US20040243018A1

US20040243018A1 - Apparatus and method for determining adequacy of electrode-to-skin contact and electrode quality for bioelectrical measurements

Info

Publication number: US20040243018A1
Application number: US10/724,458
Authority: US
Inventors: Leslie Organ; Kenneth Smith; Joel Ironstone
Original assignee: Z Tech Canada Inc
Current assignee: Z Tech Canada Inc
Priority date: 2002-11-27
Filing date: 2003-11-28
Publication date: 2004-12-02
Also published as: EP1573343A1; WO2004047636A1; CA2451054A1; EP1571996A1; WO2004047643A1; CA2451059C; AU2003286047A1; WO2004047627A2; US7457660B2; CA2451059A1; AU2003286046A1; US7212852B2; AU2003286048A1; CA2450968A1; US20040158167A1; WO2004047627A3; EP1571981A2; EP1571982A1; CA2450968C; US20040171961A1

Abstract

A system and method for diagnosing the possibility of disease in a body part is described. The system includes an electrode array containing a plurality of electrodes capable of being electrically coupled to the body part. A first measurement unit makes an electrode assessment measurement with the electrode array. An electrode assessment module determines whether the plurality of electrodes are suitably coupled to the body part based on the electrode assessment measurement. If there is suitable coupling, a second measurement unit makes a diagnosis measurement with the electrode array. An electrical property module obtains an electrical property of the body part, such as impedance, based on the diagnosis measurement. A diagnosis module diagnoses the possibility of disease based on the measured electrical property.

Description

CROSS-REFERENCE TO RELATED APPLICATION

This application claims priority from provisional application Ser. No. 60/429,316 filed Nov. 27, 2002.[0001]

FIELD OF THE INVENTION

This invention relates to medical diagnosis of disease and specifically relates to diagnosis of disease using electrical impedances of body parts.

BACKGROUND OF THE INVENTION

The onset of disease is often accompanied by physical changes in a body part. Some physical changes, while not discernible by a patient, can be detected with appropriate diagnostic equipment, often at a relatively early stage of the disease. For example, the electrical impedance of a human breast can have diagnostic value.

Electrical impedances of various body tissues are well known through studies on intact humans or from excised tissue made available following therapeutic surgical procedures. In addition, it is well documented that a decrease in electrical impedance occurs in tissue as it undergoes cancerous changes. This finding is consistent over many animal species and tissue types, including, for example human breast cancers.

There have been a number of reports of attempts to detect breast tumors using electrical impedance imaging, such as, for example, U.S. Pat. No. 4,486,835. However, image fidelity and resolution can suffer when simplifying assumptions are made in mathematical models used to construct an image from impedance data.

Despite such difficulties, a method that permits comparisons of electrical properties for diagnostic purposes has been developed that involves homologous body parts, i.e., body parts that are substantially similar, such as a left breast and a right breast. In this method, the impedance of a body part of a patient is compared to the impedance of the homologous body part of the same patient. One technique for screening and diagnosing diseased states within the body using electrical impedance is disclosed in U.S. Pat. No. 6,122,544, which is incorporated herein by reference. In this patent, data are obtained from two anatomically homologous body regions, one of which may be affected by disease. Differences in the electrical properties of the two homologous body parts could signal disease.

Published international patent application, PCT/CA01/01788, which is incorporated herein by reference, discloses a breast electrode array for diagnosing the presence of a disease state in a living organism, wherein the electrode array comprises a flexible body, a plurality of flexible arms extending from the body, and a plurality of electrodes provided by the plurality of flexible arms, wherein the electrodes are arranged on the arms to obtain impedance measurements between respective electrodes. In one embodiment, the plurality of flexible arms are spaced around the flexible body and are provided with electrode pairs, which can be used to make tetrapolar impedance measurements.

Tetrapolar impedance measurements are associated with injecting current between so called current injection electrodes and measuring a voltage drop between associated electrodes. In a preferred embodiment, the differences between corresponding homologous impedance measurements in the two body parts are compared in a variety of ways that allows the calculation of metrics that can serve either as an indicator of the presence of disease or to localize the disease to a specific breast quadrant or sector.

Despite the attractive features of this method of diagnosing disease in one of a homologous pair of body parts, there are some problems associated with this straightforward implementation. In particular, some impedances obtained from electrical measurements may be spurious because of systematic errors occurring therein. Spurious impedances can lead to a faulty diagnosis. Therefore, any test that can be performed at the outset to test and correct for such error would increase diagnostic accuracy.

SUMMARY OF THE INVENTION

To determine the impedance of a body part, such as a breast, for diagnostic purposes, several electrical measurements are performed with an electrode array having a plurality of electrodes in contact with the skin covering the underlying breast tissue. If one or more electrodes have lost contact with the skin, or if the contact with the skin is poor, errors can arise in the electrical measurements that then yield erroneous impedances.

The present invention provides a method to determine both if there is electrode contact with the skin, and, if there is such contact, what the quality of that contact is. The method involves making bipolar measurements of the impedance.

In an AC circuit, the impedance, Z, is a complex number, whose real part is the resistance R and whose imaginary part is the capacitive reactance X _C=(ωC)⁻¹, where ω is the frequency at which the voltage (and current) oscillates and C is the capacitance of the circuit. The magnitude of Z is given by

|Z|=|V|/|I|,

and the phase, φ, of Z is given by

|φ|=|arg(V)−arg(I)|=|tan⁻¹ [X _C(ω)/R]|,

where I denotes the current and V denotes the voltage.

The phase associated with a body part of a patient at a particular frequency can be found by making bipolar measurements. By comparing the phase, at one or several frequencies, to expected values, a decision can be made as to whether the electrode is in suitable contact with the skin on the body part.

Whereas impedance is most accurately measured using the tetrapolar method, bipolar measurement is better for determining adequacy of electrode-to-skin contact (herein referred to as either “contact” or “electrode contact”) because a poor contact result can be isolated to one or both electrodes. There are changes in both impedance magnitude and phase with deteriorating contact, but using phase instead of the magnitude is advantageous because a) impedance magnitude varies greatly from person to person, b) stray capacitance in the system can cause a smaller observed impedance value than would be expected from the high open-circuit value associated with a disconnected electrode, and c) sweat or some other substance could allow a low impedance to be registered even though the current traversing the skin is reduced because of poor electrode contact.

Measuring the phase at different frequencies allows this measure to be even more precise because it can identify if excessive oil or other materials obstruct the skin-electrode interface. In the case of a multi-frequency contact assessment, the expected value for human skin at each of these frequencies is considered. With multiple frequencies, the measured ratio between measured impedance values at different frequencies can be compared to the expected values oh human skin.

Described herein is a system and method for diagnosing the possibility of disease in a body part, such as a human breast. The system includes an electrode array containing a plurality of electrodes capable of being electrically coupled to the body part, and a first measurement unit for making an electrode assessment measurement for the electrode array. The system also includes an electrode assessment module for determining whether the plurality of electrodes are suitably coupled to the body part based on the electrode assessment measurement. The system further includes a second measurement unit for making a diagnosis measurement with the electrode array, and an electrical property module for obtaining an electrical property, such as electrical impedance, of the body part based on the diagnosis measurement. A diagnosis module utilizes the electrical property to diagnose the possibility of disease.

In one embodiment, the plurality of electrodes includes a current injection electrode pair and an associated voltage measurement electrode pair that are applied to the body part. One current injection electrode of the current injection electrode pair and one proximal voltage measurement electrode of the voltage measurement electrode pair are used by the first measurement unit to make a bipolar measurement.

The electrode assessment module can include a phase module for obtaining a phase, φ, from the bipolar measurement, whose absolute value is given by

|φ|=|tan⁻¹ [X _C(ω)/R]|

where X _C(ω) is a capacitive reactance at an alternating frequency, ω, of a current injected during the bipolar measurement, and R is a resistance associated with the body part. The electrode assessment module may further include a contact module for determining that at least one of the current injection electrode and the voltage measurement electrode is not in electrical contact with the body part if the phase is outside a threshold range.

The electrode assessment module can also include a magnitude module for computing a magnitude, Z, from the bipolar measurement, the magnitude given by

Z = \langle \frac{V}{I} \rangle,

where I is the current and V is a resultant voltage measured during the bipolar measurement, and a quality module for determining quality of electrical contact of the current injection electrode and the voltage measurement electrode with the body part based on the magnitude.

In one embodiment, the electrode assessment module may include a) a phase module for obtaining a phase that is a function of a capacitive reactance, at a particular frequency, and a resistance, associated with the body part, and for obtaining other phases at other frequencies, and b) a contact module for determining that at least one of the current injection electrode and the voltage measurement electrode is not in electrical contact with the body part based on the phase at the particular frequency and the other phases at the other frequencies.

The plurality of electrodes mentioned above can include n _CIcurrent injection electrode pairs and n_CIassociated voltage measurement electrode pairs that are applied to the body part. The second measurement unit injects a first current between a first pair of the n_CIcurrent injection electrode pairs, measures the resultant voltage difference V₁ ^Mbetween the voltage measurement electrode pair associated with the first current injection electrode pair, and repeats the preceding two steps of current injection and voltage difference measurement with the other electrode pairs until all n_CIvoltage differences, {V₁ ^M, V₂ ^M, . . . , V_n _CI ^M} are obtained.

In one embodiment, the electrical property module is an impedance module that uses the n _CIvoltage differences to obtain associated measured impedances, {Z₁ ^M, Z₂ ^M, . . . , Z_n _CI ^M}, where Z_j ^Mis the measured impedance between the voltage electrodes associated with the jth current injection electrode pair. The system can then further include a diagnosis module for utilizing the measured impedances, {Z₁ ^M, Z₂ ^M, . . . , Z_n _CI ^M} to diagnose the possibility of disease.

In one embodiment, the system may also include a graphical user interface to indicate a status of the coupling between the plurality of electrodes and the body part.

The present invention describes a system and/or method for measuring an electrical property, such as impedance, in a living tissue that includes an electrode array, first and second measurement units, an electrode assessment module, and an electrical property module, which are described in more detail below.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows a block diagram of the system for diagnosing the possibility of disease, according to the teachings of the present invention; [0029]
FIG. 2A shows the electrode array of FIG. 1. [0030]
FIG. 2B shows a side view of a schematic of a particular current injection electrode pair and an associated voltage measurement electrode pair on the electrode array of FIG. 1. [0031]
FIG. 3 shows the electrode assessment module of FIG. 1. [0032]
FIG. 4 shows a graphical user interface (GUI) that illustrates the status of the skin-electrode contact, according to the teachings of the present invention. [0033]
FIG. 5 shows a block diagram of a system for measuring a voltage in a body part, according to the teachings of the present invention. [0034]
FIGS. [0035] 6A-D shows modes of the controller switching unit of FIG. 5.
FIG. 7 shows a hybrid mode of the controller switching unit of FIG. 5. [0036]
FIG. 8 shows electrical connections in a particular tetrapolar impedance measurement that employs the system of FIG. 5. [0037]
FIGS. 9A and 9B show the multiplexer of FIG. 5. [0038]
FIG. 10 shows a diagnostic system that includes an internal load in addition to the components of FIG. 5. [0039]
FIG. 11 shows one embodiment of the controller switching unit, according to the principles of the present invention.[0040]

DETAILED DESCRIPTION OF THE INVENTION

FIG. 1 shows a [0041] system 100 for diagnosing the possibility of disease in a body part. The system 100 includes an electrode array 102 containing a plurality of electrodes 104 capable of being electrically coupled to the body part. The system 100 also includes a first measurement unit 106, an electrode assessment module 108, a second measurement unit 110, an electrical property module 112 and a diagnosis module 114.
The plurality of [0042] electrodes 104 are applied to the body part to obtain an electrical property of the body part, such as impedance, to diagnose disease.
For this purpose, the plurality of [0043] electrodes 104 have to be electrically connected to the body part. For example, adhesive means (not shown) can be used to connect the electrodes 104 to the skin on the body part of a subject. The electrode conductive material, generally a hydrogel, can also have adhesive properties. The combined adhesive means can fail, resulting in an electrode that is not in proper electrical contact with the body part. To assess the adequacy of electrode coupling to the body part, the first measurement unit 106 utilizes the electrode array 102 to make an electrode assessment measurement. The electrode assessment module 108 determines whether the plurality of electrodes 104 are adequately coupled to the body part based on the electrode assessment measurement, as described in more detail below.
If the [0044] electrode assessment module 108 determines that the plurality of electrodes are suitably coupled to the body part, the second measurement unit 110 can then utilize the electrode array 102 to make a diagnosis measurement. The electrical property module 112 obtains an electrical property of the body part, such as an impedance of the body part, based on the diagnosis measurement. The diagnosis module 114 diagnoses the possibility of disease based on the electrical property. For example, cancer may change the impedance of the body part, a fact that can be exploited by the diagnosis module 114 to diagnose the possible presence of cancer.
FIG. 2A shows the [0045] electrode array 102 of FIG. 1. The electrode array 102 includes the plurality of electrodes 104 that are applied to the body part. The plurality of electrodes 104 include current injection electrodes 120 and voltage measurement electrodes 122 (two of these electrodes are labeled for simplicity). In general, there are n_ecurrent injection electrodes and n_evoltage measurement electrodes in the electrode array 102 (in FIG. 2A, an example is shown with n_e=12). Consequently, there are n_CI=n_e·(n_e−1)/2 combinations of current injections, and an equal number of voltage measurements.
The [0046] electrode array 102 contains several arms 123 (one arm is labeled for simplicity). Each arm includes a current injection electrode and a voltage measurement electrode. For example, the arm 125 includes a particular current injection electrode 124 and voltage measurement electrode 126. It is to be noted, however, that these electrodes can be physically identical and that the terms “current injection” and “voltage measurement” refer to their use during tetrapolar measurement, as used in this invention for the diagnosis stage. In addition, an inner pair of electrodes is provided on some of the array arms 123. One particular inner set of electrodes 128 i and 130 i is located on arm 127. By positioning the inner set of electrodes partway on the array arms, these electrodes are placed closer to the nipple area of the breast, thus allowing better detection of cancers in the periareolar area of the breast.
For tetrapolar measurements, which are discussed below, current injection electrode pairs are used to send current through the body part, and voltage measurement electrode pairs are used to measure the resultant voltage. For example, FIG. 2B shows a side view of the particular [0047] current injection electrode 124 and the voltage measurement electrode 126 on the arm 125. Also shown in FIG. 2B is another arm 127 of the electrode array 102 having another current injection electrode 128 and voltage measurement electrode 130.
For bipolar measurements, however, a single electrode is used for both current injection and voltage measurement. For example, referring again to arm [0048] 25 of FIG. 2B, current is injected between electrodes 124 and 126, and voltage is measured between electrodes 124 and 126. More specifically, current is injected through electrode 124 into the body part, then is received from the body part through electrode 126. The resultant voltage difference between electrodes 124 and 126 is measured by a voltmeter 131. The first measurement unit 106 is used to make the bipolar impedance measurement between electrodes 124 and 126, yielding a reactance X_Cand a resistance R The result of this bipolar measurement is used to assess whether the electrodes on the arm 125 are suitably coupled to the body part before a tetrapolar measurement is performed to diagnose disease.
In FIG. 2B, [0049] adjacent electrodes 124 and 126 are used to perform the bipolar measurements. This choice is dictated by the fact that a measurement is more likely to yield predominantly electrode-to-skin contact impedance if the distance between the two electrodes used is very small.
FIG. 3 shows the [0050] electrode assessment module 108 of FIG. 1. The electrode assessment module 108 includes a phase module 132, a magnitude module 134, a contact module 136 and a quality module 138.
The [0051] phase module 132 obtains a phase φ from the bipolar measurement according to
|φ|=|tan⁻¹ [X _C(ω)/R]|
The [0052] contact module 136 uses the phase calculated by the phase module 132 to determine whether at least one of the electrodes 124 and 126 does not make adequate electrical contact with the body part. In particular, if the phase lies outside a threshold range, then the electrodes 124 and/or 126 fails to make adequate electrical contact with the skin. A useful index for this determination is the ratio X_C/R, with X_C/R<0.80 at 50 kHz indicating failed contact. For multiple frequencies, the relationship between the phases at each frequency is used to make the contact determination. Particularly, as frequency increases, the phase of the impedance reduces. If the measured phase at one frequency is larger than a measured phase at a lower frequency, something other than skin is making contact.
The [0053] magnitude module 134 obtains an impedance magnitude |Z| from the bipolar measurement, the magnitude given by $\begin{matrix} \langle Z \rangle = \langle V / I \rangle \\ = \sqrt{R^{2} + X_{C}^{}} \end{matrix}$
The [0054] quality module 138 uses the magnitude |Z| calculated by the magnitude module 134 to determine the quality of the conductive hydrogel in electrode 124 and/or 126. For example, as the electrodes are exposed to heat or air, the gel dries, decreasing its conductivity. This causes a significant increase in the magnitude of the bipolar impedance measured between electrodes 124 and 126. For example, at 50 kHz measurement, a magnitude greater than 1800 ohms has been found to indicate significant hydrogel deterioration.
Thus, the [0055] first measurement unit 106 makes bipolar measurements that allow the electrode assessment module 108 to determine a) whether the electrodes 124 and 126 are in adequate contact with the skin, as ascertained from the phase information and b) whether the conductive quality of the hydrogel component of electrodes 124 and 126 has been maintained or has deteriorated, as ascertained from the impedance magnitude. It should be understood that the electrode-to-skin contact of other electrodes can also be assessed. For this purpose, another bipolar measurement can be performed using another two electrodes on another arm of the electrode array to provide information about the suitability of the contact, and so on.
FIG. 4 shows a graphical user interface (GUI) that illustrates the status of the electrode-to-skin contact. A [0056] display 150 shows two representations 152 and 154 of electrode arrays 102, the representation 152 of the right breast array and the representation 154 of the left breast array. Each electrode array representation has twelve arms 156. In another embodiment, each electrode array representation has sixteen arms. The colour of the circles 158 indicates which electrodes have been ascertained to be in contact with the skin. In one embodiment, a red circle indicates an inadequate contact, and a blue circle indicates an adequate one. Other indicators are possible, such as flashing circles representing inadequate contacts. For the purposes of explanation, white circles represent electrodes making adequate contact, and black circles represent those that are not. This determination is made by the contact module 136.
The [0057] quality module 138, furnishes its information at the bottom of the display. Here, a bar 160 is shown with various levels of electrode quality with, in this example, three usable level—excellent, Good, and Pass—and one unacceptable level—Replace. If the quality is excellent, for example, then the word “Excellent” is highlighted on the bar 160.
Both electrode contact and quality information are made available to the user administering the diagnostic examination in real time. Thus, the user can take immediate steps to rectify a poor electrode-to-skin contact, or replace a deteriorated electrode, before proceeding with the diagnostic testing. The ability to display real time information is a direct result of using bipolar measurements for making the status determination. With bipolar measurements, one measurement relates to one electrode pair, and only the number of measurements as there air pairs is required to refresh the display. If tetrapolar measurements were used to make the contact determination, each measurement would include four electrodes and many sets of measurements per pair would be required to make the contact determination. Performing all of these measurements would take much longer. [0058]
The [0059] display 150 shown can be a computer or television monitor. In other embodiments, LED lights can signal electrode status.
If the results of the [0060] electrode assessment module 108 indicate that the status of the plurality of electrodes 104 is suitable, then the system 100 can proceed to the diagnosis stage. The second measurement unit 110 injects a first current between a first pair of the n_CIcurrent injection electrode pairs, and then measures the resultant voltage difference V₁ ^Mbetween a voltage measurement electrode pair. In a preferred embodiment, if current travels from a current injection electrode of a first arm to a current injection electrode of a second arm, then the voltage difference is measured between the voltage measurement electrodes of the same two arms. In FIG. 2B, for example, current can flow between electrodes 124 and 128. The associated resultant voltage is measured between electrodes 126 and 130. Thus, n_CIcurrent injections are possible with an equal number of associated voltage measurements. By repeating the above described current injection and voltage measurement n_CI−1 more times each, a total of n_CIvoltage differences, {V₁ ^M, V₂ ^M, . . . , V_n _CI ^M} are obtained.
The impedance module [0061] 112 uses the n_CIvoltage differences to obtain associated measured impedances, {Z₁ ^M, Z₂ ^M, . . . , Z_n _C ^IM} where Z_j ^Mis the measured impedance between the voltage electrodes associated with the jth current injection electrode pair.
The [0062] diagnosis module 114 utilizes the measured impedances, {Z₁ ^M, Z₂ ^M, . . . , Z_n _CI ^M} to diagnose the possibility of disease. For example, U.S. Pat. No. 6,122,544 describes a method that compares impedances between homologous body parts. In this method, the impedance of a body part of a patient is compared to the impedance of the homologous body part of the same patient. A difference between these two impedances could signal disease.
As described above, the [0063] system 100 employs both tetrapolar and bipolar measurements to assess the quality of electrode contact. A diagnostic system 1000 capable of both these types of measurements will now be described.
FIG. 5 shows a [0064] system 1000 for measuring a voltage in a body part 110, such as a human breast. The system 1000 includes N body leads 120. In what follows, the N body leads 120 are ordered from 1 to N for reference. The system 1000 also includes a multiplexing unit 140 having a multiplexer 160, a first MX lead 180, a second MX lead 200, a third MX lead 220 and a fourth MX lead 240.
The [0065] system 1000 further includes a controller switching unit 260 having a first switch 280 connected to the multiplexer 160 by the first MX lead 180 and the second MX lead 200, a second switch 300 connected to the multiplexer 160 by the third MX lead 220 and the fourth MX lead 240, a current input lead 320 connected to the first switch 280, a current output lead 340 connected to the second switch 300, a first voltage lead 360 connected to the first switch 280, and a second voltage lead 380 connected to the second switch 300. The controller switching unit 260 also includes a controller 390. The system 1000 further includes an impedance module 400 and a diagnosis module 420.
Also shown in FIG. 5 is an optional second set of [0066] leads 440 that can be used when making measurements on a second homologous body part 460. The description below is directed mainly to an impedance measurement on the one body part 110 with the set of N leads 120, but it should be understood that the discussion could be analogously expanded to include an impedance measurement on the second homologous body part 460 with the second set of leads 440. Thus, the principles of the present invention can be applied to diagnosis of disease by making electrical measurements on a single body part, or by making measurements on a homologous pair of body parts. When making measurements on only a single body part, the results can be compared to standard results obtained from population studies, for example, to diagnose disease. When using a homologous pair of body parts, the results of one body part can be compared to the results of the homologous body part of the same patient, as described in U.S. Pat. No. 6,122,544.
The N body leads [0067] 120 electrically connect the multiplexing unit 140 to the body part 110. Each of the N body leads 120 includes a wire capable of carrying a current and an electrode to attach to the body part 110. A current conducting gel can act as an interface between the electrode and the skin covering the body part 110.
The multiplexing unit [0068] 140 and the controller switching unit 260 allow a current to flow through the body part 110 between any two body leads, n₁and n₂, of the N body leads 120, and a resultant voltage to be measured between any two body leads, n₃and n₄of the N body leads 120, where n₁≠n₂and n₃≠n₄, but where n₁, n₂, n₃and n₄need not otherwise be distinct. Thus, n₁, n₂, n₃, and n₄are numbers belonging to the set {1, 2, . . . , N} that identify body leads. For example, if n₁=7, then n₁denotes the seventh body lead from among the N body leads 120 used to inject current into the body part 110.
The [0069] impedance module 400 generates current that is injected into the current input lead 320 and then delivered to the body part. The current output lead 340 receives the current from the body part. When the current is traveling through the body part, the first voltage lead 360 and the second voltage lead 380 are used to measure the resultant voltage between these leads 360 and 380. The impedance module 400 uses this voltage, together with the known current injected into the current input lead 320, to calculate a corresponding impedance, which may then be used by the diagnosis module 420 to diagnose disease.
In one embodiment, N is even and the [0070] multiplexer 160 can electrically connect the first MX lead 180 and the fourth MX lead 240 to a first set of N/2 of the N leads, and the second MX lead 200 and the third MX lead 220 to a second set of the other N/2 leads. In a conventional system, the first set of N/2 leads are exclusively used to inject current into and receive current from the body part. The second set of N/2 leads are then exclusively used to measure resultant voltages in tetrapolar measurements. This configuration limits the number of impedances that can be measured.
In the [0071] system 1000, however, the second set of N/2 leads can also be used to inject and receive current, and the first set can be used to measure resultant voltages. Thus, the system 1000 can furnish a greater number of impedances. Moreover, as detailed below, the system can make both tetrapolar and bipolar measurements. The added benefits arise from the functionality of the controller switching unit 260. By using the controller switching unit 260, the system 1000 can force current to flow through the body part 110 between any two body leads, n₁and n₂, of the N body leads 120, and a resultant voltage to be measured between any two body leads, n₃and n₄of the N body leads 120, where n₁≠n₂and n₃≠n₄.
FIGS. [0072] 6A-D show several states of the switches 280 and 300 resulting in different modes of the controller switching unit 260 of the system of FIG. 5. These states of the switches 280 and 300 are controlled by the controller 390. In FIG. 6A, current is injected into the first MX lead 180 and received by the fourth MX lead 240. While this current travels through the body part 110, a resultant voltage is measured between the second MX lead 200 and the third MX lead 220. This measurement is tetrapolar because current is forced to flow between two leads and the resultant voltage is measured between two other leads.
In FIG. 6B, current is injected into the [0073] second MX lead 200 and received by the third MX lead 220. The resultant voltage is measured between the first MX lead 180 and the fourth MX lead 240. This measurement is also tetrapolar.
In FIGS. 6A and 6B, the [0074] first switch 280 and the second switch 300 are both in tetrapolar states since, for each of the switches 280 and 300, two distinct MX leads are involved in the impedance measurement. When both switch states are tetrapolar, the controller switching unit 260 is said to be in a tetrapolar mode. Thus, FIGS. 6A and 6B correspond to tetrapolar modes.
In a tetrapolar mode, the [0075] current input lead 320 is electrically connected to exactly one of the first MX lead 180 and the second MX lead 200 and the first voltage lead 360 is electrically connected to the other one of the first MX lead 180 and the second MX lead 200; likewise, the current output lead 340 is electrically connected to exactly one of the third MX lead 220 and the fourth MX lead 240 and the second voltage lead 380 is connected to the other one of the third MX lead 220 and the fourth MX lead 240.
The two tetrapolar modes shown in FIGS. 6A and 6B do not exhaust all the tetrapolar modes. For example, when the [0076] first switch 280 state is the same as the state shown in FIG. 6A and the second switch 300 state is the same as the state shown in FIG. 6B, the controller switching unit 260 is also in a tetrapolar mode. Generally, the controller switching unit 260 is in a tetrapolar mode when n₁, n₂, n₃and n₄are distinct, where n₁and n₂are leads from among the N leads 120 used to inject current into and receive current from the body part 110, and n₃and n₄are leads used to measure the resultant voltage.
In FIG. 6C, current is injected into the [0077] first MX lead 180 and received by the fourth MX lead 240. While this current travels through the body part 110, a resultant voltage is measured between the first MX lead 180 and the fourth MX lead 240. The second and third MX leads 200 and 220 are electrically unconnected to any of the N body leads 120 during this measurement. This measurement is bipolar because the pair of electrodes used for measuring a voltage is also used for current flow.
In FIG. 6D, current is injected into the [0078] second MX lead 200 and received by the third MX lead 220. The resultant voltage is measured between the same two leads 200 and 220. The first and fourth MX leads 180 and 240 are electrically unconnected during this measurement. This measurement is also bipolar.
In FIGS. 6C and 6D, the [0079] first switch 280 and the second switch 300 are both in bipolar states since, for each of the switches 280 and 300, only one MX lead is involved in the impedance measurement. When both switch states are bipolar, the controller switching unit 260 is said to be in a bipolar mode. Thus, FIGS. 6C and 6D correspond to bipolar modes.
In a bipolar mode, the [0080] current input lead 320 and the first voltage lead 360 are electrically connected to each other and to exactly one of the first MX lead 180 and the second MX lead 200, and the current output lead 340 and the second voltage lead 380 are electrically connected to each other and to exactly one of the third MX lead 220 and the fourth MX lead 240.
The two modes shown in FIGS. 6C and 6D do not exhaust all bipolar modes. For example, when the [0081] first switch 280 state is the same as the state shown in FIG. 6C and the second switch 300 state is the same as the state shown in FIG. 6D, the controller switching unit 260 is also in a bipolar mode. More generally, the controller switching unit 260 is in a bipolar mode when n₁=n₃or n₄, and n₂=n₃or n₄, where n, and n₂are leads from among the N leads 120 used to inject and receive current, and n₃and n₄are leads used to measure the resultant voltage.
In addition to the tetrapolar and bipolar modes shown in FIGS. 6A-6D, there are also hybrid modes. FIG. 7 shows a hybrid mode of the [0082] controller switching unit 260 of FIG. 5. Here, the first switch 280 is in a tetrapolar state and the second switch 300 is in a bipolar state. In a hybrid mode, n₁≠n₃and n₂=n₄, or n₁≠n₄and n₂=n₃, where again n₁and n₂are used for current flow and n₃and n₄are used for voltage measurement.
In FIG. 7, the lead n, is electrically connected to the [0083] first MX lead 180 or to the fourth MX lead 240 via the multiplexer 160. The lead n₂is connected to whichever of first MX lead 180 and the fourth MX lead 240 is not connected to the lead n₁. The lead n₃is connected to the second MX lead 200 or the fourth MX lead 240, and the lead n₄is connected to whichever of the second MX lead 200 and the fourth MX lead 240 is not connected to the n₃lead. The third MX lead 220 is electrically unconnected during this hybrid measurement.
FIG. 8 shows electrical connections in a particular tetrapolar impedance measurement that employs the [0084] system 1000 of FIG. 5. For simplicity, the system 1000 has only N=10 leads, and the controller 390, the impedance module 400 and the diagnosis module 420 are not shown. In a different embodiment, N=32. Also not shown in the FIG. 8 is the second set of leads 440. The ten electrodes of the ten leads are shown: the first set of N/2=five electrodes 1-5 lie on the outside perimeter and the other set of five electrodes 6-10 lie on the inner perimeter.
All the electrodes 1-5 of the first set can be electrically connected to the first and fourth MX leads [0085] 180 and 240, and all the electrodes 6-10 of the second set can be connected to the second and third MX leads 200 and 220 via the multiplexer 160. In the example of FIG. 8, the connections shown are for one tetrapolar measurement in which n₁=6, n₂=9, n₃=2 and n₄=5, where electrode 60 is used to inject current into the body part 110 and electrode 90 is used to receive the current. The electrodes 2 and 5 are used to measure the resultant voltage. Although all electrodes of the ten leads are shown in FIG. 8, only the four wires of the electrically active leads appear.
In particular, current is generated by the [0086] impedance module 400 and sent to the current input lead 320. From there, the current travels to the first MX lead 180 via the first switch 280 and from there to the electrode 6 via the multiplexer 160. The current next travels through the body part 110 to the electrode 9 and then through the multiplexer 160 to the fourth MX lead 240. The current then flows to the current output lead 340 via the second switch 300 and then back to the impedance module 400. The resultant voltage is measured between the first and second voltage leads 360 and 380, which corresponds to the voltage between the electrodes 2 and 5. The first voltage lead 360 is connected to the electrode 2 via the first switch 280 and the multiplexer 160, and the second voltage lead 380 is electrically connected to the electrode 5 via the second switch 300 and the multiplexer 160. The controller 390 controls the states of the switches 280 and 300 and the multiplexing states in the multiplexer 160 that determine through which leads current flows and which leads are used to measure voltage.
FIG. 9A shows the [0087] multiplexer 160 of FIG. 5 in an embodiment in which a body part is being compared to a homologous body part. The multiplexer 160 includes a first body part multiplexer 520 that includes a first body part A multiplexer unit 540 and a first body part B multiplexer unit 560. The multiplexer 160 also includes a second body part multiplexer 580 that includes a second body part A multiplexer unit 600 and a second body part B multiplexer unit 620. The first body part A multiplexer unit 540 is connected to the first MX lead 180 and the fourth MX lead 240. The first body part B multiplexer unit 560 is connected to the second MX lead 200 and the third MX lead 220. Although not shown in the interest of clarity, the second body part A multiplexer unit 600 is also connected to the first MX lead 180 and the fourth MX lead 240, and the second body part B multiplexer unit 620 is also connected to the second MX lead 200 and the third MX lead 220.
The first body part multiplexer [0088] 520 is used for multiplexing electrical signals to the first body part of the homologous pair. In particular, the first body part A multiplexer unit 540 and B multiplexer unit 560 are both capable of multiplexing current and voltage signals to and from the N leads 120. Likewise, the second body part multiplexer 580 is used for multiplexing electrical signals to the homologous body part. In particular, the second body part A multiplexer unit 600 and B multiplexer unit 620 are both capable of multiplexing current and voltage signals to and from the N leads 120, as described below.
FIG. 9B shows the first body part [0089] A multiplexer unit 540 of FIG. 9A. The multiplexer unit 540 includes four one-to-N/4 multiplexers 640, 660, 680 and 700. These, for example, can be model number MAX4051ACPE manufactured by MAXIM™. The N/4 multiplexer current leads 720 connect the multiplexer 640 to the multiplexer 680, and N/4 multiplexer current leads 740 connect the multiplexers 660 and 700. In turn, the leads 720 and 740 are connected to the first N/2 of the N leads 120. The multiplexers 640, 660, 680 and 700 each have a configurable one bit “inhibit state” and log₂(N/4) bit “control state.” The inhibit state can be either off (0) or on (1) and determines whether current can flow through the respective multiplexer 640, 660, 680 or 700. The control state determines through which one of the leads 720, 740 current flows. If N=32, then four bits are required for each active multiplexer (by “active” is meant that the inhibit state is off) and to specify a state, one for the inhibit state and three for the control state. For example, if the inhibit state of the multiplexer 640 is 1 (on) and the state of the multiplexer 660 is (0,0,0,1), where the first bit is for the inhibit state, and the last three bits identify which lead of multiplexer 660 is being activated, then current destined for the breast is directed to the tenth lead, provided the states of the switches 280 and 300 connect the current input lead 320 to the first MX lead 180, as previously described. If the states of the switches 280 and 300 do not connect the current input lead 320 to the first MX lead 180, but do connect the first voltage lead 360 to the first MX lead 180, then this lead 180, when the multiplexer 660 is in the state (0,0,0,1), measures the resultant voltage with the tenth lead.
A similar binary code for the [0090] multiplexers 680 and 700 dictates through which one of the first 16 electrodes of the 32 leads 120 current is received from the breast, provided the states of the switches 280 and 300 connect the current output lead 340 to the fourth MX lead 240. If the fourth MX lead 240 is not connected to the current output lead 340, but is connected to the second voltage lead 220, then the fourth MX lead 240 is used for measuring the resultant voltage, provided the inhibit state of the multiplexer 680 or the multiplexer 700 is off.
The [0091] B multiplexer unit 560 is similar to the A multiplexer unit 540 in that it has four one-to-N/4 multiplexers analogous to 640, 660, 680 and 700. However, the one-to-N/4 multiplexers are capable of connecting with the second and third MX leads 200 and 220, instead of the first and fourth MX leads 180 and 240. Here, the inhibit and control states determine which electrode from among the other N/2 electrodes is used to deliver current or measure voltage.
Thus, by setting inhibit and control states, in coordination with the states of the [0092] switches 280 and 300, it is possible to direct current between any pair of the N leads 120 and to make a measurement of the resultant voltage between any pair of the N leads 120.
The inhibit and control states are set by the [0093] controller 390 with a shift-register and/or a computer. A direct digital stream can be sent to the shift register for this purpose.
The function of the second [0094] body part multiplexer 580 is analogous to that of the first body part multiplexer 520 and therefore need not be described further.
FIG. 10 shows a [0095] diagnostic system 820 that includes an internal load 840 in addition to the components described above in relation to FIG. 5. The internal load 840 is electrically connected to the first MX lead 180, the second MX lead 200, the third MX lead 220 and the fourth MX lead 240. The internal load 840 is used for at least one of internal testing of the system 820 and varying the measurement range of the system 820.
Using the [0096] first switch 280 and the second switch 300, the internal load 840 can be connected to the impedance module 400 in a tetrapolar mode or in a bipolar mode. The internal load 840 has a known impedance and therefore can be used to test the diagnostic system 820.
Additionally, the [0097] internal load 840 can be used to change the measurement range of the system 820. By attaching this internal load 840 in parallel with any load, such as the body part 110, the system 820 is capable of measuring larger impedances than would otherwise be possible. If the resistance of the internal load 840 is R_intand is in parallel, the measured resistance R is given by
R=(1/R _load+1/R _int)⁻¹
where R[0098] _loadis the resistance of the load. Consequently, the measured resistance is reduced from the value without the internal load, thereby increasing the measurement range of the system 840.
The [0099] switches 280 and 300 allow current to flow between various pairs of electrodes on a body part, and resultant voltage to be measured between various pairs of electrodes, as described above with reference to FIGS. 5-10. In FIG. 11, another embodiment of the controller switching unit is shown that can be used to achieve the states of FIGS. 6A-D using a different electrical circuit topology. The controller switching unit 900 of FIG. 11 includes a first switch 920 and a second switch 940. The current input lead 320, the current output lead 340, the first voltage lead 360 and the second voltage lead 380 split to connect to both the first and second switches 920 and 940.
The [0100] switches 920 and 940 can be turned on or off and can be used to make tetrapolar and bipolar measurements. With only one of the switches 920 and 940 on, a tetrapolar measurement can be made. With both switches 920 and 940 on, a bipolar measurement can be made. For example, when the first switch 920 is on, and the second switch is off, the resultant functionality corresponds to that of FIG. 6A, albeit achieved with a different circuit topology. In this example, current flows from the impedance module 400 along the current input lead 320, through the first switch 920, and then to the first MX lead 180. From there, the current proceeds to the multiplexer 160. Current is received from the multiplexer 160 along the fourth MX lead, and delivered to the current output lead 340 via the first switch 920. The resultant voltage is measured between the second and third MX leads 200 and 220 with the use of the first and second voltage leads 360 and 380.
In another example, when the [0101] first switch 920 is off, and the second switch 940 is on, the resultant functionality corresponds to that of FIG. 6B. Here, current from the impedance module 400 travels along the current input lead 320, across the second switch 940, then jumps to the second MX lead 200. Current is received along the third MX lead 220, from where it jumps to the current output lead 340 via the second switch 940. The voltage is measured between the first and fourth MX leads 180 and 240 with the use of the first and second voltage leads 360 and 380.
In yet another example, the first and [0102] second switches 920 and 940 are both on, which corresponds to FIG. 6C or 6D. Precisely to which of these two figures this example corresponds is determined by the inhibit states of the multiplexer 160. For example, if the inhibit states of both of the one-to-N/4 multiplexers 640 and 660 are on, then bipolar measurements are performed with the second set of N/2 electrodes.
The [0103] controller switching unit 900 also includes an internal load switch 1080 that is connected to the internal load 840. The controller switching unit 900 and the internal load 840 are used to test the system and to increase the measurement range, as described above.
It should be understood that various modifications could be made to the embodiments described and illustrated herein, without departing from the present invention, the scope of which is defined in the appended claims. The present invention involves the use of an electrode array for measuring impedances of a breast to determine the condition thereof. However, although emphasis has been placed on describing a system for diagnosing breast cancer, the principles of the present invention can also be advantageously applied to other diseases of other body parts. [0104]

Claims

What is claimed is:

1. A method for diagnosing the possibility of disease in a body part, the method comprising

providing an electrode array containing a plurality of electrodes capable of being electrically coupled to the body part;

making an electrode assessment measurement with the electrode array;

determining whether the plurality of electrodes are suitably coupled to the body part based on the electrode assessment measurement;

making a diagnosis measurement with the electrode array;

obtaining an electrical property of the body part based on the diagnosis measurement; and

diagnosing the possibility of disease based on the electrical property of the body part.

2. The method of claim 1, wherein the plurality of electrodes includes a current injection electrode pair and an associated voltage measurement electrode pair, the method further comprising, before the step of making an electrode assessment measurement,

applying the current injection electrode pair to the body part; and

applying the associated voltage measurement electrode pair to the body part.

3. The method of claim 2, wherein the step of making an electrode assessment measurement includes utilizing one current injection electrode of the current injection electrode pair and one proximal voltage measurement electrode of the voltage measurement electrode pair to make a bipolar measurement.

4. The method of claim 3, wherein the step of determining whether the plurality of electrodes are suitably coupled includes

computing a phase φ, whose absolute value is given by

|φ|=|tan⁻¹ [X _C(ω)/R]|

where X_C(ω) is a capacitive reactance at an alternating frequency, ω, of a current injected during the bipolar measurement, and R is a resistance associated with the body part; and

if the phase is outside a threshold range, determining that at least one of the current injection electrode and the voltage measurement electrode is not in electrical contact with the body part.

5. The method of claim 4, wherein the step of determining whether the plurality of electrodes are suitably coupled further includes

computing a magnitude Z given by

Z = \langle \frac{V}{I} \rangle,

where I is the current and V is a resultant voltage measured during the bipolar measurement; and

determining quality of electrical contact of the current injection electrode and the voltage measurement electrode with the body part based on the magnitude.

6. The method of claim 3, wherein the step of determining includes using a phase, which is a function of the capacitive reactance and the resistance, at a particular frequency, and other phases at other frequencies to establish that at least one of the current injection electrode and the voltage measurement electrode is not in electrical contact with the body part.

7. The method of claim 1, wherein the plurality of electrodes includes n_CIcurrent injection electrode pairs, and n_CIassociated voltage measurement electrode pairs, where n_CIis an integer greater than zero.

8. The method of claim 7, wherein the step of making a diagnosis measurement includes

applying the n_CIcurrent injection electrode pairs on the body part; and

applying the n_CIvoltage measurement electrode pairs on the body part.

9. The method of claim 8, wherein the step of making a diagnosis measurement further includes

injecting a first current between a first pair of the n_CIcurrent injection electrode pairs;

measuring the resultant voltage difference V₁ ^Mbetween the voltage measurement electrode pair associated with the first current injection electrode pair; and

repeating the preceding two steps of injecting and measuring with the other electrode pairs until all n_CIvoltage differences, {V₁ ^M, V₂ ^M, . . . , V_n _CI ^M} are obtained.

10. The method of claim 9, wherein the electrical property is impedance.

11. The method of claim 10, wherein the step of obtaining includes using the n_CIvoltage differences to obtain associated measured impedances, {Z₁ ^M, Z₂ ^M, . . . , Z_n _C ^LM}, where Z_j ^Mis the measured impedance between the voltage electrodes associated with the jth current injection electrode pair.

12. The method of claim 1, further comprising indicating a status of the coupling between the plurality of electrodes and the body part with a graphical user interface.

13. A system for diagnosing the possibility of disease in a body part, the system comprising

an electrode array containing a plurality of electrodes capable of being electrically coupled to the body part;

a first measurement unit for making an electrode assessment measurement with the electrode array;

an electrode assessment module for determining whether the plurality of electrodes are suitably coupled to the body part based on the electrode assessment measurement;

a second measurement unit for making a diagnosis measurement with the electrode array; and

an electrical property module for obtaining an electrical property of the body part based on the diagnosis measurement, wherein the electrical property is used to diagnose the possibility of disease.

14. The system of claim 13, wherein the plurality of electrodes includes a current injection electrode pair and an associated voltage measurement electrode pair that are applied to the body part.

15. The system of claim 14, wherein one current injection electrode of the current injection electrode pair and one proximal voltage measurement electrode of the voltage measurement electrode pair are used by the first measurement unit to make a bipolar measurement.

16. The system of claim 15, wherein the electrode assessment module includes

a phase module for obtaining a phase, φ, from the bipolar measurement, whose absolute value is given by

|φ|=|tan⁻¹ [X _C(ω)/R]|

a contact module for determining that at least one of the current injection electrode and the voltage measurement electrode is not in electrical contact with the body part if the phase is outside a threshold range.

17. The system of claim 16, wherein the electrode assessment module includes

a magnitude module for computing a magnitude, Z, from the bipolar measurement, the magnitude given by

Z = \langle \frac{V}{I} \rangle,

a quality module for determining quality of electrical contact of the current injection electrode and the voltage measurement electrode with the body part based on the magnitude.

18. The system of claim 15, wherein the electrode assessment module includes

a phase module for obtaining a phase that is a function of a capacitive reactance, at a particular frequency, and a resistance, associated with the body part, and for obtaining other phases at other frequencies; and

a contact module for determining that at least one of the current injection electrode and the voltage measurement electrode is not in electrical contact with the body part based on the phase at the particular frequency and the other phases at the other frequencies.

19. The system of claim 13, wherein the plurality of electrodes includes n_CIcurrent injection electrode pairs and n_CIassociated voltage measurement electrode pairs that are applied to the body part.

20. The system of claim 19, wherein the second measurement unit injects a first current between a first pair of the n_CIcurrent injection electrode pairs, measures the resultant voltage difference V₁ ^Mbetween the voltage measurement electrode pair associated with the first current injection electrode pair, and repeats the preceding two steps of current injection and voltage difference measurement with the other electrode pairs until all n_CIvoltage differences, {V₁ ^M, V₂ ^M, . . . , V_n _CI ^M} are obtained.

21. The system of claim 20, wherein the electrical property is impedance, and the electrical property module is an impedance module.

22. The system of claim 21, wherein the impedance module uses the n_CIvoltage differences to obtain associated measured impedances, {Z₁ ^M, Z₂ ^M, . . . , Z_n _CI ^M}, where Z_j ^Mis the measured impedance between the voltage electrodes associated with the jth current injection electrode pair.

23. The system of claim 22, further comprising a diagnosis module for utilizing the measured impedances, {Z₁ ^M, Z₂ ^M, . . . , Z_n _CI ^M} to diagnose the possibility of disease.

24. The system of claim 13, further comprising a graphical user interface to indicate a status of the coupling between the plurality of electrodes and the body part.