SYSTEMS AND METHODS FOR WIRELESS TRANSMISSION OF BIOPOTENTIALS

Abstract

The invention relates to wireless biotelemetry of low level bioelectric and biosensor signals by directly modulating the backscatter of a resonant circuit. Low level electrical analog or digital signals are directly applied to a resonant circuit containing a voltage-variable capacitor such as a varactor diode, that proportionally shifts the resonant frequency and so amplitude of radiofrequency backscatter in a way that represents analog bioelectric or biosensor waveform data. By strongly driving the resonant circuit with a radiofrequency source, a voltage variable capacitance can be caused to amplify the bio-signal level by a parametric process and so provide sufficient sensitivity to telemeter for low millivolt and microvolt level signals without additional amplification. A feature of the device is its simplicity and that it accomplishes both modulation and preamplification of low level sensor signals by the same variable capacitance circuit which reduces the device size and power consumption.

Claims

1. An apparatus comprising: an electronic circuit configured to provide an inductance and a variable capacitance, wherein: the electronic circuit is configured to receive an excitation signal and an analog sensor signal; the electronic circuit has a resonant frequency that varies in response to a biosignal; the electronic circuit is configured to transmit a response signal when the electronic circuit receives the excitation signal and the biosignal; and a characteristic of the analog signal can be determined by measuring the response signal.

2. The apparatus of claim 1, wherein the biosignal is generated by a sensor selected from the group consisting of: a chemical, biochemical, magnetic, electromagnetic, physiological, and mechanical sensor.

3. The apparatus of claim 1, wherein the electronic circuit is configured to transmit the response signal wirelessly.

4. The apparatus of claim 1, wherein the characteristic of the analog signal is an amplitude of the analog signal.

5. The apparatus of claim 1, wherein the characteristic of the analog signal is a frequency of the analog signal.

6. The apparatus of claim 1, wherein the biosignal is generated by a biopotential.

7. The apparatus of claim 1, wherein the excitation signal is a radio frequency signal.

8. The apparatus of claim 1, wherein the excitation signal is a digital logic signal.

9. The apparatus of claim 1, wherein the electronic circuit further comprises an isolating resistor.

10. The apparatus of claim 1, wherein the electronic circuit is configured to receive the biosignal in vivo.

11. The apparatus of claim 10, wherein the electronic circuit is configured to be implanted sub-cutaneously in a test subject.

12. The apparatus of claim 11, wherein the electronic circuit is configured to be inserted with a needle into the test subject.

13. The apparatus of claim 11, wherein the electronic circuit is configured to pass through the lumen of a 1 millimeter syringe needle.

14. The apparatus of claim 10, wherein the electronic circuit is configured to be placed on the skin surface of a test subject.

15. The apparatus of claim 1, wherein the electronic circuit comprises a pair of varactor diodes coupled back-to-back to form an equivalent series capacitance.

16. The apparatus of claim 1, further comprising a remote exciter configured to emit the excitation signal at a frequency equivalent to the resonant frequency of the electronic circuit when an analog sensor signal is not being applied to the electronic circuit.

17. The apparatus of claim 1, wherein the excitation signal has a frequency between 30 MHz and 10 GHz.

18. The apparatus of claim 1, wherein the excitation signal has a frequency between 100 MHz and 3 GHz.

19. The apparatus of claim 1, wherein the excitation signal induces a voltage between 0.5 and 5.0 volts in the electronic circuit.

20. A method of measuring a biocharacteristic, the method comprising: providing an electronic circuit configured to measure a biopotential; providing an excitation signal to the electronic circuit; generating a biosignal with the biopotential and transmitting the biosignal to the electronic circuit; transmitting a response signal from the electronic circuit; and measuring the response signal to determine a characteristic of the biosignal.

21. The method of claim 20, wherein electronic circuit comprises a resonant frequency that is variable.

22. The method of claim 20, wherein the electronic circuit is configured to provide an inductance and a variable capacitance.

23. The method of claim 20, wherein electronic circuit comprises a base resonant frequency when a biosignal is not transmitted to the electronic circuit, and wherein the excitation signal is provided at the base resonant frequency.

24. The method of claim 20, wherein the biosignal is generated by a sensor selected from the group consisting of: a chemical, biochemical, magnetic, electromagnetic, physiological, and mechanical sensor.

25. The method of claim 20, wherein the characteristic of the biosignal is an amplitude of the biosignal.

26. The method of claim 20, wherein the characteristic of the biosignal is a frequency of the biosignal.

27. The method of claim 20, wherein the electronic circuit transmits the response signal wirelessly.

28. The method of claim 20, wherein the excitation signal is a radio frequency signal.

29. The method of claim 20, wherein the electronic circuit further comprises an isolating resistor.

30. The method of claim 20, wherein the electronic circuit receives the biosignal in vivo.

31. The method of claim 30, further comprising implanting the electronic circuit sub-cutaneously in a test subject.

32. The method of claim 31, further comprising implanting the electronic circuit in a test subject with a needle.

33. The method of claim 32, wherein the needle is a hollow needle.

34. The method of claim 31, wherein the electronic circuit is configured to pass through the lumen of a 1 millimeter syringe needle.

35. The method of claim 30, further comprising placing the electronic circuit on the skin surface of a test subject.

36. The method of claim 20, wherein the electronic circuit comprises a pair of varactor diodes coupled back-to-back to form an equivalent series capacitance.

37. The method of claim 20, further comprising using a remote exciter to emit the excitation signal at a frequency equivalent to the resonant frequency of the electronic circuit when an analog sensor signal is not being applied to the electronic circuit.

38. The method of claim 20, wherein the excitation signal has a frequency between 30 MHz and 10 GHz.

39. The method of claim 20, wherein the excitation signal has a frequency between 100 MHz and 3 GHz.

40. The method of claim 20, wherein the excitation signal induces a voltage between 0.5 and 5.0 volts in the electronic circuit.

41. An apparatus of electronic components constituting a device such that a voltage variable capacitive reactance is coupled to an inductance forming a resonant circuit, wherein low level analog electrical potentials from high impedance bioelectrical or biosensor sources applied to this circuit will vary the said capacitive reactance and so change the resonance of said circuit in proportion to the amplitude of the analog waveform envelope.

42. The device of claim 41, wherein the capacitive reactance is provided by at least one electronic component.

43. The device of claim 42, wherein the electronic component is a varactor diode.

44. The device of claim 41, wherein the capacitive reactance is provided by p-n junction capacitance.

45. The device of claim 41, further defined as comprising a remote radio exciter tuned to the resonant frequency of the system of components such that sufficient signal is induced in the said inductance that the assembly will detectably backscatter the radio exciter signal as well as generate remotely detectable radio harmonics of said radio exciter.

46. The device of claim 45, further defined as comprising a radio receiver that detects and demodulates the backscattered signals, the demodulation process following those techniques, wherein such methods may include direct conversion demodulation, AM, FM, or phase demodulation so as to reproduce the original modulation signal.

47. A method of using the device of claim 45, wherein the voltage variable capacitive reactance is electrically driven by an applied radio exciter signal known as a pump signal, of sufficient amplitude such that a device having time varying capacitance reactance in combination with the inductance forming a resonant circuit results in a parametric amplification of the electrical signal modulation according to principles of parametric amplification, the amplification process then substantially improving the sensitivity of the device to modulating signals.

48. A method of generating a bias voltage needed for the proper electrical operating point of the variable capacitance by a method of summing the bioelectrical or biosensor input signal with an electrical offset potential, wherein the offset potential may be generated by a small conventional on-device battery generated by dissimilar metals constituting the two biopotential electrodes used to detect the bioelectrical signal, the said bias voltage naturally resulting from the use of electrode metals having dissimilar half-cell potentials.

49. The method of claim 48, wherein the device is implanted within the human body and connected to biopotential electrodes to telemeter bioelectrical signals originating from the heart, brain, and nervous system.

50. The method of claim 48, wherein the device is connected to a biochemical or physical sensor wherein signals from the sensor are wirelessly transmitted to a base station.

51. The method of claim 48, wherein the device is used to monitor the functions of brain electrical activity for the purposes of diagnosis and detection of neurological disorders of a bioelectrical nature such as epilepsy.

52. The method of claim 48, wherein the device is placed in or on the heart to monitor the bioelectrical activity of the heart for purposes of control of devices which control the heart rhythm and electrical functionality.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0063] The following drawings form part of the present specification and are included to further demonstrate certain aspects of the present invention. The invention may be better understood by reference to one or more of these drawings in combination with the detailed description of specific embodiments presented herein.

[0064] FIG. 1. Schematic of the passive biotelemetry system. V1 models the input signal originating from biopotentials or biosensors. R1 is an isolating resistance and D1 and D2 represent back-to-back connected varactor diodes used as variable capacitances. L1 is the inductor forming a resonant circuit and also serves as an antenna.

[0065] FIG. 2. Plot of the demodulated amplitude level resulting from a test 10 KHz electrical signal level (in millivolts) applied to the circuit in FIG. 1 and having a radio exciter frequency of 265 MHz.

[0066] FIG. 3. Spectrum analyzer display of the backscattered signal from the circuit in FIG. 1 using a 1 millivolt 500 KHz modulating signal as V1. The spectrum analyzer output shows the wide achievable bandwidth through the appearance of expected AM sidebands at +/500 KHz on either side of the carrier.

[0067] FIG. 4. A 1 mV ECG waveform detected by body surface electrodes telemetered over a half-meter distance using the circuit shown in FIG. 1 using a body surface ECG signal as input signal V1 originating from biopotential electrodes applied to the chest region of a human volunteer.

[0068] FIG. 5. Plot of the demodulated signal level originating from a commercial pH electrode connected as V1 in FIG. 1 and then exposed to a changing pH buffer calibration solutions of 4, 7, and 10.

[0069] FIG. 6 Schematic drawing of a potentially injectable wireless pH sensor.

DETAILED DESCRIPTION OF INVENTION

[0070] This invention relates to the field of radio communication devices that use the coupling of tuned electrically resonant circuits to carry information between a remote unit and a base station. In one embodiment, a remote unit is of an electrically passive design containing no batteries and deriving its power needs from the incoming radio frequency carrier wave. This allows the manufacture of biopotential communication devices that have small size and potentially long lifetimes. Since there are no batteries to wear out, they are suited to tasks such as wireless telemetry of bioelectrical and sensor data from small physical or chemical sensors implanted in the body of humans or other living things.

[0071] Certain embodiments of the invention employ the principle whereby small voltages applied to resonant circuits constructed with voltage variable capacitances will shift resonant frequencies by a small percentage amount of the resonant frequency. At high operating frequencies in the UHF and microwave region, the absolute frequency change is a relatively large number of Hertz and so sensitively demodulated by conventional frequency demodulation techniques.

[0072] A second aspect of this invention is the aspect of preamplification of low level electrical signals by the parametric amplification that occurs by the circuit configuration of the voltage variable capacitors with an inductor forming a resonant circuit. Time varying capacitances arranged such that a signal voltage is applied across their capacitance will be amplified by a process of parametric amplification. This amplification occurs concurrently with the backscatter modulation of the applied

[0073] RF carrier. Thus two processes, amplification and modulation, are accomplished at the same time by using the same time-varying capacitances with a minimum of electrical circuitry.

[0074] Another aspect of this invention is a circuit design using variable capacitance devices in a way that presents high input port impedance for modulating electrical signals originating from sources such as high impedance bioelectrodes and high impedance biochemical and biophysical sensors. This high input port impedance for parametric devices is advantageous since it allows direct connection of high resistance bioelectrodes and biosensors to the resonant circuitry without need for power-consuming impedance matching amplifiers or circuitry. This simplifies the circuitry even further over the use of conventional FET and transistor buffer amplifiers that would ordinarily be required to match high impedance signal sources.

[0075] Another aspect of this invention is the design of a telemetry system of wide bandwidth. This feature arises through the modulation method of applying signals directly across the voltage variable capacitors rather than the use of conventional FET or transistor circuitry prior to modulation and so would restrict bandwidths to that of these prior circuitry.

[0076] Another feature of this invention is that it allows a considerable miniaturization of the remote unit circuitry compared to the current art of integrated circuit design by virtue of its greatly reduced parts count compared to the usual FET amplifiers, RF power conversion circuitry, and often analog to digital conversion requirements as often is the case in current art.

[0077] Using components from commercial manufacturers, it is possible to achieve form factors that will pass through the lumen of a 1 mm syringe needle yet have sufficient range to telemeter biopotentials to an externally worn receiver. By a simple process of duplicating the simple circuit and shifting the frequency of each circuit it is possible to achieve multichannel operation.

[0078] Exemplary Electrical Circuit

[0079] In its simplest yet functional and illustrative configuration, the telemetry device employs a pair of varactor diodes in a half-bridge configuration and a miniature inductor to form a resonant circuit. An external RF exciter pumps energy into this system which the circuit then re-radiates on a different harmonic frequency.

[0080] Electrical signals originating from high impedance sources such as biopotential electrodes or miniature chemical or physical sensors, are applied to the voltage variable capacitors through an isolating resistor or alternately an inductive choke to prevent loading of the resonant circuit by the signal source.

[0081] The frequency of operation as defined by the component values of the inductance and variable capacitances can encompass a wide range that is desirably but not limited to frequencies of above about 100 MHz and extending into the multiple-GHz microwave range with the appropriate choice of inductors and voltage variable capacitances.

[0082] This assembly of electrical components is a wireless biotelemetry device that utilizes the simple structure of an inductive-capacitive (LC) resonant circuit. In a typical configuration where the voltage variable circuit elements are varactor diodes, they are connected back-to-back to form an equivalent series capacitance. Their p-n junction capacitance can be controlled over a wide range such as 2 to 10 pF with typically 1-10 volts of applied voltage such as commonly found in data sheets from manufacturers such as the MA4ST2000 series made by Microwave Associates (Massachusetts, USA).

[0083] FIG. 1 shows the configuration of this circuit. Millivolt and microvolt order biopotential signals for example denoted by V1 are placed across the varactors D1 and D2 through an isolating resistor R1. The series varactors are in combination with inductance L1 to form a resonant circuit for a frequency preferably above about 100 MHz. This circuit is electrically excited by an external and remote RF pump source which induces as much as several volts across the diodes and inductor before saturation. At the same time, the small voltage V1 applied across the resonant circuit varies the baseline capacitance of the series diodes and hence vary the system fundamental resonant frequency.

[0084] High order harmonics of the pump frequency are naturally radiated from the diode-inductor in this circuit according to principles of nonlinear response of the diodes, and these harmonics propagate outward from the inductor and through space. These radiated harmonics are shifted slightly in frequency by the action of the modulating signal V1. The absolute frequency variation due to the modulating source is multiplied in by a factor that is the same as the harmonic number and so by detecting the frequency shift at higher harmonics there is a greater overall sensitivity to changes in V1.

[0085] Detection and frequency demodulation of the radiated harmonics can occur through common methods of radio communication, such as direct conversion, superheterodyne, FM, and slope detection AM demodulation schemes.

[0086] Changes in voltage across the varactor affects the frequency of both the fundamental resonance as well as the radiated harmonics. Even microvolt level signals can modulate the varactor diode capacitance to a remotely detectable degree by using conventional radio demodulation techniques. Operating frequencies are desirably in the UHF and GHz band to allow the more efficient use of small loop antennas on the device leading to compact size. Varactor-based L-C circuits are tunable to specific resonant frequencies. This lends to specific channels of operation and possible multichannel designs by an array of varactor circuits tuned to non-overlapping frequency bands.

Parametric Amplification

[0087] This invention employs the process of signal parametric amplification to boost sensitivity to low level microvolt level signals from bioelectrodes or biosensors. It has been long known that parametric amplifiers have in theory both an infinite input resistance and no Johnson noise and so are noiseless methods of amplification. Parametric amplifiers depend on a time varying circuit parameter, usually a capacitance to provide gain. The functioning of parametric amplifiers is a mathematically rigorous field of study and the reader is referred to references by Matthaei et al, and Sard et al., for examples.

[0088] Conventional parametric amplifiers employ a time varying capacitance by AC driving the junction of a varactor diode. An electrical signal applied to the junction of the diode can be increased in amplitude when the junction capacitance is forced to change in value by an electrical pump signal. Since V=Q/C, for a given signal charge Q, the potential V across the capacitor will increase to a larger value if C decreases. In our system, the junction capacitance of a varactor diode or similar volt-variable device is driven by an AC pump voltage. Biopotentials applied to the time varying capacitor shift its base capacitance and so this modulates the current flow in a companion inductive loop forming a resonant circuit.

[0089] Parametric amplification of the applied signal V1 occurs when the amplitude of the RF exciting signal is drives the varactor diodes to significant changes in capacitance at the excitation frequency. By this invention the signal frequency is converted to an RF frequency. The RF frequency amplitude and frequency modulation is relatively larger than is achieved when the varactor diodes are not driven to large capacitance excursions by the applied RF excitation.

[0090] FIG. 2 shows the level of remotely detected envelope amplitude modulation caused by a one millivolt sine wave applied as source V1 to the circuit in FIG. 1.

[0091] FIG. 3 shows the remotely detected spectrum of a backscattered signal with a 1 millivolt 500 kHz test signal used as the signal source V1. The bandwidth of the system is seen in this example to be much larger than the few kilohertz typically achieved with more conventional circuit designs targeted for implantable wireless telemetry systems and showing that it may transmit wide bandwidth digital data as well.

[0092] FIG. 4 shows the remotely demodulated signal using two silver silver-chloride surface electrodes attached to the human chest and the roughly 1 mV detected ECG biopotential used as V1 as in FIG. 1.

[0093] FIG. 5 Shows the remotely demodulated signal obtained from using a commercial (VWR Inc.) glass pH electrode bulb of conventional design and well known to chemists and connected up as the signal source V1. The electrode was exposed to pH calibration solutions at pH 4, 7, and 10. To detect steady dc levels from the pH sensor electrodes, the demodulator used a direct conversion synchronous demodulation scheme.

[0094] FIG. 6 illustrates a schematic of a potentially injectable wireless pH sensor 100. Sensor 100 comprises a pH sensitive electrode 10 and a reference electrode 20. Sensor 100 further comprises microtelemetry sections 30. In specific embodiments, microtelemetry section 30 has a length L that is approximately 3 mm. In certain embodiments, sensor 100 is approximately 1 mm or less in diameter. As s result, sensor 100 may be injected through the lumen of a 14, 16, or 18 gauge needle

[0095] Certain aspects of the present invention are described in the white paper entitled Wireless Implantable Micro-Biosensors (submitted in consideration for DARPA BAA03-02) incorporated by reference.

[0096] While the present disclosure may be adaptable to various modifications and alternative forms, specific embodiments have been shown by way of example and described herein. However, it should be understood that the present disclosure is not intended to be limited to the particular forms disclosed. Rather, it is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the disclosure as defined by the appended claims. Moreover, the different aspects of the disclosed apparatus and methods may be utilized in various combinations and/or independently. Thus the invention is not limited to only those combinations shown herein, but rather may include other combinations, as well.

REFERENCES

[0097] The following references are incorporated by reference:

Heetderks, W., RF Powering Of Millimeter- and Submillimeter-Sized Neural Prosthetic Implants, IEEE Transactions on Biomedical Engineering, Vol. 35, No. 5, 323. May 1988.

[0098] Matthaei, G. L., A Study of the Optimum Design of Wide-Band Parametric Amplifiers and Up Converters, IRE Transactions on Microwave Theory Tech., Vol. MTT-10, pp. 23-28 Jan 1961.

Mohseni, P., K. Najafi, S. J. Eliades, and X. Wang, Wireless Multichannel Biopotential Recording Using An Integrated Fm Telemetry Circuit, IEEE Transactions On Neural Systems And Rehabilitation Engineering, Vol. 13, No. 3, September 2005.

[0099] Sard, E., B. Peyton, S. Okwit, A positive resistance up-converter for ultra-low noise amplification, IEEE Trans. Micro Theory Tech., Vol. 14, pp. 608-618, Dec. 1966.
Towe, B. C., Passive Biotelemetry by Frequency Keying, IEEE Transactions on Biomedical Engineering, Vol. BME-33, No. 10, October 1986.

Wise, K. D., D. J. Anderson, J. F. Hetke, D. R. Kipke, K. Najafi, Wireless Implantable Microsystems: High-Density Electronic Interfaces to the Nervous System, Proceedings of the IEEE, Vol. 92, No. 1, January 2004.

[0100] U.S. Pat. No. 7,158,010 to Fischer et al.