Electroencephalography dry electrode and electroencephalography measurement apparatus having same

Abstract

An electroencephalography dry electrode (100) and an electroencephalography measurement apparatus having same. The electroencephalography dry electrode (100) comprises a substrate and plating layers, wherein the substrate comprises a base (10) and a plurality of column members (20), an end portion of one end of each of the plurality of column members (20) is fixed to the base (10), at least the surfaces of the column members (20) are provided with the plating layers, and the plating layers on the surfaces of the column members (20) are electrically connected to the base (10).

Description

EEG dry electrode and EEG measuring device having the same

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS

[0002] This application is based on application numbers 2023118101684, filed on December 26, 2023, and entitled “ECG dry electrode and ECG measuring device having the same”, 2023118142468, filed on December 26, 2023, and entitled “ECG measuring device and control method of signal acquisition electrode thereof”, and 2023116572279, filed on December 5, 2023, and entitled “ECG measuring device, acquisition method And acquisition circuit”, Chinese patent applications No. 2023116572391, filed on December 5, 2023, entitled “Electroencephalogram measurement device, acquisition method and acquisition circuit”, and No. 2023116579189, filed on December 5, 2023, entitled “Electroencephalogram measurement device, acquisition method and acquisition circuit”, and claim priority to the above Chinese patent applications, the entire contents of the above Chinese patent applications are hereby incorporated into this application by reference. Technical Field

[0003] The present application relates to the technical field of electroencephalogram (EEG) measurement, and in particular to an EEG dry electrode and an EEG measurement device having the same. Background Art

[0004] Conventional EEG measurement electrodes commonly use a type that applies a conductive paste between the subject's scalp and the electrode. This paste not only reduces the contact impedance between the scalp and the electrode but also stabilizes the measurement site. However, since the paste must be removed after measurement, its use is cumbersome.

[0005] Dry electrodes can ensure low contact impedance without the use of conductive paste. In related technologies, flat dry electrodes directly contact the skin through their conductive surface, which can closely adhere to the skin, but cannot be used in hairy areas. Summary of the Invention

[0006] The present application aims to solve at least one of the technical problems existing in the prior art. To this end, one purpose of the present application is to provide an EEG dry electrode that can pass through the hair and contact the scalp, and can be used for EEG measurement in the hairy area.

[0007] According to the embodiment of the first aspect of the present application, the EEG dry electrode includes a substrate and a coating, the substrate includes a base and a plurality of columnar parts, one end portion of the plurality of columnar parts are fixed to the base, at least the surface of the columnar part is provided with the coating, and the coating on the surface of the columnar part is electrically connected to the base.

[0008] According to the EEG dry electrode of the embodiment of the present application, a plurality of cylindrical members are provided, one end of each of the plurality of cylindrical members is connected to the base. When it is necessary to collect EEG signals from an area with hair, the plurality of cylindrical members are inserted into the hair so that the other end of the cylindrical member contacts the scalp. The cylindrical member in the EEG dry electrode of the present application can pass through the hair so that the other end of the cylindrical member can remain in contact with the scalp, thereby solving the problem in the related art that flat-plate dry electrodes cannot be used in areas with hair. At the same time, the provision of multiple cylindrical members can increase the contact area between the EEG dry electrode and the scalp to reduce contact impedance.

[0009] In some embodiments, the column member includes a first member, a second member and a first elastic member, the first member is sleeved on the second member, the second member can move relative to the first member along the axial direction, the first elastic member is arranged in the first member, and the two end portions of the first elastic member are respectively connected to the first member and the second member, and the first elastic member is used to apply a restoring force to the second member to move outward from the first member.

[0010] In some embodiments, the column member comprises a copper member.

[0011] In some embodiments, the second piece has a concave cavity having a first opening facing the first elastic piece, the first elastic piece is passed through the first opening and one end portion is located in the concave cavity, and the second piece is a stamped and stretched part.

[0012] In some embodiments, a limiting portion is provided on the circumferential edge of the first opening, and the size of the limiting portion is larger than the outer diameter of the second piece in the direction perpendicular to the axis; the first piece includes a tube body, both ends of the tube body are open, and the inner diameter of the edge of the tube body close to the opening of the second piece is smaller than the size of the limiting portion in the direction perpendicular to the axis, the limiting portion is provided in the tube body, and the tube body is integrally stamped, stretched and blanked.

[0013] In some embodiments, the plating layer is provided on the surface of the base, the plating layer on the surface of the base is electrically connected to the plating layer on the surface of the column, and the base and the plurality of column members are integrally injection molded.

[0014] In some embodiments, a conductive sheet is further included, and the base is provided with a connecting hole, which is used to connect with a connector to fix the conductive sheet to the base, and the conductive sheet is electrically connected to the plating layer on the surface of the base.

[0015] In some embodiments, the EEG dry electrode also includes a second elastic member and a mounting member, the second elastic member is connected to the side of the base facing away from the columnar member, the second elastic member can be extended and retracted along the axial direction of the columnar member, and the second elastic member is connected between the base and the mounting member.

[0016] In some embodiments, the EEG dry electrode also includes a guide plate, which is arranged around the circumferential outside of the second elastic member. At least one of the base and the mounting member is connected to the guide plate through a guide structure. The guide structure includes a guide groove and a guide portion. The guide portion is movably inserted into the guide groove along the axial direction of the columnar member.

[0017] The second aspect of the present application also proposes an electroencephalogram (EEG) measuring device.

[0018] The EEG measurement device according to the embodiment of the second aspect of the present application includes the EEG dry electrode according to any one embodiment of the first aspect of the present application.

[0019] In some embodiments, the device comprises: a wearing component, a pushing component, and an EEG dry electrode;

[0020] The wearing assembly is suitable for being worn on the head of a user and has a mounting cavity, and the pushing assembly is located in the mounting cavity;

[0021] The EEG dry electrodes are movably connected to the wearable component;

[0022] The pushing component is used to push the EEG dry electrode to move toward the head when the contact impedance between the EEG dry electrode and the head is greater than or equal to a first impedance threshold.

[0023] In some embodiments, the pushing component is configured to push the EEG dry electrode toward the head according to a reference pushing intensity when the contact impedance between the EEG dry electrode and the head is greater than or equal to the first impedance threshold;

[0024] The reference pushing strength is determined based on the contact impedance and obtained from a corresponding relationship between impedance and strength. The corresponding relationship records a plurality of impedances, and any two of the impedances are different.

[0025] In some embodiments, the EEG measurement device includes a body and a frontal lobe electrode group and a non-frontal lobe electrode group disposed on the body;

[0026] The frontal lobe electrode group includes a plurality of sheet-shaped dry electrodes, which are installed on the main body corresponding to the user's frontal lobe brain area, and the non-frontal lobe electrode group includes a plurality of needle-shaped dry electrodes, which are installed on the main body corresponding to the user's non-frontal lobe brain area; wherein, the frontal lobe brain area includes at least one of the following: the anterior frontal lobe brain area, the posterior frontal lobe brain area, and the non-frontal lobe brain area includes at least one of the following: the parietal lobe brain area, the occipital lobe brain area, and the temporal lobe brain area.

[0027] In some embodiments, the present invention includes: at least two electrode group modules corresponding to different brain regions, each electrode group module is a hard semi-ring structure, and each electrode group module is interconnected to form an integrated structure; at least one of each electrode group module is a retractable structure, so that the module can move in a direction close to or away from its own center to adjust its size; the brain regions include: the frontal lobe brain region, the posterior frontal lobe brain region, the parietal lobe brain region, the occipital lobe brain region and / or the temporal lobe brain region.

[0028] In some embodiments, each electrode group module includes at least two of the following: a first electrode group module corresponding to the prefrontal brain region and / or the posterior frontal brain region, a second electrode group module corresponding to the occipital brain region, and a third electrode group module corresponding to the parietal brain region and / or the temporal brain region.

[0029] In some embodiments, a first plug-in structure is formed at the connection portion of the first electrode group module and the second electrode group module, wherein a protruding first plug-in block is formed at at least one end of one module, and a recessed first plug-in slot is formed at the corresponding end of the other module, and the first plug-in block can move in the first plug-in slot to achieve telescoping.

[0030] In some embodiments, the EEG measurement device includes a body and a brain signal host board integrated on the body, a plurality of electrodes and a signal transmission line;

[0031] Wherein, the body is an integrated hard structure, and a wiring channel is formed inside or on the surface of the structure;

[0032] The electrodes are arranged in groups in at least one brain signal acquisition area of ​​the body;

[0033] The wiring channel of the body extends from the brain signal acquisition area to the area of ​​the body for installing the brain signal host board, and is used for embedding the signal transmission line;

[0034] The signal transmission line is used to connect the electrodes and the brain signal host board to transmit the brain signals collected by the electrodes.

[0035] In some embodiments, the brain signal acquisition area of ​​the main body includes one or more of the following: a frontal lobe brain signal acquisition area, a posterior frontal lobe brain signal acquisition area, a parietal lobe brain signal acquisition area, an occipital lobe brain signal acquisition area, and a temporal lobe brain signal acquisition area;

[0036] The wiring channel includes a horizontal wiring channel and a longitudinal wiring channel, which are used to guide the signal transmission lines connected from the brain signal host board to the electrodes set in each brain signal collection area.

[0037] In some embodiments, at least one of the electrodes provided in the brain signal acquisition area includes: a transcranial direct current stimulation (TDCS) positive electrode and a negative electrode.

[0038] In some embodiments, the wiring channel is embedded in the interior of the body;

[0039] The body includes a first body, a second body, and a third body; the occipital lobe brain region acquisition area is located on the inner side of the second body, the prefrontal lobe brain region acquisition area and / or the posterior frontal lobe brain region acquisition area are located on the inner side of the first body, and the parietal lobe brain region acquisition area and / or the temporal lobe brain region acquisition area are located on the inner side of the third body;

[0040] The second body is fixedly arranged. With respect to the second body, the first body can be telescopically inserted in front of the second body, and the third body can be telescopically inserted in the upper part of the second body.

[0041] The brain signal host board is arranged in the second body, part of the horizontal wiring channel is formed in the plug-in structure of the first body, and part of the longitudinal wiring channel is formed in the plug-in structure of the third body.

[0042] Compared with the prior art, the advantages of the EEG measurement device of the present application are the same as those of the EEG dry electrodes in the embodiments of the present application, and will not be repeated here.

[0043] Additional aspects and advantages of the present application will be given in part in the description below, and in part will become obvious from the description below, or will be learned through practice of the present application. BRIEF DESCRIPTION OF THE DRAWINGS

[0044] The above and / or additional aspects and advantages of the present application will become apparent and easily understood from the description of the embodiments in conjunction with the following drawings, in which:

[0045] FIG1 is a schematic structural diagram of an EEG dry electrode according to an embodiment of the present application;

[0046] FIG2 is a front view of an EEG dry electrode according to an embodiment of the present application;

[0047] FIG3 is a schematic structural diagram of a cylindrical member in an EEG dry electrode according to an embodiment of the present application;

[0048] FIG4 is a front view of a cylindrical member in an EEG dry electrode according to an embodiment of the present application;

[0049] FIG5 is a cross-sectional view of a cylindrical member in an EEG dry electrode according to an embodiment of the present application;

[0050] FIG6 is a schematic diagram of a first structure of an EEG dry electrode according to another embodiment of the present application, wherein the axial length of the cylindrical member is 8 mm;

[0051] FIG7 is a schematic diagram of a second structure of an EEG dry electrode according to another embodiment of the present application, wherein the axial length of the cylindrical member is 8 mm;

[0052] FIG8 is a schematic diagram of a first structure of an EEG dry electrode according to another embodiment of the present application, wherein the axial length of the cylindrical member is 10 mm;

[0053] FIG9 is a schematic diagram of a second structure of an EEG dry electrode according to another embodiment of the present application, wherein the axial length of the cylindrical member is 10 mm;

[0054] FIG10 is a schematic diagram of the first structure of an EEG dry electrode according to another embodiment of the present application, wherein the axial length of the cylindrical member is 8 mm;

[0055] FIG11 is a schematic diagram of a second structure of an EEG dry electrode according to another embodiment of the present application, wherein the axial length of the cylindrical member is 8 mm;

[0056] FIG12 is a schematic diagram of the first structure of an EEG dry electrode according to another embodiment of the present application, wherein the axial length of the cylindrical member is 10 mm;

[0057] FIG13 is a schematic diagram of a second structure of an EEG dry electrode according to another embodiment of the present application, wherein the axial length of the cylindrical member is 10 mm;

[0058] FIG14 is a schematic structural diagram of an EEG dry electrode according to another embodiment of the present application;

[0059] FIG15 is a cross-sectional view of an EEG measurement device provided in an embodiment of the present application;

[0060] FIG16 is a schematic diagram of a partial structure of an EEG measurement device provided in an embodiment of the present application;

[0061] FIG17 is a schematic structural diagram of an EEG measurement device provided in an embodiment of the present application;

[0062] FIG18 is a schematic diagram of an EEG measurement device using a soft structure according to an embodiment of the present application;

[0063] FIG19 is a top view of an EEG measurement device using a rigid structure in another embodiment of the present application;

[0064] FIG20 is a right side view of an EEG measurement device using a rigid structure according to another embodiment of the present application;

[0065] FIG21 is a perspective view of a retractable EEG measurement device in one embodiment of the present application;

[0066] FIG22 is a schematic diagram of the structure of the frontal lobe electrode group and the sheet-shaped dry electrode in one embodiment of the present application;

[0067] FIG23 is a schematic diagram of the structure of the occipital electrode group (or parietal electrode group) and the needle-shaped dry electrode in one embodiment of the present application;

[0068] FIG24 is a schematic diagram of the electrode arrangement of a brain signal acquisition device in one embodiment of the present application;

[0069] FIG25 is a human body model database of the size design of the brain signal acquisition device in one embodiment of the present application;

[0070] FIG26 is a schematic structural diagram of a spring needle assembly used in a needle-shaped dry electrode in one embodiment of the present application;

[0071] FIG27 is a schematic structural diagram of a claw-shaped electrode used in a needle-shaped dry electrode in another embodiment of the present application;

[0072] FIG28 is a schematic structural diagram of a needle-shaped dry electrode using an active claw-shaped electrode in another embodiment of the present application;

[0073] FIG29 is a perspective view of an EEG measurement device in one embodiment of the present application;

[0074] FIG30 is a top view of an EEG measurement device in one embodiment of the present application;

[0075] FIG31 is a right side view of an EEG measurement device in one embodiment of the present application;

[0076] FIG32 is an exploded view of an EEG measurement device in one embodiment of the present application;

[0077] FIG33 is a perspective view of the EEG measurement device after extension and contraction in one embodiment of the present application;

[0078] FIG34 is a partial enlarged view of FIG33;

[0079] FIG35 is a cross-sectional view of the EEG measurement device after extension and contraction in one embodiment of the present application;

[0080] FIG36 is a schematic structural diagram of an EEG measurement device according to an embodiment of the present application with part of the housing hidden;

[0081] FIG37 is a top view of an EEG measurement device according to an embodiment of the present application;

[0082] FIG38 is a side view of an EEG measurement device according to an embodiment of the present application;

[0083] FIG39 is a partially enlarged view of an EEG measurement device according to an embodiment of the present application;

[0084] FIG40 is an exploded view of an EEG measurement device according to an embodiment of the present application;

[0085] FIG41 is a schematic structural diagram of an electrode sheet in one embodiment of the present application;

[0086] FIG42 is a schematic diagram of the structure of an electrode needle in an embodiment of the present application;

[0087] FIG43 is a schematic diagram of the installation structure of the electrode needle in one embodiment of the present application.

[0088] Reference numerals:

[0089] EEG dry electrode 100; base 10; connecting hole 101; button male member 102; column member 20; first member 201; tube body 2011; cover 2012; second member 202; cavity 2021; stopper 2022; first elastic member 203; conductive sheet 30; connecting member 40; second elastic member 50; mounting member 60; guide plate 70; guide groove 801; guide portion 802; signal transmission line 90;

[0090] First half ring 1b; second half ring 2b; third half ring 3b; frontal electrode group 4-1b; sheet dry electrode 41b; occipital electrode group 4-2b; needle dry electrode 42b; spring needle assembly 42A; ejector pin 42A-1; sleeve 42A-2; spring 42A-3; claw electrode 42B; base 42B-1; first electrode pin 42B-2; circuit board 43; parietal electrode group 4-3b;

[0091] First electrode assembly module 1c; first plugging block 11c; first limiting slot 111c; second electrode assembly module 2c; first plugging slot 21c; first locking tongue member 211c; first protruding end 2111c; second plugging slot 22c; second limiting slot 221c; three-way connecting portion 25c; third electrode assembly module 3c; second plugging block 31c; second locking tongue member 311c; second protruding end 3111c; guide post 32c; second electrode sheet 41c; second electrode needle 43c; second arc-shaped housing 51c; second electrode assembly bracket 52c; second electrode hole 521c; second intermediate layer 53c; function board 61c; second power board 62c; second ear clip 7c;

[0092] First body 1d; first locking structure 11d; card slot 111d; second body 2d; third body 3d; second locking structure 31d; wire tube 32d; third electrode sheet 41d; third electrode needle 43d; third arc-shaped shell 51d; third electrode group bracket 52d; third electrode hole 521d; third intermediate layer 53d; brain signal host board 61d; third power board 62d; third ear clip 7d; horizontal wiring channel 81d; vertical wiring channel 82d. DETAILED DESCRIPTION

[0093] The following describes in detail embodiments of the present application. Examples of the embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals throughout represent the same or similar elements or elements having the same or similar functions. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain the present application and are not to be construed as limiting the present application.

[0094] To make the purpose, technical solutions, and advantages of the embodiments of this application more clear, the technical solutions in the embodiments of this application will be clearly described below in conjunction with the drawings in the embodiments of this application. Obviously, the described embodiments are part of the embodiments of this application, not all of the embodiments. Based on the embodiments in this application, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of this application.

[0095] The following describes the EEG dry electrode 100 and the EEG measurement device of the present application with reference to FIG. 1 to FIG. 14 .

[0096] According to the embodiment of the present application, the EEG dry electrode 100 includes a substrate and a coating. The substrate includes a base 10 and a plurality of columnar members 20. One end portion of the plurality of columnar members 20 is fixed to the base 10 (as shown in Figures 1, 2, 6 to 14). At least the surface of the columnar member 20 is provided with a coating, and the coating on the surface of the columnar member 20 is electrically connected to the base 10.

[0097] More specifically, the substrate can be a copper piece, and correspondingly, the coating can be a silver coating or a silver / silver chloride coating. Alternatively, the substrate can be an ABS material piece (ABS material is a terpolymer of acrylonitrile (A)-butadiene (B)-styrene (S)), and the coating can be a silver / silver chloride coating. In this way, first, the contact resistance between the electrode and the scalp is small. Second, the electrode has good reversibility and is not easy to polarize. A slightly large current flows through it for a short time, and the potential can quickly return to the potential in the initial state after power failure. Third, the electrode potential is relatively stable and close to zero potential, and is not easy to polarize or passivate. Fourth, the potential reproducibility is good; the temperature coefficient is small, that is, the potential changes little with temperature; when the temperature returns to the original temperature, the potential can quickly return to the potential at the original temperature. Fourth, the preparation, actual use and maintenance are relatively convenient, and it is durable.

[0098] At least the surface of the column part 20 is provided with a coating, that is, the coating can be provided only on the surface of the column part 20, and the surface of the base 10 is not provided with a coating, the base 10 includes a conductive metal material part, and the coating on the surface of the column part 20 is electrically connected to the base 10; or the coating can be provided on both the surface of the column part 20 and the surface of the base 10, and the coating on the surface of the column part 20 is electrically connected to the coating on the surface of the base 10.

[0099] The base includes a base 10 and a plurality of columns 20. One end of each of the columns 20 is fixed to the base 10. It is understood that when in use, the other ends of the columns 20 contact the user's scalp. At least the surface of the columns 20 is provided with a coating. The coating on the surface of the columns 20 is electrically connected to the base 10, so that EEG signals can be transmitted to the base 10 via the coating on the surface of the columns 20. The base 10 can be connected to a signal transmission line 90 to transmit the EEG signals to an external receiving device via the signal transmission line 90. At the same time, the base 10 can also be used for mechanical connection to an external fixing device.

[0100] According to the EEG dry electrode 100 of the embodiment of the present application, a plurality of cylindrical members 20 are provided, one end of each of the plurality of cylindrical members 20 is connected to the base 10. When it is necessary to collect EEG signals from an area with hair, the plurality of cylindrical members 20 are inserted into the hair so that the other end of the cylindrical member 20 contacts the scalp. The cylindrical member 20 in the EEG dry electrode 100 of the present application can pass through the hair so that the other end of the cylindrical member 20 can remain in contact with the scalp, thereby solving the problem in the related art that flat-plate dry electrodes cannot be used in areas with hair. At the same time, the provision of multiple cylindrical members 20 can increase the contact area between the EEG dry electrode 100 and the scalp to reduce contact impedance.

[0101] In some embodiments, the length of the column member 20 in the axial direction can be 8 mm to 12 mm. For example, the length of the column member 20 in the axial direction can be 8 mm (for example, as shown in Figures 6 and 7, Figures 10 and 11), 9 mm, 10 mm (for example, as shown in Figures 8 and 9, Figures 12 and 13), 11 mm or 12 mm or any value between any two of them. In this way, the column member 20 will not be too long, resulting in the position of the EEG dry electrode 100 being difficult to fix; nor will the column member 20 be too short, and can be applied to hair of normal thickness, which is conducive to making the EEG dry electrode 100 more versatile.

[0102] In some embodiments, the number of the cylindrical members 20 can be reasonably set according to the size of the base 10, different usage scenarios, etc. For example, the number of the cylindrical members 20 can be 3, 4 (as shown in Figures 10 to 13), 5, 6 (as shown in Figures 6 to 9), 7 (as shown in Figures 1 and 2), 8, etc. For example, in areas with sparse hair, an EEG stem electrode 100 with a smaller number of cylindrical members 20 can be used, for example, an EEG stem electrode 100 with 4 cylindrical members 20 (as shown in Figures 10 to 13); in areas with dense hair, an EEG stem electrode 100 with a larger number of cylindrical members 20 can be used, for example, an EEG stem electrode 100 with 6 cylindrical members 20 (as shown in Figures 6 to 9).

[0103] According to some embodiments of the present application, as shown in FIG3 to FIG5 , the column member 20 includes a first member 201, a second member 202, and a first elastic member 203. The first member 201 is sleeved within the second member 202, and the second member 202 is movable relative to the first member 201 along an axial direction. The first elastic member 203 is disposed within the first member 201, with both ends of the first elastic member 203 connected to the first member 201 and the second member 202, respectively. The first elastic member 203 is configured to apply a restoring force to the second member 202 to cause it to move outward from the first member 201. In other words, when the second member 202 is pressed, the second member 202 moves inward from the first member 201 along the axial direction. When the external force applied to the second member 202 is stopped, the second member 202 moves outward from the first member 201 along the axial direction under the action of the restoring force of the first elastic member 203, wherein the axial direction is the axial direction of the column member 20.

[0104] To ensure that the other end of the column member 20 is in good contact with the scalp, if the column member 20 is a rigid column member, it needs to be pressed tightly against the user's scalp to ensure good contact between the column member 20 and the scalp. Prolonged wear can cause discomfort to the user. In this embodiment of the application, the column member 20 is provided with a first member 201, a second member 202, and a first elastic member 203. The elastic and resilient properties of the column member 20 help ensure that the other end of the column member 20 always forms good contact with the scalp. At the same time, the compressive force on the scalp is not excessive, which helps reduce user discomfort.

[0105] More specifically, the first elastic member 203 may be a spring. When the column member 20 comprising the first member 201, the second member 202 and the first elastic member 203 is extended or contracted, the minimum length of the column member 20 in the axial direction is not less than 8 mm.

[0106] According to some embodiments of the present application, the column 20 comprises copper. Experimental studies have shown that, during use, the potential of the EEG dry electrode 100, when the column 20 is made of copper, is stable and does not change significantly with increasing acquisition time, resulting in higher accuracy of the acquired data.

[0107] In some embodiments, as shown in FIG5 , the first piece 201 and the second piece 202 are both copper pieces. The second piece 202 has a concave cavity 2021, which has a first opening facing the first elastic piece 203. The first elastic piece 203 is inserted into the first opening and one end portion is located within the concave cavity 2021. The second piece 202 is a stamped and stretched part. The second piece 202 has a concave cavity 2021, which has a first opening facing the first elastic piece 203. This facilitates the use of stamping and stretching to form the second piece 202. It should be noted that copper pieces are relatively soft, and the second piece 202 is a long strip. If conventional milling is used, the yield rate of the second piece 202 is very low, the processing difficulty is high, and the processing time is long. In the embodiment of the present application, the second piece 202 is produced by stamping and stretching, which greatly reduces the processing difficulty, has a high yield rate, and has a good structural accuracy. At the same time, the column member 20 in the embodiment of the present application is larger in size than the traditional spring pin, that is, the second member 202 is larger in size and is suitable for being formed by stamping and stretching.

[0108] According to some embodiments of the present application, both the first member 201 and the second member 202 are copper members, as shown in FIG5 . A stopper 2022 is provided on the circumferential edge of the first opening. The stopper 2022 is larger than the outer diameter of the second member 202 in a direction perpendicular to the axis. The first member 201 includes a tube body 2011, which is open at both ends. The inner diameter of the edge of the tube body 2011 near the opening of the second member 202 is smaller than the size of the stopper 2022 in a direction perpendicular to the axis. The stopper 2022 is provided within the tube body 2011, which is integrally formed by stamping, stretching, and blanking. It is understood that the stopper 2022 can cooperate with the edge of the opening of the tube body 2011 near the second member 202 to limit the maximum movement of the second member 202 in the axial direction and away from the first member 201.

[0109] More specifically, the integral stamping, stretching, and blanking of the tube body 2011 includes: stamping and stretching a copper plate to form a first intermediate piece having a recessed portion, one end open, and the other end closed; then blanking the other end surface of the first intermediate piece to form an opening thereon, thereby obtaining a second intermediate piece; wherein the diameter of the opening at the other end surface of the second intermediate piece is smaller than the inner diameter of the circumferential sidewall of the second intermediate piece; and the second intermediate piece can serve as the first piece 201. Alternatively, a blanking operation can be performed on the edge of the opening at one end of the second intermediate piece to remove a portion of the edge of the opening at one end of the second intermediate piece that protrudes from the circumferential sidewall of the second intermediate piece in a direction perpendicular to the axis, thereby obtaining the first piece 201.

[0110] It should be noted that the copper component is relatively soft, and the tube body 2011 is a long strip. Conventional milling results in a low yield rate, high processing difficulty, and long processing time for the tube body 2011. The present embodiment utilizes integrated stamping, stretching, and blanking to produce the tube body 2011, significantly reducing the processing difficulty and achieving a high yield rate. The resulting tube body 2011 exhibits superior structural precision. Furthermore, the columnar member 20 in the present embodiment is larger than conventional spring pins, meaning that the tube body 2011 is larger, making it suitable for integrated stamping, stretching, and blanking.

[0111] According to some embodiments of the present application, the first member 201 further includes a cover 2012, which covers the opening of the tube body 2011 away from the second member 202, and the first elastic member 203 is connected to the cover 2012. More specifically, the cover 2012 is a flat plate. During assembly, the second member 202 can be first placed within the first member 201, then the first elastic member 203 can be placed within the first member 201, and finally the cover 2012 can be placed to cover the opening of the tube body 2011 away from the second member 202. Alternatively, the second member 202 can be first placed within the first member 201, then the first elastic member 203 can be connected to the cover 2012, and finally the first elastic member 203 can be placed within the first member 201, and the cover 2012 can be placed to cover the opening of the tube body 2011 away from the second member 202. The cover 2012 can be welded to the tube body 2011.

[0112] The first piece 201 includes a tube body 2011 and a cover body 2012 . This facilitates the production of the tube body 2011 by integrated stamping, stretching, and blanking, thereby reducing the difficulty of producing the first piece 201 .

[0113] According to some embodiments of the present application, a coating is provided on the surface of the base 10. The coating on the surface of the base 10 is electrically connected to the coating on the surface of the pillars 20. The base 10 and the plurality of pillars 20 are integrally injection molded, that is, the pillars 20 and the base 10 form a single piece. The use of integral injection molding to manufacture the base 10 and the pillars 20 improves the continuity of the coating on the surfaces of the base 10 and the pillars 20. Furthermore, the coating is more effectively bonded to the surfaces of the base 10 and the pillars 20, making it less likely for the coating to fall off.

[0114] According to some embodiments of the present application, the EEG dry electrode 100 further includes a conductive sheet 30, and the base 10 is provided with a connection hole 101, which is used to connect with the connector 40 to fix the conductive sheet 30 to the base, and the conductive sheet 30 is electrically conductive with the coating on the surface of the base 10. It should be noted that since the base 10 and the plurality of columnar members 20 are injection molded parts, it is not possible to directly weld and connect the signal transmission line 90 on the surface of the base 10. In the embodiment of the present application, by fixing the conductive sheet 30 on the base 10, one end of the signal transmission line 90 can be welded and connected to the conductive sheet 30, and the conductive sheet 30 is electrically connected to the coating on the surface of the base 10, so that the electrical signal can be transmitted to the external receiving device through the coating on the surface of the base 10, the conductive sheet 30 and the signal transmission line 90.

[0115] In some embodiments, one end of the signal transmission line 90 may be sandwiched between the conductive sheet 30 and the plating layer on the surface of the base 10 , so that the signal transmission line 90 may also be electrically connected to the plating layer on the surface of the base 10 .

[0116] In some embodiments, the conductive sheet 30 can be disposed on the side of the base 10 where the column 20 is disposed, or the conductive sheet 30 can also be disposed on the side of the base 10 facing away from the column 20. Specifically, by disposing the conductive sheet 30 on the side of the base 10 facing away from the column 20, and connecting one end of the signal transmission line 90 to the side of the conductive sheet 30 facing away from the base, the signal transmission line 90 can be as far away from the hair as possible. Furthermore, the conductive sheet 30 and one end of the signal transmission line 90 can be prevented from occupying the space defined between the multiple column members 20, thereby facilitating that the length of the column member 20 can be as short as possible.

[0117] More specifically, as shown in FIG14 , the connector 40 can be a screw and a nut. When connecting, the screw is passed through the conductive sheet 30 and the connection hole 101, and the nut is then tightened onto the screw to complete the fixation. This allows for a convenient, quick, and stable connection. Alternatively, the connector 40 can be an adhesive, with one end of the adhesive bonded to the side of the conductive sheet 30 facing away from the base 10 and the other end bonded to the base 10 to secure the conductive sheet 30. Alternatively, the connector 40 can be a screw, which passes through the conductive sheet 30 and extends into the connection hole 101, where the screw is directly threaded into the connection hole 101.

[0118] According to some embodiments of the present application, the base 10 and the plurality of columns 20 are made of ABS (ABS is a terpolymer of acrylonitrile (A)-butadiene (B)-styrene (S)). Experimental studies have shown that, during use, the potential of the EEG dry electrodes 100, when the columns 20 are made of ABS, is stable and does not change significantly with increasing acquisition time, resulting in highly accurate data.

[0119] In some embodiments, the ABS material piece is a hard ABS material piece.

[0120] According to some embodiments of the present application, as shown in FIG14 , the EEG dry electrode 100 further includes a second elastic member 50 and a mounting member 60. The second elastic member 50 is connected to the side of the base 10 facing away from the column member 20. The second elastic member 50 is retractable along the axis of the column member 20. The second elastic member 50 is connected between the base 10 and the mounting member 60. To ensure that the other end of the column member 20 is in good contact with the scalp, when the column member 20 is a rigid column member, it is necessary to press the column member 20 against the user's scalp to ensure good contact between the column member 20 and the scalp. However, wearing the column member 20 for a long time can cause discomfort to the user. In this embodiment of the present application, by providing the second elastic member 50 on the side of the base 10 facing away from the column member 20, the second elastic member 50 helps ensure that the other end of the column member 20 can always form good contact with the scalp. At the same time, it also prevents excessive pressure on the scalp, which helps reduce user discomfort. The mounting member 60 is used to connect to an external fixing device. More specifically, the second elastic member 50 may be a spring.

[0121] According to some embodiments of the present application, the EEG dry electrode 100 further includes a flexible shielding member, which is disposed around the circumferential outer side of the second elastic member 50. The two end edges of the flexible shielding member in the axial direction are respectively connected to the base 10 and the mounting member 60. More specifically, the flexible shielding member can be a silicone member, a rubber member, a cortical layer, a cloth, etc.

[0122] According to some embodiments of the present application, as shown in FIG14 , the EEG dry electrode 100 further includes a guide plate 70, which is disposed around the circumferential outer side of the second elastic member 50. At least one of the base 10 and the mounting member 60 is connected to the guide plate 70 via a guide structure. The guide structure includes a guide groove 801 and a guide portion 802. The guide portion 802 is movably inserted into the guide groove 801 along the axis of the cylindrical member 20. It can be understood that, on the one hand, the guide plate 70 and the guide structure cooperate to guide the relative movement between the base 10 and the mounting member 60. On the other hand, the guide plate 70 can shield the second elastic member 50, thereby reducing the possibility of the second elastic member 50 contacting hair, thereby reducing the possibility of hair entanglement with the second elastic member 50. On the other hand, the appearance of the EEG dry electrode 100 is also more beautiful. In addition, the connection stability between the base 10 and the mounting member 60 can be improved, so that the base 10 and the mounting member 60 will not be offset in the direction perpendicular to the axis.

[0123] More specifically, the guide plate 70 can be an annular plate member arranged around the circumferential outside of the second elastic member 50 (as shown in Figure 14); or, a plurality of guide plates 70 are arranged at intervals along the circumference of the second elastic member 50, and the plurality of guide plates 70 are arranged around the circumferential outside of the second elastic member 50.

[0124] In some embodiments, the guide structure is provided with one, the guide structure is provided on the base 10, that is, the guide groove 801 is provided on the base 10, the guide plate 70 is connected between the mounting member 60 and the guide portion 802, and the guide portion 802 is movably inserted into the guide groove 801 along the axial direction of the column member 20.

[0125] In some embodiments, the guide structure is provided with one, the guide structure is provided on the mounting member 60, that is, the guide groove 801 is provided on the mounting member 60, the guide plate 70 is connected between the base 10 and the guide part 802, and the guide part 802 is movably inserted into the guide groove 801 along the axial direction of the column member 20.

[0126] As shown in Figure 12, in some embodiments, there are two guide structures, which are respectively provided on the base 10 and the mounting member 60, that is, two guide grooves 801 are respectively provided on the base 10 and the mounting member 60, and the two guide parts 802 are respectively connected to the two end portions of the guide plate 70 in the axial direction, and the guide parts 802 are movably inserted into the guide grooves 801 along the axial direction of the column member 20, so that the range of relative movement between the base 10 and the mounting member 60 is larger.

[0127] In some embodiments, as shown in Figures 1 and 3, the base 10 can be a circuit board, and the EEG dry electrode 100 also includes a button male component 102. The base 10 can be connected to the button male component 102, such as by welding. The external fixing device includes a button female component. The button male component 102 and the button female component can be plugged into each other for quick connection.

[0128] This application also proposes an electroencephalogram (EEG) measuring device.

[0129] The EEG measurement device according to an embodiment of the present application includes the EEG dry electrode 100 according to any one embodiment of the present application.

[0130] Compared with the prior art, the advantages of the EEG measurement device of the present application are the same as those of the EEG dry electrode 100 of the embodiment of the present application, which will not be repeated here.

[0131] The present application provides some embodiments of an EEG measurement device. Referring to Figure 15 , the device includes a wearable component 01a, a propulsion component 02a, and a signal collection electrode 03a. As shown in Figure 15 , the device may include multiple propulsion components 02a and multiple signal collection electrodes 03a. The multiple signal collection electrodes 03a may correspond one-to-one with the multiple propulsion components 02a.

[0132] The wearable component 01a is suitable for being worn on the user's head and has a mounting cavity A. The pushing component 02a is located in the mounting cavity A. The signal collection electrode 03a is movably connected to the wearable component 01a. For example, the signal collection electrode 03a can be movably connected to the inner side of the wearable component 01a (i.e., the side closer to the user's head).

[0133] After a user wears the wearable assembly 01a on their head, the pushing assembly 02a is configured to push the signal acquisition electrode 03a toward the head when the contact impedance between the signal acquisition electrode 03a and the head is greater than or equal to a first impedance threshold, thereby automatically adjusting the contact impedance between the signal acquisition electrode 03a and the head. The contact impedance between the signal acquisition electrode 03a and the head refers to the contact impedance between the signal acquisition electrode 03a and the skin of the head.

[0134] It is understood that the pushing component 02a can push the signal collection electrode 03a multiple times until the contact impedance is less than a first impedance threshold. The first impedance threshold refers to the maximum contact impedance allowed between the signal collection electrode 03a and the user's head, provided that the EEG signal quality collected by the EEG measurement device meets quality requirements. In other words, the first impedance threshold is the maximum contact impedance that does not affect the quality of EEG signal collection.

[0135] In summary, an embodiment of the present application provides an EEG measurement device, which includes a wearable component, a signal acquisition electrode movably connected to the wearable component, and a pushing component located in the mounting cavity of the wearable component. The pushing component can automatically push the signal acquisition electrode toward the user's head when the contact impedance between the signal acquisition electrode and the user's head is greater than or equal to a first impedance threshold, so that the signal acquisition electrode is in full contact with the head. Since there is no need for the staff to manually adjust the signal acquisition electrode to make the signal acquisition electrode in full contact with the head, the EEG measurement device provided by the embodiment of the present application is highly intelligent and can simplify the operation of the staff.

[0136] In an embodiment of the present application, referring to FIG16 , the EEG measurement device may further include: a conductive rod 04a. A through hole (not shown in FIG16 ) is provided on one side of the mounting cavity A of the wearable component 01a. The conductive rod 04a may be located in the through hole to be movably connected to the wearable component 01a. One end of the conductive rod 04a is connected to the signal acquisition electrode 03a, and the other end of the conductive rod 04a may abut against the push component 02a.

[0137] The pushing component 02a can push the conductive rod 04a toward the user's head when the contact impedance between the signal collection electrode 03a and the user's head is greater than or equal to a first impedance threshold. The conductive rod 04a can then drive the signal collection electrode 03a toward the user's head.

[0138] In an embodiment of the present application, the EEG measurement device can be connected to an electronic device (such as a computer). After the user wears the wearable component 01a on the user's head, the electronic device can obtain the contact impedance between the signal acquisition electrode 03a and the head, and can control the pushing component 02a to automatically push the signal acquisition electrode 03a toward the head when it is determined that the contact impedance is greater than or equal to a first impedance threshold. The electronic device can be independent of the EEG measurement device, and the electronic device can pre-store the first impedance threshold.

[0139] Alternatively, referring to FIG17 , the EEG measurement device may further include: a controller 05a, which may be connected to a pushing component 02a. After the user wears the wearable component 01a on the user's head, the controller 05a may obtain the contact impedance between the signal acquisition electrode 03a and the head. If the controller 05a determines that the contact impedance is greater than or equal to a first impedance threshold, it may be determined that the signal acquisition electrode 03a is not in sufficient contact with the skin of the head, and then the pushing component 02a may be controlled to push the signal acquisition electrode 03a toward the direction close to the head so that the signal acquisition electrode 03a can be in sufficient contact with the head. The controller 05a may pre-store the first impedance threshold.

[0140] In the embodiment of the present application, there are many ways to implement the pushing component 02a. The embodiment of the present application takes the following optional implementations as examples to illustrate the pushing component 02a:

[0141] In a first optional implementation, the propulsion component 02a may be an airbag. One end of the airbag may be fixedly connected to the inner wall of the mounting cavity A of the wearable component 01a, for example, by bonding. The other end of the airbag may abut against the signal acquisition electrode 03a after inflation. The airbag is configured to inflate when the contact impedance between the signal acquisition electrode 03a and the head is greater than or equal to a first impedance threshold, thereby pushing the signal acquisition electrode 03a toward the head.

[0142] For the first implementation, the EEG measurement device may further include an inflation assembly connected to the airbag. The inflation assembly may be configured to inflate the airbag when the contact impedance between the signal acquisition electrode 03a and the head is greater than or equal to a first impedance threshold. Optionally, the inflation assembly may be a blower or an air pump.

[0143] In an embodiment of the present application, the EEG measurement device may further include an airway tube. One end of the airway tube may be connected to the airbag, and the other end of the airway tube may be connected to the inflation assembly. In this way, the inflation assembly can inflate the airbag through the airway tube.

[0144] It is understood that the inflatable component can be connected to the controller 05a of the EEG measurement device. The controller 05a can be used to control the inflatable component to inflate the airbag when the contact impedance between the signal acquisition electrode 03a and the head is greater than or equal to a first impedance threshold. Alternatively, the inflatable component can be connected to an electronic device. The electronic device can be used to control the inflatable component to inflate the airbag when the contact impedance between the signal acquisition electrode 03a and the head is greater than or equal to the first impedance threshold.

[0145] It is understood that the inner wall of the mounting cavity A of the wearable component 01a may be provided with a storage groove. The airbag may be disposed within the storage groove, for example, by bonding to the groove wall. When the airbag is not inflated, it may be located within the storage groove to accommodate the airbag. After the airbag is inflated, part of the airbag may be located outside the storage groove.

[0146] In a second optional implementation, the pushing component 02a can be a telescopic component, such as a telescopic rod. One end of the telescopic component can be connected to the inner wall of the mounting cavity A of the wearable component 01a, and the other end of the telescopic component can abut against the signal collection electrode 03a when in an extended state. The telescopic component can be configured to be in the extended state when the contact impedance between the signal collection electrode and the head is greater than or equal to a first impedance threshold, thereby pushing the signal collection electrode 03a toward the user's head.

[0147] In a third optional implementation, the pushing component 02a can be an electromagnet connected to the signal acquisition electrode 03a. In this case, the inner wall of the mounting cavity A of the wearable component 01a can also be provided with a magnet, which is arranged opposite to the pushing component 02a. For example, the orthographic projection of the magnet on the plane where the pushing component 02a is located coincides with the pushing component 02a, or is located within the pushing component 02a. The magnet can be a permanent magnet or an electromagnet.

[0148] The pushing component 02a can be used to energize when the contact impedance between the signal collection electrode and the head is greater than or equal to a first impedance threshold to generate a magnetic field opposite to the magnet, thereby pushing the signal collection electrode 03a to move closer to the user's head.

[0149] For the third optional implementation, the EEG measurement device may further include: a power supply component, which may be connected to the pushing component 02a and may be used to provide an electrical signal to the pushing component 02a so that the pushing component 02a may generate a magnetic field opposite to that of the mounting member.

[0150] For example, the power supply component can provide an electrical signal to the driving component 02a under the control of the controller 05a of the EEG measurement device or an electronic device, wherein the electrical signal can be a current signal or a voltage signal.

[0151] In an embodiment of the present application, referring to FIG17 , the EEG measurement device may further include an impedance detection component 06a. As shown in FIG17 , the impedance detection component 06a may be connected to the signal acquisition electrode 03a and the controller 05a, respectively. When the EEG measurement device is worn on the user's head and the impedance test process is initiated, the impedance detection component 06a may detect the contact impedance between the signal acquisition electrode 03a and the user's head and transmit the contact impedance to the controller 05a. Accordingly, the controller 05a may obtain the contact impedance.

[0152] Optionally, the pushing component 02a can be configured to push the signal collection electrode 03a according to a reference strength corresponding to the contact impedance between the signal collection electrode 03a and the head. The reference strength is determined based on the contact impedance and from a corresponding relationship between impedance and strength. This relationship records multiple impedances, and any two impedances are different. Any strength is also different.

[0153] It can be seen that the pushing component 02a can push the signal collection electrode 03a in different strengths, thereby improving the control flexibility of the signal collection electrode 03a.

[0154] It is understood that the intensity recorded in this correspondence can increase with increasing impedance, that is, the intensity recorded in this correspondence is positively correlated with impedance. This allows the signal acquisition electrode to be pushed with a greater force when the contact impedance is high, thereby enabling the signal acquisition electrode 03a to quickly and closely contact the head, shortening the time it takes for the contact impedance between the signal acquisition electrode and the head to fall below the first impedance threshold, thereby improving the control efficiency of the signal acquisition electrode.

[0155] In an embodiment of the present application, the controller 05a (or electronic device) may pre-store a correspondence between impedance and strength. After the controller 05a (or electronic device) obtains the contact impedance between the signal acquisition electrode and the user's head, it may determine the reference pushing strength corresponding to the contact impedance from the correspondence.

[0156] It is understood that if the pushing component 02a is an airbag, the intensity recorded in the corresponding relationship between impedance and intensity may refer to the amount of air inflated by the inflatable component each time the airbag is inflated. If the pushing component 02a is a telescopic component, the intensity recorded in the corresponding relationship between impedance and intensity may refer to the length of the telescopic component extended each time. If the pushing component 02a is an electromagnet, the intensity recorded in the corresponding relationship between impedance and intensity may refer to the magnitude of the electrical signal provided by the power supply component to the electromagnet each time.

[0157] In an embodiment of the present application, if the controller 05a (or electronic device) determines that the contact impedance of a target number of signal acquisition electrodes 03a among the multiple signal acquisition electrodes 03a of the EEG measurement device meets the target condition, the EEG signal can be collected through the multiple signal acquisition electrodes 03a. Among them, the target number is less than or equal to the total number of the multiple signal acquisition electrodes 03a and is greater than the quantity threshold. The target condition is that the duration of the contact impedance less than the first impedance threshold reaches the target duration. Both the quantity threshold and the target duration can be pre-stored by the controller 05a. For example, the quantity threshold can be four-fifths of the total. The target duration can be 10 minutes (min).

[0158] For example, the target number can be the total number of signal acquisition electrodes. Specifically, after the controller 05a (or electronic device) determines that the contact impedances of all signal acquisition electrodes 03a of the EEG measurement device meet the target conditions, it can then collect the user's EEG signals. Specifically, the controller 05a only begins collecting EEG signals after determining that the signal acquisition electrodes 03a are relatively stable relative to the head. This prevents excessive noise in the collected EEG signals, thereby ensuring high quality of the collected EEG signals.

[0159] According to the above description, the EEG measurement device provided in the embodiment of the present application can realize automatic adjustment of contact impedance, and can automatically start collecting EEG signals after the contact impedances of the target number of signal collection electrodes 03a all meet the target conditions.

[0160] In an embodiment of the present application, the signal acquisition electrode 03a can be a needle-shaped electrode. The wearable component 01a can be in the shape of a cap, or the wearable component 02 can be in the shape of a ring. In the case where the wearable component 01a can be in the shape of a ring, the EEG measurement device can further include: a plurality of sheet electrodes. The plurality of sheet electrodes and the plurality of needle electrodes can be arranged relative to each other. For example, the number of sheet electrodes can be 5, and the number of needle electrodes can be 4. One of the 5 sheet electrodes is a ground (GND) electrode. That is, the EEG measurement device is an 8-lead EEG measurement device.

[0161] During the process of collecting the user's brain electrical signals, multiple sheet electrodes may be in contact with the user's forehead, and multiple needle electrodes may be in contact with the back of the user's head.

[0162] Optionally, the wearing component 01a can be made of flexible material.

[0163] In summary, an embodiment of the present application provides an EEG measurement device, which includes a wearable component, a signal acquisition electrode movably connected to the wearable component, and a pushing component located in the mounting cavity of the wearable component. The pushing component can automatically push the signal acquisition electrode toward the user's head when the contact impedance between the signal acquisition electrode and the user's head is greater than or equal to a first impedance threshold, so that the signal acquisition electrode is in full contact with the head. Since there is no need for the staff to manually adjust the signal acquisition electrode to make the signal acquisition electrode in full contact with the head, the EEG measurement device provided by the embodiment of the present application is highly intelligent and can simplify the operation of the staff.

[0164] In view of the disadvantage of poor brain signal acquisition effect of using a single-form brain signal acquisition device in the prior art, the present application provides some embodiments of an EEG measurement device, which uses dual-form electrodes according to different acquisition areas to reduce the difficulty of brain signal acquisition and improve the signal quality of brain signal acquisition.

[0165] The present application provides some embodiments of an EEG measurement device, wherein the acquisition device includes a main body and a frontal lobe electrode group 4-1b and a non-frontal lobe electrode group disposed on the main body; wherein the frontal lobe electrode group 4-1b includes a plurality of sheet-shaped dry electrodes 41b, which are mounted on the main body corresponding to the user's frontal lobe brain region, and the non-frontal lobe electrode group includes a plurality of needle-shaped dry electrodes 42b, which are mounted on the main body corresponding to the user's non-frontal lobe brain region. wherein the frontal lobe brain region includes at least one of the following: the anterior frontal lobe brain region and the posterior frontal lobe brain region, and the non-frontal lobe brain region includes at least one of the following: the parietal lobe brain region, the occipital lobe brain region, and the temporal lobe brain region.

[0166] Among them, the frontal lobe, parietal lobe, occipital lobe and temporal lobe are common EEG signal collection areas.

[0167] As a frontal brain region, the frontal lobe is located in the front of the brain and includes the anterior frontal lobe and the posterior frontal lobe. The anterior frontal lobe is the front part of the frontal lobe, adjacent to the lower edge of the frontal bone, and is involved in functions such as emotion, decision-making, cognitive control, and social behavior. The posterior frontal lobe is the posterior part of the frontal lobe and is involved in functions such as visual information processing and spatial cognition. As a non-frontal brain region, the parietal lobe is located in the central area of ​​the brain and is involved in functions such as sensory information processing and attention. The occipital lobe is located in the back of the brain and is involved in functions such as visual information processing and spatial navigation. The temporal lobe is located on the side of the brain and is involved in functions such as auditory information processing, language, and memory.

[0168] Based on the contact characteristics of different areas of the head, the EEG measurement device of the embodiment of the present application introduces dual-form dry electrodes. A sheet-shaped dry electrode 41b is set in an area with less or no hair (such as the frontal lobe or its prefrontal lobe) to collect brain signals in this area. The sheet-shaped dry electrode 41b can contact the scalp more directly, improve the stability and sensitivity of the signal, and thus effectively collect brain signals in this area. A needle-shaped dry electrode 42b is set in an area with more hair (such as the parietal lobe, occipital lobe, and temporal lobe) to collect brain signals in this area. The needle-shaped dry electrode 42b can penetrate the hair and contact the scalp more easily, reducing the interference of hair on signal contact. At the same time, it can also better maintain the contact stability between the electrode and the scalp, which helps to improve the signal quality of brain signal collection in this brain area.

[0169] Compared with the frontal lobe brain region which still uses needle-shaped dry electrodes for collecting data, the collection device of the embodiment of the present application uses sheet-shaped dry electrodes in the frontal lobe brain region, which is more comfortable for the subjects to wear, and the sheet-shaped dry electrodes are more firmly fixed, and the signal collection is more stable.

[0170] In the above embodiment, this dual-pattern dry electrode arrangement fully accounts for the characteristics of different head regions, effectively reducing the difficulty of brain signal acquisition and improving the signal quality. This design not only helps improve the accuracy and reliability of brain signal acquisition, but also enhances the comfort and participation of the subjects, thereby better meeting the needs of scientific research and clinical applications.

[0171] The advantage of this brain signal acquisition device is that it can be flexibly adjusted according to the characteristics of different regions of the head, thereby reducing the difficulty of brain signal acquisition and improving the quality and reliability of the signal. This design is expected to be widely used in the field of brain signal acquisition, providing more reliable and accurate brain signal data for scientific research, medical treatment and other fields, helping to promote the development and progress of related fields.

[0172] In some embodiments, the body is an integrated hard structure or an integrated elastic cap structure.

[0173] For example, the body in the embodiment shown in FIG18 adopts a soft, one-piece elastic cap-type structure, in which the large disc in the frontal lobe brain region represents a sheet-like dry electrode, and the small disc electrode in the non-frontal lobe brain region represents a needle-like dry electrode (the electrode needle is located on the side in contact with the model scalp and is not shown); the body in the embodiments shown in FIG19-FIG21 adopts an one-piece hard structure.

[0174] The electrode cap (main body) of the EEG device can use a variety of soft materials or forms to improve wearing comfort and signal acquisition effects, such as silicone materials, cloth, elastic materials, etc. Silicone is soft and elastic, and can fit the contour of the head, providing good wearing comfort. At the same time, silicone materials are also durable and easy to clean. Soft fabrics or foam materials can be used to make electrode caps, providing a soft fit and ventilation, reducing the wearer's discomfort. The electrode cap made of a material with a certain degree of elasticity can provide a certain degree of elasticity while maintaining stability, and can adapt to people with different head circumferences. Regardless of the soft material or form chosen, the key is to ensure that the electrode cap fits well with the head, maintains stable contact, and provides a comfortable wearing experience. The forms of the electrode cap of the EEG device include but are not limited to mesh caps, closed helmets, or linear caps.

[0175] The electrode cap (main body) of the EEG device can also be made of hard materials. Hard materials can better fix and support the electrode group, reduce the possibility of electrode position movement due to head movement and other reasons, and thus improve the stability of signal acquisition. The electrode cap made of hard materials can better maintain the consistency of shape and size, thereby improving the repeatability of signal acquisition and facilitating the comparison and analysis of experimental data. Hard materials can be adjusted through expansion or pressurization to adapt to the wearing requirements of different head shapes and improve wearing comfort. Compared with soft materials, the surface of hard materials is easier to clean, reducing the possibility of bacterial growth, thereby improving the hygiene of wearing.

[0176] As shown in Figures 18 and 19-21, in some embodiments, the non-frontal electrode group includes a parietal electrode group 4-3b and an occipital electrode group 4-2b (the temporal lobe brain region can be distributed in any electrode group or multiple electrode groups), and the parietal electrode group 4-3b and the occipital electrode group 4-2b each include a plurality of needle-shaped dry electrodes 42b. The parietal electrode group 4-3b is installed on the parietal brain region of the main body corresponding to the user, and the occipital electrode group 4-2b is installed on the occipital brain region of the main body corresponding to the user.

[0177] In addition to the frontal lobe, the EEG device in the embodiment of the present application also has acquisition electrodes in the parietal, occipital, and temporal lobes. This allows for acquisition of brain signals from the front, middle, and back regions of the brain, enabling comprehensive brain signal acquisition. Brain signals from different regions have different frequency and amplitude characteristics. Multi-region acquisition can improve the spatiotemporal resolution of brain signals, helping to more accurately reflect changes in brain function and activity, and also contributing to in-depth exploration of brain function and its related mechanisms.

[0178] Multi-region acquisition also allows for comparative analysis, such as comparing the frontal lobe with the parietal, occipital, and temporal lobes. This helps study the interactions and coordination between different brain regions. Brain signals from different regions are distinctive, and multi-region acquisition can reduce confounding signals such as muscle and eye movements, improving the purity and reliability of the acquisition.

[0179] The electrodes of the brain signal acquisition device in the embodiment of the present application are all dry electrodes. Compared with wet electrodes and water electrodes, which require gel and saline as conductive media to collect brain signals, dry electrodes do not need any conductive medium to collect brain signals, so the selection of materials and shapes of dry electrodes need to be more stringent. Due to the access of conductive media, the EEG contact impedance of wet electrodes and water electrodes is reduced, the noise of the input analog signal is reduced, and brain signals can be better collected. As for dry electrodes, according to the calculation formula of contact resistance, it is as follows:

[0180] in:

[0181] The K value is a coefficient related to the material;

[0182] F represents the contact pressure;

[0183] m represents the contact form, m = 0.5 for point contact, m = 0.5~0.7 for line contact, and m = 1 for surface contact.

[0184] The EEG device in the embodiment of the present application can use active electrodes or passive electrodes. The active electrodes have integrated amplifiers to amplify brain signals and suppress noise interference to improve the signal-to-noise ratio.

[0185] Passive electrodes are generally less expensive than active electrodes because they do not require additional circuitry and power. Passive electrodes are simple in structure and relatively easy to use.

[0186] In some embodiments, the sheet-like dry electrode 41b is a passive dry electrode, and the sheet-like dry electrode 41b is in a disc structure of predetermined thickness, with a base material of copper and a coating of silver, or a base material of copper and a coating of silver-plated silver chloride. The electrode is designed with a disc-shaped structure, which is convenient for fixation and contact on the skin surface, thereby achieving stable signal acquisition. The electrode has a predetermined thickness, which helps to ensure the contact quality and stability between the electrode and the skin. Silver is an excellent conductive material, which is conducive to ensuring good signal transmission and contact quality. In some cases, in order to further improve the conductivity and corrosion resistance, a silver-plated silver chloride coating structure can be used.

[0187] In some embodiments, as shown in FIG. 26 and FIG. 27 , the needle-shaped dry electrode 42 b is a passive dry electrode, and its structure can adopt various forms to achieve stable bioelectric signal acquisition and minimize interference to the tested subject.

[0188] For example, in the embodiment shown in Figure 26, the needle-shaped dry electrode 42b is a spring needle assembly 42A for a single acquisition point, comprising a pin 42A-1, a sleeve 42A-2, and a spring 42A-3 disposed within the sleeve 42A-2. The pin 42A-1 is disposed within the sleeve 42A-2 via the spring 42A-3 and has a working stroke that allows it to extend and retract along the axis of the sleeve 42A-2. This structural design helps adapt to different skin surface shapes and human head circumferences, thereby achieving better contact quality. The base material of the needle-shaped dry electrode 42b is copper, with a silver coating. Copper as a base material has excellent mechanical and electrical properties, while the silver coating helps ensure good signal transmission quality.

[0189] Furthermore, relative to the fixed sleeve 42A-2, the setting of the ejector pin 42A-1 may also have a certain tilt or swing angle, such as 1-5°, optionally 3°. The ejector pin 42A-1 having a certain tilt or swing angle can make the needle-shaped dry electrode 42b better adapt to the curve and shape of the skin surface, thereby improving the stability and quality of contact. This design can have a positive impact on the effect of signal acquisition in practical applications, especially when it needs to be worn for a long time, and can reduce the problem of electrode displacement or poor contact caused by movement or other factors. Such a swinging design helps to improve the stability and accuracy of signal acquisition, and meets the requirements of signal acquisition accuracy in fields such as biomedicine.

[0190] Furthermore, the needle-shaped dry electrode 42b is a spring needle assembly 42A of a single collection point, whose maximum contact impedance at the working height is 50mΩ, the elastic force at the normal working height is 10g~30g, the working stroke is 3.5mm±0.02, and the working height is 6.5mm±0.02.

[0191] For another example, in the embodiment shown in FIG27 , the needle-shaped dry electrode 42 b is a passive dry electrode. The needle-shaped dry electrode 42 b is a claw-shaped electrode 42BB with multiple acquisition points. It includes a base 42B-1 and multiple electrode needles 42B-2 disposed on the base 42B-1, each of which is evenly distributed along one side of the base 42B-1. This design integrates multiple electrode needles 42B-2 on a single base 42B-1, facilitating electrode placement and enabling multi-point acquisition, thereby improving the spatial resolution of signal acquisition.

[0192] The active dry electrode design effectively reduces noise interference caused by the electrodes themselves and connecting cables, while also providing signal amplification and conditioning, all of which contribute to improved biopotential signal acquisition quality. Active electrodes have low input impedance, reducing contact resistance between the electrode and skin and improving signal acquisition sensitivity. Due to their internal amplifier design, active electrodes are highly resistant to interference from external power sources and the environment.

[0193] In some embodiments, the sheet-shaped dry electrode 41b and / or the needle-shaped dry electrode 42b are active dry electrodes, and are disposed on a circuit board 43 comprising a voltage follower circuit. The voltage follower circuit on the circuit board 43 can help amplify and process the signal during signal acquisition, thereby improving the signal-to-noise ratio and ensuring signal accuracy. The voltage follower circuit can also be used to ensure signal stability under various conditions. For example, it can automatically adjust operating parameters to ensure stable signal acquisition when varying skin resistance or environmental interference occurs.

[0194] In the embodiment shown in FIG28 , where the needle-shaped dry electrode 42 b is an active dry electrode, the needle-shaped dry electrode 42 b is a claw-shaped electrode 42B with multiple collection points, comprising a base 42B-1 and multiple electrode needles 42B-2 disposed on the base 42B-1. Each electrode needle 42B-2 is evenly distributed on one side of the base 42B-1, and the base 42B-1 is welded to the circuit board 43. This design enables multiple collection points, improving the spatial resolution and accuracy of signal acquisition. Each electrode needle 42B-2 can be considered an independent collection channel, enabling simultaneous acquisition of bioelectrical activity from multiple signal sources. The welded fixation of the base 42B-1 ensures electrode stability and reliability, thereby reducing signal distortion or interference caused by electrode displacement or poor contact.

[0195] Furthermore, the circuit board 43 is shaped to accommodate at least one claw-shaped electrode 42B, and at least one fixing hole (optionally two symmetrically arranged for secure fixation) is also provided on the circuit board 43. In addition to the voltage follower circuit 431, the circuit board 43 may also be provided with a solder pad 432 or a plug-in interface for connecting a signal line.

[0196] The output voltage of a voltage follower is the same as the input voltage, meaning its voltage amplification factor is always less than and close to 1. A voltage follower's defining characteristic is its high input impedance and low output impedance. Generally speaking, it's easy to achieve an input impedance of several megohms. The output impedance is low, typically reaching a few ohms or even lower. Voltage followers are used in the design of active dry EEG electrodes because some materials of dry electrodes have significantly higher impedance when in contact with the scalp than do water or wet electrodes. When using dry electrodes, the excessively high inherent impedance causes the electrodes to enter the lead-off state. Using a voltage follower circuit can reduce this impedance.

[0197] In some embodiments, one of the plurality of sheet-shaped dry electrodes 41b included in the frontal lobe electrode group 4-1b is a GND electrode. One of the sheet-shaped dry electrodes 41b is designated as a GND (ground) electrode, such as the front-most middle electrode. The GND electrode serves to provide a reference potential or as a location in a circuit for comparison and measurement of signals collected by other electrodes.

[0198] The GND electrode can share the same physical contact location with other sheet-shaped dry electrodes 41b, such as being placed at a specific point on the scalp. By designating one sheet-shaped dry electrode 41b as the GND electrode, the signals collected by the other electrodes are compared with this electrode as a reference, and the potential difference relative to the ground is calculated, thereby obtaining more accurate measurement results. In applications such as electroencephalography (EEG), the correct setting of the GND electrode is crucial for obtaining accurate signals. It helps reduce common-mode noise between electrodes and provides a stable reference point, making the measurement results more reliable and comparable.

[0199] In the embodiment of the present application, the frontal lobe electrode group 4-1b can be provided with five sheet-shaped dry electrodes 41b, of which four sheet-shaped dry electrodes 41b serve as EEG activity electrodes and one sheet-shaped dry electrode 41b serves as an EEG GND electrode. The parietal lobe electrode group 4-3b and the occipital lobe electrode group 4-2b can each be provided with four needle-shaped dry electrodes 42b. Of course, the needle-shaped dry electrodes 42b described here can adopt the structure of the claw-shaped electrodes 42B described above, that is, a single needle-shaped dry electrode 42b can also include multiple electrode needles 42B-2.

[0200] The number of electrodes in the embodiment of the present application is adjusted according to the brain area to be sampled and is not limited to a fixed number. The electrode positions can be symmetrical according to the international 10-20 system electrode placement method as shown in Figure 24.

[0201] In some embodiments, the body is a rigid structure. To increase its applicability to different populations, the body can be designed as a retractable structure. The body includes a first semi-ring 1b corresponding to the parietal, occipital, and temporal regions, a second semi-ring 2b corresponding to the occipital region, and a third semi-ring 3b corresponding to the parietal and / or temporal regions. The three semi-rings of the body are interconnected to form an integrated structure, and a retractable structure is provided between at least two of the first semi-ring 1b, the second semi-ring 2b, and the third semi-ring 3b.

[0202] Optionally, the non-frontal electrode group is provided on the inner side of the second semi-ring 2b and / or the third semi-ring 3b. Furthermore, the frontal electrode group 4-1b is provided on the inner side of the first semi-ring 1b, the occipital electrode group 4-2b is provided on the inner side of the second semi-ring 2b, and the parietal electrode group 4-3b is provided on the inner side of the third semi-ring 3b. The first semi-ring 1b and the second semi-ring 2b form a closed annular shape, and the third semi-ring 3b is provided to intersect with the first semi-ring 1b or the second semi-ring 2b. Relative to the second semi-ring 2b, the first semi-ring 1b and the third semi-ring 3b are both configured as retractable structures.

[0203] In the above embodiment, the body is a rigid structure used to secure the electrodes and secure them to the scalp for signal acquisition. In the body design, the first half ring 1b and the third half ring 3b intersect with the second half ring 2b, and both are designed to be retractable. This retractable structure can employ a plug-in and locking mechanism with a certain depth. The plug-in and locking mechanism is typically designed with interlocking convex and concave shapes. Once the two parts are inserted to a certain depth, a locking mechanism automatically secures them together, ensuring that the body will not loosen or shift due to external forces. This design is not only simple and easy to implement, but also provides stable support and a comfortable experience during wear. This allows the body to adapt to people of different head sizes and shapes, thereby improving its applicability and comfort. Furthermore, the retractable structure of the first half ring 1b and the third half ring 3b helps reduce the sense of pressure on the head when worn.

[0204] Optionally, the size design of the first half ring 1b, the second half ring 2b and the third half ring 3b of the above-mentioned body can refer to Figure 8, which is a human body model database. The size design of the body can cover head circumference data of different genders, different ages, etc.

[0205] The present application also provides some embodiments of an EEG measurement device, which is an integrated design to avoid interference from the movement of cables, making the whole device more convenient to wear. Brain signals are a type of bioelectric signal that reflects the electrical activity of brain neurons. When neurons in the brain emit electrical pulses, weak currents are generated, which propagate through the scalp and brain tissue and can be captured by EEG electrodes. Brain signals usually appear as periodic wave patterns, and their characteristics include frequency, amplitude, and morphology. Depending on the frequency, brain signals can be divided into different frequency bands, such as delta waves (0.5-4Hz), theta waves (4-8Hz), alpha waves (8-13Hz), beta waves (13-30Hz), and gamma waves (above 30Hz).

[0206] Brain signals can provide information about brain activity, such as sleep states, levels of consciousness, attention, cognitive processes, and emotional states. They have broad applications in clinical medicine, neuroscience research, and brain-computer interfaces. Analyzing brain signals can reveal brain functions and abnormalities, aiding in the diagnosis of certain diseases and monitoring brain health. Brain signals can also be used to study the fundamental mechanisms of learning, memory, consciousness, and other cognitive processes.

[0207] The division of brain regions is a key concept in neuroscience and neuroimaging, with different brain regions responsible for different functions. Common brain regions include the anterior frontal lobe, posterior frontal lobe, parietal lobe, occipital lobe, and / or temporal lobe. The anterior frontal lobe, located at the front of the brain, is primarily involved in decision-making, behavioral control, emotional regulation, and motor control. The posterior frontal lobe, located at the front of the top of the brain, is involved in spatial cognition, sensory information processing, attention, and spatial orientation. The parietal lobe, located at the back of the top of the brain, is primarily responsible for processing and interpreting visual information. The occipital lobe, located at the back of the brain, is involved in auditory processing, memory function, emotion recognition, and language comprehension. The temporal lobe, located at the side of the brain, is responsible for some visual information processing and face recognition.

[0208] First, the present application provides some embodiments of an electroencephalogram (EEG) measurement device (hereinafter referred to as an acquisition device). In some embodiments, the acquisition device includes at least two electrode assembly modules corresponding to different brain regions. Each electrode assembly module is a rigid semi-ring structure, and the electrode assembly modules are interconnected to form an integrated structure. At least one of the electrode assembly modules is a retractable structure, allowing the module to move toward or away from its own center to adjust its size.

[0209] The acquisition device in the embodiment of this application utilizes a retractable structure for at least one of the at least two electrode modules, allowing for adjustment of the electrode module's fit within the corresponding brain region to accommodate subjects with varying head circumferences. This approach also allows for adjustment of the contact pressure between the electrode and the skin. Appropriate contact pressure can improve contact quality between the electrode and skin, thereby reducing contact resistance.

[0210] Contact pressure refers to the amount of pressure the electrode applies to the skin. Too little contact pressure can cause a gap between the electrode and the skin, increasing contact resistance; too much contact pressure can damage the skin or cause discomfort.

[0211] Most of the common brain signal acquisition devices on the market currently use a soft hat structure. When worn, the electrodes are not easy to align and are easily pulled and damaged, or affect brain signal acquisition. The soft hat structure does present some challenges when worn. Due to differences in head shapes of different subjects, the wearer may need to adjust the position and tightness of the hat to ensure that the electrodes fit the scalp. This process is not completely precise and may result in inaccurate electrode alignment and different electrode contact pressures for different subjects, thus affecting the accuracy and quality of signal acquisition. In addition, pulling, friction, etc. may occur during wearing, which may destroy the contact between the electrode and the scalp, resulting in signal distortion or loss. In addition, wearing a soft hat for a long time may also cause discomfort and pressure, affecting the user's comfort.

[0212] Compared to the soft cap structure, the three modular components in the embodiment of the present application can all adopt a hard structure, that is, the brain signal acquisition device in the embodiment of the present application adopts an adjustable hard cap, which can better solve the problem of inaccurate electrode alignment. Since the adjustable hard cap can be adjusted in size according to the shape of the user's head, the accurate position and correspondence of the electrodes can be better guaranteed. This can improve the accuracy and precision of brain signal acquisition, thereby better reflecting the state of brain activity. The adjustable hard cap adopts a retractable adjustment structure, which enables the device to adapt to people with different head circumferences. Users can adjust it according to the size of their head circumference to obtain a more comfortable and suitable wearing experience.

[0213] Secondly, the adjustable hard cap offers improved stability and durability. It provides enhanced support and protection, better shielding the electrodes and sensors from external physical interference. It also prevents deformation or damage during wear, extending the lifespan and performance of the device. Furthermore, the hard shell structure provides enhanced support and stability, making it easier to accurately position the electrodes on the head while wearing. This helps ensure good contact between the electrodes and the scalp, improving the precision and accuracy of signal acquisition.

[0214] Finally, a hard cap can improve wearer comfort. Because it can be customized or adjusted to the wearer's head shape, it can better fit the head shape, reducing pressure and discomfort. This improves the wearer's user experience and promotes their acceptance and use of brain signal acquisition devices, making them easier to promote. Furthermore, a hard shell structure is generally easier to carry and use than a soft cap structure. Users can carry the device in a bag or case, making it convenient for brain signal acquisition in different situations.

[0215] The brain signal acquisition device in the embodiment of the present application adopts an adjustable hard cap structure, which has better electrode alignment accuracy, stability, durability and comfort, and can be used to improve the performance and user experience of the brain signal acquisition device.

[0216] In some embodiments, each electrode group module may be provided with the same type of electrodes or different electrodes, and multiple electrodes within an electrode group may also be provided with the same type of electrodes or different electrodes. At least one electrode group module in each electrode group module is provided with multiple brain signal acquisition electrode groups of the same type; or at least one electrode group module in each electrode group module is provided with at least two different types of brain signal acquisition electrode groups.

[0217] It is understandable that the categories described here can be morphologies, such as electrode needles or electrode sheets, dry electrodes versus wet electrodes, or used to collect different types of brain signals. The device can be used for a variety of purposes and applications. For example, in some studies, in order to obtain a wider range of EEG activity information, multiple electrode groups of the same type may be used to increase the coverage of data collection. If an electrode group module is provided with at least two different categories of brain signal acquisition electrode groups, neural activity data at different levels and resolutions can be recorded simultaneously, which can provide a more comprehensive understanding and analysis of brain function and activity.

[0218] In some embodiments, the brain signal acquisition electrode group includes electroencephalogram (EEG) acquisition electrodes. EEG acquisition electrodes are used to record electrical activity in the cerebral cortex. These acquisition electrodes can be placed on the scalp to measure electrical signals from brain activity. These acquisition electrodes can capture the electrical activity of neurons in the brain and convert it into digital signals that can be analyzed and studied. By analyzing EEG signals, it is possible to understand brain activity patterns in different states, such as sleep, attention, and cognitive tasks.

[0219] In the above embodiments, in addition to electroencephalogram (EEG) acquisition electrodes, other types of electrodes can also be used for brain signal acquisition, such as electrocorticogram (ECoG) acquisition electrodes, computed tomography (CT) electrodes, and deep brain stimulation (DBS) electrodes. CoG electrodes are electrodes that are directly implanted on the surface of the brain or placed under the dura mater. Compared with EEG, ECoG can provide higher spatial resolution and signal quality, and can record more detailed neural activity. CT electrodes are electrodes used for positioning and navigation inside brain tissue, and are commonly used in neurosurgery. They can be accurately positioned using computed tomography technology to collect brain signals in specific areas. DBS electrodes are electrodes implanted in deep brain structures and are used to treat neurological diseases such as Parkinson's disease and depression. In addition to the stimulation function, they can also be used to record brain signals to monitor the effectiveness of treatment.

[0220] In some embodiments, the EEG acquisition electrode comprises an EEG dry electrode; the dry electrode comprises a base material and a coating, wherein the base material is made of copper and the coating is made of silver. Dry electrodes using a copper base material and a silver coating can provide excellent electrical conductivity and signal quality. The copper base material has excellent mechanical strength and electrical conductivity, enabling stable attachment to the scalp. The silver coating material has lower electrical resistance and better electrical conductivity, reducing signal loss and improving signal quality.

[0221] In some embodiments, the brain signal acquisition electrode group includes: a functional near-infrared spectroscopy (FNIRS) light source, an emitter, and a detector. Functional Near-Infrared Spectroscopy (FNIRS) is a non-invasive neuroimaging technology used to measure changes in cerebral blood oxygen levels. The functional near-infrared spectroscopy (FNIRS) light source uses a near-infrared light source to emit invisible light into the scalp tissue. The light source can use infrared light or near-infrared light (650-1000 nanometer wavelength range), which can penetrate the skull and most soft tissues. The emitter is a component that guides the light from the light source to the measured area. It can include one or more optical fiber bundles that direct the light emitted by the light source to a specific brain area. The detector is used to measure the light reflected or transmitted back from the measured area, and can be composed of a photosensitive detector (such as a photodiode) to measure the intensity of the reflected or transmitted light.

[0222] In some embodiments, the brain signal acquisition electrode group includes: a transcranial direct current stimulation (TDCS) anode electrode and a cathode electrode. Transcranial Direct Current Stimulation (TDCS) is a technology that regulates brain activity by placing an anode and a cathode on the scalp to deliver a weak direct current. In TDCS, the anode and cathode electrodes can be placed on the scalp to apply current to specific brain areas. The anode electrode is usually the positive electrode, and the brain area under it will be enhanced by the current, thereby promoting the excitation of neurons. The cathode electrode is usually the negative electrode, and it will inhibit the brain area under it by the current, resulting in neuronal inhibition.

[0223] In some embodiments, each electrode group module includes at least two of the following: a first electrode group module corresponding to the frontal lobe brain region and / or the posterior frontal lobe brain region, a second electrode group module corresponding to the occipital lobe brain region, and a third electrode group module corresponding to the parietal lobe brain region and / or the temporal lobe brain region. The frontal lobe brain region, the posterior frontal lobe brain region, the occipital lobe brain region, the parietal lobe brain region, and the temporal lobe brain region are common target brain regions, and different combinations of electrode groups can be used to collect signals from the target brain regions. The choice of electrode combination and the specific placement position vary according to the research or treatment purpose. For example, to explore the impact of the frontal lobe brain region on cognitive function, the first electrode group module placed in the frontal lobe brain region and / or the posterior frontal lobe brain region can be used; and to explore the impact of the parietal lobe brain region on motor function, the third electrode group module placed in the top and center area can be used. The specific electrode combination and placement position need to be determined according to the specific experimental design, research hypothesis and treatment needs.

[0224] The brain signal acquisition device in the embodiment of the present application can adopt a combination of any two electrode group modules, or a combination of three electrode group modules. Taking the three-electrode group module as an example, its specific structure is explained in detail.

[0225] In some embodiments, as shown in Figures 29 and 30, the EEG measurement device includes: a first electrode group module 1c, a second electrode group module 2c, and a third electrode group module 3c. The overall structure of these three modules is significantly different from the cap body in the prior art. The cap body of the EEG device in the prior art is mostly composed of a mesh-like flexible material, while the shells of the first electrode group module 1c, the second electrode group module 2c, and the third electrode group module 3c in the present application are all made of a rigid material, making the wearing process simple and convenient, and the time required is greatly reduced.

[0226] Furthermore, the first electrode group module 1c, the second electrode group module 2c, and the third electrode group module 3c are all rigid semi-ring structures, and the three modules are interconnected to form an integrated structure. The first electrode group module 1c and the second electrode group module 2c form a closed ring, and the third electrode group module 3c is arranged to intersect with the first electrode group module 1c or the second electrode group module 2c. Optionally, the closed ring formed by the first electrode group module 1c and the second electrode group module 2c is located in the same plane, making the front and back symmetrical, the appearance more beautiful, and the arrangement of the electrodes more convenient, but not limited to this. The first electrode group module 1c and the second electrode group module 2c can also have a slight angle to suit different application scenarios.

[0227] Furthermore, at least one of the first electrode group module 1c, the second electrode group module 2c and the third electrode group module 3c is a retractable structure, so that the module can move in a direction close to or away from its own center to adjust its size.

[0228] In some embodiments, as shown in Figures 32-34, the connection parts of the first electrode group module 1c and the second electrode group module 2c are formed with a first plug-in structure, wherein at least one end of one module is formed with a protruding first plug-in block 11c, and the corresponding end of the other module is formed with a recessed first plug-in slot 21c, and the first plug-in block 11c can move in the first plug-in slot 21c to achieve telescoping.

[0229] The design of the first plug-in blocks 11c at both ends of the "first electrode group module 1c" is taken as an example to further illustrate. The end of the first electrode group module 1c forms a protruding plug-in block, while the corresponding end of the second electrode group module 2c forms a recessed plug-in slot. The purpose of this design is to achieve the telescopic function between modules. When the plug-in block is inserted into the plug-in slot, it can move within the plug-in slot so that the entire connection part can be telescoped. This telescopic design can adjust the distance or angle between the two modules as needed to adapt to different usage requirements or head sizes. Such a structural design can provide better adaptability and comfort, allowing the EEG measurement device to better fit the shape of the head and provide more reliable signal contact. At the same time, during use, the user can freely adjust the length or angle of the connecting part as needed to obtain a better user experience and signal quality.

[0230] In some embodiments, the first plug-in structure further includes a first locking structure for locking the first plug-in block 11c in the first plug-in slot 21c, and the first locking structure includes: a plurality of first limiting grooves 111c arranged along the first direction formed on the first plug-in block 11c, each first limiting groove 111c extending along the second direction, the first direction intersecting with the second direction, the first direction being the extension and contraction direction of the first electrode group module 1c or the second electrode group module 2c; a first locking tongue member 211c formed on one side of the first plug-in slot 21c and fixedly arranged, the body of the first locking tongue member 211c is elastic, and the first locking tongue member 211c has a first protruding end 2111c, and when the first protruding end 2111c is clamped in one of the first limiting grooves 111c, the first electrode group module 1c and the second electrode group module 2c are clamped to each other.

[0231] The first limiting groove 111c extends along the second direction, and the first direction intersects with the extension and contraction direction of the first electrode group module 1c or the second electrode group module 2c. The function of these limiting grooves is to provide position restrictions to ensure the range of movement of the plug-in block in the plug-in slot. The body of the first locking tongue member 211c is elastic. The first locking tongue member 211c has a first protruding end 2111c, which, when clamped in a first limiting groove 111c, realizes the mutual clamping of the first electrode group module 1c and the second electrode group module 2c. In other words, the first protruding end 2111c can be embedded in a limiting groove and locked with it, thereby ensuring a stable connection. Through the above design, the first plug-in block 11c can be extended and contracted in the first plug-in slot 21c and locked to a specific plug-in slot position by the first locking structure. This locking mechanism can maintain the stability of the plug-in block and prevent it from loosening or falling off during use.

[0232] In some embodiments, a second plug-in structure is formed at the connection portion between the third electrode group module 3c and the first electrode group module 1c or the second electrode group module 2c, wherein a protruding second plug-in block 31c is formed at at least one end of one module, and a recessed second plug-in slot 22c is formed at the corresponding end of the other module, and the second plug-in block 31c can move within the second plug-in slot 22c to achieve telescoping.

[0233] Taking the third electrode group module 3c provided with the second plug-in block 31c as an example, it is further described in detail. The two ends of the third electrode group module 3c are formed with a protruding second plug-in block 31c, and the corresponding end of the second electrode group module 2c is formed with a recessed second plug-in slot 22c. Through this design, the second plug-in block 31c can be moved in the second plug-in slot 22c, thereby realizing the expansion and contraction between modules. The second plug-in block 31c has a protruding shape and can be inserted and pulled out of the second plug-in slot 22c. The recessed second plug-in slot 22c can accommodate the second plug-in block 31c and provide the functions of fixing and positioning. By adjusting the position of the second plug-in block 31c in the second plug-in slot 22c, the expansion and contraction between modules can be realized to adapt to different usage requirements.

[0234] In some embodiments, as shown in Figures 33 to 29, the second plug-in structure further includes a second locking structure for locking the second plug-in block 31c in the second plug-in slot 22c, and the second locking structure includes: a plurality of second limiting grooves 221c arranged along a third direction formed on the second plug-in slot 22c, each second limiting groove 221c extending along a first direction, the third direction intersecting with the first direction, and the third direction being the extension and contraction direction of the third electrode group module 3c; a second locking tongue member 311c formed on one side of the second plug-in block 31c and fixedly arranged, the body of the second locking tongue member 311c is elastic, and the second locking tongue member 311c has a second protruding end 3111c, and when the second protruding end 3111c is clamped in one of the second limiting grooves 221c, the third electrode group module 3c is clamped with the first electrode group module 1c or the second electrode group module 2c.

[0235] The second insertion slot 22c includes several second limiting slots 221c arranged along a third direction. Each second limiting slot 221c extends along the first direction, which intersects the direction of extension and retraction of the third electrode assembly module 3c. These second limiting slots 221c function to provide positional constraints, ensuring the range of movement of the second insertion block 31c within the second insertion slot 22c. The body of the second locking tongue 311c is elastic. The second locking tongue 311c has a second protruding end 3111c, which, when engaged with a second limiting slot 221c, secures the third electrode assembly module 3c to the first electrode assembly module 1c or the second electrode assembly module 2c. In other words, the second protruding end 3111c can be inserted into and locked with a limiting slot, thereby ensuring a secure connection. Through this design, the second insertion block 31c can extend and retract within the second insertion slot 22c and be locked into place at a specific insertion slot position by the second locking structure. This locking mechanism maintains the stability of the plug-in block and prevents it from loosening or falling off during use.

[0236] In some embodiments, as shown in Figure 32, the end of the first plug-in block 11c extends forward to form a guide structure. A co-directing guide post 32c is provided near the second plug-in block 31c at one end of the third electrode assembly module 3c. These structural designs can ensure a smoother extension and retraction process. Furthermore, limit mechanisms can be provided at both ends of the travel between the first plug-in block 11c and the first insertion slot 21c, and between the second plug-in block 31c and the second insertion slot 22c to prevent the components from falling off or being damaged.

[0237] In some embodiments, the first electrode group module 1c, the second electrode group module 2c, and the third electrode group module 3c are each provided with a plurality of dry electrodes. Currently, the more common EEG acquisition methods on the market are divided into three types: gel electrodes, water electrodes, and dry electrodes. Gel electrodes and water electrodes both require scalp pretreatment before collecting brain signals. Dry electrodes can avoid the inconvenience of scalp pretreatment and can be applied more quickly and flexibly in various natural scenarios.

[0238] As an implementation method, the second electrode assembly module 2c is equipped with a three-way connector 25c at the intersection of the three modules. This allows for docking not only with the first electrode assembly module 1c but also with the third electrode assembly module 3c, thus fulfilling the functions of both the first and third electrode assembly modules 1c and 3c. Furthermore, the three-way connector 25c may also be equipped with a function board 61c and a second power board 62c. The function board 61c is responsible for collecting, processing, and analyzing brain signals, while the second power board 62c provides power supply and corresponding power management functions. The synergistic effect of these two components enables the EEG measurement device to operate effectively and provide accurate and reliable EEG data.

[0239] In some embodiments, each module includes a second curved outer shell 51c, a second curved outer shell 51c, and a second intermediate layer 53c. The second curved outer shell 51c has a second electrode hole 521c for fixing an electrode. The second intermediate layer 53c is disposed between the second curved outer shell 51c and the second curved outer shell 51c, and the second curved outer shell 51c is located within the inner layer of the second curved outer shell 51c. The second intermediate layer 53c is elastic or used to mount wires for electrically connecting the electrodes. Each electrode is mounted within the second electrode hole 521c of the second curved outer shell 51c via an elastic member. The first electrode group module 1c, the second electrode group module 2c, or the third electrode group module 3c is provided with a GND electrode. The elastic member can be a spring or an elastic pad.

[0240] The EEG measurement device of the embodiment of the present application can be provided with four sheet-shaped active electrodes and one sheet-shaped GND electrode in the first electrode group module 1c, four needle-shaped active electrodes in the second electrode group module 2c, and four needle-shaped active electrodes in the third electrode group module 3c, for a total of 12 data channels. The number of electrodes in the EEG measurement device of the embodiment of the present application can be adjusted arbitrarily, and its data derivatives can also be set to various derivatives, such as 16 channels, 32 channels, etc.

[0241] The GND electrode is an electrode connected to the ground, acting as a ground in a circuit. It is typically used to establish a reference potential or provide a reference point for a loop to ensure normal circuit operation and stable signal transmission. Components and wires connected to the GND electrode will have the same potential, ensuring sharing and balance between various parts of the circuit. The GND electrode can provide a reference potential for the circuit, allowing signals to be transmitted reliably and consistently; it can safely release static electricity or electromagnetic interference in the circuit; it can protect human safety by connecting the metal casing or contact parts of the circuit to the ground to avoid the risk of electric shock; it can provide protection against circuit noise and interference, directing them to the ground without interfering with other parts; and it can serve as a loop path for the circuit, ensuring the normal flow of current in the circuit.

[0242] As shown in Figure 29, the EEG measuring device also includes a second ear clip 7c used as a reference electrode, and the second ear clip 7c is connected to the main body of the EEG measuring device via an ear clip wire. The ear clip of the EEG measuring device is used as a reference electrode to provide a reference point for correcting the measurement of brain signals. Brain signals are measured using electrodes on the scalp, which are usually distributed in different positions on the head. In electroencephalogram (EEG) measurements, the reference electrode is a technology used to eliminate the interference of environmental and physiological noise on brain signals. It is done by placing an electrode at a position unrelated to the brain signal and using it as a reference point for correction. By placing the ear clip electrode on or behind the ear, it can provide a stable reference potential that is not easily interfered with by external noise. This can reduce the common noise in brain signals and improve the accuracy and reliability of the measurement.

[0243] It can be understood that the EEG measurement device in the embodiment of the present application only illustrates the second ear clip 7c in Figure 29, and the ear clip is omitted in other figures or the reference electrode is set in other ways, such as a rubber disc electrode or an elastic band electrode.

[0244] In some embodiments, the first electrode group module 1c includes several electrodes in the form of second electrode sheets 41c. There is a certain relationship between electrode size and contact resistance. Generally speaking, when the electrode size is larger, the contact resistance is relatively small; and when the electrode size is smaller, the contact resistance is relatively large. This is because an increase in electrode size can increase the area of ​​contact between the electrode and the skin, thereby reducing the length of the path through which the current passes and reducing the resistance encountered by the current at the contact interface. Conversely, a decrease in electrode size will lead to a decrease in contact area, an increase in the length of the path through which the current passes, and an increase in the resistance of the current at the contact interface.

[0245] In some embodiments, the plurality of electrodes included in the second electrode group module 2c and the third electrode group module 3c are in the form of second electrode needles 43c.

[0246] This EEG measurement device uses portable dry electrodes in two configurations: a second electrode sheet 41c and a second electrode needle 43c. The second electrode needle 43c can be spring-loaded to provide consistent, comfortable pressure, enhancing electrode-skin contact while reducing motion artifacts. The signal quality is comparable to that of wet-electrode EEG systems and is currently primarily used in neurofeedback, brain-computer interfaces, and psychology research. The electrodes utilize active / passive shielding to prevent electromagnetic interference.

[0247] Combined with the calculation formula of contact resistance in the existing technology:

[0248] Where Rj is the contact resistance;

[0249] K is a material-related coefficient, such as copper-tin plating, copper-silver plating, etc.

[0250] F is the contact pressure in Newtons;

[0251] m is the contact form, m = 0.5 for point contact, m = 0.5~0.7 for line contact, and m = 1 for surface contact.

[0252] Typically, metal electrodes (such as silver / silver chloride electrodes) have low contact resistance, providing good signal quality and minimal electrode noise. Other materials, such as stainless steel and carbon nanotubes, can also be used for electrode fabrication, but their contact resistance may be higher than that of metal electrodes.

[0253] In the embodiments of the present application, the dry electrode comprises a base material and a coating, wherein the base material is made of copper and the coating is made of silver. The choice of contact electrode material has a significant impact on contact resistance. The dry electrode in this application uses copper-silver-plated material, which offers advantages in terms of cost, electrical conductivity, conductive stability, oxidation resistance, and biocompatibility. Copper, as a base material, has excellent electrical conductivity and can effectively transmit brain signals. Silver's high electrical conductivity makes it an excellent coating material, further improving the electrode's electrical conductivity. This reduces resistance and better captures weak brain signals. Copper-silver-plated electrodes have good conductive stability and can maintain a certain level of conductivity stably for a long time. This is very important for long-term EEG monitoring and experimental research, ensuring signal stability and reliability. The silver coating can provide a certain antioxidant effect, reducing the effects of oxidation on the electrode material. Oxidation may cause corrosion on the electrode surface or form an insulating layer, thereby affecting signal transmission and quality. The silver coating protects the copper electrode from damage due to oxidation, extending the electrode's service life. Silver-plated copper electrodes have good biocompatibility with the skin and scalp and do not cause severe allergic or irritating reactions. This is very important for long-term electrode wear, as well as for human experiments and clinical applications.

[0254] It should be noted that although copper-silver-coated electrodes have these advantages, correct electrode placement, stable contact, and complete and detailed data processing and analysis are also key factors in ensuring the quality of brain signals.

[0255] In order to solve or alleviate the problems of electrode cable assembly in soft cap-type EEG devices in the prior art, the present application also provides some embodiments of EEG measurement devices. The acquisition device integrates the electrode cables into a hard body, and there is no need to assemble or disassemble the electrode cables before and after use. This greatly facilitates the use of the EEG device, improves user acceptance, and provides convenience for the large-scale promotion of EEG devices.

[0256] The embodiments of the present application also provide some embodiments of EEG measurement devices, as shown in Figures 36 to 40, where the acquisition device includes a main body and a brain signal host board 61d integrated on the main body, a number of electrodes and signal transmission lines, etc.

[0257] Existing EEG devices in the form of soft caps need to be able to fit the scalp stably and maintain good contact quality to ensure accurate and stable signal acquisition. However, due to differences in head shape and size, the fit and stability of the soft cap can be challenging. The soft cap needs to remain comfortable when worn for extended periods of time to accommodate the needs of long-term brain signal acquisition. However, some soft cap-style EEG devices may cause discomfort to the wearer due to improper material selection or design.

[0258] Compared to the soft cap structure, the main body in the embodiment of the present application is an integrated hard structure with wiring channels formed inside or on the surface of the structure. The hard body can provide better support and protection, and can better protect the electrodes and sensors from external physical interference. At the same time, the hard body can prevent deformation or damage during wearing, thereby extending the service life and performance of the device. The hard body can improve the comfort of the wearer. Since the hard body can be customized or adjusted according to the wearer's head shape, it can better fit the shape of the head and reduce the feeling of oppression and discomfort. This can improve the wearer's user experience and promote their acceptance and use of brain signal acquisition devices, making it easy to promote.

[0259] In the embodiment of the present application, several electrode groups are arranged in at least one brain signal acquisition area of ​​the main body; the wiring channel of the main body extends from the brain signal acquisition area to the area of ​​the main body for installing the brain signal host board 61d, for embedding the signal transmission line; the signal transmission line is used to connect the electrodes and the brain signal host board 61d to transmit the brain signals collected by the electrodes.

[0260] In the above embodiment, the EEG measurement device integrates the EEG signal host board 61d, electrodes, and signal transmission lines into a single, rigid structure, providing a more convenient user experience. The provision of wiring channels allows the signal transmission lines to form channels within or on the surface of the device, making it neater and easier to manage.

[0261] Furthermore, the electrodes are grouped in the brain signal acquisition area, effectively capturing brain signals from each region. Furthermore, the extended wiring channels allow signal transmission lines to connect the electrodes to the brain signal host board 61d, thereby transmitting the collected brain signals. This design tightly integrates the various components of the brain signal acquisition device, providing a more efficient and convenient solution for brain signal acquisition.

[0262] The EEG measurement device in the embodiments of the present application can shorten experimental preparation time. All transmission lines are placed inside the device, shielding electromagnetic crosstalk in some environments. The integrated design eliminates the need for cables and a cap assembly, unlike previous EEG measurement systems, which required the assembly of cables and a cap before each test. This significantly shortens experimental preparation time and eliminates the need for post-experimental equipment maintenance.

[0263] The main body in the embodiment of the present application is an integrated hard structure. The hard structure can effectively protect the internal electronic components, while also maintaining the overall shape and stability of the main body, making the entire device easier to carry and use. The integrated structure avoids the risk of cable disconnection caused by the transmission line being exposed to the outside. Due to the integrated design, the main body itself is a complete device, which is convenient for users to carry. Users can put it in a special bag or box for easy portability without worrying about the loss or damage of parts. Due to the stability of the hard structure, users can quickly put on and start the cap-type brain signal acquisition device when they need to use it. There is no need for a complicated assembly process, which improves the convenience and efficiency of use.

[0264] In addition, the main body has a certain weight and pressure, which can make the electrodes fit more closely to the area to be tested in the brain.

[0265] The design concept of the EEG measurement device in the embodiment of the present application meets user needs and brings better user experience and functionality.

[0266] In some embodiments, the brain signal acquisition area of ​​the body includes one or more of the following: a frontal lobe brain signal acquisition area, a posterior frontal lobe brain signal acquisition area, a parietal lobe brain signal acquisition area, an occipital lobe brain signal acquisition area, and a temporal lobe brain signal acquisition area.

[0267] Based on the anatomical structure and functional divisions of the human brain, the prefrontal lobe is located in the front of the forebrain and is associated with functions such as cognitive control, decision-making, and emotional regulation. The posterior frontal lobe is located in the back of the forebrain and is associated with functions such as motor control and sensory information processing. The parietal lobe is located in the upper part of the brain and is associated with functions such as vision and spatial cognition. The occipital lobe is located in the back of the brain and is associated with functions such as visual information processing. The temporal lobe is located on the side of the brain and is associated with functions such as hearing, memory, and language.

[0268] The main body of the acquisition device in the embodiments of this application includes at least one signal acquisition area for the aforementioned brain regions. By placing corresponding electrodes in these brain signal acquisition areas, signals such as electrical activity, blood oxygenation levels, or magnetic fields from different brain regions can be acquired, thereby studying brain function and cognitive processes. This is of great significance for understanding the working principles of the brain and developing applications such as brain-computer interfaces.

[0269] In some embodiments, multiple brain signal acquisition electrodes of the same type are provided in at least one of the brain signal acquisition areas; alternatively, at least two different types of brain signal acquisition electrodes are provided in at least one of the brain signal acquisition areas. In this embodiment, multiple brain signal acquisition electrodes of the same type can be provided in the same brain signal acquisition area, or multiple different types of brain signal acquisition electrodes can be provided in the same brain signal acquisition area. The types described here can include electrodes of different shapes, different principles, and dry or wet electrodes.

[0270] In some embodiments, at least one of the electrodes provided in the brain signal acquisition area includes an electroencephalogram (EEG) acquisition electrode. Electroencephalogram (EEG) acquisition electrodes are used to record changes in electrical potential resulting from the electrical activity of neurons in the cerebral cortex. EG electrodes are placed on the surface of the scalp to acquire signals from brain electrical activity. These electrodes are typically made of metal or conductive materials and contact the scalp by means of pasting or clamping to record changes in brain potential. Different numbers and layouts of EEG electrodes can be selected based on the experimental design and research requirements.

[0271] In other embodiments, in addition to electroencephalogram (EEG) acquisition electrodes, other types of electrodes can also be used for brain signal acquisition. For example, electrocorticogram (ECoG) acquisition electrodes, computed tomography (CT) electrodes, deep brain stimulation (DBS) electrodes, etc. ECoG electrodes are electrodes directly implanted on the surface of the brain or placed under the dura mater. ECoG can provide higher spatial resolution and signal quality, and can record more detailed neural activity. CT electrodes are electrodes used for positioning and navigation inside brain tissue, commonly used in neurosurgery, and can be accurately positioned by computed tomography technology to collect brain signals in specific areas. DBS electrodes are electrodes implanted in deep brain structures and are used to treat neurological diseases such as Parkinson's disease and depression. In addition to the stimulation function, they can also be used to record brain signals to monitor the effectiveness of treatment.

[0272] In some embodiments, the EEG acquisition electrodes include dry electrodes, which include electrode sheets and / or electrode needles. An electrode sheet is a flat metal sheet, typically made of a conductive material (such as silver / silver chloride). These electrode sheets can be placed on the surface of the scalp and in contact with the scalp to record brain electrical activity. The electrode sheets can be adhered to the scalp and fixed using conductive glue or electrode caps to ensure good contact. Electrode needles are slender conductive needles, typically made of stainless steel or other conductive materials. The electrode needles can be inserted directly into the scalp to acquire EEG signals. When using electrode needles, it is necessary to carefully follow hygiene and safety regulations and ensure that the electrodes are placed and fixed correctly. Dry electrodes have some advantages over other types of electrodes (such as wet electrodes), such as being easier to use, more comfortable, and not requiring additional conductive media (such as electrolytic gel).

[0273] In some embodiments, the electrodes provided in at least one of the brain signal acquisition areas include: a functional near-infrared spectroscopy (FNIRS) light source, an emitter, and a detector. Functional Near-Infrared Spectroscopy (FNIRS) is a non-invasive neuroimaging technique used to measure changes in cerebral blood oxygen levels. The functional near-infrared spectroscopy (FNIRS) light source uses a near-infrared light source to emit invisible light into the scalp tissue. The light source can use infrared light or near-infrared light (650-1000 nanometer wavelength range), which can penetrate the skull and most soft tissues. The emitter is a component that directs the light from the light source to the measured area. It can include one or more optical fiber bundles that direct the light emitted by the light source to a specific brain area. The detector is used to measure the light reflected or transmitted back from the measured area and can be composed of a photosensitive detector (such as a photodiode) to measure the intensity of the reflected or transmitted light.

[0274] In some embodiments, the electrodes provided in at least one of the brain signal acquisition areas include: a transcranial direct current stimulation (TDCS) anode electrode and a cathode electrode. Transcranial Direct Current Stimulation (TDCS) is a technology that regulates brain activity by placing an anode and a cathode on the scalp to deliver a weak direct current. In TDCS, anode and cathode electrodes can be placed on the scalp to apply current to specific brain areas. The anode electrode is usually the positive electrode, and the area of ​​the brain beneath it will be enhanced by the current, thereby promoting the excitation of neurons. The cathode electrode is usually the negative electrode, and it will inhibit the area of ​​the brain beneath it by the current, resulting in neuronal inhibition.

[0275] In some embodiments, as shown in FIG36 , the wiring channels include a transverse wiring channel 81d and a longitudinal wiring channel 82d, which are used to guide the signal transmission lines connected to the brain signal host board 61d to the electrodes provided in each brain signal acquisition area. This design allows the acquisition device to comprehensively capture brain signals from different brain regions, providing more comprehensive and accurate brain signal input for subsequent data analysis and processing. Furthermore, the provision of wiring channels also helps manage and protect the signal transmission lines, making the entire device more stable and reliable.

[0276] In some embodiments, the body of the acquisition device is configured as a retractable structure or a size-adjustable structure to accommodate different head circumferences of subjects. The wiring channel may be embedded in the body.

[0277] Specifically, the body includes a second body 2d, a first body 1d, and a third body 3d; the occipital lobe brain region acquisition area is located on the inner side of the second body 2d, the prefrontal lobe brain region acquisition area and / or the posterior frontal lobe brain region acquisition area are located on the inner side of the first body 1d, and the parietal lobe brain region acquisition area and / or the temporal lobe brain region acquisition area are located on the inner side of the third body 3d. In other embodiments, the temporal lobe brain region acquisition area may be located at either end of the second body 2d, the first body 1d, and the third body 3d, corresponding to the two sides of the human brain.

[0278] In some embodiments, as shown in FIG40 , each body includes a third curved outer shell 51d, a third electrode group support 52d, and a third intermediate layer 53d. The third electrode group support 52d has a third electrode hole 521d for fixing the electrode. The third intermediate layer 53d is disposed between the third curved outer shell 51d and the third electrode group support 52d. The third electrode group support 52d is located on the inner layer of the third curved outer shell 51d. The third intermediate layer 53d (or a PCB) is elastic or used to mount wires for electrically connecting the electrodes. Each electrode can be mounted in the third electrode hole 521d of the third electrode group support 52d via an elastic member.

[0279] As shown in Figures 36-40, the brain signal host board 61d is located within the second body 2d. Specifically, it can be located at the intersection of the second body 2d, the first body 1d, and the third body 3d. The brain signal host board 61d and the occipital lobe brain signal acquisition area are located within the same second body 2d. The transverse wiring channel 81d is relatively simple to set up and can be used to facilitate the cavity within the shell. The connection between the brain signal host board 61d and the frontal lobe brain signal acquisition area and the posterior frontal lobe brain signal acquisition area requires the use of the transverse wiring channel 81d provided through the connecting structure of the second body 2d and the first body 1d. The connection between the brain signal host board 61d and the parietal lobe brain signal acquisition area requires the use of the longitudinal wiring channel 82d provided through the connecting structure of the second body 2d and the third body 3d. The transverse and longitudinal directions mentioned here primarily refer to being generally located on the same horizontal or vertical plane.

[0280] In the above embodiment, the second body 2d is fixed. As shown in Figure 38 , the first body 1d is telescopically inserted horizontally in front of the second body 2d. As shown in Figure 39 , the third body 3d is telescopically inserted vertically above the second body. The first body 1d's insertion structure partially forms the transverse wiring channel 81d, while the third body 3d's insertion structure partially forms the longitudinal wiring channel 82d.

[0281] This design allows the data acquisition device to be adjusted to the subject's head circumference, improving comfort and adaptability. Furthermore, the internal routing of the wiring channels helps reduce external wiring clutter, protects wiring from damage, and enhances overall aesthetics. This design provides greater flexibility and adaptability for the data acquisition device, while also improving user comfort and practicality.

[0282] In some embodiments, as shown in Figures 36, 39 and 40, the plug-in structure between the transverse wiring channel 81d and the first body 1d includes a first locking structure 11d, and the first locking structure 11d is provided with a through card slot 111d, forming part of the transverse wiring channel 81d. The first locking structure 11d can use an elastic locking tongue, which will not be described here. This design provides a mechanism for the realization of the transverse wiring channel 81d through the first locking structure 11d and the through card slot 111d. The provision of the card slot 111d allows the wiring to pass through and be connected to the corresponding area smoothly. At the same time, the first locking structure 11d can effectively fix the first body 1d and the wiring channel to ensure that the head circumference is adjustable.

[0283] In some embodiments, as shown in Figures 36 and 40, the plug-in structure of the third body 3d includes a second locking structure 31d and a wire tube 32d that are separately arranged. The wire tube 32d is located on one side of the second locking structure 31d. The wire tube 32d is a hollow structure, forming part of the longitudinal wiring channel 82d. The second locking structure 31d can use an elastic locking tongue, which will not be described here. Such a design realizes the setting of the longitudinal wiring channel 82d through the second locking structure 31d and the wire tube 32d. As a hollow structure, the wire tube 32d provides a channel to accommodate and guide the transmission of the line, while the second locking structure 31d can fix and adjust the third body 3d to ensure that the head circumference is adjustable.

[0284] In some embodiments, when using dry electrodes of the same shape, each electrode in the prefrontal lobe brain signal acquisition area, the posterior frontal lobe brain signal acquisition area, the parietal lobe brain signal acquisition area, the occipital lobe brain signal acquisition area, and the temporal lobe brain signal acquisition area all uses a third electrode sheet 41d or a third electrode needle 43d; this means that no matter which brain signal acquisition area the electrode group is in, the electrode shape they use is the same, which has advantages in terms of unified specifications or production convenience, control consistency, etc.

[0285] In the case of using dry electrodes of different shapes, at least some of the dry electrodes in the frontal lobe brain signal acquisition area use a third electrode sheet 41d, the shape of which is shown in FIG41; and the dry electrodes in at least one of the posterior frontal lobe brain signal acquisition area, the parietal lobe brain signal acquisition area, the occipital lobe brain signal acquisition area, and the temporal lobe brain signal acquisition area use a third electrode needle 43d, the shape of which is shown in FIG42. For example, the third electrode sheet 41d is used in hairless or sparsely haired areas such as the frontal lobe brain area (or including the posterior frontal lobe brain area), while the third electrode needle 43d is used in hairy areas such as the parietal lobe brain area, the occipital lobe brain area, and the temporal lobe brain area. In electrode groups at different locations, there may be differences in the specific selection of electrode shapes, which may be due to different functional requirements or application scenarios.

[0286] The acquisition device in the embodiment of the present application provides flexibility in the selection of dry electrode morphology to meet the changing requirements for electrode morphology in different usage scenarios or needs, thereby better serving the performance and applicability of the brain signal acquisition device.

[0287] Alternatively, the third electrode needle 43d may be a third electrode needle 43d without an elastic structure. Alternatively, the third electrode needle 43d may be mounted in the brain signal acquisition area of ​​the body via an elastic member. Alternatively, the third electrode needle 43d may have an elastic structure, comprising a needle tube, a needle with a rebound range, and an elastic member disposed within the needle tube for rebounding the needle.

[0288] In some embodiments, the dry electrode is set in an integrated structure within the housing of the brain signal acquisition device, and the dry electrode needs to be fixed. Regarding the method of fixing the dry electrode, a variety of different fixing methods are determined mainly based on different electrode shapes.

[0289] Active and passive electrodes are two common types of electrodes used in biosignal acquisition. The main difference between them lies in whether they have an amplifier or gain device. Active electrodes contain built-in amplifiers or gain devices, which amplify the biosignal upon contact. These electrodes are often used to amplify and acquire weak biosignals, such as electroencephalograms (EEGs) or electromyograms (EMGs). Active electrodes can effectively reduce interference from cables or transmission media and provide a higher signal-to-noise ratio. Passive electrodes lack built-in amplifiers or gain devices and serve only as a carrier for transmitting biosignals. Therefore, the signals collected by passive electrodes are relatively small and require amplification during subsequent signal processing. These electrodes are often used for general biosignal acquisition, such as electrocardiograms (ECGs) or biopotential measurements. Passive electrodes are generally simpler, less expensive, and easier to maintain and manage.

[0290] For example, when the dry electrode is fixed to the brain signal acquisition area of ​​the body:

[0291] If the dry electrode includes a third electrode sheet 41d of a passive electrode, the third electrode sheet 41d is fixedly welded on a PCB board, and the PCB board is then fixed in the body through a connector;

[0292] If the dry electrode includes a third electrode needle 43d of a passive electrode, the third electrode needle 43d of the passive electrode is fixedly welded on a PCB board, and then the PCB board is fixed in the body through a connector; or, as shown in FIG43 , a threaded column 432 is provided at the tail end of the electrode needle of the passive electrode, which is inserted into the third electrode hole 521d of the third electrode group bracket 52d in the brain signal acquisition area through the threaded column 432, and a nut 433 is used in the body to fix the gasket 433 with the signal transmission line 434 on the threaded column 432.

[0293] If the dry electrode includes a third electrode sheet 41d of an active electrode or a third electrode needle 43d of an active electrode, the third electrode sheet 41d of the active electrode or the third electrode needle 43d of the active electrode is fixedly welded on one side of the PCB board, a processing circuit is placed on the other side of the PCB board, and the PCB board is fixed in the body through a connector.

Claims

1. An electroencephalogram (EEG) dry electrode, wherein: The EEG stem electrode includes a substrate and a coating, wherein the substrate includes a base and a plurality of columnar members, one end of each of the plurality of columnar members is fixed to the base, at least the surface of the columnar member is provided with the coating, and the coating on the surface of the columnar member is electrically connected to the base.

2. The EEG dry electrode according to claim 1, wherein: The column member includes a first member, a second member and a first elastic member, the first member is sleeved on the second member, the second member can move relative to the first member along the axial direction, the first elastic member is arranged in the first member, the two end portions of the first elastic member are respectively connected to the first member and the second member, and the first elastic member is used to apply a restoring force to the second member to move outward from the first member.

3. The EEG dry electrode according to claim 2, wherein: The column part comprises a copper part.

4. The EEG dry electrode according to claim 3, wherein: The second piece has a concave cavity having a first opening facing the first elastic piece. The first elastic piece is passed through the first opening and one end portion is located in the concave cavity. The second piece is a stamping and stretching formed piece.

5. The EEG dry electrode according to claim 4, wherein: A limiting portion is provided on the circumferential edge of the first opening, and the size of the limiting portion is larger than the outer diameter of the second piece in a direction perpendicular to the axis; the first piece includes a tube body, both ends of the tube body are open, the inner diameter of the edge of the tube body close to the opening of the second piece is smaller than the size of the limiting portion in a direction perpendicular to the axis, the limiting portion is provided in the tube body, and the tube body is integrally stamped, stretched and punched.

6. The EEG dry electrode according to any one of claims 1 to 5, wherein: The plating layer is provided on the surface of the base, the plating layer on the surface of the base is electrically connected to the plating layer on the surface of the column member, and the base and the plurality of column members are integrally injection-molded.

7. The EEG dry electrode according to claim 6, wherein: It also includes a conductive sheet. The base is provided with a connecting hole, which is used to connect with a connecting piece to fix the conductive sheet to the base. The conductive sheet is electrically connected to the plating layer on the surface of the base.

8. The EEG dry electrode according to claim 6 or 7, wherein: It also includes a second elastic member and a mounting member, wherein the second elastic member is connected to a side of the base away from the column member, the second elastic member can be extended and retracted along the axial direction of the column member, and the second elastic member is connected between the base and the mounting member.

9. The EEG dry electrode according to claim 8, wherein: It also includes a guide plate, which is arranged around the circumferential outer side of the second elastic member. At least one of the base and the mounting member is connected to the guide plate through a guide structure. The guide structure includes a guide groove and a guide portion. The guide portion is movably inserted into the guide groove along the axial direction of the column member.

10. An electroencephalogram measuring device, wherein: Comprising the EEG dry electrode according to any one of claims 1-9.

11. The electroencephalogram measuring device according to claim 10, wherein: The device comprises: a wearing component, a pushing component, and an EEG dry electrode; The wearing component is suitable for being worn on the user's head and has a mounting cavity, and the pushing component is located in the mounting cavity; The EEG dry electrode is movably connected to the wearable component; The pushing component is used to push the EEG dry electrode to move towards the head when the contact impedance between the EEG dry electrode and the head is greater than or equal to a first impedance threshold.

12. The electroencephalogram measuring device according to claim 11, wherein: The pushing component is used to push the EEG dry electrode to move towards the head according to a reference pushing intensity when the contact impedance between the EEG dry electrode and the head is greater than or equal to the first impedance threshold; The reference pushing strength is determined based on the contact impedance from a corresponding relationship between impedance and strength. A plurality of impedances are recorded in the corresponding relationship, and any two of the impedances are different.

13. The electroencephalogram measuring device according to claim 10, wherein: The electroencephalogram measuring device comprises a body and a frontal lobe electrode group and a non-frontal lobe electrode group arranged on the body; The frontal lobe electrode group includes a plurality of sheet-shaped dry electrodes, which are installed on the main body corresponding to the frontal lobe brain area of ​​the user, and the non-frontal lobe electrode group includes a plurality of needle-shaped dry electrodes, which are installed on the main body corresponding to the non-frontal lobe brain area of ​​the user; wherein, the frontal lobe brain area includes at least one of the following: the prefrontal lobe brain area, the posterior frontal lobe brain area, and the non-frontal lobe brain area includes at least one of the following: the parietal lobe brain area, the occipital lobe brain area, and the temporal lobe brain area.

14. The electroencephalogram measuring device according to claim 10, wherein: include: At least two electrode group modules corresponding to different brain regions, each electrode group module is a hard semi-ring structure, and each electrode group module is interconnected to form an integrated structure; At least one of the electrode group modules is a retractable structure, so that the module can move in a direction close to or away from its own center to adjust its size; The brain regions include: the frontal lobe region, the posterior frontal lobe region, the parietal lobe region, the occipital lobe region and / or the temporal lobe region.

15. The electroencephalogram measuring device according to claim 14, wherein: Each electrode group module includes at least two of the following: a first electrode group module corresponding to the prefrontal brain region and / or the posterior frontal brain region, a second electrode group module corresponding to the occipital brain region, and a third electrode group module corresponding to the parietal brain region and / or the temporal brain region.

16. The electroencephalogram measuring device according to claim 15, wherein: A first plug-in structure is formed at the connection portion between the first electrode group module and the second electrode group module, wherein a first protruding plug-in block is formed at at least one end of one module, and a first recessed plug-in slot is formed at the corresponding end of the other module, and the first plug-in block can move in the first plug-in slot to achieve telescoping.

17. The electroencephalogram measuring device according to claim 10, wherein: The electroencephalogram measuring device comprises a main body and a brain signal host board card integrated on the main body, a plurality of electrodes and a signal transmission line; Wherein, the body is an integrated hard structure, and a wiring channel is formed inside or on the surface of the structure; A plurality of electrodes are arranged in groups in at least one brain signal acquisition area of ​​the body; The wiring channel of the body extends from the brain signal acquisition area to the area of ​​the body for installing the brain signal host board, and is used for embedding the signal transmission line; The signal transmission line is used to connect the electrodes and the brain signal host board to transmit the brain signals collected by the electrodes.

18. The electroencephalogram measuring device according to claim 17, wherein: The brain signal collection area of ​​the main body includes one or more of the following: a frontal lobe brain signal collection area, a posterior frontal lobe brain signal collection area, a parietal lobe brain signal collection area, an occipital lobe brain signal collection area, and a temporal lobe brain signal collection area; The wiring channel includes a transverse wiring channel and a longitudinal wiring channel, which are used to guide the signal transmission lines connected from the brain signal host board to the electrodes set in each brain signal collection area.

19. The electroencephalogram measuring device according to claim 18, wherein: The electrodes arranged in at least one of the brain signal acquisition areas include: a transcranial direct current stimulation (TDCS) positive electrode and a negative electrode.

20. The electroencephalogram measuring device according to claim 19, wherein: The wiring channel is buried inside the body; The body includes a first body, a second body and a third body; the occipital lobe brain region acquisition area is located on the inner side of the second body, the prefrontal lobe brain region acquisition area and / or the posterior frontal lobe brain region acquisition area are located on the inner side of the first body, and the parietal lobe brain region acquisition area and / or the temporal lobe brain region acquisition area are located on the inner side of the third body; The second body is fixedly arranged. With respect to the second body, the first body can be telescopically inserted in front of the second body in a transverse manner, and the third body can be telescopically inserted in the upper part of the second body in a longitudinal manner. The brain signal host board is arranged in the second body, a part of the horizontal wiring channel is formed in the plug-in structure of the first body, and a part of the longitudinal wiring channel is formed in the plug-in structure of the third body.

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