Multiple electrode strip

Field of the Invention

The invention relates to monitoring systems and, in particular, to an electrode strip for use in monitoring electrical activities of a living body.

Background of the Invention

Conventional electrocardiography is concerned with the measurement and analysis of voltage potential readings taken from a limited number of anatomically defined locations. The voltages between various locations are combined to form electrocardiograph (ECG) leads that are represented as waveforms and are compared to clinically developed criteria to diagnose or classify the state of a person's heart. One type of conventional electrocardiographic system has focused on the application of ten electrodes to a person's skin; six across the precordial or chest area of the person and one on each of the arms and legs. This type of system is typically called the standard 12-lead ECG system. The electrodes are commonly attached to the body by a conductive gel within an adhesive structure, or by a gel which is both conductive and adhesive.

More recently, electrocardiologists have been experimenting with a body surface potential mapping technique as a tool in scientific investigations and in improving clinical diagnosis of heart disease. In body surface potential mapping, a large number of electrodes are applied to a person's torso to obtain an estimate of the total body surface distribution of cardiac-generated potentials. This distribution is commonly displayed as a series of isopotential contours plotted on a map that represents the person's torso. The resultant isopotential map is then evaluated for the presence of features representing the particular cardiac characteristic of interest.

Proper electrode placement is a major concern in electrocardiography. More particularly, to allow a person's ECG data to be meaningfully compared to clinical data obtained from known populations, the electrode readings must be made at uniformly defined, anatomical locations. Proper placement poses difficulties, in part, because the electrodes must be positioned on people of different sizes. In body surface mapping, the desired electrode sites are arranged in a number of columns and rows, with some mapping systems utilizing as many as 240 body surface electrodes. Thus, proper electrode placement may be further complicated by the large number of electrodes to be attached.

In an attempt to alleviate electrode placement problems, a number of electrocardiograph electrode systems have been developed. One type of system such as that described in US 4 353 372 simply uses individual electrodes whose relative positions are unconstrained by the separate and distinct conductive wires that couple the electrodes to a cable that is connected to monitoring equipment. Thus, this system allows individual positioning of the electrodes upon the subject person. A second type of system such as that described in US 4 854 323 provides a number of electrodes directly attached to a cable, with differently proportioned electrode-cable sets used with different-sized bodies. Other systems implement a cable or harness whereby individual electrodes attached thereto can be selectively positioned along the cable or harness structure. In one device, the electrodes are connected with spring clips to the harness allowing individual electrodes to be slidingly positioned along the harness.

The electrode arrangements described above are generally cumbersome to use and are often relatively expensive. The time required for proper placement with the more cumbersome prior art systems can be particularly important in emergency situations or when a large number of electrodes are required, for example, to perform body surface mapping. Care must be exercised with a system utilizing a separate lead for each individual electrode so that individual electrodes do not become entangled, a problem that can increase the chance that any given electrode will be placed in the wrong position, particularly in emergency situations. If differently-sized electrode-cable sets are to be used to compensate for differences in body sizes, an electrocardiologist must have electrode-cable sets of several sizes at his or her fingertips. More important, the person charged with placement of electrodes is also required to select the proper size and accurately place the electrodes onto the body in a minimum amount of time. Even then, the electrode-cable set selected may riot allow accurate electrode placement on persons between two sizes or at each end of the spectrum of average-sized bodies. Devices utilizing a scheme whereby the individual electrodes can be slidably positioned along an electrode cable or harness are disadvantageous in their bulk and complexity, and again, are not particularly well suited for body surface potential mapping because of the large number of electrodes required.

As can be seen, there is a continuing need to provide an electrode device which allows accurate and timely placement of individual electrodes on the body of a person, whether it can be conventional electrocardiography or a technique utilizing body surface potential mapping, while reducing the complexity and cost of the device.

We are aware of WO-A-90-1898 which comprises the pre-characterising portion of Claim 1.

According to our invention, in an electrode strip according to the pre-characterising portion of claim 1, a region of extensibility is defined in the substrate between a pair of adjacent electrodes sites and the layer of material causes the regions of extensibility to tend to retain any shape induced upon them.

This allows selective positioning of the adjacent electrode sites on the body.

The electrode strip further includes conductive elements for providing an electrical path to each electrode site.

An electrode strip in accordance with the present invention is a unitary strip for measuring the electrical activities of the heart or other bioelectrical events of a body while still providing a degree of flexibility in the positioning of individual electrodes. A plurality of regions of extensibility in the strip provide adaptive spacing between electrodes. The electrode strip is a potentially disposable alternative to costlier and less manageable cables known in the art. In addition, a number of electrode strips can be configurated to be simultaneously and conveniently placed on a patient for use in applications such as body surface potential mapping.

In a preferred embodiment of the invention, the electrode strip includes a layer malleable material attached to the substrate. The malleable material provides nonelastic extensibility out of the inextendible substrate. The electrode strip includes a plurality of spaced-apart conductors, each one of which extends from the connector area to an individual conductive element at each of the electrode sites. The electrode strip further includes a plurality of dielectric cover layers, a different one of which extends over each conductor.

In one disclosed embodiment of the invention, each region of extensibility is formed by a plurality of transverse folds in the electrode strip to allow adaptive spacing between adjacent apertures. Each fold, in cross section, defines a U-shaped section in the substrate. Other illustrative configurations that can be employed as the regions of extensibility are disclosed.

In currently preferred embodiments of the invention, the conductors are formed on a substrate of polyester resin. Each electrode site is connected to a conductive gel pad which has an adhesive surface to contact a body. A protective release liner is included to protect the adhesive surface of each gel pad prior to attaching the strip to the body.

Brief Description of the Drawings

The various features and advantages of the invention will be understood in view of the following detailed description taken in conjunction with the following drawings in which: <ul id="ul0001" list-style="none" compact="compact"><li>FIGURE 1 is a perspective view of a exemplary embodiment of an electrode strip of the present invention shown in a operative position on a person, with electrodes located at a plurality of precordial and limb sites;</li><li>FIGURE 2 is a top elevation view of the electrode strip of FIGURE 1 prior to the formation of regions of extensibility between adjacent electrode sites;</li><li>FIGURE 3 is an elevation view of the electrode strip of FIGURE 1;</li><li>FIGURE 4 is an exploded view of a section of the electrode strip of FIGURE 1;</li><li>FIGURE 5 illustrates a alternative means for connecting the electrode sites of the electrode strip of FIGURE 1 or FIGURE 1 to monitoring equipment;</li><li>FIGURE 6 is a perspective view of a body surface potential mapping assembly utilizing a number of electrode strips in accordance with the invention;</li><li>FIGURE 7 is a schematic view of the body surface potential mapping assembly shown in FIGURE 6 and illustrating the placement of the electrode sites along a plane superimposed on a person;</li><li>FIGURE 8 is a perspective view of a connector used to couple the electrode strip to medical and diagnostic equipment; and</li><li>FIGURE 9 is an exploded perspective view of the connector of FIGURE 8.</li></ul>

Detailed Description

In accordance with the present invention, the electrode strip provides a relatively inexpensive and potentially disposable device for measuring the activities of the heart and other muscles and organs of a body while including electrodes which can be selectively positioned to accommodate different-sized bodies.

FIGURES 1-3 illustrate an exemplary electrode strip 100 constructed in accordance with the invention. Electrode strip 100 is tailored for use with a standard 12-lead ECG system, wherein six electrodes are placed across the chest of a person at precordial placement positions V₁-V₆ and four electrodes are placed on the arms and legs (or torso) at right arm RA, left arm LA, left leg LL, and right leg RL placement positions. As is shown most clearly in FIGURE 3, the electrode strip includes a plurality of regions of extensibility 102 that allow selective and adjustable spacing of the electrodes on the body of a person 18. The regions of extensibility 102 are suited to provide curvilinear bending, as well as longitudinal extension and contraction of the strip. Thus, the required curvature of strip 100 between the precordial placement positions is readily achieved.

A top, elevation view of the electrode strip 100 prior to formation of the regions of extensibility 102, is illustrated in FIGURE 2. The electrode strip 100 includes a substantially elongate substrate 104 that is separable into five substantially elongate sections 104a-104e along cut-lines 106. It is assumed in FIGURE 2 that the substrate 104 is transparent to allow the conductors and electrode sites on the lower, patient-side of the strip to be clearly shown. The entire substrate 104 may be formed of a single material and then cut along the cut-lines 106. In a preferred use, the cut-lines 106 are only perforated and the electrode strip 100 is packaged and sent to the end-user as a single, elongate piece, with each substrate section 104a-104e including the regions of extensibility 102 (not shown in FIGURE 2). During placement of the device, the substrate sections 104b-104e are then partially separated from each other at a first end 108 along the perforated cut-lines 106 and stretched to contact the limb placement positions RA, LA, LL and RL, respectively.

In a preferred configuration, the substrate 104 includes an end segment 110 that extends perpendicularly from a second end 112 of the electrode strip. A plurality of spaced-apart conductors 114 begin at the end segment 110, extend along the lower (patient-side) surface of the substrate 104, and terminate at spaced-apart locations along the electrode strip. Each conductor includes a circular-shaped area at the end segment 110, providing a sufficient surface area to allow contact by a connector clamp, described below. Opposite the connector end, i.e., at the terminating end, each conductor includes an elongate oval-shaped area of conductive material. Preferably, a second elongate oval-shaped layer 116 of conductive material is placed in electrical contact with the terminating end of each conductor 114 to form electrode Sites, i.e., precordial sites (V₁-V₆) and limb sites (RA, LA, LL and RL). Each oval-shaped layer 116 is then coupled to the person's skin, preferably through a conductive interface such as the gel pads 38. The conductors 114, including the circular-shaped beginning end and oval-shaped terminating end, are preferably formed of silver ink tracings. Excluding the ends, a suitable width for the conductors is a width on the order of 60 mils (1.5 mm).

With reference again to FIGURE 1, the conductors (not shown) couple electrical signals between the person 18 and medical and therapeutic equipment, for example, monitoring device 20 via a cable 118. The cable 118 includes at least ten conductive leads to couple each of the conductors of the electrode strip to the monitoring device 20. The cable 118 is releasably coupled to the electrode strip by a spring-loaded clamp 120 that is configured to mate with the end segment 110 of the strip. In one embodiment, the clamp includes at least ten conductive teeth, one for each conductor, with each tooth being coupled to a different one of the conductive leads in cable 118. When coupled to the end segment 110, the teeth engage their respective conductors in the circular-shaped area of each conductor (shown in FIGURE 2) and are held against the conductors by the spring housed within the clamp The clamp 120 is described and illustrated in greater detail in FIGURES 8 and 9 and accompanying text.

The particular arrangement of conductors 114, as they extend from end segment 110 to the precordial and limb electrode sites, is not of substantial importance as long as the conductors remain insulated from one another. In the particular embodiment shown in FIGURE 2, the conductors generally extend in a parallel fashion from the end segment toward the electrode sites.

The conductors on substrate section 104a extend from the end segment 110 along the substrate until reaching individual precordial electrode sites V₁-V₆. In that regard, the outermost conductors 114a and 114b (on substrate section 104a) extend to sites V₆ and V₅, respectively. The conductors 114c and 114d, adjacent the outermost conductors, extend to sites V₁ and V₃, respectively. The innermost conductors, 114e and 114f, extend to sites V₄ and V₂, respectively.

The conductors on substrate sections 104b-104e extend from the end segment 110 to the limb sites RA, LA, LL and RL, respectively. The substrate sections are relatively narrow as they extend from the end segment 110 to each limb site. At each limb site, however, the associated substrate section becomes wider and has a substantially square-shaped segment to accommodate the limb sites, i.e., including the oval-shaped layers 116. As the conductors extend from the end segment and reach the square-shaped segments, they form a right-angle out and away from the center of substrate 104a to intersect the limb sites RA, LA, LL and RL.

Each of the conductors 114 is insulated from the person by a separate dielectric cover layer 122. The cover layers 122 are preferably formed of a UV curable dielectric coating such as those manufactured by Acheson Colloids Company. The cover layers 122 are preferably deposited onto the electrode strip through a single silk screening process whereby only those areas needing insulation are covered. This method of dielectric placement is advantageous as it conserves dielectric material. As will be appreciated, the entire lower patient-side surface of the electrode strip, with the exception of the electrode sites and the end of each conductor, may be covered with a single dielectric layer if desired.

An exploded sectional view of the first end 108 of the substrate 104a is shown in FIGURE 4, including the conductors 114, oval-shaped layers 116 and cover layers 122. Only three of the cover layers 122 are shown in FIGURE 4. The cover layers are slightly wider than the conductors they insulate and extend from the end segment 110 to the oval-shaped layers 116. For example, if the conductors are 60 mils (1.5 mm) wide, the cover layers 122 are preferably on the order of 100 mils (2.5 mm) wide. As will be appreciated, the conductors may alternatively be insulated by a continuous layer of dielectric having a plurality of apertures extending orthogonally therethrough, and spaced along the dielectric at locations corresponding to the oval-shaped layers 116.

The electrode strip 100 is constructed by depositing or otherwise forming the conductors 114 on a lower (patient-side) surface 124 of the substrate 104. In this regard, various known processes such as painting, screen printing, vacuum coating or sputtering can be used. As an alternative method of forming the conductors 114, the substrate may be clad with a layer of conductive material in which the conductors are formed by conventional photolithographic and chemical etching techniques. The cover layers may also be formed using painting, screen printing, vacuum coating or sputtering techniques.

The substrate 104 itself is preferably formed of a polyester resin, such as that commercially available under the trade name Mylar®, being on the order of 3 mils (0.076 mm) thick. The substrate may also be formed of Kapton®, or other suitable material. The preferred length of the substrate section 104a is 23.75" (60 cm), with a distance of 3.75" (9.5 cm) between each precordial electrode site V₁-V₆. A suitable width for the substrate section 104a is 1.2" (3 cm), excluding end segment 110. A suitable length for the substrate sections 104b and 104e is 19.25" (49 cm). A suitable width for the substrate sections 104b-104e is on the order of 0.3" (7.6 mm).

Once the conductors 114 have been formed on the substrate 104, the oval-shaped layers 116 are deposited or otherwise placed onto the lower surface 124 of the substrate, with a different layer 116 being in electrical contact with each conductor 114. Although not depicted in FIGURE 2, the precordial and limb sites may be ionically coupled to a person's skin through a conductive interface. The oval-shaped layers 116 provide better contact with a conductive interface such as the gel pads 38, as opposed to simply having the end of the conductors 114 contact the interface. The oval-shaped layers 116 may also be of other shapes, for example, circular or of various thicknesses. The oval-shaped layers 116 are preferably of a silver/silver chloride compound. The silver/silver chloride layer converts the ionic current flow of the body into electron flow that the monitor can amplify in a chemically reversible manner which is well known to those skilled in the art. The conductors 114 could be formed of silver/silver chloride but are generally formed of silver which is more conductive and does not represent a source of chloride ions which would corrode the connector. The silver by itself does not bidirectionally transform ionic flow to electron flow. After deposition of the oval-shaped layers 116, the cover layers 122 are deposited or otherwise formed on the conductors 114 to insulate the portions of the conductors between the end segment 110 and each oval-shaped layer 116.

After formation of the conductors 114, oval-shaped layers 116 and cover layer 122, a band 126 of malleable metal or other material is attached to the upper surface 128 of each substrate section 104a-104e, i.e., opposite the conductors 114 (only substrate section 104a is shown in FIGURE 4). Each band 126 is somewhat narrower than the substrate section on which it is placed. The band attached to the substrate section 104a is significantly wider than the bands attached to substrate sections 104b-104e, although the bands have not been illustrated in FIGURE 3 for purposes of clarity in the illustration. In an actual embodiment, the bands 126 are formed of a dead-soft aluminum on the order of 6 mils (0. 15 mm) thick. Other malleable metals or plastics may also be used.

The bands 126 are attached, for example, by including a pressure-sensitive adhesive layer on one side thereof and firmly pressing the adhesive layer against the upper surface 128 of the electrode strip. The band 126 need not be a continuous band that extends the entire length of the substrate sections 104a-104e. Rather, it is useful in some applications to have sections of the band attached only to the areas upon which regions of extensibility are to be formed. Thus, for example, substrate section 104a would include five separate malleable bands, each separated by one of the electrode sites V₁-V₆.

The substrate 104, including the conductors 114, cover layers 122 and bands 126, is flexible but substantially inextendible along its length prior to formation of the regions of extensibility 102. The regions of extensibility 102 are formed into the substrate section 104a between pairs of adjacent precordial electrode sites V₁-V₆. Preferably, the regions of extensibility 102 are also formed into the substrate sections 104b-104e during the same process. However, it is noted that the regions of extensibility do not have to be formed into the substrate sections 104b-104e, but formation therein is often a manufacturing convenience. As will be appreciated, if regions of extensibility are not formed in the substrate sections 104b-104e, the band 126 may be omitted from these sections, if desired.

With reference again to FIGURE 4, the electrode strip 100 preferably includes gel pads 38, that are preattached to the area surrounding each electrode site. The gel pads 38 each have a lower surface 42 that provides ionic conductivity between the conductors 114 and a person's skin. An outer liner 44 protects the adhesive lower surface of the gel pads 38 and is removed just prior to attaching the strip to a body.

A preferred arrangement of the regions of extensibility 102 is shown in FIGURE 3, wherein each region includes four transverse, upwardly extending folds 130 in the substrate/band assembly. In cross section, each fold 130 defines an inverted, U-shaped section of substrate. The bands 126 retain the initially formed four-fold configuration of each region of extensibility until acted upon during placement of the electrode strip. Upon adjusting the regions of extensibility during placement of the strip, the regions will retain the adjusted form (as a result of the bands 126), and thus the electrode sites will have a tendency to remain where they are positioned, even before coupling each site to the body. As will be appreciated, other configurations of the regions of extensibility 102 may be used. For example, fewer or additional transverse folds 130 may be induced into the substrate. Moreover, various shapes and sizes of folds may also be implemented to form the regions of extensibility 102.

The regions of extensibility 102 are formed into the electrode strip 100 through mechanical processes. One process involves (1) aligning the strip along the top of a toothed surface, (2) extending an arm downwardly between a pair of adjacent teeth, thereby forcing the electrode strip into the groove formed by the adjacent teeth and creating one of the transverse folds, (3) positioning the arm above the next pair of teeth, and (4) repeating steps (2) and (3) until each region of extensibility is formed. Other processes known and used for the general formation of malleable material may also be used to form the regions of extensibility 102.

In the process of forming the regions of extensibility 102 heating is not required a desired shape is mechanically induced into the electrode strip, wherein the shape is held by the malleable layer attached to the substrate. The process has manufacturing advantages including that it is generally quicker and does not require heating and cooling of the electrode strip.

As will be appreciated, formation of each fold 130 decreases the longitudinal length of the strip, bringing the precordial electrode sites on either side of the fold closer together. In the application of the electrode strip 100 to person 18, the longitudinal distance between the electrode sites can then be increased by deforming the regions of extensibility 102, i.e., stretching the folds 130. Further, the strip may be bent laterally at the regions of extensibility by holding one side of the strip and pulling the free end of the strip, on the opposite side, in the direction of the desired bend. Thus, the resultant regions of extensibility 102 allow extension and curvilinear motion between adjacent electrode sites on the otherwise inextendible substrate 104.

The regions of extensibility 102 in strip 100, as a result of the bands 126, tend to conform to and retain any shape induced upon them, for example, as the electrode strip 100 is manipulated to properly position the precordial and limb sites on the body of a person. In effect, each region of extensibility 102 has a memory-like feature that allows the strip 100 to be shaped prior to actually connecting the electrode sites to the person. This provides an opportunity for greater accuracy in electrode placement. Further, as is illustrated most clearly in FIGURE 3, the multifolded structure of each region of extensibility 102 provides for an accordion-like bending of the regions of extensibility, whereby curves in the electrode strip are readily achieved along with the desired electrode site separations.

It is noted that the bands 126 may also act as a shielding layer to shield the conductors 114 from electromagnetic waves if the bands 126 are connected to ground. As is known in the art, highly sensitive medical instruments will typically have shielded cables to block at least a portion of the spurious currents induced by ambient electromagnetic waves. In a somewhat similar fashion, the bands 126 could shield the conductors 114 from electromagnetic interference, thereby enhancing the accuracy of the ECG readings. The amount of shielding provided by each band will generally depend upon the composition of the material used to form the band, the dimension thereof, and mainly where it is connected to the electrical ground reference.

FIGURE 5 is a partial illustration of an exemplary embodiment of an electrode strip in accordance with the invention. In the embodiment of FIGURE 5, a variation of strip 100 is shown, including the substrate section 104a and band 126. However, the conductors 114, oval-shaped layers 116 and cover layers 122 are not manufactured as part of the strip. Rather, the conductors and cover layers are in effect replaced by a plurality of electrode pads 140 and separate and distinct cables 142 that carry electrical signals from the electrode pads 140 to therapeutic and monitoring equipment.

An alternative embodiment to that depicted in FIGURE 5 would be an extendible substrate that did not require the use of a plurality of transverse folds 130. Examples of such a material might be Coban® manufactured by 3M, a natural rubber, or an inelastic plastically deformable material such as thin polyethylene sheet.

Each electrode pad 140 has adhesive layers on oppositely disposed surfaces: an upper adhesive layer 144 to attach the electrode pad 140 to the electrode strip, and a lower conductive adhesive layer 146 to detachably mount the pad to the body of a person (not shown). The lower adhesive layer 146 is exposed by removing a protective liner 148. Each electrode pad 140 further includes a conductive tabular region 150 that projects from the pad. An alligator clip 152, coupled to the cable 142, is then used to provide an electrical connection to the cable. A conductive element within the electrode pad couples electrical signals from the lower adhesive layer 146 (i.e., which provides a conductive interface with the person's skin) to the tabular region 150.

In the embodiment of FIGURE 5, the electrode sites are first positioned on the body of the person, and then each site is coupled to medical equipment through a different one of the cables 142. As will be appreciated, conductive gel pads may be used as an alternative to the electrode pads 140 if they are provided with a conductive tabular region to allow electrical connection between the pad and cables 142. Use of the adhesive electrode pads 140 and cables 142 is advantageous from a manufacturing standpoint in that the electrode strip does not need conductors or the dielectric cover layers. However, use of the pad/cable combination in lieu of the conductors is disadvantageous because care must be exercised to ensure that the right cable is connected to the corresponding electrode. Errors in the connection scheme can lead to incorrect computer analysis of the results

FIGURES 6 and 7 illustrate an exemplary body surface potential mapping assembly 160 constructed in accordance with the present invention. As will be appreciated, any number of other body surface potential mapping patterns may also be realized.

The mapping assembly 160 includes 29 electrode sites provided on four separate electrode strips 162, 164, 166 and 168, each employing the basic constructional techniques described in connection with the electrode strip 100 of FIGURE 1. Although not explicitly illustrated in FIGURES 6 and 7, each electrode strip preferably includes (a) a substrate, (b) a plurality of conductors that extend from a connector segment 170 of each electrode strip, along a lower surface of the substrate, to individual electrode sites, (c) a malleable band attached to an upper surface of the substrate, (d) a plurality of cover layers that extend over the conductors to insulate all but a portion of the conductors from the body of a person, (e) a silver/silver chloride layer over each electrode site, and (f) an adhesive layer positioned over each silver/silver chloride layer to attach the strip to a person. Other methods of constructing the electrode strips, may also be employed.

As is shown in FIGURE 6, a number of clamps 120 cooperate with the connector segments 170 to releasably couple the conductors of each electrode strip to individual cables 172. The connector segments 170 are constructed similar to the end segment 110 of the electrode strip 100, shown in FIGURE 2. The cables 172, in turn, couple the conductors to medical and therapeutic equipment (not shown) through a main cable connector 174 including four sets of receptacles and a main cable 176. The cables 172 each include a connector at the end thereof, opposite clamp 120. The connectors are releasably coupleable to the receptacles in the main cable connector 174, which has at least as many conductors as the four strips 162, 164, 166 and 168 combined. Each conductor in the main cable connector 174 is coupled to medical equipment through the cable 176, which also includes at least as many conductors as the number contained in the strips.

A plurality of regions of extensibility 102 are provided between at least some of the electrode sites on the strips to provide electrode site separation and strip curvature, thereby allowing the electrode sites to be properly positioned on the body of a person 18. The regions of extensibility 102 have in some instances been labeled with different reference numeral for clarity in the description of the electrode strips. With reference to FIGURE 6, the electrode sites positioned on the person's sides are not shown because of the view presented. FIGURE 7 is provided to better visualize the location of all of the 29 electrodes, particularly those not illustrated in FIGURE 6. In FIGURE 7 the electrode strips and electrode sites are illustrated on a plane superimposed on the body of a person 18. A pair of mid-lines 178 and 180, located along the right and left sides of the person 18, respectively, represent imaginary lines that would extend along the person's sides, separating the body into front and back portions, in the event the strips were applied to the person's body.

Reviewing each electrode strip in greater detail, electrode strip 162 includes left and right columns 162L and 162R of electrode sites 182a-182h that are coupled together at their respective upper and lower ends by regions of extensibility 184a and 184b, respectively. Each column includes four electrode sites. When strip 162 is properly applied to the person's chest, columns 162L and 162R are positioned on opposite sides of the person's sternum. It is noted that regions of extensibility are not included between the electrode sites within a column because the preferred locations and separations of these electrode sites along the sternum are generally the same for a large percentage of the population.

Electrode strip 164 is positioned on the left, mid-level chest area of the person and includes two rows 164a and 164b of electrode sites that are separable from one another at an end of the strip opposite the connector segment 170. The upper electrode strip 164a includes four electrode sites 186a-186d; the lower electrode strip 164b includes three electrode sites 186e-186g. With reference to FIGURE 7, the electrode sites 186c and 186g (third from the connector segment 170) are positioned on the person's left side, in front of mid-line 180. The electrode site 186d, fourth from the connector segment 170, is also positioned on the person's left side, but behind mid-line 180.

The electrode strips 166 and 168 are positioned above and below, respectively, the electrode strips 162 and 164. The electrode strips 166 and 168 are identical, with strip 166 including seven electrode sites 188a-188g and strip 168 including sites 190a-190g. The right outermost electrode sites, 188a and 190a, are positioned on the person's right side, behind mid-line 178. The electrode sites adjacent the right outermost electrode sites, 188b and 190b, are positioned on the person's right side, in front of mid-line 178. The left outermost electrode sites, 188g and 190g, are positioned on the person's left side, behind mid-line 180. The electrodes adjacent the left outermost electrode sites, 188f and 190f, are positioned on the person's left side, in front of mid-line 180.

The remaining electrode sites on the top electrode strip 166 are positioned across the chest area of the person, one on the person's right, 188c, and two on the left 188c and 188d. The remaining electrode sites on the bottom electrode strip 168 are positioned across the abdominal area, with electrode site 190c being on the right side and electrode sites 190d and 190e being on the person's left side.

The electrode assembly 160 utilizes the technology described in the present invention to provide a 29 electrode site body surface potential mapping scheme. It will be appreciated by those skilled in the art that virtually any number of electrode sites may be implemented using this technology. Moreover, various other conductor-electrode site arrangements may be employed in accordance with the present invention.

FIGURES 8 and 9 illustrate in greater detail the clamp 120 used to connect the electrode strip 100 of FIGURE 1-4 to medical and diagnostic equipment (not shown) through cable 118. A similar clamp configuration would be used to couple the electrode strips of FIGURES 6 and 7 to medical and diagnostic equipment. Clamp 120 includes an upper and lower housing 200 and 202, respectively, that are coupled together by a pin 204. A pair of springs 206 are captured between the upper and lower housing near a back side 208 of the clamp. The lower housing 202 includes a plurality of conductive teeth 210 that are located in a pattern such that they intersect the terminating ends 212 of the conductors 114, when the electrode strip 100 is positioned within the clamp 120. As is shown, each terminating end 212 includes a circular conductive region that is slightly larger than the surface area of the conductive teeth 210. The arrangement of the conductive teeth 210 is based on the configuration of the terminating ends of the electrode strip.

In the embodiment of FIGURES 8 and 9 twelve conductive teeth are included in the lower housing 202, ten of which correspond to the conductors 114a-114 j of FIGURE 2, and two that may be connected to ground or used for other purposes. For example, additional conductive teeth may be used to determine whether the electrode strip has been inserted into the connector properly or whether the appropriate connector/electrode strip pairing has been implemented. Each of the conductive teeth 210 are coupled to a separate conductor within the cable 118. A plurality of resistors 213 may be coupled between at least some of the conductive teeth and cable 118. The resistors 213 are used to limit defibrillation current through the cable and monitor. In the embodiment of FIGURE 9, nine resistors 213 are depicted, although one of the resistors is partially hidden by the lower housing 202.

The upper housing 200 includes a pad 214 having a plurality of apertures 216 extending therethrough. The apertures 216 are positioned directly above the conductive teeth 210 when the upper housing is seated on the lower housing such that the pad 214 abuts the electrode strip 100, which in turn is pressed against the conductive teeth 210. Apertures allow elastic deformation of the compliant electrode strip connector end segment 110 between the conductive teeth 210 and the aperture perimeter which is also resiliently deformable. This secondary spring action helps assure electrical contact without the added manufacturing expense of spring loaded contacts and or tighter tolerances.

To releasably connect the clamp 120 to the electrode strip 100, the upper and lower housings are pressed together at the back 208 of the clamp, causing the upper housing 200 to rotate, relative to the lower housing 202, around the pin 204. Rotation of the upper housing 200 provides an opening for insertion of the end segment 110 of the electrode strip 100 into the clamp. The lower housing 202 includes a back wall 218 that prevents the end segment 110 from being inserted too far into the clamp 120, and left and right side walls 220 and 222 that ensure the electrode strip is properly seated as it is positioned into the clamp. After the end segment has been inserted, pressure is released from the back 218 of the clamp. The springs 206 cause the upper housing 200 to rotate about the pin 204, pressuring the pad 214 into abutment with the electrode strip 100 and the terminating ends 212 of the conductors 114 against the conductive teeth 210, thereby making electrical contact.

A suitable material for constructing the upper and lower housings is a plastic that has been molded into the depicted shapes. The pad is preferably comprised of a compliant material such as silicone rubber. The conductive teeth are preferably noble metal plated electrical contacts.