ELECTRODE STRUCTURE FOR ELECTROCARDIOGRAM (ECG) WAVEFORM MEASUREMENT

Abstract

An electrode for electrocardiogram (ECG) waveform measurement of the present disclosure is proposed. The present disclosure provides an electrode device capable of accurately measuring and monitoring an electrocardiogram of a person by maintaining a uniform amount of electric charge even when a contact area of the electrode changes due to vigorous physical activity such as walking or running, or moisture permeation due to ambient conditions or sweat released during exercise.

Claims

1. An electrode for electrocardiogram waveform measurement, wherein the electrode is a biosignal measuring electrode and comprises: an upper electrode layer made of a conductive material to transmit signals; a transmission line made of a coaxial cable, and coupled to the upper electrode layer so as to transmit measured signals to a receiving device; a dielectric layer made of a biocompatible nano inorganic material coated on a side of the upper electrode layer to be in direct contact with skin; a lower electrode layer grounded to offset frictional electricity generated by clothing; a ground line coupled to the lower electrode layer and connected to a ground part; and an insulation layer insulating between the upper electrode layer and the lower electrode layer.

2. The electrode for electrocardiogram waveform measurement of claim 1, wherein the conductive material is made of gold (Au), silver (Ag), platinum (Pt), copper (Cu), and stainless steel to transmit the signals.

3. The electrode for electrocardiogram waveform measurement of claim 1, wherein the upper electrode layer is provided in a circular shape of 1 cm to 10 cm in diameter.

4. The electrode for electrocardiogram waveform measurement of claim 1, wherein the dielectric layer is made of a biocompatible dielectric material.

5. The electrode for electrocardiogram waveform measurement of claim 1, wherein the dielectric layer has a thickness of 20 nm (nanometer) or more and 2 m (micrometer) or less.

6. The electrode for electrocardiogram waveform measurement of claim 1, wherein the nano inorganic material is made of silica (SiO.sub.2) containing alkali metal.

7. The electrode for electrocardiogram waveform measurement of claim 1, wherein the biosignal measuring electrode is capable of measuring the signals during physical activity.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0016] Various embodiments are illustrated in the drawings, in which:

[0017] FIG. 1 is a perspective view illustrating an electrode according to the present disclosure.

[0018] FIG. 2 is a block diagram illustrating the electrode according to the present disclosure.

[0019] FIG. 3 is an ideal ECG waveform.

[0020] FIG. 4 is an ECG waveform measured using the electrode according to the present disclosure in the absence of physical activity.

[0021] FIG. 5 is an ECG waveform measured using the electrode according to the disclosure during physical activity.

DETAILED DESCRIPTION

[0022] Hereinafter, an embodiment of the present disclosure is described in detail with reference to the accompanying drawings.

[0023] FIG. 1 is a perspective view illustrating an electrode device according to the present disclosure.

[0024] The electrode device 100 of the present disclosure comprises: an upper electrode layer 110 providing an electrode of a sensing part by using a conductive material to transmit signals; a transmission line 111 coupled to the upper electrode layer 110 to transmit sensed signals to a receiving device; a dielectric layer 130 accumulating electric charge, the dielectric layer made of a biocompatible material coated on one side of the upper electrode layer 110 to be in direct contact with the skin; a lower electrode layer 120 providing a ground part electrode made of a conductive material for offsetting frictional electricity by clothing or textiles, and providing a reference point for the signals; a ground line 121 coupled to the lower electrode layer 120 and connected to a ground part for a reference potential; and an insulation layer 140 serving as an insulation between the upper electrode and the lower electrode.

[0025] The upper electrode layer 110 may be made of a conductive material such as circular copper (Cu) of 1 cm to 10 cm in diameter with a thickness of several m (micrometer) or less. The thickness of the dielectric layer 130 coated with a thin film on the upper electrode layer 110 shows a better effect as the thickness is reduced at the level of nm (nanometer) unit. The thickness of the dielectric layer presents best results when being coated more than 20 nm (nanometer) and less than 2 m (micrometer). The upper electrode layer 110 is not limited to a circular shape and may be provided in various shapes.

[0026] Here, the upper electrode layer 110 may be made of conductive metals comprising gold (Au), silver (Ag), platinum (Pt), copper (Cu), and stainless steel and a conductive material comprising conductive rubber (comprising fibers).

[0027] The dielectric layer 130 made of silica (SiO.sub.2), which is a nano inorganic material, is coupled to one surface of the upper electrode layer 110 to accumulate the electric charge so that the ECG output signals are not distorted even when the human body moves.

[0028] Practically, the dielectric layer 130 uses biocompatible dielectric materials which do not cause irritation upon skin contact, such as skin-friendly silica (SiO.sub.2) containing alkali metals, and which are nano inorganic materials.

[0029] The transmission line 111 is coupled to the upper electrode layer 110 to transmit information sensed from the electrode layer to the receiving device.

[0030] Practically, the transmission line 111 uses a coaxial cable in order to reduce noise caused by external electrical interference.

[0031] The insulation layer 140 is fixed to the upper electrode layer 110 and the lower electrode layer 120 to enable insulation therebetween.

[0032] The insulation layer 140 may be made of an insulating material such as polyimide as a polymer material.

[0033] The lower electrode layer 120 removes the noise caused by the frictional electricity in a way that the frictional electricity generated by clothing or textiles, that is, the effect of the external environment, is eliminated by connecting to the ground electrode of the measurement system through the ground line 121.

[0034] The lower electrode layer 120 may be made of the same material, the same thickness, the same size, and the same shape as the upper electrode layer 110. However, different conductive materials, thicknesses, sizes, and shapes may be used to make up the electrode layers in one electrode device.

[0035] Practically, the ground line 121 uses a metal cable having a low resistance.

[0036] The electrode device 100 of the present disclosure is compatible with the existing receiver by adding and connecting a signal conversion device to an existing electric charge transfer type receiver.

[0037] FIG. 3 is a diagram illustrating an electrical current of the heart muscle with an ideal ECG waveform. Typical electrocardiogram graphs show P waves representing atrial depolarization, QRS waves representing ventricular depolarization, and T waves representing ventricular repolarization. The time interval or distance interval of each waveform represents the conduction time according to the electrogenesis of each muscle, and the PR interval is formed within 0.12 to 0.2 seconds in normal cases, and becomes the atrioventricular nodule conduction time. The interval of QRS wave occurs within 0.06 to 0.1 seconds in normal cases, and is the time when ventricular depolarization occurs. QT interval occurs within about 0.42 to 0.43 seconds in normal cases, as an electrical systole of the electrocardiogram.

[0038] FIG. 4 is an electrocardiogram waveform measured by a detailed embodiment according to the present disclosure and measured during a stationary state or inactivity.

[0039] FIG. 5 is an electrocardiogram waveform measured by the detailed embodiment of the present disclosure in an active environment such as walking, jumping, or running.