CN219480115U - High density electroencephalogram cap - Google Patents

Abstract

The utility model provides a high-density electroencephalogram cap, which comprises a cap body, electrodes and a fixing belt, wherein a window is arranged on the cap body, and the window is configured to expose only the area corresponding to F1, FC1, C1 leads and/or F2, FC2 and C2 leads of a high-density electroencephalogram 64 lead; the fixing strap is fixedly connected to the bottom of the cap body; the high density electroencephalogram cap further includes a shielding member for opening or shielding the fenestration. The high-density electroencephalogram cap can synchronously acquire scalp electroencephalogram signals and intra-brain electroencephalogram signals in the external hanging period of deep brain electro-stimulation.

Description

High density electroencephalogram cap

Technical Field

The utility model relates to the field of medical equipment, in particular to a high-density electroencephalogram cap capable of being used for simultaneously collecting scalp and brain-in brain electroencephalogram signals and a scalp and brain-in brain-signals synchronous collecting device comprising the high-density electroencephalogram cap.

Background

With the development of bioelectricity and computer technology, application research based on scalp and cortical brain electrical data has achieved some results. Such as electroencephalogram-based diagnosis of epilepsy and cortical electroencephalogram-based application of brain-computer interfaces such as imagination. At present, an electroencephalogram cap is still an important component part of an electroencephalogram acquisition device, has the advantages of no wound, convenience and multiple channels, and is related to the acquisition performance of electroencephalogram data and can directly influence subsequent analysis and processing.

In order to conduct brain diseases and brain science research on loops of deep brain and cortex, high-density scalp electroencephalogram signals and deep brain signals need to be synchronously acquired, but the acquisition of deep brain signals cannot be considered by a traditional electrode cap, and in addition, the risk of infection can be increased by using the traditional electroencephalogram cap for a patient in an externally hung period.

Therefore, there is a need to develop a high-density electroencephalogram cap which can collect scalp and intra-brain electroencephalogram signals simultaneously, and a scalp and intra-brain electroencephalogram signal synchronous collection device including the high-density electroencephalogram cap.

Disclosure of Invention

In order to achieve the above purpose, the utility model provides a high-density electroencephalogram cap and a scalp and brain electroencephalogram synchronous acquisition device comprising the high-density electroencephalogram cap.

The utility model provides a high-density electroencephalogram cap which comprises a cap body, electrodes and a fixing belt, wherein the electrodes are distributed on the inner surface of the cap body according to the high-density electroencephalogram 64 lead layout; a fenestration is arranged on the cap body, and the fenestration is configured to expose only the region corresponding to the F1, FC1, C1 lead and/or the F2, FC2, C2 lead of the high-density electroencephalogram 64 lead;

the fixing belt is fixedly connected to the bottom of the cap body;

the high-density electroencephalogram cap further comprises a zipper connector, wherein the zipper connector is used for opening or shielding the fenestration;

wherein the window is rectangular, the long side of the window is 8-10cm, and the short side is 2-3cm.

In a first aspect, the present utility model provides a high density electroencephalogram cap that can be used to collect scalp and intra-brain electroencephalogram signals simultaneously. The high-density electroencephalogram cap comprises a cap body, electrodes and a mandibular support belt. The cap body is used for being worn on the head of a tester. The electrodes are distributed on the inner surface of the cap body according to the high-density electroencephalogram 64 lead layout. A fenestration is provided on the cap, the fenestration being configured to expose only a region corresponding to the F1, FC1, C1 and/or F2, FC2, C2 leads of the high density electroencephalogram 64 lead. The lower jaw supporting belt is fixedly connected to the bottom of the cap body, and is supported on the lower jaw of a tester to fix the high-density electroencephalogram cap when in use. The high density electroencephalogram cap further includes a shielding member for opening or shielding the fenestration.

The high-density electroencephalogram cap body used in the utility model can be made of materials such as cloth, leather, rubber, polymer, non-woven fabric and the like, preferably made of light and thin breathable polymer composite materials or non-woven fabric, and can also be made of elastic materials by weaving.

In the present utility model, the high density electroencephalogram 64 lead layout adopted for the electrodes in the electroencephalogram cap includes electrodes A1 and A2 (see fig. 1) arranged at the corresponding two-sided mastoid processes in addition to the conventional electroencephalogram 62 lead electrodes, namely, 62 electroencephalogram lead electrodes and two mastoid lead electrodes A1 and A2.

In one embodiment, two windows are provided on the cap body, the two windows are symmetrically arranged on two sides of the sagittal axis of the cap body respectively along the sagittal axis, and the high-density electroencephalogram cap comprises two shielding parts, and each shielding part shields one window respectively.

In the present utility model, the shape of the opening is not limited as long as the exposed area thereof includes only the area corresponding to the F1, FC1, C1 lead and/or the F2, FC2, C2 lead of the high density electroencephalogram 64 lead, preferably being rectangular. Specifically, in the case of rectangular shape, the long side diameter of the window may be generally 8-10cm, and the short side may be 2-3cm.

In a preferred embodiment, the shielding member may be a zipper connector. Specifically, the zipper connector may include a zipper tooth, a slider and a chain connected with an edge of the window to be fixedly connected to the cap body, the zipper tooth and the slider being engaged with each other to open or shield the window.

In the present utility model, the zipper connector may take the form of a conventional variety of zipper constructions, preferably the zipper tape is a flexible tape woven from cotton, chemical or hybrid fibers, such as nylon zippers. The element and the slider are preferably made of plastic, more preferably medical plastic, such as polyethylene, polypropylene, polyvinyl chloride, etc. When the brain electrical measurement electrode is used in the external hanging period, the brain electrical measurement electrode led out from the cranium top incision can be fixed on either side of the zipper through the zipper connecting piece.

In a preferred embodiment, the high density electroencephalogram cap further comprises two securing members disposed on an outer surface of the cap body and disposed adjacent one side of each fenestration. It will be appreciated that the purpose of the securing means is to further stabilize the electroencephalogram electrodes secured by the zipper connection against axial movement by excessive pulling. In the present utility model, the fixing member may employ a structure for fixing a cable or an electrode, which is commonly used, for example, a buckle, a harness, a fishbone winder, etc.

In a second aspect, the utility model provides a scalp and intra-brain electroencephalogram synchronous acquisition device, which comprises the high-density electroencephalogram cap, one or more intra-brain electroencephalogram electrodes and a signal processing device, wherein the electrodes of the high-density electroencephalogram cap and the intra-brain electroencephalogram electrodes are electrically connected with the signal processing device.

In the present utility model, the electroencephalographic electrodes are configured to be disposed within the brain for acquiring an electroencephalographic signal, wherein the electroencephalographic signal comprises an electroencephalographic signal of the cortex or deep nuclei.

In one embodiment, the signal processing apparatus includes:

1) A receiving module configured to receive raw scalp electroencephalogram signals acquired by electrodes of the high density electroencephalogram cap;

2) A scalp signal compensation module configured to acquire the original scalp electroencephalogram signal received from the receiving module, reconstruct F1, FC1, C1, F2, FC2, signals of C2 leads as compensation signals of the F1, FC1, C1, F2, FC2, C2 leads from the original scalp electroencephalogram signal acquired by the electrode of the high-density electroencephalogram cap,

3) A scalp signal combining module configured to combine an original scalp brain electrical signal and the compensation signal reconstructed by the scalp signal compensation module to output as a compensated complete scalp brain electrical signal,

4) And the output module is configured to receive the compensated complete scalp electroencephalogram signal and the brain electroencephalogram signal output by the signal combining module and send the compensated complete scalp electroencephalogram signal and the brain electroencephalogram signal to the electroencephalogram analysis system together.

In one embodiment, the raw scalp electroencephalogram signal collected by the electrodes of the high density electroencephalogram cap is a scalp electroencephalogram signal collected by 58 electrodes. It is noted that, since the high density electroencephalogram cap of the present utility model lacks electrodes corresponding to the F1, FC1, C1, F2, FC2, C2 leads, the original scalp electroencephalogram collected does not include signals collected by the F1, FC1, C1, F2, FC2, C2 electrodes, but the original scalp electroencephalogram collected by the other 56 electrodes plus the mastoid electrodes A1 and A2, and the final compensated complete scalp electroencephalogram contains scalp electroencephalogram corresponding to 64 leads.

In a preferred embodiment, the scalp signal reconstructing module reconstructs the signals of the F1, FC1, C1, F2, FC2, C2 leads by taking the following steps: firstly, extracting original scalp electroencephalogram signals acquired by 56 electrodes which do not comprise mastoid electrodes, reconstructing 62 brain electric lead signals according to the distribution coordinates of the 56 electrodes, and then obtaining corresponding F1, FC1, C1, F2, FC2 and C2 lead signals as F1, FC1, C1, F2, FC2 and C2 lead compensation signals. Preferably, the method for reconstructing partial electrode signals according to the distribution coordinates of 56 electrodes can be calculated by adopting a spherical surface method and a brain positive model. In this case, the step of reconstructing the signal may be accomplished by means of a built-in function tool in the EEGLAB, mno, fieldtrip brain electrical engineering package.

In another preferred embodiment, where an accurate signal is not required, the scalp signal compensation module reconstructs the signals of the F1, FC1, C1, F2, FC2, C2 leads by averaging, i.e., using the average of the signals of 2 or 4 leads surrounding each of the F1, FC1, C1, F2, FC2, C2 leads as the respective signal values for those leads. For example, the electroencephalogram signal corresponding to the F1 lead can be obtained on average with the raw signals acquired from the F3 and FZ electrodes; the electroencephalogram signals corresponding to the FC1 leads can be averaged from the raw signals acquired from the FC3 and FCZ electrodes; the signal corresponding to the C1 lead may be averaged with the raw signals acquired from the C3 and CZ electrodes; the electroencephalogram signal corresponding to the F2 lead can be obtained on average from the raw signals acquired from the F4 and FZ electrodes; the electroencephalogram signals corresponding to the FC2 leads can be averaged from the raw signals acquired from the FC4 and FCZ electrodes; the electroencephalogram signal corresponding to the C2 lead can be obtained on average from the raw signals acquired from C4 and CZ.

In a preferred embodiment, the signal processing apparatus may further include an electroencephalogram signal amplifying module and an electroencephalogram signal preprocessing module configured to amplify and preprocess an electroencephalogram signal, respectively, to obtain an amplified and preprocessed electroencephalogram signal, wherein the preprocessing includes filtering, noise reduction, artifact removal, and the like. The brain electrical signals may include scalp brain electrical signals and/or brain electrical signals within the brain, but since brain electrical signals are relatively weak and noisy, brain electrical signals that amplify and pre-process brain electrical signals within the brain are preferred. Thus, in a preferred embodiment, the brain electrical signal received by the output module is an amplified and preprocessed brain electrical signal.

In a third aspect, the utility model provides a method for synchronously collecting scalp and brain electrical signals, which comprises the following steps:

1. receiving an original scalp electroencephalogram signal collected by an electrode of a high-density electroencephalogram cap and an electroencephalogram signal collected by an electroencephalogram measurement electrode;

2. reconstructing signals of F1, FC1, C1, F2, FC2 and C2 leads according to the original scalp electroencephalogram signals acquired by the high-density electroencephalogram cap electrode, wherein the signals are used as compensation signals of the F1, FC1, C1, F2, FC2 and C2 leads;

3. combining the original scalp electroencephalogram signal and the reconstructed compensation signal to be output as a compensated complete scalp electroencephalogram signal,

4. and sending the compensated complete scalp electroencephalogram signal serving as a scalp electroencephalogram signal and an electroencephalogram signal to an electroencephalogram analysis system together for subsequent analysis.

In a specific embodiment, the signal reconstruction in step 2 may be performed according to any of the reconstruction methods described above.

In one embodiment, the scalp and/or intra-brain electrical signals may be amplified and pre-processed, including filtering, noise reduction, and artifact removal, among others.

Advantageous effects

Since deep brain electro-stimulation surgical incisions are typically relatively fixed, the inventors have measured that they have found that the surgical incision overlaps with F1, FC1, C1 and the F2, FC2, C2 lead locations on the right. Based on this finding, the inventors designed a high-density electroencephalogram cap which can be used for synchronously collecting scalp and brain-in-brain electroencephalogram signals, and developed a scalp and brain-in-brain electroencephalogram signal synchronous collecting device based on the high-density electroencephalogram cap.

The utility model has the following advantages:

1. the leads F1, FC1, C1, F2, FC2 and C2 of the traditional high-density electroencephalogram cap are not provided with electrodes, a window is arranged, and a double-side zipper is arranged on the window. The design is not only convenient for leading out the external electrode wire; the compression to the lower incision is reduced, and the potential infection risk and discomfort brought to the incision of a patient during the high-density electroencephalogram recording of the external hanging period of the deep brain electro-stimulation operation are avoided; in addition, the whole electroencephalogram cap has moderate tension after the zipper is pulled up, and the electrode position is kept better without displacement.

2. The missing electroencephalogram signals of the leads are compensated by reconstructing the signals of the F1, FC1, C1, F2, FC2 and C2 leads, so that the complete scalp electroencephalogram signals are obtained.

3. The scalp electroencephalogram and the intra-brain electroencephalogram can be synchronously acquired in the external hanging period of the deep brain electro-stimulation operation, which cannot be realized by the conventional high-density electroencephalogram cap.

Drawings

Various other advantages and benefits will become apparent to those of ordinary skill in the art upon reading the following detailed description of the preferred embodiments. The drawings are only for purposes of illustrating the preferred embodiments and are not to be construed as limiting the utility model. Like parts are designated with like reference numerals throughout the drawings. In the drawings:

fig. 1 is a schematic diagram of a high density electroencephalogram 64 lead layout in the present utility model.

Fig. 2 is a schematic view of one embodiment of the high density electroencephalogram cap of the present utility model.

Fig. 3 shows a schematic view of the arrangement of fenestration in one embodiment of the high density electroencephalogram cap of the present utility model.

FIG. 4 is a partial schematic view of one embodiment of the high density electroencephalogram cap of the present utility model illustrating the arrangement of the zipper connectors, leads and securing members.

Fig. 5 is a block diagram of one embodiment of a synchronous scalp and deep brain electrical signal acquisition device of the present utility model.

Fig. 6 schematically shows a signal processing flow diagram in one embodiment of the synchronous scalp and intra-brain electroencephalogram signal acquisition apparatus of the present utility model.

The various references in the drawings are as follows:

1 cap body

2. Electrode

3. Window opening

4. Mandibular support belt

5. Fixing component

6. Intra-brain measuring electrode

7. Zipper connecting piece

Detailed Description

Exemplary embodiments of the present utility model will be described in more detail below with reference to the accompanying drawings. While exemplary embodiments of the present utility model are shown in the drawings, it should be understood that the present utility model may be embodied in various forms and should not be limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the utility model to those skilled in the art.

Definition:

in the description of the present utility model, it should be noted that, unless explicitly stated and limited otherwise, the terms "mounted," "disposed," and "connected" are to be construed broadly, and may be, for example, fixedly connected, detachably connected, or integrally connected; can be mechanically or electrically connected; can be directly connected or indirectly connected through an intermediate medium, and can be communication between two elements. The specific meaning of the above terms in the present utility model will be understood in specific cases by those of ordinary skill in the art.

In the description of the present utility model, it should be noted that the azimuth or positional relationship indicated by the terms "upper", "lower", "front", "rear", etc. are based on the azimuth or positional relationship shown in the drawings, and are merely for convenience of describing the present utility model and simplifying the description, and do not indicate or imply that the system or element referred to must have a specific azimuth, be configured and operated in a specific azimuth, and thus should not be construed as limiting the present utility model.

Sagittal axis: an axis perpendicular to the vertical axis of the human body in the front-rear direction.

Coronary axis: an axis perpendicular to the sagittal axis and the vertical axis in the left-right direction.

It should be noted that in describing the electroencephalogram cap electrode in the present utility model, "lead" and "electrode" have the same meaning and may sometimes be used interchangeably. For the sake of non-ambiguity, however, reference is generally made to the layout of the electroencephalogram cap electrode when describing "leads" (see fig. 1), and to the components of the device of the present utility model when describing "electrodes".

The utility model relates to a high-density electroencephalogram cap

Fig. 1 shows the layout of the high density electroencephalogram 64 leads of the present utility model, where A1 and A2 are mastoid leads corresponding to the mastoid of the skull.

Fig. 2 illustrates one embodiment of the high density electroencephalogram cap of the present utility model, including the cap body 1, the electrode 2, and the mandibular carrier 4. The electrodes 1 are arranged on the inner surface of the cap 1 in a 64-lead layout as shown in fig. 1. In the embodiment shown in fig. 2, a fenestration 3 is provided on the cap 1, the fenestration 3 being configured to expose an area corresponding to the F1, FC1, C1 lead and/or the F2, FC2, C2 lead. The mandibular support belt 4 is fixedly connected to the bottom of the cap body 1, and when in use, after the testee wears the high-density electroencephalogram cap, the mandibular support belt 4 is supported on the mandible of the testee to further fix the electroencephalogram cap. The cap body 1 is also provided with a zipper connector 7, and the zipper connector 7 is used for opening or shielding the window 3.

In the embodiment shown in fig. 3, two fenestrations 3 are provided, the two fenestrations 3 being symmetrically arranged on the left and right sides of the sagittal axis a of the cap 1 along the sagittal axis a and exposing the areas corresponding to the F1, FC1, C1 leads and/or the F2, FC2, C2 leads, respectively.

Fig. 4 is a partial schematic view of one embodiment of the high density electroencephalogram cap of the present utility model. As shown in fig. 4, two zipper connectors 7,7' are provided on the high density electroencephalogram cap for opening or shielding the two windows, respectively. In fig. 4, it is also illustrated that the intra-brain electroencephalogram electrodes 6 are led out from the incision and are fixed by the closed zipper connectors 7,7', while the closed zipper connectors 7,7' conceal the fenestration. The electroencephalogram electrodes 6 led out from the electroencephalogram cap are further fixed by the fixing part 5, and the externally hung electroencephalogram electrodes 6 can be connected to an electroencephalogram acquisition device to acquire deep brain nuclear cluster electrical signals.

Deep brain electro-stimulation surgical incisions are typically relatively fixed, and extend forward about 6-8cm 3-4cm forward of the coronal suture. The inventors have measured that the surgical incision overlaps with the F1, FC1, C1 and the F2, FC2, C2 lead positions on the right. Thus, in the present utility model, the shape of the window is not limited as long as it exposes only the region corresponding to the F1, FC1, C1 lead and/or the F2, FC2, C2 lead, and in the embodiment shown in FIGS. 2 to 4, the window is rectangular, the length of the long side may be generally set to 8 to 10cm, and the length of the short side may be generally set to 2 to 3cm.

The utility model relates to a scalp and brain electrical signal synchronous acquisition device and method

Fig. 5 is a block diagram of an embodiment of a synchronous scalp and intra-brain electroencephalogram signal acquisition apparatus of the present utility model. As shown in fig. 5, the scalp and brain electrical signal synchronous acquisition device comprises a high-density electroencephalogram cap, a brain measuring electrode and a signal processing device, wherein the electrode of the high-density electroencephalogram cap is electrically connected with the brain measuring electrode and the signal processing device. In the present utility model, an electroencephalogram electrode is configured to be disposed within the brain for acquiring an electroencephalogram signal, wherein the electroencephalogram signal comprises an electroencephalogram signal of the cortex or deep nuclei.

In this embodiment, the signal processing device may include at least: 1) A receiving module; 2) A scalp signal compensation module; 3) A scalp signal combining module; and 4) an output module. Preferably, the signal processing device may further include 5) an electroencephalogram signal amplifying module and 6) an electroencephalogram signal preprocessing module.

Fig. 6 shows a signal processing flow diagram in one embodiment of the synchronous scalp and intra-brain electroencephalogram signal acquisition apparatus of the present utility model.

S1, acquiring original scalp electroencephalogram signals of a tester through a high-density electroencephalogram cap, and acquiring electroencephalogram signals through an electroencephalogram measuring electrode;

s2, a receiving module receives an original scalp electroencephalogram signal acquired by an electrode of the high-density electroencephalogram cap and an electroencephalogram signal acquired by an electroencephalogram measuring electrode in the brain;

s3, reconstructing signals of F1, FC1, C1, F2, FC2 and C2 leads according to original scalp electroencephalogram signals acquired by the high-density electroencephalogram cap electrode by using the scalp signal compensation module as compensation signals of the F1, FC1, C1, F2, FC2 and C2 leads;

s4, combining the original scalp electroencephalogram signals and the compensation signals of the F1, FC1, C1, F2, FC2 and C2 leads reconstructed by the scalp signal compensation module by the scalp signal combination module to be used as compensated complete scalp electroencephalogram signals to be output;

s5, the output module sends the compensated complete scalp electroencephalogram signal serving as a scalp electroencephalogram signal and an electroencephalogram signal to an electroencephalogram analysis system together for subsequent analysis.

In the present utility model, the signal reconstruction in step S3 may be performed by an averaging method or by using a spherical surface method and a brain positive model.

If a particularly accurate signal is not required, an averaging method can be used to obtain the compensation signal for the F1, FC1, C1, F2, FC2, C2 leads, i.e., the signal value for each of the F1, FC1, C1, F2, FC2, C2 leads is replaced by an average of 2 or 4 leads around that lead. In one embodiment, the electroencephalogram signal corresponding to the F1 lead can be averaged with the raw signals acquired from the F3 and FZ electrodes; the electroencephalogram signals corresponding to the FC1 leads can be averaged from the raw signals acquired from the FC3 and FCZ electrodes; the signal corresponding to the C1 lead may be averaged with the raw signals acquired from the C3 and CZ electrodes; the electroencephalogram signal corresponding to the F2 lead can be obtained on average from the raw signals acquired from the F4 and FZ electrodes; the electroencephalogram signals corresponding to the FC2 leads can be averaged from the raw signals acquired from the FC4 and FCZ electrodes; the electroencephalogram signal corresponding to the C2 lead can be obtained on average from the raw signals acquired from C4 and CZ.

Because the human head is spherical, the reconstruction of signals can also be accomplished by using a spherical surface method and a brain positive model, and the step can be accomplished by using a built-in correlation function tool in EEGLAB, MNE, fieldtrip brain electrical engineering package. The specific process can be as follows: firstly, extracting original scalp electroencephalogram signals acquired by 56 electrodes which do not comprise mastoid electrodes, reconstructing 62 brain electric lead signals according to the distribution coordinates of the 56 electrodes, and then obtaining signals corresponding to F1, FC1, C1, F2, FC2 and C2 leads from the signals as compensation signals of the F1, FC1, C1, F2, FC2 and C2 leads.

In a preferred embodiment, the step S4 may further comprise a step of amplifying and preprocessing an electroencephalogram signal to obtain an amplified and preprocessed electroencephalogram signal, in addition to the compensated complete scalp electroencephalogram signal, wherein the electroencephalogram signal may comprise a scalp electroencephalogram signal and/or an intra-brain electroencephalogram signal. Since the brain electrical signal is weaker and noisier than the scalp brain electrical signal, the brain electrical signal obtained by amplifying and preprocessing the brain electrical signal is preferable. As shown in fig. 6, the intra-brain electrical signals may be amplified and preprocessed, including filtering, noise reduction, artifact removal, etc., and then output to the brain electrical analysis system via the output module.

Examples

The scalp and brain electrical signal synchronous acquisition device can be matched with DBS to realize synchronous acquisition of scalp and brain electrical signal. For example, the brain signals recorded by the DBS electrode and scalp brain signals are synchronously analyzed, and the brain signals can be used for dynamically feeding back the movement disorder and the epileptic patient condition or evaluating the curative effect of DBS stimulation.

The following is a brief description of the method of using the synchronous scalp and brain electrical signal acquisition device in DBS operation according to the present utility model.

Preparation period and operation period: imaging (e.g., CT scan, magnetic resonance imaging, etc.) of a subject (e.g., a patient suffering from Parkinson's disease), determining a target site (e.g., subthalamic nucleus) to be operated on based on the imaging results, performing an electrode implantation, and placing a DBS electrode 6 at the target site. After the electrode is placed at the target point of the tester, the optimal implantation position of the target point is determined by combining the signal recorded by electrophysiology in the operation and the improvement degree of the curative effect during temporary electrical stimulation. The DBS electrode 6 is then led out of the incision and into the electrode connection plug.

External hanging no stimulation period:

the tester wears the high density electroencephalogram cap of the present utility model, passes the DBS electrode led out from the cranium top incision through the fenestration of the high density electroencephalogram cap of the present utility model, pulls the zipper to fix one or more DBS electrodes at one side or both sides of the fenestration, and fixes the extension lead of the DBS electrode 6 to the cap body 1 by the fixing member 5.

The brain electro-physiological signals (including but not limited to brain neuron electrical signals, local field potential signals, brain deep impedance signals and the like) generated at all contacts of the target point in the brain are collected in real time, and meanwhile, scalp brain electrical signals are collected in real time. When the original signal does not need to be accurately restored (such as clinically visually observing the brain wave shape), preliminary signal reconstruction can be performed by an average method. When the original signal is required to be accurately restored (such as analyzing the functional connection of the deep brain electrophysiological signal and the scalp brain electrophysiological signal), the signal reconstruction is required to be completed through a spherical surface method and a brain positive model. The reconstructed brain electrical signals can be amplified and preprocessed and then output to an electroencephalogram analysis system through an output module, wherein the preprocessing comprises filtering, noise reduction, artifact removal and the like. Meanwhile, the scalp electroencephalogram signal and the deep brain electric signal of the target point are subjected to analysis (such as Coherence, C). In conclusion, the brain electrical change condition of a tester (for example, a parkinsonism patient) can be dynamically displayed, and the brain electrical change condition has clinical significance for monitoring and treating symptoms.

Externally hung stimulation period:

before DBS stimulation, the tester wears the high-density electroencephalogram cap of the present utility model, passes the DBS electrode led out from the cranium top incision through the fenestration of the high-density electroencephalogram cap of the present utility model, pulls the zipper to fix one or more DBS electrodes on one side or both sides of the fenestration, and fixes the extension lead of the DBS electrode 6 on the cap body 1 by the fixing member 5.

The method comprises the steps of applying a stimulation signal to a DBS electrode, stimulating a target (such as 130Hz,60 mu s and 1.5V), removing stimulation artifacts through hardware and an algorithm, and collecting and analyzing the stimulation artifacts in real time, wherein the flow is the same as the external non-stimulation period, so that the brain electricity change condition of a tester (such as a parkinsonism patient) in different stimulation modes can be dynamically displayed, and the method has clinical significance for monitoring and treating symptoms.

Finally, it should be noted that: the above embodiments are only for illustrating the technical solution of the present utility model, and are not limiting; although the utility model has been described in detail with reference to the foregoing embodiments, it will be understood by those of ordinary skill in the art that: the technical scheme described in the foregoing embodiments can be modified or some technical features thereof can be replaced by equivalents; such modifications and substitutions do not depart from the spirit and scope of the technical solutions of the embodiments of the present utility model.

Claims (4)

1. The utility model provides a high density electroencephalogram cap, includes the cap body, electrode and fixed band, its characterized in that:

the electrodes are distributed on the inner surface of the cap body according to the high-density electroencephalogram 64 lead layout; a fenestration is provided on the cap, the fenestration being configured to expose only a region corresponding to the F1, FC1, C1 lead and/or the F2, FC2, C2 lead of the high density electroencephalogram 64 lead;

the fixing strap is fixedly connected to the bottom of the cap body;

the high-density electroencephalogram cap further comprises a zipper connector, wherein the zipper connector is used for opening or shielding the fenestration;

wherein the window is rectangular, the long side of the window is 8-10cm, and the short side is 2-3cm.

2. The high density electroencephalogram cap according to claim 1, characterized in that: the high-density electroencephalogram cap comprises a cap body and is characterized in that two open windows are arranged on the cap body, the two open windows are symmetrically arranged on two sides of the sagittal axis of the cap body respectively along the sagittal axis of the cap body, and each zipper connector covers one open window respectively.

3. The high density electroencephalogram cap according to claim 1, characterized in that: the zipper connecting piece comprises a zipper tooth, a zipper head and a chain belt, wherein the chain belt is connected with the edge of the window so as to be fixedly connected to the cap body, and the zipper tooth and the zipper head are matched with each other to open or shield the window.

4. The high density electroencephalogram cap according to claim 1, characterized in that:

the high-density electroencephalogram cap further comprises a fixing part, and the fixing part is arranged on the outer surface of the cap body and is arranged adjacent to one end of the fenestration.