ECG CABLE FOR CONNECTION WITH AN ECG MONITOR

Abstract

The present invention relates to an ECG cable for connection with an ECG monitor. To achieve a miniaturization of the ECG cable and omitting the conventionally used trunk cable and trunk cable connector, the ECG cable comprises a core (2), a resistive wire cable (3a-3h) comprising a plurality of resistive wires (31-37) wound around the core and isolated with respect to each other, and two or more flexible lead wires (4), each connected to a respective resistive wire at its one end (40) and to an electrode (5) at its other end (41).

Claims

1. ECG cable for connection with an ECG monitor, said ECG cable comprising: a core (2), a resistive wire cable (3a-3h) comprising a plurality of resistive wires (31-37) wound around the core and isolated with respect to each other, wherein each resistive wire has a resistance of at least 500 and wherein the resistive wires are made of a material having a resistivity of at least 0.135 *m, and two or more flexible lead wires (4), each connected to a respective resistive wire at its one end (40) and to an electrode (5) at its other end (41).

2. ECG cable as claimed in claim 1, wherein the resistive wire cable is spirally wound around at least part of the core.

3. ECG cable as claimed in claim 1, wherein the resistive wire cable is substantially made of a FeCrAl alloy.

4. ECG cable as claimed in claim 1, wherein the resistive wires have a diameter in the range of 50 to 500 m, in particular in the range of 100 to 200 m.

5. ECG cable as claimed in claim 1, wherein the resistive wire comprises a bundle of multiple resistive wires.

6. ECG cable as claimed in claim 1, wherein the resistive wire cable comprises two bifilar wound resistive wires for conducting opposite current flows.

7. ECG cable as claimed in claim 1, wherein the resistive wire cable comprises parallel resistive wires wound in opposite direction around the core.

8. ECG cable as claimed in claim 1, wherein the resistive wire cable comprises a woven shield of non-isolated wires.

9. ECG cable as claimed in claim 1, wherein two or more resistive wire cable are wound in parallel around the core.

10. ECG cable as claimed in claim 1, wherein the core is made of plastic, ferrite or a material having a high permeability, in particular having a permeability above 10, preferably above 100.

11. ECG cable as claimed in claim 2, wherein the pitch of the windings of the resistive wire cable varies over the length of the resistive wire cable.

12. ECG cable as claimed in claim 1, wherein each resistive wire has a resistance of at least 1 k.

13. ECG cable as claimed in claim 1, wherein the resistive wires are made of a material having a resistivity in the range of 1.35 to 1.45 *m.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0028] These and other aspects of the invention will be apparent from and elucidated with reference to the embodiment(s) described hereinafter. In the following drawings

[0029] FIG. 1 shows a schematic drawing of the general layout of an ECG cable according to the present invention,

[0030] FIG. 2 shows a schematic drawing of an embodiment of an ECG cable according to the present invention with multiple parallel wires,

[0031] FIG. 3 shows a schematic drawing of an embodiment of an ECG cable according to the present invention spirally wound wires in parallel,

[0032] FIG. 4 shows a schematic drawing of an embodiment of an ECG cable according to the present invention with spirally wound wires in antiparallel direction,

[0033] FIG. 5 shows a schematic drawing of an embodiment of an ECG cable according to the present invention with woven wires,

[0034] FIGS. 6A and 6B show schematic drawings of two embodiments of an ECG cable according to the present invention with spirally wound wires with different pitches,

[0035] FIGS. 7A and 7B show schematic drawings of two embodiments of an ECG cable according to the present invention with different cores, and

[0036] FIG. 8 shows a schematic drawing of an embodiment of an ECG cable according to the present invention with a spirally wound wire having a variable pitch.

DETAILED DESCRIPTION OF EMBODIMENTS

[0037] FIG. 1 shows a schematic drawing of the general layout of an ECG cable 1 according to the present invention. It comprises a core 2, a resistive wire cable 3a wound, e.g. like a helix, around the core and formed by resistive wires 31, and two or more flexible lead wires 4, each connected to a corresponding resistive wire 31 at its one end 40 and to an electrode 5 at its other end 41. There are various embodiments of arranging the resistive wire cable and of forming the resistive wire cable by resistive wires, as will be illustrated and explained in the following.

[0038] There a number of potentially useful metal materials that can meet all or part of the requirements of the proposed solution, e.g. on resistive values, Temperature Coefficient of Resistance (TCR), mechanical properties, etc. A preferred material is FeCrAl. A family of iron-chromium-aluminum (FeCrAl) alloys used in a wide range of resistance and high-temperature applications are e.g. available under the trade name Kanthal. Kanthal FeCrAl alloys consist of mainly iron, chromium (20-30%) and aluminum (4-7.5%), e.g. Kanthal A-1, Kanthal D, Kanthal AF, have a resistivity of 1.35-1.45 *m. This material, for instance, allows designing a resistor with the desired resistance of 1 kOhm by winding this wire around a plastic core. However, several other stable resistive metal alloys exist with similar or lower resistivity, which may alternatively be applied.

[0039] Taking a temperature increase of 50 K (due to the energy of the defibrillation pulse) as a suggested specification, a required length of approx. 13 m of 0.16 mm diameter resistive wire may be used to reach 1 kOhm. Embedding a 13 m long resistive wire in the envisioned 0.5 m length of a lead wire requires a helix pitch of 0.25 mm. If a 4 times higher temperature increase (200 K) would be allowed the ECG wire length could be reduced to 6.5 m using 0.11 mm diameter resistive wire. For a resistance of 3.3 kOhm the diameter can be reduced by a factor of sqrt (3.3)=1.8 at the same length (because the absorbed energy due to defibrillation pulse in the higher resistance is reduced, the thermal mass of the wire is allowed to be lower). This would allow either using a non-winded solution or a much more relaxed winding technology.

[0040] Calculated values are illustrated in the following table (for the assumption that there is a resistive heat pulse for defibrillation with 40 J; generally the defibrillation pulse is approx. 360 J, but at 1 kOhm only approx. 40 J ends up in the lead wires):

TABLE-US-00001 Temperature increase 50 K 200 K Min. wire volume cm.sup.3 0.245 0.061 Min. wire length m 13.0 6.5 Min. wire diameter mm 0.155 0.110 Helix winding diameter mm 1.845 1.890 Helix inner diameter mm 1.690 1.781 Number of turns 2242 1094 Helix pitch mm 0.223 0.457 Max wire insulation thickness mm 0.034 0.174 Self-inductance H 33.8 8.4 Reactance at f_carrier Ohm 10.2 2.5

[0041] Respiration measurements require low inductive lead wires. The self-inductance of a 13 m long resistive wire wound to a helix of 0.5 m long is 32 pH. In many ECG applications also respiration is measured by using bio-impedance at a carrier frequency of typically 48 kHz. The reactance of the helix at 48 kHz is approx. 10 Ohm, and about 2.5 Ohm for a 6.5 m long wire.

[0042] The ECG cable may be fabricated by winding the resistive wire cable on a metal rod, where after the rod is removed and isolation is applied at the outside of the helix. Finally the inside may be filled with a silicone rubber with high flexibility. In a possible and suggested future reel-to-reel production method the helix could be wound continuously around plastic core and immediately covered with insulation via an extrusion process.

[0043] There are a number of embodiments for implementing the proposed idea, which shall be further elucidated in the following.

[0044] FIG. 2 shows a schematic drawing of an embodiment of a resistive wire 32 according to the present invention with multiple parallel wires 320. The lead wires are not shown in this figure. Similar to electricity wires a single resistive wire 31 as shown in FIG. 1 can be replaced by a wire 32 comprising multiple thin wires 320. This will increase the flexibility and reduce the chance of repeated stress failures. The total volume of resistive wire 32 should be kept constant to ensure that the thermal energy still can be absorbed. The total diameter of the wire 32 will be slightly increased due to the small air gap between the thin wires 320. A single wire with a diameter of 150 m can thus be replaced by e.g. 36 wires of 25 m or 9 wires of 50 m diameter.

[0045] FIG. 3 shows a schematic drawing of an embodiment of an ECG cable according to the present invention spirally wound wires 33, 34 forming the resistive wire cable 3b. The lead wires are not shown in this figure. Bio-impedance measurements (e.g. for respiration measurement) require a low self-inductance lead set, which requires reduction of the magnetic stray field as much as possible. This can be achieved by bifilar wound (resistive) wires 33, 34, where the opposite current flows in the adjacent wire 33, 34. In this case an additional (normal) wire may be used as with this winding the beginning and end are the same location. Alternatively, a normal winding may be added to end on the opposite side of the lead wire.

[0046] An alternative embodiment is depicted in FIG. 4 showing a schematic drawing of an embodiment of an ECG cable according to the present invention with spirally wound wires in antiparallel direction. This resistive wire cable 3c uses parallel (resistive) wires 35, 36 wound in helixes having an opposite rotational direction (like the double helix structure in a DNA molecule).

[0047] FIG. 5 shows a schematic drawing of an embodiment of an ECG cable according to the present invention with woven wires. In this embodiment, the resistive wire cable 3d is formed by a woven shield of non-isolated wires 37. Again, instead of a single wire (e.g. with a pitch of 0.225 m) of 150 m diameter, a coax woven structure of e.g. 10 wires of 50 m diameter with the same pitch can be used. When an even number of wires is used combined with this structure, the self-inductance of the single wires will cancel, reducing the self-inductance to a very low level. This will reduce the noise and make respiration detection possible. In an embodiment the braiding angle should be as in the helix wound wire, as e.g. shown in FIG. 1, i.e. in practice a very different angle is used than the angle shown in FIG. 5.

[0048] Another disturbing and hence to-be-solved effect is the tribo-electric effect or handling-noise that causes impact-related slapping noise as the cable hits a mechanical stiffness or is stepped upon during use. This is related to capacitance, specifically the change in capacitance that takes place as the insulation or dielectric is deformed. The best work-around is by using soft, impact-absorbing insulation and jacket materials in a very solid construction with ample fillers to ensure that the cable retains its shape.

[0049] FIGS. 6A and 6B show schematic drawings of two embodiments of an ECG cable according to the present invention with one spirally wound wire cable 3a (FIG. 6A) and a wire cable arrangement 3e with two spirally (parallel) wound wires cables 3f, 3g (FIG. 6B). Instead of having 5 or 10 separate lead wires with the wound wire resistors, the winding pitch can be increased to hold 5 or even 10 parallel wire resistors (i.e. wire cables) on a single core, e.g. with a 2 mm diameter (pitch 50.175 mm=approx. 0.9 mm) in approx. 2 m, or for 10 wires 5 m. If the diameter of the core is increased to approx. 8 mm, the pitch can again be reduced to 0.5 m for the 5 lead ECG cable. It should, however, be noted that these are only exemplary numbers for an exemplary implementation.

[0050] FIGS. 7A and 7B show schematic drawings of two embodiments of an ECG cable according to the present invention with different cores. Instead of winding the resistive wire on an electro-magnetically inactive (e.g. plastic) core 2a, as shown in FIG. 7A, alternatively a high-t (i.e. highly permeable, e.g. ferrite) core 2b can be used to increase the inductance, as shown in FIG. 7B. The inductance may be physically separated from the resistance by applying low resistive wire windings at a different position. This further miniaturizes the OR ECG cable set by omitting the need of separate 6.8 mH and 9 kOhm lead set connector.

[0051] This inductance can e.g. be implemented by replacing the magnetic inactive (e.g. plastic) core by a material with .sub.r (relative permeability) of about 200 in a helix of 0.5 m length and 13 m wire. However, the ECG cable can also be redesigned or optimized to be functional with a lower resistance. Generally, the total resistance should remain above e.g. 1 kOhm, whereas the wire resistance can be changed and with this more or less length may be needed.

[0052] FIG. 8 shows a schematic drawing of an embodiment of an ECG cable according to the present invention with a spirally wound wire cable 3h having a variable pitch. By varying the winding pitch regions of higher resistance (for protection) and lower resistance can be created, while using the same resistive wire. In this way the same (standardized) cable technology can be applied to create different lengths of cables. Said regions may be indicated visually and used to cut the cable to the desired length. An additional advantage is that the length of low-impedance regions does not influence the total impedance too much so that different cable lengths may be feasible.

[0053] The present invention thus enables replacing the conventionally used trunk cable and trunk cable connector so that the ECG cable becomes more compact, lightweight and flexible.

[0054] While the invention has been illustrated and described in detail in the drawings and foregoing description, such illustration and description are to be considered illustrative or exemplary and not restrictive; the invention is not limited to the disclosed embodiments. Other variations to the disclosed embodiments can be understood and effected by those skilled in the art in practicing the claimed invention, from a study of the drawings, the disclosure, and the appended claims.

[0055] In the claims, the word comprising does not exclude other elements or steps, and the indefinite article a or an does not exclude a plurality. A single element or other unit may fulfill the functions of several items recited in the claims. The mere fact that certain measures are recited in mutually different dependent claims does not indicate that a combination of these measures cannot be used to advantage.

[0056] Any reference signs in the claims should not be construed as limiting the scope.