Voltage sensing system with input impedance balancing for electrocardiogram (ECG) sensing applications

[0002] This invention relates generally to a voltage sensing system and particularly, but not by way of limitation, to a voltage sensing system with input impedance balancing for electrocardiogram (ECG) sensing applications.

[0003] When functioning properly, the human heart maintains its own intrinsic rhythm, and is capable of pumping adequate blood throughout the body's circulatory system. The body's autonomous nervous system generates intrinsic electrical heart activity signals that are conducted to atrial and ventricular heart chambers on the left and right sides of the heart. The electrical heart activity signals trigger resulting heart contractions that pump blood.

[0004] The intrinsic electrical heart activity signals can be monitored to provide an electrocardiogram (ECG) signal to a physician, clinician, diagnostician, or researcher to obtain information about heart function. In one such technique, a first external skin patch electrodes is adhesively affixed to the patient's right arm. A second external skin patch electrode is adhesively affixed to the patient's left arm. An instrumentation amplifier is used to detect the electrical heart activity signals at the first and second electrodes. The instrumentation amplifier outputs an ECG signal based on the difference of the signals at the first and second electrodes.

[0005] If no further electrodes are used, the ECG signal obtained between the first and second electrodes is typically severely degraded by common-mode (CM) noise signals, such as 60 Hertz or other environmental noise signals that are present at both of the first and second electrodes. Common-mode noise problems generally result even if a high-quality instrumentation amplifier is used. Skin-electrode interface impedance differences between the first and second electrodes contribute to such common-mode noise problems. Differences in skin-electrode interface impedances result from differences in body morphology, adhesion of the electrode, perspiration by the patient, etc. Because of the high input-impedance of the instrumentation amplifier, even small differences in the skin-electrode impedance (e.g., 10 kiloohms) can result in a common-mode noise signal amplitude that exceeds the amplitude of the desired ECG signal.

[0006] One technique of reducing the common-mode noise signal is to attach a third electrode, such as at the patient's right leg, for use in a feedback arrangement. The third electrode is driven by an offsetting common-mode signal to cancel a portion of the unwanted common-mode noise signal. However, this technique is inconvenient for the physician, because it requires attachment of the third electrode to the patient. This increases the complexity of the medical procedure. In a medical emergency, for example, such increased complexity is highly undesirable. Thus, there is a need for improved ECG measurement techniques providing adequate common-mode noise immunity without relying exclusively on attaching additional electrodes to the patient.

[0007] The present system provides, among other things, a voltage sensing system with input impedance balancing for electrocardiogram (ECG) sensing or other applications. The present system allows sensing of ECG or other input voltage signals and reduces sensing of unwanted common-mode noise signals. The present system is capable of use with two electrodes, while still providing good signal-to-noise characteristics.

[0008] According to one aspect of the present system, signals are received at first and second electrodes or terminals, each having an impedance associated therewith. An effective impedance associated with the second electrode is adjusted based on an effective impedance associated with the first electrode. In one embodiment, an impedance circuit adjusts the effective impedance associated with the second electrode based on difference and common mode signals obtained from signals at the first and second electrodes. As a result, signals associated with each electrode undergo a similar degree of gain/attenuation and/or phase-shift. This reduces common mode noise and enhances the signal-to-noise characteristics of a desired ECG or other output signal, without requiring the use of more than two electrodes. Thus, in an ECG signal acquisition application, the present system enhances the noise immunity of the ECG signal without increasing the complexity of the associated medical procedure. Other aspects of the invention will be apparent on reading the following detailed description of the invention and viewing the drawings that form a part thereof.

[0009] In the drawings, like numerals describe substantially similar components throughout the several views.

[0010] FIG. 1 is a schematic/block diagram illustrating generally one embodiment of portions of a voltage sensing system and an environment in which it is used.

[0011] FIG. 2 is a schematic/block diagram that illustrates generally one embodiment of portions of a voltage sensing system, such as an ECG detector, and an environment in which it is used.

[0012] FIG. 3A is a schematic diagram illustrating generally one embodiment of a first input circuit.

[0013] FIG. 3B is a schematic diagram illustrating generally another embodiment of a first input circuit.

[0014] FIG. 4A is a schematic diagram illustrating generally one embodiment of a second input circuit.

[0015] FIG. 4B is a schematic diagram illustrating generally another embodiment of a second input circuit.

[0016] FIG. 5A is a schematic diagram illustrating generally one embodiment of a configuration of a first amplification circuit and an averager.

[0017] FIG. 5B is a schematic diagram illustrating generally one embodiment of a merged first amplification circuit and averager.

[0018] FIG. 6A is a schematic/block diagram illustrating generally one embodiment of an impedance circuit.

[0019] FIG. 6B is a schematic/block diagram illustrating generally one embodiment of a feedback controller circuit portion of the impedance circuit.

[0020] FIG. 7 is a schematic diagram illustrating generally one embodiment of an impedance control subcircuit.

[0021] FIG. 8A is a signal waveform diagram illustrating generally one embodiment of operating a feedback controller circuit in which a filtered ECG signal is substantially in phase with a filtered common mode signal.

[0022] FIG. 8B is a signal waveform diagram illustrating generally one embodiment of operating a feedback controller circuit in which a filtered ECG signal is substantially 180 degrees out of phase with a filtered common mode signal.

[0023] FIG. 9A is a signal waveform diagram illustrating generally one embodiment of operating a feedback controller circuit in which a filtered ECG signal is substantially in phase with a filtered phase-shifted common mode signal.

[0024] FIG. 9B is a signal waveform diagram illustrating generally one embodiment of operating a feedback controller circuit in which a filtered ECG signal is substantially 180 degrees out of phase with a filtered phase-shifted common mode signal.

[0025] FIG. 10 is a computer simulation signal waveform diagram showing an ECG output signal (where electrode impedances are mismatched) before and after activation of the impedance circuit.

[0026] In the following detailed description, reference is made to the accompanying drawings which form a part hereof, and in which is shown by way of illustration specific embodiments in which the invention may be practiced. These embodiments are described in sufficient detail to enable those skilled in the art to practice the invention, and it is to be understood that the embodiments may be combined, or that other embodiments may be utilized and that structural, logical and electrical changes may be made without departing from the spirit and scope of the present invention. The following detailed description is, therefore, not to be taken in a limiting sense, and the scope of the present invention is defined by the appended claims and their equivalents. In the drawings, like numerals describe substantially similar components throughout the several views.

[0027] In this document, the term gain is understood to refer to both gains greater than one and gains that are less than or equal to one (i.e., the term gain includes attenuation). Similarly, the term amplification is understood to include both gains greater than one and gains that are less than or equal to one. Furthermore, amplification refers to amplification of differential mode signals and/or amplification of common mode signals. Amplifier is understood to incorporate the above understanding of amplification.

[0028] This document describes, among other things, a voltage sensing system with input impedance balancing for electrocardiogram (ECG) sensing or other applications. The present system allows sensing of ECG or other input voltage signals and reduces sensing of unwanted common-mode noise signals. The present system does not require the use of more than two electrodes. However, it is understood that more than two electrodes can be used in the present system such as, for example, to further improve its signal-to-noise ratio.

[0029] FIG. 1 is a schematic/block diagram illustrating generally, by way of example, but not by way of limitation, one embodiment of portions of the present voltage sensing system and an environment in which it is used. In FIG. 1, a voltage sensing system includes, for example, an ECG detector 100. The ECG detector 100 is coupled, via leadwires or otherwise, to input terminals, such as first and second electrodes 110A-B located at or communicatively coupled to a living organism, such as human or other patient 105. In one embodiment, first electrode 110A is disposed at or near a right arm of patient 105 and second electrode 110B is disposed at or near a left arm of patient 105. First and second electrodes 110A-B are optionally skin patch electrodes that are affixed to the patient's skin, such as using a conductive adhesive or otherwise. Although the embodiment illustrated in FIG. 1 utilizes external electrodes 110A-B, it is understood that other embodiments of the present voltage sensing system use electrodes that are implanted in patient 105.

[0030] In one embodiment, ECG detector 100 is optionally included in a cardiac rhythm management system. In one such example, the cardiac rhythm management system also includes an implanted cardiac rhythm management device 115, such as a pacer, a defibrillator, or a pacer/defibrillator. The implanted device 115 is coupled to heart 120, such as by one or more leadwires or otherwise, for delivering cardiac rhythm management therapy (e.g., electrical pulses or defibrillation countershocks). In one embodiment, the cardiac rhythm management system further includes an external programmer 125. A communication device, such as telemetry device 130, communicatively couples external programmer 125 to implanted device 115. Programmer 125 includes ECG detector 100.

[0031] FIG. 2 is a schematic/block diagram that illustrates generally, by way of example, but not by way of limitation, one embodiment of portions of a voltage sensing system, such as ECG detector 100, and an environment in which it is used. In FIG. 2, body voltages including an electrical heart activity signal are received at first and second electrodes 110A-B, which are modeled schematically. First electrode 110A has an effective skin-electrode impedance modeled by resistor 200A in parallel with capacitor 205A. Similarly, second electrode 110A has an effective skin-electrode impedance modeled by resistor 200B in parallel with capacitor 205B. Electrodes 110A-B are coupled, at respective nodes 210A-B, to respective first and second input circuits 215A-B associated with ECG detector 100. Input circuits 215A-B provide outputs at respective nodes 220A-B. Nodes 220A-B are each coupled to both of first amplification circuit 225 and averager 230.

[0032] An output of first amplification circuit 225, at node 235, provides an ECG signal output and is coupled to impedance circuit 239. An output of averager 230, at node 245, provides a common mode signal that is coupled to impedance circuit 239. At least one output of impedance circuit 239 is coupled to second input circuit 215B for controlling its impedance to reduce the common mode noise signal at the ECG signal output node 235.

[0033] As discussed above, the effective impedances of first electrode 110A and second electrode 110B may be different. This causes the amount of signal attenuation from the input of electrode 110A to node 210A to be different from the amount of signal attenuation from the input of electrode 110B to node 210B. According to prior art techniques, this resulted in an unwanted common-mode noise signal amplitude, at node 235, that exceeds the desired ECG signal amplitude at node 235. According to one aspect of the present system, however, impedance circuit 239 substantially offsets, corrects, or compensates for effects of the impedance mismatch between electrodes 110A-B. As a result, the effective signal attenuation from the input of electrode 110A to node 220A is approximately equal to the effective signal attenuation from the input of electrode 110B to node 210B. This, in turn, decreases the common-mode noise at ECG signal output node 235, such that the desired ECG signal is more readily discernable at node 235.

[0034] FIG. 3A is a schematic diagram illustrating generally, by way of example, but not by way of limitation, one embodiment of first input circuit 215A. The input signal from first electrode 110A is received at node 210A through series protection resistor 300A. Resistor 300A limits a current received by subsequent circuits when high energy is received, such as from electrostatic discharges (ESD) or from the delivery of a defibrillation countershock to heart 120. This protects such circuits against possible damage. Similarly, protection diodes 305A and 310A clamp the voltage at node 315A, such that it does not exceed the positive power supply voltage, V_DD, at node 320, by more than a diode voltage, and such that the voltage at node 315A does not fall below the negative power supply voltage, V_SS, at node 325, by more than a diode voltage.

[0035] In one embodiment, input circuit 215A also includes a phase shifter 330A. In one example, phase shifter 330A includes a series phase lead network formed by resistor 335A in parallel with capacitor 340A. An output of phase shifter 330A is coupled, at node 345A, to a positive input of a buffer such as that of buffer amplifier 350A. An output, at node 220A, of amplifier 350A is fed back to its negative input. The output at node 220A of amplifier 350A is also fed back to its positive input through feedback resistor 355 and input resistor 360A. An intermediate node 365A, between series-connected feedback resistor 355 and input resistor 360A, is coupled to a stable reference voltage, such as a ground node, through resistor 370. Input capacitor 375A is coupled between the positive input, at node 345A, of amplifier 350A, and the ground node.

[0036] Amplifier 350A and the network of resistors 355, 360A, and 370 form an impedance bootstrap circuit that effectively increases the effective impedance of input resistor 360A, as seen at node 345A, as compared what such impedance would be if resistor 360A directly coupled node 345A to the ground node. The impedance bootstrap circuit operates such that an increase in voltage at node 345A results in an increase in voltage at nodes 220A and 365A. This reduces the voltage across resistor 360A which, in turn, reduces the current through resistor 360A. Because the resulting current through resistor 360A, in response to a given change in voltage at node 345A, is less than it would be if resistor 360A directly coupled node 345A to ground, Ohm's Law indicates that the effective impedance seen at node 345A is increased. Similarly, a decrease in voltage at node 345A results in a decrease in voltage at nodes 220A and 365A which, in turn, also reduces the current through resistor 360A, thereby increasing the effective resistance of resistor 360A as seen at node 345A.

[0037] FIG. 4A is a schematic diagram illustrating generally, by way of example, but not by way of limitation one embodiment of second input circuit 215B. As illustrated in FIG. 4A, second input circuit 215B is similar to first input circuit 215A. Operation of correspondingly numbered elements (but with a different suffix letter “B”) is as described with respect to FIG. 3A. In FIG. 4A, however, input resistor 360B couples a signal received at node 270A, from impedance circuit 239, to the positive input, at node 345B, of a buffer, such as buffer amplifier 350B. Similarly, input capacitor 375B couples a signal received at node 270B, from impedance circuit 239, to the positive input, at node 345B, of buffer amplifier 350B.

[0038] FIG. 4A illustrates resistor 360B and capacitor 375B as being part of second input circuit 215B, for convenience of illustrating similarities and differences between first and second input circuits 215A-B. It is understood, however, that resistor 360B and capacitor 375B are alternatively regarded as being part of impedance circuit 239 rather than as being part of second input circuit 215B, and could alternatively be illustrated therewith.

[0039] In operation, the voltages at nodes 270A-B are adjusted by impedance circuit 239 (analogous to operation of the impedance bootstrap circuit described above with respect to FIG. 3A) to vary the effective impedance of resistor 360B and capacitor 375B such that a gain/attenuation between first electrode 110A and node 345A is approximately or substantially equal to a gain/attenuation between second electrode 110B and corresponding node 345B. In one embodiment, this results in an attenuation between first electrode 110A and node 220A that is approximately or substantially matched to an attenuation between second electrode 110B and corresponding node 220B.

[0040] By increasing the voltage at node 270A, relative to the voltage at node 345B, the effective resistance of input resistor 360B is increased. By decreasing the voltage at node 270A, relative to the voltage at node 345B, the effective resistance of input resistor 360B is decreased. According to one aspect of the present system, the voltage at input node 270A is controlled by impedance circuit 239 such that the effective resistance of input resistor 360B matches a resistive component of the effective impedance seen at node 345A of first input circuit 215A (when the resistor 200A of first electrode 110A is approximately equal to the resistor 200B of second electrode 110B and the capacitor 205A of first electrode 110A is approximately equal to the capacitor 205B of second electrode 110B).

[0041] By decreasing the voltage at node 270B, relative to the voltage at node 345B, the effective capacitance of input capacitor 375B is increased. By increasing the voltage at node 270B, relative to the voltage at node 345B, the effective capacitance of input capacitor 375B is decreased. According to one aspect of the present system, the voltage at input node 270B is controlled by impedance circuit 239 such that the effective capacitance of input capacitor 375B matches the reactive (e.g., capacitive) component of the effective impedance seen at node 345A of first input circuit 215A (when the resistor 200A of first electrode 110A is approximately equal to the resistor 200B of second electrode 110B and the capacitor 205A of first electrode 110A is approximately equal to the capacitor 205B of second electrode 110B).

[0042] The system is described above as including phase-lead networks 330A and 330B to accommodate a full range of phase lags introduced by impedance circuit 239, resistor 360B, and capacitor 375B. Alternatively, phase lead networks 330A and 330B are omitted, and a negative impedance circuit is used in place of at least one of resistor 360B and capacitor 375B, as illustrated in FIGS. 3B and 4B by way of example, but not by way of limitation. In FIG. 4B, for example, an additional capacitor 375C is included, and capacitor 375B is implemented as a negative capacitance circuit. In this embodiment, capacitors 375A and 375C each have an approximately equal nominal capacitance value (“C”), and negative capacitor circuit 375B has a nominal capacitance value of −2C. Alternatively, capacitor 375A has a nominal capacitance value C, capacitor 375B has a nominal capacitance value 2C, and capacitor 375C is implemented as a negative capacitance network having a capacitance value of approximately −C.

[0043] FIG. 5A is a schematic diagram illustrating generally, by way of example, but not by way of limitation, one embodiment of a configuration of first amplification circuit 225 and averager 230, such as illustrated in FIG. 2. In one embodiment, as illustrated in FIG. 5A, first amplification circuit 225 includes a differential input, single-ended output amplifier, such as an off-the-shelf or other instrumentation amplifier. First amplification circuit 225 receives input signals at nodes 220A-B from first and second input circuits 215A-B, respectively, and outputs an ECG signal at node 235.

[0044] In this embodiment, averager 230 includes a differential input, single-ended output operational amplifier 500. Amplifier 500 includes a positive input that is coupled to a ground node and an output, at node 245, that provides a common mode voltage of the signals at nodes 220A and 220B. The common mode signal at the node 245 is fed back to the inverting input, at node 505, of amplifier 500, such as through feedback resistor 510. The inverting input of amplifier 500, at node 505, is coupled via first input resistor 512 to receive a signal, at node 220A, from first input circuit 215A. The inverting input of amplifier 500, at node 505, is also coupled via second input resistor 515 to receive a signal, at node 220B, from second input circuit 215B. In an alternate embodiment, averager 230 includes a passive network (i.e., without using operational amplifier 500) for averaging the signals at nodes 220A-B.

[0045] In this embodiment, first amplifier 225 is configured as an instrumentation amplifier, which includes first operational amplifier 520, second operational amplifier 522 and third operational amplifier 524, each having differential inputs and a single-ended output. A noninverting input of first operational amplifier 520 is coupled to first input circuit 215A at node 220A. The output, at node 526, of first operational amplifier 520 is fed to the inverting input of third operational amplifier 524 through resistor 528, and is also fed back through resistor 530 to the inverting input, at node 529, of first operational amplifier 520. A noninverting input of second operational amplifier 522 is coupled to second input circuit 215B at node 220B. The output, at node 532, of second operational amplifier 522 is fed to the noninverting input of third operational amplifier 524 through resistor 534, and is also fed back to the inverting input, at node 535, of second operational amplifier 522 through resistor 536. The inverting input node 529 of first operational amplifier 520 is coupled to the inverting input node 535 of second operational amplifier 522 through series-coupled resistors 538 and 540. The output of third operational amplifier 524 provides the ECG signal at node 235, and is coupled back to the inverting input of third operational amplifier through resistor 542. The noninverting input of third operational amplifier 524 is coupled to a ground node through resistor 544.

[0046] FIG. 5B is a schematic diagram illustrating generally, by way of example, but not by way of limitation, one embodiment of a configuration of a merged first amplification circuit 225 and averager 230. In this embodiment, a single instrumentation amplifier 225 is used, and the common mode-signal at node 245 is provided by the common mode output of the instrumentation amplifier taken between resistors 538 and 540.

[0047] FIG. 6A is a schematic/block diagram illustrating generally, by way of example, but not by way of limitation, one embodiment of impedance circuit 239. Impedance circuit 239 receives the ECG signal, at node 235, the common mode signal, at node 245, and the output, at node 220B, of second input circuit 215B. The ECG signal at node 235 is amplified at buffer 602, which provides an output at node 604 that is then filtered by filter 606, which, in one embodiment, is a bandpass filter that attenuates frequencies outside the range of approximately 6-600 Hz (e.g., single pole rolloff frequencies). This, in turn, provides a filtered ECG signal output at node 608 to feedback controller 610. In one alternate embodiment, buffer 602 and filter 606 are combined. In another alternate embodiment, filter 606 is a highpass filter.

[0048] The common mode signal at node 245 is amplified at buffer 612, which provides an output at node 614 that is then filtered by filter 616, which, in one embodiment, is a bandpass filter that attenuates frequencies outside the range of approximately 6-600 Hz. This, in turn, provides a filtered common mode signal output at node 618 to feedback controller 610. In one alternate embodiment, buffer 612 and filter 616 are combined. In another alternate embodiment, filter 616 is a highpass filter.

[0049] The filtered common mode signal output at node 618 is also received by phase-shifter 620, which provides a filtered phase-shifted common mode signal output at node 622 to feedback controller 610. In one embodiment, phase-shifter 620 includes an integrator circuit that includes differential input, single-ended output operational amplifier 624. Amplifier 624 has a positive input, which is coupled to ground, and an output at node 622 that is fed back to its inverting input, at node 626, through a feedback capacitor 628. The inverting input of amplifier 624 is also coupled, via input resistor 630, to receive the filtered common mode output signal, at node 618, from the output of filter 616. Phase-shifter 620 provides a filtered phase-shifted common mode output signal, at node 622 (which, in one embodiment, is approximately 90 degrees out of phase with the common mode signal at node 245 and is also referred to as a filtered quadrature common mode signal). In an alternative embodiment, phase-shifter 620 is configured as a differentiator, rather than as an integrator (i.e., resistor 630 is configured in the feedback path around amplifier 624 and capacitor 628 is interposed between nodes 618 and 626).

[0050] Based on the filtered ECG signal at node 608, the filtered common mode signal at node 618, and the filtered quadrature common mode signal at node 622, feedback controller 610 provides a resistive matching control signal, at node 632, and a capacitive matching control signal, at node 634, to impedance control subcircuit 636. Impedance control subcircuit 636 also receives the output signal, at node, 220B, from second input circuit 215B. Based on these input signals, impedance control subcircuit 636 provides control voltages, at node/bus 270 to second input circuit 215B for controlling its impedance to reduce the common mode noise signal at the ECG signal output node 235.

[0051] FIG. 6B is a schematic/block diagram illustrating generally, by way of example, but not by way of limitation, one embodiment of feedback controller circuit 610. Feedback controller circuit 610 receives the filtered ECG signal, at node 608, the filtered common mode signal, at node 618, and the filtered phase-shifted common mode signal at node 622.

[0052] In one embodiment, the filtered common mode signal, at node 618, is phase-detected with respect to the filtered ECG output signal, at node 608, as described below. The filtered ECG signal at node 608 is mixed or multiplied with the filtered common mode signal, at node 618, by a mixer or multiplier (referred to interchangeably herein) such as analog multiplier 640, which provides a resulting signal, referred to as an in-phase signal, at node 645. The in-phase signal at node 645 is received by low pass filter 650. In one embodiment, low pass filter 650 attenuates frequency components above a cutoff frequency of approximately 40 Hertz, and provides a resulting low pass filtered in-phase signal, at node 655, to integrator 660. Integrator 660 integrates the low pass filtered in-phase signal, providing a resulting resistive-matching control signal, at node 632, to impedance control subcircuit 636.

[0053] The filtered phase-shifted common mode signal, at node 622, is phase-detected with respect to the filtered ECG output signal, at node 608, as described below. The filtered ECG signal at node 608 is mixed or multiplied with the filtered phase-shifted common mode signal, at node 622, by a mixer or multiplier, such as analog multiplier 665, which provides a resulting signal, referred to as a quadrature phase signal, at node 670. The quadrature phase signal at node 670 is received by low pass filter 675. In one embodiment, low pass filter 675 attenuates frequency components above a cutoff frequency of approximately 40 Hertz, and provides the resulting low pass filtered quadrature phase signal, at node 680, to an integrator, such as inverting integrator 685. Inverting integrator 685 integrates and inverts the low pass filtered quadrature phase signal, providing a resulting capacitive-matching control signal, at node 634, to impedance control subcircuit 636.

[0054] FIG. 7 is a schematic diagram illustrating generally, by way of example, but not by way of limitation, one embodiment of portions of impedance control subcircuit 636. In this embodiment, impedance control subcircuit 636 includes one or more variable gain or similar circuits, such as analog multiplier circuits, or first voltage controlled amplifier (VCA) 700A and second VCA 700B. A negative input of each of VCAs 700A-B is grounded. A positive input of each of VCAs 700A-B is coupled to node 220B to receive the output signal from second input circuit 215B.

[0055] In one embodiment, the gain of first VCA 700A is adjusted by the resistive-matching control signal received at node 632 from feedback controller circuit 610. The gain of second VCA 700B is adjusted by the capacitive-matching control signal received at node 634 from feedback controller circuit 610. The gain of respective VCAs 700A-B is increased for more positive signals at respective nodes 632 and 634, and decreased for more negative signals at respective nodes 632 and 634. First VCA 700A provides an output voltage, at node 270A, to resistor 360B in second input circuit 215B. Second VCA 700B provides an output voltage, at node 270B, to capacitor 375B in second input circuit 215B.

[0056] FIG. 4 illustrates resistor 360B and capacitor 375B as being part of second input circuit 215B, for convenience of illustrating similarities and differences between first and second input circuits 215A-B. It is understood, however, that resistor 360B and capacitor 375B are alternatively regarded as being part of impedance control subcircuit 636 rather than as being part of second input circuit 215B (or other portion of impedance circuit 239) and could alternatively be illustrated therewith.

[0057] In one embodiment, first and second VCAs 700A-B provide independent impedance bootstraps, as discussed above with respect to amplifier 350A in first input circuit 215A. However, the gain of first and second VCAs 700A-B is adjusted by feedback controller circuit 610 to control the respective node voltages 270A-B to substantially offset or approximately correct the impedance mismatch between electrodes 110A-B. As a result, the effective signal attenuation from the input of electrode 110A to node 220A is approximately equal to the effective signal attenuation from the input of electrode 110B to node 210B. This, in turn, decreases the common-mode noise at ECG signal output node 235, such that the ECG signal is more readily discernable at node 235.

[0058] FIG. 8A is a signal waveform diagram illustrating generally, by way of example, but not by way of limitation, one embodiment of operating impedance circuit 239. In FIG. 8A, V₆₀₈represents an illustrative example of a filtered ECG signal at node 608 and V₆₁₈represents an illustrative example of a filtered common mode signal at node 618. In the example illustrated in FIG. 8A, V₆₀₈and V₆₁₈are in phase with each other. The signals V₆₀₈and V₆₁₈are multiplied with each other at multiplier 640, providing V₆₄₅, a resulting in-phase signal at node 645. For the illustrated signals V₆₀₈and V₆₁₈, which are in phase with each other, the resulting in-phase signal at node 645 is frequency-doubled and positive-valued. The in-phase signal at node 645 is filtered by low pass filter 650, which attenuates high-frequency components, resulting in a positive-valued signal V₆₅₅at node 655. The low pass filtered in-phase signal at node 655 is integrated by integrator 660, resulting in an upward ramping resistive-matching control signal, V₆₃₂at node 632. An increase in the resistive-matching control signal at node 632 increases the gain of first VCA 700A, which increases the effective resistance of resistor 360B.

[0059] FIG. 8B is a signal waveform diagram, similar to FIG. 8A, but providing an illustrative example of signals V₆₀₈and V₆₁₈being out of phase with each other. After multiplication, the resulting in-phase signal V₆₄₅at node 645 is frequency-doubled and negative-valued. As a result, the low pass filtered in-phase signal V₆₅₅at node 655 is also negative-valued. Integration yields a downward ramping resistive-matching control signal V₆₃₂at node 632, which decreases the gain of first VCA 700A, and decreases the effective resistance of resistor 360B.

[0060] FIG. 9A is a signal waveform diagram illustrating generally, by way of example, but not by way of limitation, another aspect of one embodiment of operating impedance circuit 239. In FIG. 9A, V₆₀₈represents an illustrative example of a filtered ECG signal at node 608 and V₆₁₈represents an illustrative example of a filtered phase-shifted common mode signal at node 618. In the example illustrated in FIG. 9A, V₆₀₈and V₆₁₈are in phase with each other. The signals V₆₀₈and V₆₁₈are multiplied with each other at multiplier 665, providing V₆₇₀, a resulting quadrature-phase signal at node 670. For the illustrated signals V₆₀₈and V₆₁₈, which are in phase with each other, the resulting quadrature-phase signal at node 670 is frequency-doubled and positive-valued. The quadrature-phase signal at node 670 is filtered by low pass filter 675, which attenuates high-frequency components, resulting in a positive-valued signal V₆₈₀at node 680. The low pass filtered quadrature-phase signal at node 680 is integrated and inverted by inverting integrator 685, resulting in a downward ramping capacitive matching control signal at node 634. A decrease in the capacitive matching control signal at node 634 decreases the gain of second VCA 700B, which increases the effective capacitance of capacitor 375B.

[0061] FIG. 9B is a signal waveform diagram, similar to FIG. 9A, but providing an illustrative example of signals V₆₁₈and V₆₀₈being out of phase with each other. After multiplication, the resulting quadrature-phase signal at node 670 is frequency-doubled and negative-valued. As a result, the low pass filtered quadrature-phase signal at node 680 is also negative-valued. Integration and signal inversion by inverting integrator 685 yields an upward ramping capacitive matching control signal at node 634, which increases the gain of second VCA 700B, and decreases the effective capacitance of capacitor 375B.

[0062] FIGS. 8A-B provide illustrative examples of the phase relationship between the filtered ECG signal at node 608 and the filtered common mode signal at node 618. According to one aspect of operation, impedance circuit 239 provides a negative feedback configuration that tends to minimize the magnitude of the low pass filtered in-phase signal at node 655. This effectively matches the effective resistance of resistor 360B in second input circuit 215B to the effective resistance seen at node 345A in first input circuit 215A (when the resistor 200A of first electrode 110A is approximately equal to the resistor 200B of second electrode 110B and the capacitor 205A of first electrode 110A is approximately equal to the capacitor 205B of second electrode 110B).

[0063] Similarly, FIGS. 9A-B provide illustrative examples of the phase relationship between the filtered ECG signal at node 608 and the filtered phase-shifted common mode signal at node 618. Impedance circuit 239 provides a negative feedback configuration that tends to minimize the magnitude of the low pass filtered quadrature phase signal at node 680. This effectively matches the effective capacitance of capacitor 375B in second input circuit 215B to the effective capacitance seen at node 345A in first input circuit 215A (when the resistor 200A of first electrode 110A is approximately equal to the resistor 200B of second electrode 110B and the capacitor 205A of first electrode 110A is approximately equal to the capacitor 205B of second electrode 110B).

[0064] Even when the resistor 200A of first electrode 110A is not approximately equal to the resistor 200B of second electrode 110B and the capacitor 205A of first electrode 110A is not approximately equal to the capacitor 205B of second electrode 110B, the gain/attenuation from the input of electrode 110A to node 345A in first input circuit 215A is kept substantially identical to the gain/attenuation from the input of electrode 110B to node 345B in second input circuit 215B. As a result, the gain/attenuation from the input of electrode 110A to node 220A is approximately equal to the gain/attenuation from the input of electrode 110B to node 220B. This, in turn, keeps the common mode noise signal at node 245 at a reasonably small value, improving the signal-to-noise characteristics of the ECG signal at node 235.

[0065] Operation of one embodiment of a voltage sensing circuit was simulated using a SPICE computer simulation. The component values that were used are listed below (by way of example, but not by way of limitation).

[0066] First electrode 110A: R_200A=26 KΩ, C_205A=25 nF. First input circuit 215A: R_300A=10 KΩ, R_335A=10 KΩ, C_340A=240 nF, R_360A=10 MΩ, C_375A=120 pF, R₃₇₀=2.6 KΩ, R₃₅₅=1 KΩ. Second electrode 110B: R_200B=20 KΩ, C_205B=10 nF. Second input circuit 215B: R_300B=10 KΩ, R_335B=10 KΩ, C_340B=240 nF, R_360B=12 MΩ, C_375B=300 pF. Averager 230: R₅₁₀=100 KΩ, R₅₁₂=50 KΩ, R₅₁₅=50 KΩ. Phase Shifter 620: C₅₃₅=6 nF, R₅₃₀=100 KΩ (configured as a differentiator). Filters 606 and 616 were configured as high pass filters and each included an RC network where R=10 MΩ and C=10 nF. Low pass filters 650 and 675 each included an RC network where R=400 KΩ and C=10 nF. Integrators 660 and 685 each included an RC integration time constant where R=800 KΩ and C=100 nF.

[0067] FIG. 10 is a computer simulation signal waveform diagram, using above-described component values having mismatched electrode impedances, and showing the ECG output signal at node 235. Before time t=1 second, the feedback controller circuit was turned off, and the ECG output signal is swamped by common mode-noise. At time t=1 second, the impedance circuit 239 was activated. As illustrated in FIG. 10, this initiated the gain/attenuation matching described above. As a result, the common mode noise signal was substantially reduced, as illustrated in FIG. 10 for times greater than 2 seconds, such that the underlying ECG signal waveform was readily discernable as having good signal-to-noise characteristics. The circuit was also resimulated with the impedance mismatch being incorporated into the opposite electrodes, and obtained similar results.

[0068] The above-described system provides, among other things, a voltage sensing system with input impedance balancing for electrocardiogram (ECG) sensing or other applications. The present system allows sensing of ECG or other input voltage signals and reduces sensing of unwanted common-mode noise signals. The present system does not require the use of more than two electrodes. Instead, a common mode signal is generated from the two electrodes, and a feedback network operates to minimize the common mode signal. It is understood, however, that more than two electrodes can be used in the present system such as, for example, by including a third electrode that provides feedback cancellation of the common mode voltage to further improve its signal-to-noise ratio of the system. It is also understood that signal inversions (such as from inverting integrator 685, for example) can be moved elsewhere in the signal flow.

[0069] It is to be understood that the above description is intended to be illustrative, and not restrictive. Many other embodiments will be apparent to those of skill in the art upon reviewing the above description. The scope of the invention should, therefore, be determined with reference to the appended claims, along with the full scope of equivalents to which such claims are entitled.