High-density EEG cap, scalp and brain EEG signal synchronous acquisition device and method

Abstract

The present invention provides a high-density EEG cap, comprising a cap body, electrodes, and a fixing strap, wherein a window is provided on the cap body, and the window is configured to expose only the area corresponding to the F1, FC1, C1 leads and / or the F2, FC2, C2 leads of the high-density EEG 64-lead; the fixing strap is fixedly connected to the bottom of the cap body; the high-density EEG cap also includes a shielding component, which is used to open or shield the window. The present invention also provides a scalp and brain EEG signal synchronous acquisition device, comprising a high-density EEG cap, one or more brain EEG measurement electrodes, and a signal processing device. The scalp and brain EEG signal synchronous acquisition device of the present invention can synchronously acquire scalp EEG signals and brain EEG signals during the external period of deep brain stimulation.

Description

Technical Field

[0001] The present invention relates to the field of medical devices, and in particular to a high-density electroencephalogram (EEG) cap that can be used to simultaneously collect scalp and brain EEG signals, and a scalp and brain EEG signal synchronous collection device and method comprising the high-density EEG cap. Background Art

[0002] With the advancement of bioelectronics and computer technology, research on applications based on scalp and cortical EEG data has yielded some promising results. Examples include EEG-based epilepsy diagnosis and brain-computer interface applications such as motor imagery. Currently, EEG caps remain a crucial component of EEG data collection systems, offering advantages such as non-invasiveness, portability, and a high number of channels. These caps significantly impact the performance of EEG data collection, directly influencing subsequent analysis and processing.

[0003] In order to conduct brain disease and brain science research in the deep brain and cortical circuits, it is necessary to simultaneously collect high-density scalp EEG and deep brain signals. However, traditional electrode caps cannot take into account the collection of deep brain signals. In addition, using traditional EEG caps on patients in the external use period will increase the risk of infection.

[0004] Therefore, it is necessary to develop a high-density EEG cap that can simultaneously collect EEG signals from the scalp and the brain, and a device for synchronously collecting EEG signals from the scalp and the brain including the high-density EEG cap. Summary of the Invention

[0005] To achieve the above objectives, the present invention provides a high-density EEG cap and a device and method for synchronously collecting EEG signals from the scalp and brain including the high-density EEG cap.

[0006] In the first aspect, the present invention provides a high-density EEG cap that can be used to simultaneously collect EEG signals from the scalp and the brain. The high-density EEG cap includes a cap body, electrodes and a chin strap. The cap body is used to be worn on the head of a test subject. The electrodes are arranged on the inner surface of the cap body according to the high-density EEG 64-lead layout. A window is provided on the cap body, and the window is configured to expose only the area corresponding to the F1, FC1, C1 leads and / or the F2, FC2, C2 leads of the high-density EEG 64 leads. The chin strap is fixedly connected to the bottom of the cap body, and when in use, the chin strap supports the test subject's chin to fix the high-density EEG cap. The high-density EEG cap also includes a shielding component, which is used to open or shield the window.

[0007] The high-density EEG cap used in the present invention can be made of materials such as cloth, leather, rubber, polymer, non-woven fabric, etc., preferably made of light, thin and breathable polymer composite materials or non-woven fabric, and can also be woven from elastic materials.

[0008] In the present invention, the high-density 64-lead EEG layout of the electrodes in the EEG cap includes, in addition to the conventional 62-lead EEG electrodes, electrodes A1 and A2 arranged at the corresponding mastoids on both sides (see Figure 1 ), which includes 62 EEG lead electrodes and two mastoid lead electrodes A1 and A2.

[0009] In one embodiment, two windows are provided on the cap body, and the two windows are symmetrically arranged on both sides of the sagittal axis along the sagittal axis of the cap body, and the high-density EEG cap includes two shielding parts, each shielding part shields one window respectively.

[0010] In the present invention, the shape of the fenestration is not limited, as long as the exposed area only includes the areas corresponding to leads F1, FC1, and C1 and / or leads F2, FC2, and C2 of the 64-lead high-density EEG. Preferably, the shape is rectangular. Specifically, in the case of a rectangular shape, the long side of the fenestration can generally be set to 8-10 cm, and the short side can be 2-3 cm.

[0011] In a preferred embodiment, the shielding component may be a zipper connector. Specifically, the zipper connector may include chain teeth, a slider, and a chain belt, wherein the chain belt is connected to the edge of the window to be fixedly connected to the cap body, and the chain teeth and the slider cooperate with each other to open or shield the window.

[0012] In the present invention, the zipper connector can utilize any common zipper structure. Preferably, the zipper strip is a flexible belt woven from cotton yarn, chemical fiber, or a blend of chemical fibers, such as a nylon zipper. The chain elements and slider are preferably made of plastic, more preferably medical-grade plastics such as polyethylene, polypropylene, or polyvinyl chloride. During external use, the EEG measurement electrodes, extending from the cranial incision, can be secured to either side of the zipper via the zipper connector.

[0013] In a preferred embodiment, the high-density EEG cap further includes two fixing components, which are arranged on the outer surface of the cap body and adjacent to one side of each window. It should be understood that the purpose of the setting of the fixing components is to further stabilize the intracerebral EEG measurement electrodes fixed by the zipper connector to prevent them from being excessively pulled and moving axially. In the present invention, the fixing components can adopt a commonly used structure for fixing cables or electrodes, such as a buckle, a cable tie, a fishbone cable winder, etc.

[0014] In a second aspect, the present invention provides a device for synchronously collecting scalp and brain EEG signals, the device comprising the high-density EEG cap of the present invention, one or more brain EEG measurement electrodes, and a signal processing device, wherein the electrodes of the high-density EEG cap and the brain EEG measurement electrodes are electrically connected to the signal processing device.

[0015] In the present invention, the electroencephalogram (EEG) measuring electrodes are configured to be arranged in the brain for collecting EEG signals in the brain, wherein the EEG signals in the brain include EEG signals of the cerebral cortex or deep nuclei.

[0016] In one embodiment, the signal processing device comprises:

[0017] 1) a receiving module configured to receive raw scalp EEG signals collected by electrodes of the high-density EEG cap;

[0018] 2) a scalp signal compensation module, the scalp signal compensation module being configured to obtain the original scalp EEG signals received from the receiving module, and reconstruct the signals of the F1, FC1, C1, F2, FC2, and C2 leads based on the original scalp EEG signals collected by the electrodes of the high-density EEG cap as compensation signals for the F1, FC1, C1, F2, FC2, and C2 leads,

[0019] 3) a scalp signal merging module, the signal merging module being configured to merge the original scalp EEG signal and the compensated signal reconstructed by the scalp signal compensation module into a compensated complete scalp EEG signal for output;

[0020] 4) An output module, wherein the output module is configured to receive the compensated complete scalp EEG signal and the intra-brain EEG signal output by the signal merging module, and send them together to an EEG analysis system.

[0021] In one embodiment, the raw scalp EEG signals collected by the electrodes of the high-density EEG cap are scalp EEG signals collected by 58 electrodes. It should be noted that since the high-density EEG cap of the present invention lacks the electrodes corresponding to the F1, FC1, C1, F2, FC2, and C2 leads, the raw scalp EEG signals collected do not include the signals collected by the F1, FC1, C1, F2, FC2, and C2 electrodes, but rather the raw scalp EEG signals collected by the other 56 electrodes plus the mastoid electrodes A1 and A2. The final compensated complete scalp EEG signal includes the scalp EEG signals corresponding to the 64 leads.

[0022] In a preferred embodiment, the scalp signal reconstruction module reconstructs the signals of the F1, FC1, C1, F2, FC2, and C2 leads by taking the following steps: first, extract the original scalp EEG signals collected by 56 electrodes excluding the mastoid electrodes, reconstruct the signals of 62 EEG leads based on the distribution coordinates of the 56 electrodes, and then obtain the signals corresponding to the F1, FC1, C1, F2, FC2, and C2 leads as compensation signals for the F1, FC1, C1, F2, FC2, and C2 leads. Preferably, the method of reconstructing the partial electrode signals based on the distribution coordinates of the 56 electrodes can be calculated using the spherical surface method and the brain positive electrical model. In this case, the signal reconstruction step can be completed with the help of the built-in function tools in EEGLAB, MNE, and fieldtrip EEG work packages.

[0023] In another preferred embodiment, when precise signals are not required, the scalp signal compensation module can reconstruct the signals of leads F1, FC1, C1, F2, FC2, and C2 using an averaging method, i.e., using the average of the signals of two or four leads surrounding each of leads F1, FC1, C1, F2, FC2, and C2 as the signal value of each lead. For example, the EEG signal corresponding to lead F1 can be obtained by averaging the raw signals collected from the F3 and FZ electrodes; the EEG signal corresponding to lead FC1 can be obtained by averaging the raw signals collected from the FC3 and FCZ electrodes; the signal corresponding to lead C1 can be obtained by averaging the raw signals collected from the C3 and CZ electrodes; the EEG signal corresponding to lead F2 can be obtained by averaging the raw signals collected from the F4 and FZ electrodes; the EEG signal corresponding to lead FC2 can be obtained by averaging the raw signals collected from the FC4 and FCZ electrodes; and the EEG signal corresponding to lead C2 can be obtained by averaging the raw signals collected from the C4 and CZ electrodes.

[0024] In a preferred embodiment, the signal processing device may further include an EEG signal amplification module and an EEG signal preprocessing module, wherein the EEG signal amplification module and the EEG signal preprocessing module are configured to amplify and preprocess the EEG signals respectively to obtain amplified and preprocessed EEG signals, wherein the preprocessing includes filtering, noise reduction, and artifact removal. The EEG signals may include scalp EEG signals and / or intracerebral EEG signals, but because EEG signals are relatively weak and noisy, it is preferred to amplify and preprocess the intracerebral EEG signals. Therefore, in a preferred specific embodiment, the intracerebral EEG signals received by the output module are amplified and preprocessed intracerebral EEG signals.

[0025] In a third aspect, the present invention provides a method for synchronously collecting scalp and brain EEG signals, comprising the following steps:

[0026] 1. Receive the original scalp EEG signals collected by the electrodes of the high-density EEG cap and the intra-brain EEG signals collected by the intra-brain EEG measurement electrodes;

[0027] 2. Reconstructing the signals of the F1, FC1, C1, F2, FC2, and C2 leads based on the original scalp EEG signals collected by the high-density EEG cap electrodes as compensation signals for the F1, FC1, C1, F2, FC2, and C2 leads;

[0028] 3. Combining the original scalp EEG signal and the reconstructed compensation signal as a compensated complete scalp EEG signal output,

[0029] 4. Sending the compensated complete scalp EEG signal as a scalp EEG signal and an intracerebral EEG signal together to an EEG analysis system for subsequent analysis.

[0030] In a specific embodiment, the signal reconstruction in step 2 can be performed according to any of the reconstruction methods described above.

[0031] In one embodiment, the scalp EEG signals and / or brain EEG signals may be amplified and preprocessed, and the preprocessing may include filtering, noise reduction, and artifact removal.

[0032] Beneficial effects

[0033] Because deep brain stimulation surgical incisions are typically fixed, the inventors discovered through measurements that the incision overlaps with the locations of leads F1, FC1, C1, and the right side, F2, FC2, and C2. Based on this discovery, the inventors designed a high-density EEG cap for synchronously collecting scalp and brain EEG signals. Based on this high-density EEG cap, they developed a device for synchronously collecting scalp and brain EEG signals.

[0034] The present invention has the following advantages:

[0035] 1. Instead of electrodes at leads F1, FC1, C1, F2, FC2, and C2 on traditional high-density EEG caps, windows are provided, with double-sided zippers. This design not only facilitates the extraction of external electrode cables but also reduces pressure on the underlying incision, avoiding potential infection risks and discomfort to the patient's incision during external high-density EEG recording during deep brain stimulation. Furthermore, when the zipper is closed, the entire EEG cap maintains moderate tension, ensuring that the electrodes remain in place without displacement.

[0036] 2. By reconstructing the signals of leads F1, FC1, C1, F2, FC2, and C2, the missing EEG signals of these leads are compensated to obtain a complete scalp EEG signal.

[0037] 3. It can synchronously collect scalp EEG signals and brain EEG signals during deep brain stimulation, which is impossible to achieve with existing conventional high-density EEG caps. BRIEF DESCRIPTION OF THE DRAWINGS

[0038] Various other advantages and benefits will become apparent to those skilled in the art upon reading the detailed description of the preferred embodiment below. The accompanying drawings are for illustration purposes only and are not to be considered as limiting the present invention. Throughout the drawings, the same reference numerals are used to denote the same components. In the drawings:

[0039] Figure 1 It is a schematic diagram of the high-density EEG 64-lead layout in the present invention.

[0040] Figure 2 Schematic diagram of one embodiment of the high-density EEG cap of the present invention.

[0041] Figure 3 A schematic diagram showing the arrangement of windows in one embodiment of a high-density EEG cap of the present invention is shown.

[0042] Figure 4 It is a partial schematic diagram of an embodiment of the high-density EEG cap of the present invention, illustrating the arrangement of the zipper connector, wires and fixing components.

[0043] Figure 5 This is a schematic diagram of the skull incision after a patient underwent deep brain stimulation surgery.

[0044] Figure 6 It is a structural block diagram of an embodiment of the scalp and deep brain electrical signal synchronous acquisition device of the present invention.

[0045] Figure 7 The signal processing flow chart of one embodiment of the device for synchronously collecting scalp and brain EEG signals of the present invention is schematically shown.

[0046] The symbols in the accompanying drawings represent the following:

[0047] 1 cap body

[0048] 2 electrodes

[0049] 3. Open windows

[0050] 4 Mandibular support strap

[0051] 5. Fixing parts

[0052] 6 Intracerebral measurement electrodes

[0053] 7 Zipper connectors DETAILED DESCRIPTION

[0054] Exemplary embodiments of the present invention will be described in more detail below with reference to the accompanying drawings. Although exemplary embodiments of the present invention are shown in the accompanying drawings, it should be understood that the present invention can be implemented in various forms and should not be limited by the embodiments described herein. Rather, these embodiments are provided to enable a more thorough understanding of the present invention and to fully convey the scope of the present invention to those skilled in the art.

[0055] definition:

[0056] In the description of the present invention, it should be noted that, unless otherwise expressly specified or limited, the terms "assembly," "disposition," and "connection" should be understood in a broad sense. For example, they may refer to fixed connection, detachable connection, or integral connection; mechanical connection or electrical connection; direct connection or indirect connection through an intermediate medium; and internal communication between two components. Those skilled in the art will understand the specific meanings of the above terms in the present invention based on the specific circumstances.

[0057] In the description of the present invention, it should be noted that the terms "upper", "lower", "front", "back", etc., indicating directions or positional relationships, are based on the directions or positional relationships shown in the accompanying drawings. They are only for the convenience of describing the present invention and simplifying the description, and do not indicate or imply that the system or element referred to must have a specific direction, be constructed and operated in a specific direction. Therefore, they cannot be understood as limiting the present invention.

[0058] Sagittal axis: The axis that is perpendicular to the vertical axis of the human body in the front-to-back direction.

[0059] Coronal axis: The axis perpendicular to the sagittal and vertical axes in the left-right direction.

[0060] It should be noted that in the present invention, when describing the EEG cap electrodes, "lead" and "electrode" have the same meaning and can sometimes be used interchangeably. However, in order to avoid ambiguity, when describing "lead", it generally refers to the layout of the EEG cap electrodes (see Figure 1 ), and when describing an "electrode" it generally refers to a component of the device of the present invention.

[0061] High-density EEG cap of the present invention

[0062] Figure 1 The figure shows the layout of the 64-lead high-density EEG of the present invention, wherein A1 and A2 are mastoid leads corresponding to the mastoid processes of the skull.

[0063] Figure 2 The figure shows an embodiment of the high-density EEG cap of the present invention, comprising a cap body 1, electrodes 2 and a chin strap 4. Figure 1 The 64-lead layout shown is arranged on the inner surface of the cap body 1. Figure 2In the illustrated embodiment, a window 3 is provided on the cap body 1, configured to expose areas corresponding to leads F1, FC1, and C1 and / or leads F2, FC2, and C2. A chin strap 4 is fixedly connected to the bottom of the cap body 1. During use, after the subject wears the high-density EEG cap, the chin strap 4 is placed against the subject's jaw to further secure the cap. The cap body 1 is also provided with a zipper connector 7 for opening or closing the window 3.

[0064] In such Figure 3 In the embodiment shown, two windows 3 are provided, which are symmetrically arranged on the left and right sides of the sagittal axis A along the cap body 1, and each exposes an area corresponding to the F1, FC1, C1 leads and / or the F2, FC2, C2 leads.

[0065] Figure 4 FIG. 1 is a partial schematic diagram of an embodiment of the high-density EEG cap of the present invention. Figure 4 As shown, the high-density EEG cap is provided with two zipper connectors 7, 7', which are used to open or cover the two windows respectively. Figure 4 The figure also shows an intracerebral EEG measurement electrode 6 extending from the incision and secured by closed zipper connectors 7, 7', which also conceal the fenestration. The intracerebral EEG measurement electrode 6 extending from the EEG cap is further secured by a securing member 5. The external intracerebral EEG measurement electrode 6 can be connected to an EEG acquisition device to collect electrical signals from deep brain nuclei.

[0066] The incision for deep brain stimulation surgery is usually fixed, such as Figure 5 As shown, the incision is located 3-4 cm lateral to the coronal suture and extends about 6-8 cm forward. The inventors have found through measurement that the surgical incision overlaps with the positions of leads F1, FC1, C1, and the right side leads F2, FC2, and C2. Therefore, in the present invention, the shape of the fenestration is not limited, as long as it only exposes the area corresponding to leads F1, FC1, C1 and / or leads F2, FC2, and C2. Figure 2-4 In the embodiment shown in , the window is rectangular, the length of the long side can generally be set to 8-10 cm, and the length of the short side can generally be set to 2-3 cm.

[0067] Scalp and brain electroencephalogram signal synchronous acquisition device and method of the present invention

[0068] Figure 6 This is a block diagram of an embodiment of the scalp and brain EEG signal synchronous acquisition device of the present invention. Figure 6As shown, the device for synchronously collecting scalp and brain EEG signals includes a high-density EEG cap, brain measurement electrodes, and a signal processing device. The electrodes of the high-density EEG cap are electrically connected to the brain measurement electrodes and the signal processing device. In the present invention, the EEG measurement electrodes are configured to be arranged in the brain to collect brain EEG signals, wherein the brain EEG signals include EEG signals from the cerebral cortex or deep nuclei.

[0069] 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 merging module; and 4) an output module. Preferably, the signal processing device may also include 5) an EEG signal amplification module and 6) an EEG signal preprocessing module.

[0070] Figure 7 A signal processing flow chart of an embodiment of the device for synchronously collecting scalp and brain EEG signals of the present invention is shown.

[0071] S1. Collect the subject's raw scalp EEG signals using a high-density EEG cap and collect intra-brain EEG signals using intra-brain measurement electrodes;

[0072] S2. The receiving module receives the raw scalp EEG signals collected by the electrodes of the high-density EEG cap and the intracerebral EEG signals collected by the intracerebral EEG measurement electrodes;

[0073] S3. The scalp signal compensation module reconstructs the signals of the F1, FC1, C1, F2, FC2, and C2 leads according to the original scalp EEG signals collected by the high-density EEG cap electrodes as the compensation signals of the F1, FC1, C1, F2, FC2, and C2 leads;

[0074] S4. The scalp signal merging module merges the original scalp EEG signal and the compensation signals of the F1, FC1, C1, F2, FC2, and C2 leads reconstructed by the scalp signal compensation module as a compensated complete scalp EEG signal output;

[0075] S5. The output module sends the compensated complete scalp EEG signal as a scalp EEG signal and an intracerebral EEG signal to an EEG analysis system for subsequent analysis.

[0076] In the present invention, the signal reconstruction in step S3 can be performed by an averaging method or by using a spherical surface method and an electroencephalographic model.

[0077] If a particularly precise signal is not required, an averaging method can be used to obtain compensation signals for leads F1, FC1, C1, F2, FC2, and C2, that is, the average value of the two or four leads surrounding each lead in leads F1, FC1, C1, F2, FC2, and C2 is used to replace the signal value of that lead. In one embodiment, the EEG signal corresponding to lead F1 can be obtained by averaging the original signals collected from the F3 and FZ electrodes; the EEG signal corresponding to lead FC1 can be obtained by averaging the original signals collected from the FC3 and FCZ electrodes; the signal corresponding to lead C1 can be obtained by averaging the original signals collected from the C3 and CZ electrodes; the EEG signal corresponding to lead F2 can be obtained by averaging the original signals collected from the F4 and FZ electrodes; the EEG signal corresponding to lead FC2 can be obtained by averaging the original signals collected from the FC4 and FCZ electrodes; and the EEG signal corresponding to lead C2 can be obtained by averaging the original signals collected from the C4 and CZ electrodes.

[0078] Since the human head is spherical, the reconstructed signal can also be completed using the spherical surface method and the electroencephalographic model. This step can be completed with the built-in correlation function tools in EEGLAB, MNE, and fieldtrip EEG work packages. The specific process can be as follows: first, extract the original scalp EEG signals collected by 56 electrodes excluding the mastoid electrodes, reconstruct the signals of 62 EEG leads based on the distribution coordinates of the 56 electrodes, and then obtain the signals corresponding to the F1, FC1, C1, F2, FC2, and C2 leads as compensation signals for the signals of the F1, FC1, C1, F2, FC2, and C2 leads.

[0079] In a preferred embodiment, in addition to obtaining the compensated complete scalp EEG signal, step S4 may also include the step of amplifying and preprocessing the EEG signal to obtain an amplified and preprocessed EEG signal, wherein the EEG signal may include a scalp EEG signal and / or an intra-brain EEG signal. Since EEG signals are weaker and have greater noise than scalp EEG signals, it is preferred to amplify and preprocess the intra-brain EEG signal. Figure 7 As shown in , the EEG signals in the brain can be amplified and preprocessed and then output to the EEG analysis system through the output module, wherein the preprocessing includes filtering, noise reduction and artifact removal.

[0080] Example

[0081] The present invention's device for synchronously collecting scalp and brain EEG signals can be used in conjunction with DBS to achieve synchronized acquisition of scalp and brain EEG signals. For example, synchronous analysis of brain signals recorded by DBS electrodes and scalp EEG signals can be used to provide dynamic feedback on the condition of patients with movement disorders and epilepsy, or to evaluate the efficacy of DBS stimulation.

[0082] The following briefly describes the method of using the device for synchronously collecting scalp and brain EEG signals of the present invention in DBS surgery with reference to embodiments.

[0083] Preparation and Surgery: The subject (e.g., Parkinson's disease patient) undergoes an imaging examination (e.g., CT scan, magnetic resonance imaging, etc.). Based on the imaging findings, the target site requiring surgery (e.g., the subthalamic nucleus) is identified. Electrode implantation is then performed, and a DBS electrode 6 is placed at the target site. After the electrode is placed at the subject's target site, the optimal implantation location is determined based on the intraoperative electrophysiological recordings and the improvement in efficacy during temporary electrical stimulation. The DBS electrode 6 is then removed from the incision, and the electrode wiring and externalization phase begins.

[0084] No stimulation period for plug-ins:

[0085] The tester wears the high-density EEG cap of the present invention and makes an incision on the top of the skull (see Figure 5 ) is passed through the window of the high-density EEG cap of the present invention, and a zipper is zipped up to fix one or more DBS electrodes on one or both sides of the window, and the extension wire of the DBS electrode 6 is fixed to the cap body 1 using the fixing component 5.

[0086] The electrophysiological signals (including, but not limited to, brain neuron electrical signals, local field potential signals, deep brain impedance signals, etc.) generated at all contacts of the target point in the brain are collected in real time, and the scalp EEG signals are collected in real time. When there is no need to accurately restore the original signal (such as visual observation of EEG waveforms in clinical practice), preliminary signal reconstruction can be performed by averaging. When the original signal needs to be accurately restored (such as analyzing the functional connection between deep brain electrophysiological signals and scalp brain electrophysiological signals), signal reconstruction is completed by spherical surface method and brain positive electrical model. The reconstructed brain EEG signal can be amplified and preprocessed and then output to the EEG analysis system through the output module, wherein the preprocessing includes filtering, noise reduction and artifact removal. At the same time, the scalp EEG signal is functionally connected with the deep brain electrical signal of the target point (such as coherence, Coherence, C). In summary, the EEG changes of the test subject (for example, Parkinson's patients) can be dynamically displayed, which is clinically meaningful for symptom monitoring and treatment.

[0087] Cheating stimulation period:

[0088] Before DBS stimulation, the tester wore the high-density EEG cap of the present invention and made an incision on the top of the skull (see Figure 5 ) is passed through the window of the high-density EEG cap of the present invention, and a zipper is zipped up to fix one or more DBS electrodes on one or both sides of the window, and the extension wire of the DBS electrode 6 is fixed to the cap body 1 using the fixing component 5.

[0089] A stimulation signal is applied to the DBS electrode to stimulate the target point (e.g., 130Hz, 60μs, 1.5V). After removing the stimulation artifacts through hardware and algorithms, the real-time acquisition and analysis process is the same as the plug-in without stimulation period. It can dynamically display the EEG changes of the test subject (e.g., Parkinson's disease patients) under different stimulation modes, which has clinical significance for symptom monitoring and treatment.

[0090] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some of the technical features therein. However, these modifications or replacements do not deviate the essence of the corresponding technical solutions from the spirit and scope of the technical solutions of the various embodiments of the present invention.

Claims

1. A device for synchronously collecting scalp and brain EEG signals, characterized in that: It includes a high-density EEG cap, one or more EEG measurement electrodes and a signal processing device. The high-density EEG cap includes a cap body, electrodes, and a fixing strap. The electrodes are arranged on the inner surface of the cap body according to the high-density EEG 64-lead layout. A window is provided on the cap body. The window is configured to expose only the areas corresponding to the F1, FC1, C1 leads and / or the F2, FC2, C2 leads of the high-density EEG 64-lead. The fixing strap is fixedly connected to the bottom of the cap body. The high-density EEG cap also includes a shielding component, which is used to open or shield the window. Wherein, the electrodes of the high-density EEG cap and the intracerebral EEG measurement electrodes are electrically connected to the signal processing device; Wherein, the signal processing device includes: a receiving module configured to receive raw scalp EEG signals collected by electrodes of the high-density EEG cap; A scalp signal compensation module is configured to obtain the original scalp EEG signals received from the receiving module, and reconstruct the signals of the F1, FC1, C1, F2, FC2, and C2 leads according to the original scalp EEG signals collected by the electrodes of the high-density EEG cap as compensation signals for the F1, FC1, C1, F2, FC2, and C2 leads. a scalp signal merging module configured to merge the original scalp EEG signal and the compensated signal reconstructed by the scalp signal compensation module into a compensated complete scalp EEG signal and output it; and An output module is configured to receive the compensated complete scalp EEG signal and the intra-brain EEG signal output by the signal merging module, and send them together to an EEG analysis system.

2. The device for synchronously collecting scalp and brain EEG signals according to claim 1, characterized in that: The scalp signal compensation module reconstructs the signals of the F1, FC1, C1, F2, FC2, and C2 leads by taking the following steps: First, the original scalp EEG signals collected by 56 electrodes excluding the mastoid electrodes are extracted, and the signals of 62 EEG leads are reconstructed according to the distribution coordinates of the 56 electrodes. Then, the signals corresponding to the F1, FC1, C1, F2, FC2, and C2 leads are obtained as compensation signals for the F1, FC1, C1, F2, FC2, and C2 leads.

3. The device for synchronously collecting scalp and brain EEG signals according to claim 1, characterized in that: The scalp signal compensation module reconstructs the signals of the F1, FC1, C1, F2, FC2, and C2 leads as follows: The average value of the signals of two or four leads around each of the F1, FC1, C1, F2, FC2, and C2 leads is used as the compensation signal of the F1, FC1, C1, F2, FC2, and C2 leads.

4. The device for synchronously collecting scalp and brain EEG signals according to claim 1, characterized in that: The signal processing device further includes: EEG signal amplification module; and EEG signal preprocessing module, The EEG signal amplification module and the EEG signal preprocessing module are configured to amplify and preprocess the EEG signal respectively to obtain an amplified and preprocessed EEG signal.

5. The device for synchronously collecting scalp and brain EEG signals according to claim 4, characterized in that: The EEG signal is an intra-brain EEG signal.

6. A method for synchronously collecting scalp and brain EEG signals, comprising the following steps: collecting raw scalp EEG signals through electrodes of a high-density EEG cap of the device for synchronously collecting EEG signals from the scalp and the brain according to any one of claims 1 to 5, and collecting intra-brain EEG signals through intra-brain EEG measurement electrodes of the device for synchronously collecting EEG signals from the scalp and the brain according to any one of claims 1 to 5; Reconstructing the signals of the F1, FC1, C1, F2, FC2, and C2 leads according to the original scalp EEG signals collected by the electrodes of the high-density EEG cap as compensation signals of the F1, FC1, C1, F2, FC2, and C2 leads; The original scalp EEG signal and the reconstructed compensation signal are combined to output as a compensated complete scalp EEG signal, The compensated complete scalp EEG signal is sent as a scalp EEG signal together with the intra-brain EEG signal to an EEG analysis system.

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