Noninvasive electroencephalogram sensor

Abstract

The utility model relates to the technical field of electroencephalogram sensors, in particular to a non-invasive electroencephalogram sensor which comprises a connecting piece at the end position, a plurality of electrode plates located on one side of the connecting piece and a plurality of electrode wires used for connecting the connecting piece and the electrode plates, electrode pads are arranged at the tops of the electrode plates, through holes are formed in the middles of the electrode pads, and the electrode pads are arranged in the through holes. And a conductive circular ring, a sponge and a conductive adhesive are sequentially arranged in the through hole from bottom to top. According to the electroencephalogram sensor, the skin surface layer does not need to be punctured, the infection risk can be reduced, meanwhile, the conductivity of the sensor can be improved, and high-quality electroencephalogram signal collection is ensured.

Description

Technical Field

[0001] This utility model relates to the technical field of electroencephalogram (EEG) sensors, and in particular to a non-invasive EEG sensor. Background Technology

[0002] An electroencephalogram (EEG) sensor is a device used to capture and record the electrical activity of the brain. It typically consists of multiple electrodes and its main function is to monitor the brain's electrophysiological activities, which can reflect the brain's functional state and possible abnormal changes.

[0003] Existing EEG sensors, such as the utility model with patent application number 2023200808906, provide a disposable non-invasive EEG sensor: including a device connector and a flexible circuit board, the device connector and the flexible circuit board are fixedly connected, the flexible circuit board is provided with electrode plates, each electrode plate includes a conductive substrate, the conductive substrate is provided with foam, the foam is provided with a pre-set hole in the center, and the pre-set hole is provided with a conductive electrode, a stylus, a sponge and a conductive adhesive connected in sequence from the inside to the outside.

[0004] The above method uses a probe structure, which inserts the probe into the stratum corneum to allow the sensor to form a stable connection pathway on the skin surface. However, this method can cause skin damage, carries a certain risk of infection, and can also cause discomfort to the patient. Utility Model Content

[0005] To address the problems mentioned above, this invention provides a non-invasive EEG sensor that does not require piercing the skin, reducing the risk of infection, while also improving the sensor's conductivity to ensure high-quality EEG signal acquisition.

[0006] The solution adopted by this utility model to solve its technical problem is: a non-invasive electroencephalogram (EEG) sensor, including a connector at the end position, several electrode plates located on one side of the connector, and several electrode wires for connecting the connector and the electrode plates. The top of the electrode plate is provided with an electrode pad, and the middle of the electrode pad is provided with a through hole. A conductive ring, a sponge and a conductive adhesive are arranged sequentially from bottom to top in the through hole.

[0007] Furthermore, the diameter of the sponge is smaller than the diameter of the through hole, and it forms a gel gap with the electrode pad.

[0008] Furthermore, the ring is located at the bottom of the adhesive gap and is in close contact with the electrode sheet and the sponge.

[0009] Furthermore, the ring is made of carbon nanomaterials.

[0010] Furthermore, the electrode pad surface is provided with a hydrophobic layer.

[0011] Furthermore, the hydrophobic layer is a cross-linked polymer.

[0012] Furthermore, the electrode pad has a polygonal structure and has at least four sides.

[0013] In summary, the beneficial effects of this utility model are as follows:

[0014] The non-invasive EEG sensor of this application does not require insertion into the skin during use, which reduces the risk of infection. At the same time, by setting a conductive ring, the impedance between the electrode pad and the sponge is reduced, which improves the conductivity of the sensor and ensures the acquisition of high-quality EEG signals.

[0015] In addition, the ring is placed at the bottom of the adhesive voids to ensure the conductivity consistency of the entire electrode area, including the sponge and the adhesive voids. This optimizes the transmission of electrical signals from the skin through the sponge to the electrode pad, improves the conductivity of the sensor, and helps reduce the increase in impedance caused by the drying of the conductive liquid, thereby improving the stability of the sensor for long-term measurements.

[0016] The above description is merely an overview of the technical solution of this utility model. In order to better understand the technical means of this utility model and to implement it in accordance with the contents of the specification, and to make the above and other objects, features and advantages of this utility model more apparent and understandable, preferred embodiments are described below in detail with reference to the accompanying drawings. Attached Figure Description

[0017] Figure 1 This is the front view of this embodiment;

[0018] Figure 2 This is a schematic diagram of the structure of this embodiment.

[0019] In the diagram: 1. Connector; 2. Electrode plate; 3. Electrode wire; 4. Electrode pad; 5. Conductive ring; 6. Sponge. Detailed Implementation

[0020] To make the content of this utility model easier to understand, the present utility model will be further described below with reference to specific embodiments and accompanying drawings.

[0021] It should be noted that the terms "center," "upper," "lower," "front," "rear," "left," "right," "inner," and "outer" used herein to indicate the orientation or positional relationship are based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this utility model and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this utility model. Unless otherwise stated, "a plurality of" means two or more.

[0022] Unless otherwise expressly specified and limited, the terms "installation," "connection," and "linking" should be interpreted broadly. For example, they can refer to fixed connections, detachable connections, or integral connections; they can refer to mechanical connections or electrical connections; they can refer to direct connections or indirect connections through an intermediate medium; and they can refer to the internal connection between two components. Those skilled in the art can understand the specific meaning of the above terms in this utility model based on the specific circumstances.

[0023] like Figures 1 to 2 As shown, a non-invasive electroencephalogram (EEG) sensor includes a connector 1 at its end, three electrode pads 2 located on one side of the connector 1, and three electrode wires 3 for connecting the connector 1 and the electrode pads 2. In this embodiment, the electrode pads 2 have electrode pads 4 on their tops, and the electrode pads 4 are made of foam. The foam can absorb and retain conductive adhesive, thereby ensuring sufficient conductive medium between the electrodes and the skin and preventing the conductive adhesive from being lost.

[0024] like Figure 2 As shown, the electrode pad 4 in this embodiment has a through hole in the middle. A conductive ring 5, a sponge 6, and conductive adhesive are sequentially arranged from bottom to top within the through hole. The conductive ring 5, sponge 6, and conductive adhesive are all bonded together with adhesive. In this embodiment, the conductive ring 5 is made of carbon nanomaterials, and the sponge 6 layer can absorb the conductive adhesive, ensuring sufficient conductive medium between the electrode and the skin, reducing the risk of the conductive adhesive being lost due to drying or movement. The conductive adhesive in this application contains dispersed carbon nanoparticles, which can reduce the contact impedance between the electrode and the skin, improving signal clarity and quality. By setting the conductive ring 5, sponge 6, and conductive adhesive, this application improves the conductivity of the sensor, ensuring high-quality EEG signal acquisition without requiring skin puncture, thus improving user comfort and reducing the risk of infection.

[0025] like Figure 1 As shown, in this embodiment, the diameter of the sponge 6 is smaller than the diameter of the through hole and forms a conductive adhesive gap with the electrode pad 4. Through the above settings, it is ensured that there is sufficient conductive adhesive on the sponge 6, so as to effectively transmit the electrical signal from the skin to the EEG sensor, while preventing the conductive adhesive from overflowing during use and affecting the electrode performance.

[0026] The ring in this application is located at the bottom of the adhesive void and is in close contact with the electrode sheet 2 and the sponge 6, ensuring the conductivity consistency of the entire electrode area including the sponge 6 and the adhesive void, optimizing the transmission of electrical signals from the skin to the electrode sheet 2 through the sponge 6, improving the conductivity of the sensor, and helping to reduce the increase in impedance caused by the drying of the conductive liquid, thereby improving the stability of the sensor for long-term measurement.

[0027] The ring is made of carbon nanomaterials, which have excellent conductivity and help maintain the long-term performance of the sensor. In this embodiment, the connector 1 has a rough surface to facilitate better connection with the electrode wires 3.

[0028] In this embodiment, the electrode pad 4 has a hydrophobic layer formed by a cross-linked polymer on its surface. Through the above design, the hydrophobic layer can reduce the accumulation of sweat between the electrode and the skin, while reducing friction between the electrode and the skin, reducing signal interference caused by head movement. The hydrophobic layer formed by the cross-linked polymer is durable, can resist wear and mechanical damage, extend the service life of the electrode, and provide good adhesion while maintaining superhydrophobic properties.

[0029] In this embodiment, the electrode pad 4 is a quadrilateral and a trapezoid with curved edges. The curved edge design allows the electrode pad 4 to better conform to the curve of the head. At the same time, the polygonal design increases the contact area between the electrode and the skin, improves the quality of the electrode signal and reduces impedance.

[0030] The method of using the non-invasive EEG sensor in this embodiment is as follows: First, moisten a dry cloth with saline solution, then clean the forehead, temples and auricles with the moistened dry cloth, and then add conductive fluid into the non-invasive EEG sensor and attach it to the forehead.

[0031] The embodiments described above are merely preferred embodiments of this utility model and should not be construed as limiting the scope of protection of this utility model. Any non-substantial changes and modifications made by those skilled in the art based on this utility model shall fall within the scope of protection of this utility model.

Claims

1. A non-invasive electroencephalogram (EEG) sensor, comprising a connector (1) at an end position, a plurality of electrode pads (2) located on one side of the connector (1), and a plurality of electrode wires (3) for connecting the connector (1) and the electrode pads (2), characterized in that, The electrode sheet (2) is provided with an electrode pad (4) at the top, and a through hole is provided in the middle of the electrode pad (4). A conductive ring (5), a sponge (6) and a conductive adhesive are arranged sequentially from bottom to top in the through hole.

2. The non-invasive EEG sensor according to claim 1, characterized in that, The diameter of the sponge (6) is smaller than the diameter of the through hole and forms a gel gap between it and the electrode pad (4).

3. The non-invasive EEG sensor according to claim 2, characterized in that, The ring is located at the bottom of the adhesive void and is in close contact with the electrode sheet (2) and the sponge (6).

4. The non-invasive EEG sensor according to claim 3, characterized in that, The ring is made of carbon nanomaterials.

5. The non-invasive EEG sensor according to claim 1, characterized in that, The electrode pad (4) has a hydrophobic layer on its surface.

6. A non-invasive EEG sensor according to claim 5, characterized in that, The hydrophobic layer is a cross-linked polymer.

7. The non-invasive EEG sensor according to claim 1, characterized in that, The electrode pad (4) has a polygonal structure and has at least four sides.

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