
Zs U.S. Patent No. 3,943,915 (Severson) discloses an intracranial pressure monitoring device that incorporates a lumped-constant tuned circuit. The typical Q of such a circuit is on the order of 50. The Q value ("quality factor") basically corresponds to the width of the response curve in the frequency domain for a resonant circuit. The quantity Q can be defined as 2n x maximum energy stored in the resonant circuit 2 o divided by the total energy lost per period from the resonant circuit.
U.S. Patent No. 4,026,276 (Chubbuck) discloses an intracranial pressure monitoring device with a lumped-constant tuned circuit. The typical Q of such a circuit is on the order of 50.
U.S. Patent No. 4,114,606 (Seylar) discloses a monitoring device for 2'~:~ implanted resonant circuits. They are not able to even estimate the signal-to-noise ratio, but use a °grid-dip meter" approach, i.e.; the detector voltage "dips° whenever the interrogating circuit sweeps by the resonant frequency of the implanted resonant frequency circuit.
U.S. Patent No. 4,265,252 (Chubbuck) discloses an intracraniai pressure 3 o monitoring device with a lumped-constant tuned circuit.
U.S. Patent No. 4,354,506 (Sakaguchi) discloses an intracranial pressure monitoring device with a lumped-constant tuned circuit, and purposed using a "grid-dip meter" monitoring system.
U.S. Patent No. 5,873,840 (Neff) discloses an intracranial pressure 35 sensor with a microwave cavity resonator. The preferred embodiment discussed includes a reflected energy measurement approach.
AMENDED SHEET
However, all of these devices suffer from poor signal-to-noise ratios.
Thus, there remains a need for an implanted resonant circuit that provides for a response signal with good signal-to-noise ratio when interrogated.
OBJECTS OF THE INVENTION
s Accordingly, it is the object of this invention to provide a system and method for determining the resonant frequency of a circuit, lumped-constant or other, implanted in a person.
It is further the object of this invention to provide a system and method that can work over a wide range of frequencies, and uses commercially available 1 o components.
It is further the object of this invention to provide a system and method with a high signal-to-noise ratio, which allows it to work without direct contact with the patient.
It is further the object of this invention to provide a system and method 15 that exposes the patient to acceptable levels of irradiation, suitable for continuous monitoring.
It is still yet a further object of this invention to provide a system and method for whose performance is much less sensitive to path loss.
It is even still another object of this invention to provide a system and 2 o method for that it is completely insensitive to dispersion (frequency-dependent reflection, absorption, and transmission characteristics) of the tissue.
SUMMARY OF THE INVENTION
These and other objects of the instant invention are achieved by providing a system for monitoring the pressure within the cranium of a living being. The 25 system comprises: a resonant frequency circuit that is implanted within the cranium;
a remotely-located transmitter (e.g., a voltage-controlled YIG oscillator) and a remotely-located receiver coupled through alternation means (e.g., a pair of MMIC
switches) that operates the transmitter and receiver in alternation such that when the transmitter is transmitting an interrogation signal to the resonant frequency circuit, the 3 o remotely-located receiver is de-activated and when the receiver is listening to a response signal from the resonant frequency circuit the transmitter is de-activated; the interrogation signal comprises high frequency electromagnetic excitation waves (e.g., 3.8 - 3.82 Ghz) wherein one of the excitation waves causes the resonant frequency circuit to resonate at an altered resonance frequency corresponding to the pressure of the cranium; the remotely-located receiver detects the altered resonance frequency in the response signal; and a display, coupled to the remotely-located receiver, displays s the pressure of the cranium corresponding to the detected altered resonance frequency.
These and other objects of the instant invention are also achieved by providing a method for monitoring the pressure within the cranium of a living being.
The method comprises the steps of: implanting a resonant frequency circuit within the 1 o cranium; transmitting high frequency electromagnetic excitation waves (e.g., 3.8 - 3.82 Ghz) from a transmitter (e.g., a voltage-controlled YIG oscillator) to the resonant frequency circuit while precluding a receiver from receiving any response signal from the resonant frequency circuit during the transmitting and wherein one of the excitation waves causes the resonant frequency circuit to resonate at an altered resonance 1s frequency corresponding to the pressure of the cranium; precluding the transmitter from transmitting the high frequency electromagnetic waves while the receiver receives a response signal from the resonant frequency circuit; detecting the altered resonance frequency in the response signal by the receiver; and displaying the pressure of the cranium corresponding to the detected altered resonance frequency.
2 o DESCRIPTION OF THE DRAWINGS
Other objects and many of the attendant advantages of this invention will be readily appreciated as the same becomes better understood by reference to the following detailed description when considered in connection with the accompanying drawings wherein:
2 s Fig. 1 a block diagram of the present invention;
Fig. 2 is a timing diagram of the transmitter and receiver MMIC switches;
Fig. 3A is a circuit schematic of the timing circuit and the voltage sweeper/pressure display; and Fig. 3B is a circuit schematic of the receiver.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT
The present invention is an improvement of the intercranial pressure monitoring system of U.S. Patent No.
The present invention is an improvement of the intercranial pressure monitoring system of U.S. Patent No.
5,873,840 (Neff).
Referring now in detail to the various figures of the drawing wherein like reference characters refer to like parts, there is shown at 320 in Fig. 1, a system for interrogating an implanted resonant circuit 322 (e. g., the cavity resonator unit 22 of U.S. Patent No. 5,873,840 (Neff)) that is embedded below the scalp of a patient (not shown) . The system 320 comprises a transmitter 332, a receiver 334, a transmit MMIC(monolithic microwave integrated circuit) switch 380, a receive MMIC switch 382, a timing circuit 384 and a voltage sweeper/pressure display (hereinafter referred to as VSPD) 386. The probe 324 comprises a stripline transmit antenna 388 and a stripline receiver antenna 390. When activated, as discussed below, the transmitter MMIC switch 380 permits the transmitter 332 to transmit a signal 333 through the stripline transmit antenna 338; similarly, when the receiver MMIC switch 382 is activated, the receiver MMIC switch 382 permits the receiver 334 to receive a return signal 335 from the implanted resonant frequency circuit 322.
It should be understood that the resonance frequency of the implanted resonant frequency circuit 322 is changed as a function of the patient's cranium pressure. See U.S.Patent No.
5,873,840 (Neff). Thus, depending upon the cranium pressure, the resonance frequency will change. Furthermore, embedded in the return signal 335 is a peak value signal that corresponds to the resonant frequency. As a result, the phrase "altered resonant wave".
The transmitter 332 (e.g., a voltage-controlled YIG
(Yitrium iron garnet) oscillator such as the Micro Lambda MLPB-0406 or MLPB-0204) and the receiver 334 are swept in frequency over the range of possible resonant frequencies of the implanted resonant circuit 322. The output signal 333 of the transmitter 332 and the return signal 335 to the receiver 334 are switched synchronously using monolithic GaAs FET MMIC RF
switches 380 and 382, respectively, (e. g., Alpha Industries AS018R1-00). This synchronous switching effectively disconnects the transmitter 332 when the receiver 334 is on, and effectively disconnects the receiver 334 while the transmitter 332 is on (see Fig. 2). The switches 380/382 are keyed from an 02-07-2001 US001882~
oscillator/counter/demultiplexing timing circuit 384 that compensates for the nanosecond switching time of the MMIC switches 380 and 382. The connection between the transmitter 332 and the receiver 334 is loosely coupled (i.e., the s transmitter 332lreceiver 334 and the implanted resonant frequency circuit are displaced from each other over a finite distance, in addition to the scalp of the patient acting as a lossy dielectric) to the implanted resonant frequency circuit 322.
In particular, the transmitter 332 is slowly swept across the resonant frequency of the implanted resonant frequency circuit 322. The timing circuit 1 o alternatively switches the receiver 334 and the transmitter 332 in and out of the system 320. During each pulse from the transmitter 332, the receiver 334 is "off" , i.e., i disconnected at >80dB attenuation by the receiver MMIC switch 382. Similarly, during each period when the receiver 334 is "listening," the transmitter 332 is "off." With the transmitter 332 off, the receiver 334 amplifies and detects only the decay of the energy stored in the implanted resonant frequency circuit 322. This energy decay is defined as:
a Q
where F = frequency in Hertz; and . Q = Q factor of implanted resonant frequency circuit 322.
Typical operating values of the system 320 are as follows:
Operating frequency of transmitter 332: 3.8-3.82 Ghz ~Q of implanted resonant frequency circuit 322: 8000 Keying waveform for transmitter 332: 10 ns pulses spaced 20 ns Keying waveform for receiver 334: 10 ns pulses spaced 20 ns, synchronized 15 ns behind transmitter 3 0 Total path loss (including coupling to implanted resonant frequency in tissue): 70 dB
Minimum discernable signal of receiver: -110 dBm AMENDED SHEET
Referring now in detail to the various figures of the drawing wherein like reference characters refer to like parts, there is shown at 320 in Fig. 1, a system for interrogating an implanted resonant circuit 322 (e. g., the cavity resonator unit 22 of U.S. Patent No. 5,873,840 (Neff)) that is embedded below the scalp of a patient (not shown) . The system 320 comprises a transmitter 332, a receiver 334, a transmit MMIC(monolithic microwave integrated circuit) switch 380, a receive MMIC switch 382, a timing circuit 384 and a voltage sweeper/pressure display (hereinafter referred to as VSPD) 386. The probe 324 comprises a stripline transmit antenna 388 and a stripline receiver antenna 390. When activated, as discussed below, the transmitter MMIC switch 380 permits the transmitter 332 to transmit a signal 333 through the stripline transmit antenna 338; similarly, when the receiver MMIC switch 382 is activated, the receiver MMIC switch 382 permits the receiver 334 to receive a return signal 335 from the implanted resonant frequency circuit 322.
It should be understood that the resonance frequency of the implanted resonant frequency circuit 322 is changed as a function of the patient's cranium pressure. See U.S.Patent No.
5,873,840 (Neff). Thus, depending upon the cranium pressure, the resonance frequency will change. Furthermore, embedded in the return signal 335 is a peak value signal that corresponds to the resonant frequency. As a result, the phrase "altered resonant wave".
The transmitter 332 (e.g., a voltage-controlled YIG
(Yitrium iron garnet) oscillator such as the Micro Lambda MLPB-0406 or MLPB-0204) and the receiver 334 are swept in frequency over the range of possible resonant frequencies of the implanted resonant circuit 322. The output signal 333 of the transmitter 332 and the return signal 335 to the receiver 334 are switched synchronously using monolithic GaAs FET MMIC RF
switches 380 and 382, respectively, (e. g., Alpha Industries AS018R1-00). This synchronous switching effectively disconnects the transmitter 332 when the receiver 334 is on, and effectively disconnects the receiver 334 while the transmitter 332 is on (see Fig. 2). The switches 380/382 are keyed from an 02-07-2001 US001882~
oscillator/counter/demultiplexing timing circuit 384 that compensates for the nanosecond switching time of the MMIC switches 380 and 382. The connection between the transmitter 332 and the receiver 334 is loosely coupled (i.e., the s transmitter 332lreceiver 334 and the implanted resonant frequency circuit are displaced from each other over a finite distance, in addition to the scalp of the patient acting as a lossy dielectric) to the implanted resonant frequency circuit 322.
In particular, the transmitter 332 is slowly swept across the resonant frequency of the implanted resonant frequency circuit 322. The timing circuit 1 o alternatively switches the receiver 334 and the transmitter 332 in and out of the system 320. During each pulse from the transmitter 332, the receiver 334 is "off" , i.e., i disconnected at >80dB attenuation by the receiver MMIC switch 382. Similarly, during each period when the receiver 334 is "listening," the transmitter 332 is "off." With the transmitter 332 off, the receiver 334 amplifies and detects only the decay of the energy stored in the implanted resonant frequency circuit 322. This energy decay is defined as:
a Q
where F = frequency in Hertz; and . Q = Q factor of implanted resonant frequency circuit 322.
Typical operating values of the system 320 are as follows:
Operating frequency of transmitter 332: 3.8-3.82 Ghz ~Q of implanted resonant frequency circuit 322: 8000 Keying waveform for transmitter 332: 10 ns pulses spaced 20 ns Keying waveform for receiver 334: 10 ns pulses spaced 20 ns, synchronized 15 ns behind transmitter 3 0 Total path loss (including coupling to implanted resonant frequency in tissue): 70 dB
Minimum discernable signal of receiver: -110 dBm AMENDED SHEET
Transmitter 332 output: + 10 dBm.
With these values, the implanted resonant frequency circuit 322 decay is approximated as:
(10 dBm - 70 dB) ~ a Q
_, - -60 dBm ~ e2.~~~ ( with t in nanoseconds) In other words, it will take approximately 2.1 y~sec for the decay to reach 36.8% (i.e., at ~ o t = 2.1 x 10'~ sec, the decay is given by e'' = 0.368) of its initial value (-60 dBm). This means thatwith the transmitter 332 clocked at 100 MHz (10ns), very little decay occurs during the next 10ns when the receiver 334 is "connected." Therefore, the received energy at the start of the receiver MMIC switch 382 °on-time" is -60 dBm, well above the minimum discernable signal (-110 dBm) of the receiver 334. During the "off time"
s5 of the receiver 334, the leakage input from the transmitter 332 is:
-70 dBm - (coupling between transmitter antenna 388 and receiver antenna 390).
Conservatively estimating the coupling of the two parallel stripline antennas is at -20 dB, the final value of -90 dBm is 30 dB below the desired signal.
The result of the system 320 and method is that rather than looking for 20 a small change in a large signal, as the grid-dip method requires, the "pulse-detector"
operation of the system 3201method only provides an output when at the resonant frequency of the circuit 322. In particular, as will be discussed later, the system 320/method detects the peak value in the return signal 335 which corresponds to the resonant frequency of the implanted resonant frequency circuit 322. The pressure in 2 5 the patient's cranium that corresponds to that frequency is then displayed to the operator via a display DIS (Fig. 3A).
In comparison, if the °grid-dip" approach, (i.e., without the alternate transmitterlreceiver switching) were used, and applying the operating values listed above, the input to the receiver from the transmitter is -10 dBm (in a classic, grid-dip 3 o meter the receiver and transmitter are the same circuit, but this does not change the AMENDED SHEET
With these values, the implanted resonant frequency circuit 322 decay is approximated as:
(10 dBm - 70 dB) ~ a Q
_, - -60 dBm ~ e2.~~~ ( with t in nanoseconds) In other words, it will take approximately 2.1 y~sec for the decay to reach 36.8% (i.e., at ~ o t = 2.1 x 10'~ sec, the decay is given by e'' = 0.368) of its initial value (-60 dBm). This means thatwith the transmitter 332 clocked at 100 MHz (10ns), very little decay occurs during the next 10ns when the receiver 334 is "connected." Therefore, the received energy at the start of the receiver MMIC switch 382 °on-time" is -60 dBm, well above the minimum discernable signal (-110 dBm) of the receiver 334. During the "off time"
s5 of the receiver 334, the leakage input from the transmitter 332 is:
-70 dBm - (coupling between transmitter antenna 388 and receiver antenna 390).
Conservatively estimating the coupling of the two parallel stripline antennas is at -20 dB, the final value of -90 dBm is 30 dB below the desired signal.
The result of the system 320 and method is that rather than looking for 20 a small change in a large signal, as the grid-dip method requires, the "pulse-detector"
operation of the system 3201method only provides an output when at the resonant frequency of the circuit 322. In particular, as will be discussed later, the system 320/method detects the peak value in the return signal 335 which corresponds to the resonant frequency of the implanted resonant frequency circuit 322. The pressure in 2 5 the patient's cranium that corresponds to that frequency is then displayed to the operator via a display DIS (Fig. 3A).
In comparison, if the °grid-dip" approach, (i.e., without the alternate transmitterlreceiver switching) were used, and applying the operating values listed above, the input to the receiver from the transmitter is -10 dBm (in a classic, grid-dip 3 o meter the receiver and transmitter are the same circuit, but this does not change the AMENDED SHEET
physics). The input from the implanted resonant frequency circuit 322 is -60 dBm, (and even smaller when off-resonance). Thus, the receiver is attempting to detect a change that is 50 dB smaller than the signal itself, or .001 % of the signal strength.
Although it is possible to do this in the laboratory, routine clinical use of such a device is not realistic.
Figs. 3A-3B show an exemplary implementation of the timing circuit 384, the VSPD 386 and the receiver 334.
The timing circuit 384 (Fig. 3A) comprises a 100 MHz crystal oscillator (e.g., JDR Microdevices #OSC100.0 oscillator) whose output is fed to inverters 11 and 12 (e.g., Fairchild Semiconductor 74VHC04 Hex inverter). The output of inverter 11 is fed into the receiver MMIC switch 382. The output of inverter 12 is fed to the and to another inverter 13 (e.g., Fairchild Semiconductor 74VHC04 Hex inverter). The output of the inverter 13 is fed to the transmitter MMIC switch 380.
The VSPD 386 receives its input from the inverter 13. A pair of 4-bit binary counters BC1 and BC2 (e.g., Fairchild Semiconductor 74VHC93) are incremented by the 100 MHz crystal oscillator signal, from inverter 12, in 256 (28) increments. The digital incrementation is converted by an 8-bit digital/analog converter (e.g., JDR #DAC-0800) and resistor/capacitor network RC into an analog ramp voltage signal that is used to sweep the oscillator of the transmitter 332 through the pertinent 2 o frequency range, e.g., 3.8-3.82 GHz.
The ramp voltage signal (see Fig. 3A) exhibits linearly-increasing portions and substantially-vertical re-trace portions. The digital incrementation is simultaneously fed to a clocked frequency display DIS which converts the frequency into the corresponding cranial pressure in the range from 0 - 30 Torr (mmHg).
When the resonant frequency of the implanted circuit 322 is detected by the receiver 334, a latch input signal LI from the receiver 334 (to be discussed below) is transmitted to the display DIS which latches the frequency value supplied from the binary counters BC1/BC2 and the display DIS then displays the pressure corresponding to that latched frequency value.
3 o The receiver 334 (Fig. 3B) comprises three MMIC amplifiers U1, U2 and U3 (e.g., ERA-3 MMIC amplifiers) connected in series through 1 pF coupling capacitors.
Input to amplifier U1 is controlled by the receiver MMIC switch 382. Thus, when the - 02-07-2001 US001$$2~
Although it is possible to do this in the laboratory, routine clinical use of such a device is not realistic.
Figs. 3A-3B show an exemplary implementation of the timing circuit 384, the VSPD 386 and the receiver 334.
The timing circuit 384 (Fig. 3A) comprises a 100 MHz crystal oscillator (e.g., JDR Microdevices #OSC100.0 oscillator) whose output is fed to inverters 11 and 12 (e.g., Fairchild Semiconductor 74VHC04 Hex inverter). The output of inverter 11 is fed into the receiver MMIC switch 382. The output of inverter 12 is fed to the and to another inverter 13 (e.g., Fairchild Semiconductor 74VHC04 Hex inverter). The output of the inverter 13 is fed to the transmitter MMIC switch 380.
The VSPD 386 receives its input from the inverter 13. A pair of 4-bit binary counters BC1 and BC2 (e.g., Fairchild Semiconductor 74VHC93) are incremented by the 100 MHz crystal oscillator signal, from inverter 12, in 256 (28) increments. The digital incrementation is converted by an 8-bit digital/analog converter (e.g., JDR #DAC-0800) and resistor/capacitor network RC into an analog ramp voltage signal that is used to sweep the oscillator of the transmitter 332 through the pertinent 2 o frequency range, e.g., 3.8-3.82 GHz.
The ramp voltage signal (see Fig. 3A) exhibits linearly-increasing portions and substantially-vertical re-trace portions. The digital incrementation is simultaneously fed to a clocked frequency display DIS which converts the frequency into the corresponding cranial pressure in the range from 0 - 30 Torr (mmHg).
When the resonant frequency of the implanted circuit 322 is detected by the receiver 334, a latch input signal LI from the receiver 334 (to be discussed below) is transmitted to the display DIS which latches the frequency value supplied from the binary counters BC1/BC2 and the display DIS then displays the pressure corresponding to that latched frequency value.
3 o The receiver 334 (Fig. 3B) comprises three MMIC amplifiers U1, U2 and U3 (e.g., ERA-3 MMIC amplifiers) connected in series through 1 pF coupling capacitors.
Input to amplifier U1 is controlled by the receiver MMIC switch 382. Thus, when the - 02-07-2001 US001$$2~
receiver MMIC switch 382 is active, the received signal 335 is passed to the input of amplifier U1. The output of amplifier U3 is fed through a peak detector formed by a half-wave rectifier, a DC amplifier U4 and a differentiator circuit U5. The half wave rectifier comprises a diode D1 (e.g., Hewlett-Packard 5082-2835 diode) coupled to ground through a capacitor. The output of the half wave rectifier is fed to a DC
amplifier U4 (e.g., LM301 op amp) which in tum is fed to a differentiator circuit U5 (e.g., LM301 op amp).
The differentiator circuit U5 provides a zero output under two conditions:
i o (1 ) when the received signal 335 is at the resonant frequency of the implanted resonant frequency circuit 322 (i.e., at the peaks of the return signal 335);
and (2) when the ramp voltage, generated by the VSPD 386, is re-tracing, i.e., the vertical portion of the ramp is occurring. In order for the system 320 to operate properly, it is necessary to distinguish between these two conditions such that the display DIS only displays under condition (1 ) and not under condition (2). To that end, the output of the differentiator circuit U5 is fed as one input to a receiver NAND gate U6. The other input to the receiver NAND gate U6 is a cany out (sync) signal from binary counter BC2 that corresponds to the re-trace portion of the ramp voltage. Thus, the output of the NAND gate U6 is asserted (i.e., permits latching to the display DIS) only when the 2 o differentiator circuit U5 output is zero (which corresponds to a peak in the received signal 335 which corresponds to the received signal 335 being at the resonant frequency) and the ramp voltage is not experiencing a re-trace.
A further advantage of this system 320 and method is that the performance is much less sensitive to path loss. In the exemplary embodiment 2 s discussed above the receiver 334 could easily be placed a small (line-of sight) distance from the patient A further advantage of this system and method is that it.is completely insensitive to dispersion (frequency-dependent reflection, absorption, and transmission characteristics) of the tissue. Only the implanted resonant frequency circuit 3 o provides a signal during the time the receiver 334 is "on.°
Without further elaboration, the foregoing will so fully illustrate my invention that others may, by applying current or future knowledge, readily adopt the same for use under various conditions of service.
AMENDED SHEET
amplifier U4 (e.g., LM301 op amp) which in tum is fed to a differentiator circuit U5 (e.g., LM301 op amp).
The differentiator circuit U5 provides a zero output under two conditions:
i o (1 ) when the received signal 335 is at the resonant frequency of the implanted resonant frequency circuit 322 (i.e., at the peaks of the return signal 335);
and (2) when the ramp voltage, generated by the VSPD 386, is re-tracing, i.e., the vertical portion of the ramp is occurring. In order for the system 320 to operate properly, it is necessary to distinguish between these two conditions such that the display DIS only displays under condition (1 ) and not under condition (2). To that end, the output of the differentiator circuit U5 is fed as one input to a receiver NAND gate U6. The other input to the receiver NAND gate U6 is a cany out (sync) signal from binary counter BC2 that corresponds to the re-trace portion of the ramp voltage. Thus, the output of the NAND gate U6 is asserted (i.e., permits latching to the display DIS) only when the 2 o differentiator circuit U5 output is zero (which corresponds to a peak in the received signal 335 which corresponds to the received signal 335 being at the resonant frequency) and the ramp voltage is not experiencing a re-trace.
A further advantage of this system 320 and method is that the performance is much less sensitive to path loss. In the exemplary embodiment 2 s discussed above the receiver 334 could easily be placed a small (line-of sight) distance from the patient A further advantage of this system and method is that it.is completely insensitive to dispersion (frequency-dependent reflection, absorption, and transmission characteristics) of the tissue. Only the implanted resonant frequency circuit 3 o provides a signal during the time the receiver 334 is "on.°
Without further elaboration, the foregoing will so fully illustrate my invention that others may, by applying current or future knowledge, readily adopt the same for use under various conditions of service.
AMENDED SHEET
Claims (20)
1. A system for monitoring the pressure within the cranium of a living being, said system comprising: a resonant frequency circuit that is implanted within the cranium; a remotely-located transmitter and a remotely-located receiver coupled through alternation means that operates said transmitter and receiver in alternation such that when said transmitter is transmitting an interrogation signal to said resonant frequency circuit said remotely-located receiver is de-activated and when said receiver is listening to a response signal from said resonant frequency circuit said transmitter is de-activated;
said interrogation signal comprising high frequency electromagnetic excitation waves wherein one of said excitation waves causes said resonant frequency circuit to resonate at an altered resonance frequency corresponding to the pressure of the cranium; said remotely-located receiver detecting said altered resonance frequency in said response signal; and a display, coupled to said remotely-located receiver, for displaying the pressure of the cranium corresponding to said detected altered resonance frequency.
said interrogation signal comprising high frequency electromagnetic excitation waves wherein one of said excitation waves causes said resonant frequency circuit to resonate at an altered resonance frequency corresponding to the pressure of the cranium; said remotely-located receiver detecting said altered resonance frequency in said response signal; and a display, coupled to said remotely-located receiver, for displaying the pressure of the cranium corresponding to said detected altered resonance frequency.
2. The system of Claim 1 wherein said alternation. means comprises: a timing circuit; a first switch coupled between said timing circuit and said remotely-located transmitter, said first switch having a first closed state that activates said transmitter and a first open state that de-activates said transmitter; a second switch coupled between said timing circuit and said remotely-located receiver, said second switch having a second closed state that activates said receiver and a second open state for de-activating said receiver; and said timing circuit closing said first switch in said first closed state while opening said second switch in said second open state and then opening said first switch in said first open state while closing said second switch in said second closed state.
3. The system of Claim 2 wherein said first closed state is approximately nanoseconds and said first open state is approximately 20 nanoseconds.
4. The system of Claim 2 wherein said second closed state is approximately 10 nanoseconds and said second open state is approximately 20 nanonseconds.
5. The system of Claim 3 wherein said first switch is a monolithic microwave integrated circuit.
6. The system of Claim 4 wherein said second switch is a monolithic microwave integrated circuit.
7. The system of Claim 1 wherein said transmitter comprises a voltagecontrolled oscillator (VCO) and wherein said system further comprises a voltage sweeper, said voltage sweeper controlling said VCO to generate said high frequency electromagnetic excitation waves.
8. The system of Claim 1 wherein said high frequency electromagnetic excitation waves are in the range of 3.8 - 3.82 GHz.
9. The system of Claim 7 wherein said high frequency electromagnetic excitation waves are in the range of 3.8 - 3.82 GHz.
10. The system of Claim 7 wherein said receiver comprises a peak detector for detecting said altered resonant frequency in said response signal.
11. The system of Claim 10 wherein said peak detector comprises a halfwave rectifier, a direct current (DC) amplifier and a differentiator coupled together in series.
12. The system of Claim 11 wherein said voltage sweeper generates a ramp voltage for controlling said VCO, said ramp voltage comprising linearly increasing portions and substantially vertical re-trace portions.
13. The system of Claim 12 wherein said receiver further comprises logic means having a first input coupled to the output of said differentiator and a second input coupled to said voltage sweeper, said logic means having an output coupled to said display and wherein said logic means decouples said receiver from said display during said re-trace portions of said ramp voltage while permitting said display to display the pressure of the cranium when said altered resonance frequency is detected by said receiver.
14. A method for monitoring the pressure within the cranium of a living being, a resonant frequency circuit having been implanted within the cranium of said living being comprising the steps of: transmitting high frequency electromagnetic excitation waves from a transmitter to said resonant frequency circuit while precluding a receiver from receiving any response signal from said resonant frequency circuit during said transmitting and wherein one of said excitation waves causes said resonant frequency circuit to resonate at an altered resonance frequency corresponding to the pressure of the cranium; precluding said transmitter from transmitting said high frequency electromagnetic waves while said receiver receives a response signal from said resonant frequency circuit; detecting said altered resonance frequency in said response signal by said receiver; and displaying the pressure of the cranium corresponding to said detected altered resonance frequency.
15. The method of Claim 14 wherein said step of transmitting high frequency electromagnetic excitation waves from a transmitter to said resonant frequency circuit while precluding a receiver from receiving any response signal comprises de-activating said receiver for approximately 20 nanoseconds while activating said transmitter for approximately 10 nanoseconds.
16. The method of Claim 15 wherein said step of precluding said transmitter from transmitting said high frequency electromagnetic waves while said receiver receives a response signal comprises de-activating said transmitter for approximately 20 nanoseconds while activating said receiver for approximately 10 nanoseconds.
17. The method of Claim 14 wherein said step of transmitting high frequency electromagnetic excitation waves comprises sweeping said transmitter through the frequency range of 3.8 -3.82 Ghz.
18. The method of Claim 17 wherein said step of sweeping said transmitter comprises using a ramp voltage control signal to sweep said transmitter, said ramp voltage control signal comprising linearly-increasing portions and substantially-vertical re-trace portions.
19. The method of Claim 14 wherein said step of detecting said altered resonance frequency in said response signal comprises detecting the peak value in said response signal.
20. The method of Claim 18 further comprising the step of decoupling said receiver from said display during said re-trace portions of said ramp voltage control signal.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US09/354,385 US6165135A (en) | 1999-07-14 | 1999-07-14 | System and method of interrogating implanted passive resonant-circuit devices |
| US09/354,385 | 1999-07-14 | ||
| PCT/US2000/018824 WO2001005302A1 (en) | 1999-07-14 | 2000-07-11 | System and method of interrogating implanted passive resonant-circuit devices |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2378044A1 CA2378044A1 (en) | 2001-01-25 |
| CA2378044C true CA2378044C (en) | 2006-05-02 |
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|---|---|---|---|
| CA002378044A Expired - Fee Related CA2378044C (en) | 1999-07-14 | 2000-07-11 | System and method of interrogating implanted passive resonant-circuit devices |
Country Status (7)
| Country | Link |
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| US (1) | US6165135A (en) |
| EP (1) | EP1202666B1 (en) |
| AT (1) | ATE287238T1 (en) |
| AU (1) | AU772092B2 (en) |
| CA (1) | CA2378044C (en) |
| DE (1) | DE60017571T2 (en) |
| WO (1) | WO2001005302A1 (en) |
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1999
- 1999-07-14 US US09/354,385 patent/US6165135A/en not_active Expired - Fee Related
-
2000
- 2000-07-11 DE DE60017571T patent/DE60017571T2/en not_active Expired - Fee Related
- 2000-07-11 AU AU59266/00A patent/AU772092B2/en not_active Ceased
- 2000-07-11 WO PCT/US2000/018824 patent/WO2001005302A1/en active IP Right Grant
- 2000-07-11 AT AT00945299T patent/ATE287238T1/en not_active IP Right Cessation
- 2000-07-11 EP EP00945299A patent/EP1202666B1/en not_active Expired - Lifetime
- 2000-07-11 CA CA002378044A patent/CA2378044C/en not_active Expired - Fee Related
Also Published As
| Publication number | Publication date |
|---|---|
| WO2001005302A1 (en) | 2001-01-25 |
| DE60017571D1 (en) | 2005-02-24 |
| ATE287238T1 (en) | 2005-02-15 |
| CA2378044A1 (en) | 2001-01-25 |
| AU772092B2 (en) | 2004-04-08 |
| EP1202666A1 (en) | 2002-05-08 |
| US6165135A (en) | 2000-12-26 |
| EP1202666B1 (en) | 2005-01-19 |
| AU5926600A (en) | 2001-02-05 |
| DE60017571T2 (en) | 2006-03-30 |
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