Epilepsy monitoring electrical stimulation system and method

Abstract

The application relates to an epilepsy monitoring and electric stimulation system and method, wherein the epilepsy monitoring and electric stimulation system comprises a multi-modal signal acquisition module, an electric stimulation module, a control module and a set of ring-shaped common electrodes distributed on a human head; in the multi-modal signal acquisition module, an electric impedance acquisition unit obtains impedance characteristics when the common electrodes are in a first acquisition state, and an electroencephalogram acquisition unit obtains electroencephalogram characteristics when the common electrodes are in a second acquisition state; the control module is used for evaluating an epilepsy pre-onset time, a lesion site and a brain edema degree based on the impedance characteristics, combining the two characteristics to evaluate an epilepsy grade, then setting electric stimulation parameters according to the brain edema degree and the epilepsy grade, selecting an electric stimulation electrode pair according to the lesion site, and controlling the electric stimulation module to apply electric stimulation with the parameters to the electrode pair before the epilepsy pre-onset time, and adjusting the parameters according to real-time signals in the stimulation. Through the application, the problems of low positioning accuracy and inability to intervene in time before epilepsy onset in the related art are solved.

Description

Technical Field

[0001] This application relates to the field of neuroscience technology, and in particular to an epilepsy monitoring electrical stimulation system and method. Background Technology

[0002] Epileptic seizures are characterized by their suddenness, brevity, and unpredictability. Severe status epilepticus can easily lead to abnormal brain metabolism, increased cerebral blood flow, and disruption of the blood-brain barrier, thereby inducing or exacerbating cerebral edema and causing damage to brain function. Therefore, real-time monitoring and precise intervention of epilepsy-related brain states are key needs in this field. Among related technologies, conventional electroencephalography (EEG) for short-term monitoring suffers from signal attenuation after passing through the skull scalp, resulting in low localization accuracy and the inability to intervene in a timely manner before a seizure.

[0003] Currently, no effective solution has been proposed to address the issues of low positioning accuracy and inability to intervene in time before an epileptic seizure. Summary of the Invention

[0004] This application provides an epilepsy monitoring electrical stimulation system and method to at least solve the problems of low positioning accuracy and inability to intervene in a timely manner before an epileptic seizure in related technologies.

[0005] In a first aspect, embodiments of this application provide an epilepsy monitoring electrical stimulation system, the system comprising: a multimodal signal acquisition module, an electrical stimulation module, a control module, and a set of shared electrodes distributed in a ring on the human head;

[0006] The multimodal signal acquisition module includes an electrical impedance acquisition unit and an electroencephalogram (EEG) acquisition unit;

[0007] The impedance acquisition unit is used to acquire the real-time impedance characteristics transmitted by the common electrode in the first acquisition state when the working state of the common electrode is configured in the first acquisition state.

[0008] The EEG acquisition unit is used to acquire real-time EEG features transmitted by the common electrode in the second acquisition state when the working state of the common electrode is configured in the second acquisition state.

[0009] The control module is used to assess the epileptic pre-seizure time, lesion location, and degree of cerebral edema based on the real-time impedance characteristics; and to assess the epilepsy grade based on the real-time EEG characteristics and the real-time impedance characteristics.

[0010] The control module is also used to obtain electrical stimulation signal parameters based on the degree of cerebral edema and the epilepsy level;

[0011] The control module is further configured to determine an electrical stimulation electrode pair from a set of shared electrodes based on the lesion site; and, before the epileptic pre-seizure time, control the electrical stimulation module to apply electrical stimulation to the electrical stimulation electrode pair in accordance with the electrical stimulation signal parameters, and adjust the electrical stimulation signal parameters based on the real-time impedance characteristics and the real-time EEG characteristics during the application of electrical stimulation.

[0012] In some embodiments, when the stimulation mode of the electrical stimulation module is configured as a transcranial alternating current stimulation mode, the control module is further configured to select, based on the lesion site, an electrode pair that can pass through the lesion site from the common electrodes as the electrical stimulation electrode pair.

[0013] In some embodiments, when the stimulation mode of the electrical stimulation module is configured as a transcranial direct current stimulation mode, the control module is further configured to select, based on the lesion site, an electrode closer to the lesion site as a cathode electrode and an electrode farther from the lesion site as an anode electrode among the common electrodes, and use the electrode pair consisting of the cathode electrode and the anode electrode as the electrical stimulation electrode pair, wherein the line connecting the cathode electrode and the anode electrode must pass through the brain region corresponding to the lesion site.

[0014] In some embodiments, the real-time EEG characteristics include discharge frequency, discharge amplitude, discharge distribution, and diffusion velocity; the real-time impedance characteristics include impedance change rate and impedance change spatial range.

[0015] In some embodiments, the system further includes a gating switch; the control module is also configured to switch the common electrode to a stimulating electrode via the gating switch before the epileptic pre-seizure time and when the impedance change rate drops to a preset range, and to control the electrical stimulation module to apply electrical stimulation to the electrical stimulation electrode pair in accordance with the electrical stimulation signal parameters.

[0016] In some embodiments, the control module is also used to assess the epilepsy grade based on the discharge frequency, the discharge amplitude, and the impedance change rate.

[0017] In some embodiments, the control module is also used to assess the epilepsy level based on the discharge distribution, the diffusion rate, and the spatial range of the impedance change.

[0018] In some embodiments, when the stimulation mode of the electrical stimulation module is configured as a transcranial direct current stimulation mode, the control module is further configured to increase the current intensity of the electrical stimulation signal parameter and / or prolong the stimulation time of the electrical stimulation signal parameter when the discharge frequency increases and / or the discharge amplitude increases.

[0019] The control module is also used to increase the stimulation frequency of the electrical stimulation signal parameters when the impedance change rate increases.

[0020] In some embodiments, when the stimulation mode of the electrical stimulation module is configured as a transcranial alternating current stimulation mode, the control module is further configured to adjust the stimulation frequency of the electrical stimulation signal parameters when a specific abnormal rhythm appears in the real-time EEG characteristics.

[0021] Secondly, embodiments of this application provide an epilepsy monitoring electrical stimulation method, the method comprising:

[0022] Real-time impedance characteristics and real-time electroencephalogram (EEG) characteristics are obtained during the pre-seizure period of epilepsy; the real-time impedance characteristics are obtained by a shared electrode in a first acquisition state, and the real-time EEG characteristics are obtained by a shared electrode in a second acquisition state; wherein, a set of shared electrodes is distributed in a ring on the human head.

[0023] Based on the real-time impedance characteristics, the epileptic pre-seizure time, lesion location, and degree of cerebral edema are assessed; based on the real-time EEG characteristics and the real-time impedance characteristics, the epilepsy grade is assessed.

[0024] Based on the degree of cerebral edema and the epilepsy grade, electrical stimulation signal parameters are obtained; based on the lesion location, electrical stimulation electrode pairs are determined from the shared electrodes;

[0025] Prior to the epileptic seizure time, electrical stimulation conforming to the electrical stimulation signal parameters is applied to the electrical stimulation electrode pair, and the electrical stimulation signal parameters are adjusted based on the real-time impedance characteristics and the real-time EEG characteristics.

[0026] Compared to related technologies, the epilepsy monitoring electrical stimulation system and method provided in this application include: a multimodal signal acquisition module, an electrical stimulation module, a control module, and a set of shared electrodes arranged in a ring on the human head; the multimodal signal acquisition module includes an impedance acquisition unit and an electroencephalogram (EEG) acquisition unit; the impedance acquisition unit is used to acquire real-time impedance characteristics transmitted by the shared electrodes in the first acquisition state when the working state of the shared electrodes is configured in a first acquisition state; the EEG acquisition unit is used to acquire real-time EEG characteristics transmitted by the shared electrodes in the second acquisition state when the working state of the shared electrodes is configured in a second acquisition state; the control module... The module is used to assess the epileptic pre-seizure time, lesion location, and degree of cerebral edema based on the real-time impedance characteristics; to assess the epilepsy grade based on the real-time EEG characteristics and the real-time impedance characteristics; the control module is also used to obtain electrical stimulation signal parameters based on the degree of cerebral edema and the epilepsy grade; the control module is also used to determine an electrical stimulation electrode pair from a set of shared electrodes based on the lesion location; and, before the epileptic pre-seizure time, to control the electrical stimulation module to apply electrical stimulation conforming to the electrical stimulation signal parameters to the electrical stimulation electrode pair, and to adjust the electrical stimulation signal parameters based on the real-time impedance characteristics and the real-time EEG characteristics during the application of electrical stimulation. This solves the problems of low positioning accuracy and inability to intervene in a timely manner before an epileptic seizure in related technologies.

[0027] Details of one or more embodiments of this application are set forth in the following drawings and description to make other features, objects and advantages of this application more readily apparent. Attached Figure Description

[0028] The accompanying drawings, which are included to provide a further understanding of this application and form part of this application, illustrate exemplary embodiments of this application and are used to explain this application, but do not constitute an undue limitation of this application. In the drawings:

[0029] Figure 1 This is a hardware structure block diagram of a terminal of an epilepsy monitoring electrical stimulation system according to an embodiment of this application;

[0030] Figure 2 This is a structural block diagram of an epilepsy monitoring electrical stimulation system according to an embodiment of this application;

[0031] Figure 3 This is a schematic diagram of electrode pair selection when the lesion is located on the left or right side and the stimulation mode is configured as transcranial alternating current stimulation mode, according to the embodiments of this application.

[0032] Figure 4This is a schematic diagram of electrode pair selection when the lesion is located on the anterior or posterior side and the stimulation mode is configured as transcranial alternating current stimulation mode, according to the embodiments of this application.

[0033] Figure 5 This is a schematic diagram of electrode pair selection when the lesion is located on the left or right side and the stimulation mode is configured as transcranial direct current stimulation mode, according to the embodiments of this application.

[0034] Figure 6 This is a schematic diagram of electrode pair selection when the lesion is located on the anterior or posterior side and the stimulation mode is configured as transcranial direct current stimulation mode, according to the embodiments of this application.

[0035] Figure 7 This is a flowchart of an epilepsy monitoring electrical stimulation method according to an embodiment of this application;

[0036] Figure 8 This is a functional flowchart of an epilepsy monitoring electrical stimulation method according to an embodiment of this application;

[0037] Figure 9 This is an imaging schematic diagram of an electrical impedance imaging system according to an embodiment of this application. Detailed Implementation

[0038] To make the objectives, technical solutions, and advantages of this application clearer, the application is described and illustrated below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and not intended to limit the application. All other embodiments obtained by those skilled in the art based on the embodiments provided in this application without inventive effort are within the scope of protection of this application. Furthermore, it is understood that although the efforts made in such a development process may be complex and lengthy, for those skilled in the art related to the content disclosed in this application, modifications to design, manufacturing, or production based on the technical content disclosed in this application are merely conventional technical means and should not be construed as insufficient disclosure of the content of this application.

[0039] In this application, the reference to "embodiment" means that a specific feature, structure, or characteristic described in connection with an embodiment may be included in at least one embodiment of this application. The appearance of this phrase in various places in the specification does not necessarily refer to the same embodiment, nor is it a separate or alternative embodiment that is mutually exclusive with other embodiments. It will be explicitly and implicitly understood by those skilled in the art that the embodiments described in this application may be combined with other embodiments without conflict.

[0040] Unless otherwise defined, the technical or scientific terms used in this application shall have the ordinary meaning understood by one of ordinary skill in the art to which this application pertains. The terms “a,” “an,” “an,” “the,” and similar words used in this application do not indicate quantity limitation and may indicate singular or plural. The terms “comprising,” “including,” “having,” and any variations thereof used in this application are intended to cover non-exclusive inclusion; for example, a process, method, system, product, or device that includes a series of steps or modules (units) is not limited to the listed steps or units, but may also include steps or units not listed, or may include other steps or units inherent to these processes, methods, products, or devices. The terms “connected,” “linked,” “coupled,” and similar words used in this application are not limited to physical or mechanical connections, but may include electrical connections, whether direct or indirect. “Multiple” used in this application means two or more. “And / or” describes the relationship between related objects, indicating that three relationships may exist; for example, “A and / or B” can represent: A alone, A and B simultaneously, and B alone. The terms “first,” “second,” “third,” etc., used in this application are merely to distinguish similar objects and do not represent a specific ordering of the objects.

[0041] The method embodiments provided in this example can be executed on a terminal, computer, or similar computing device. Taking running on a terminal as an example, Figure 1 This is a hardware structure block diagram of a terminal of an epilepsy monitoring electrical stimulation system according to an embodiment of this application. Figure 1 As shown, a terminal may include one or more ( Figure 1 Only one is shown in the diagram. A processor 102 (which may include, but is not limited to, a microprocessor MCU or a programmable logic device FPGA, etc.) and a memory 104 for storing data are also shown. Optionally, the terminal may further include a transmission device 106 for communication functions and an input / output device 108. Those skilled in the art will understand that... Figure 1 The structure shown is for illustrative purposes only and does not limit the structure of the terminal described above. For example, the terminal may also include components that are more... Figure 1 The more or fewer components shown, or having the same Figure 1 The different configurations shown.

[0042] The memory 104 can be used to store computer programs, such as application software programs and modules, like the computer program corresponding to the epilepsy monitoring electrical stimulation system in this embodiment. The processor 102 executes various functional applications and data processing by running the computer program stored in the memory 104, thus implementing the above-described method. The memory 104 may include high-speed random access memory and may also include non-volatile memory, such as one or more magnetic storage devices, flash memory, or other non-volatile solid-state memory. In some instances, the memory 104 may further include memory remotely located relative to the processor 102, and these remote memories can be connected to the terminal via a network. Examples of such networks include, but are not limited to, the Internet, corporate intranets, local area networks, mobile communication networks, and combinations thereof.

[0043] The transmission device 106 is used to receive or send data via a network. Specific examples of the network described above may include a wireless network provided by the terminal's communication provider. In one example, the transmission device 106 includes a Network Interface Controller (NIC), which can connect to other network devices via a base station to communicate with the Internet. In another example, the transmission device 106 may be a Radio Frequency (RF) module used for wireless communication with the Internet.

[0044] This embodiment provides an epilepsy monitoring electrical stimulation system. Figure 2 This is a structural block diagram of an epilepsy monitoring electrical stimulation system according to an embodiment of this application, such as... Figure 2 As shown, the system includes: a multimodal signal acquisition module 21, an electrical stimulation module 24, a control module 25, and a set of common electrodes 26 distributed in a ring on the human head;

[0045] The multimodal signal acquisition module 21 includes an electrical impedance acquisition unit 22 and an electroencephalogram (EEG) acquisition unit 23;

[0046] The impedance acquisition unit 22 is used to acquire the real-time impedance characteristics transmitted by the common electrode 26 in the first acquisition state when the working state of the common electrode 26 is configured in the first acquisition state.

[0047] The EEG acquisition unit 23 is used to acquire real-time EEG features transmitted by the common electrode 26 in the second acquisition state when the working state of the common electrode 26 is configured in the second acquisition state.

[0048] Control module 25 is used to assess the epileptic pre-seizure time, lesion location, and degree of cerebral edema based on real-time impedance characteristics; and to assess the epilepsy grade based on real-time EEG characteristics and the real-time impedance characteristics.

[0049] The control module 25 is also used to obtain electrical stimulation signal parameters based on the degree of cerebral edema and the epilepsy grade;

[0050] The control module 25 is also configured to determine an electrical stimulation electrode pair from a set of shared electrodes 26 based on the lesion site; and, before the epileptic pre-seizure time, control the electrical stimulation module 24 to apply electrical stimulation to the electrical stimulation electrode pair in accordance with the electrical stimulation signal parameters, and adjust the electrical stimulation signal parameters based on real-time impedance characteristics and real-time EEG characteristics during the application of electrical stimulation.

[0051] Specifically, the core components of the system include a multimodal signal acquisition module 21, an electrical stimulation module 24, a control module 25, and a set of shared electrodes 26 arranged in a ring around the human head. The shared electrodes 26 are the key carriers for achieving both signal acquisition and electrical stimulation functions. For ease of description, the following mainly uses a scheme with 16 electrodes as an example, but other numbers can be set according to the actual application scenario. The specific distribution strictly follows the spatial coverage requirements of clinical monitoring: electrode 1 is fixed in the temporal region above the right ear, electrode 5 is fixed in the forehead region along the midline of the eyebrows, electrode 9 is fixed in the temporal region above the left ear, electrode 13 is fixed in the occipital region below the occipital protuberance, and the remaining 12 electrodes are spaced at equal angles between the four reference electrodes to form a complete ring array. This ensures uniform acquisition of physiological signals from different regions of the whole brain, while providing sufficient electrode selection space for subsequent precise electrical stimulation.

[0052] The multimodal signal acquisition module 21, serving as the system's sensing core, is further subdivided into an impedance acquisition unit 22 and an electroencephalogram (EEG) acquisition unit 23. These two units are linked to a common electrode via a selector switch to achieve time-division or synchronous acquisition of different signals. The core function of the impedance acquisition unit 22 is to inject a weak current within a safe range into the brain through the electrode when the common electrode 26 is configured in the first acquisition state (i.e., EIT signal acquisition mode). Simultaneously, it measures the surface voltage signals fed back by other electrodes in real time. Based on the correspondence between voltage and current, it calculates and extracts real-time impedance characteristics. These characteristics specifically include the impedance change rate (the decrease in impedance in the lesion area compared to the normal state) and the spatial range of impedance change (the coverage area of ​​the low-impedance region in the entire brain). This provides core data support for subsequent assessments of epilepsy pre-seizure time, lesion location, and the degree of cerebral edema. The EEG acquisition unit 23 focuses on capturing the electrical activity signals of neurons in the brain when the shared electrode is configured in the second acquisition state (i.e., EEG signal acquisition mode), and extracting real-time EEG features with clinical diagnostic value, such as the frequency of interictal epileptiform discharges (the number of spikes and sharp waves per unit time), discharge amplitude (the voltage level of abnormal electrical activity), discharge distribution (focal, multifocal, or diffuse), and diffusion rate (the rate at which abnormal electrical activity spreads from the lesion to the surrounding brain tissue). These features, together with the impedance features, constitute the core basis for epilepsy grade assessment.

[0053] The control module 25 is the decision-making and control center of the system, undertaking multiple functions such as signal analysis, evaluation and judgment, parameter generation, and dynamic adjustment. In the evaluation phase, the control module 25 first makes a preliminary judgment based on the real-time impedance characteristics acquired by the impedance acquisition unit 22: on the one hand, it utilizes the physiological law that the impedance of the lesion site decreases due to congestion before an epileptic seizure (according to experimental data, this decrease occurs approximately 20 seconds earlier than the onset of EEG abnormality), combined with historical monitoring data, to estimate the epileptic seizure time; on the other hand, by analyzing the spatial distribution of impedance changes, it locates the lesion site corresponding to low impedance (represented by the red area in EIT imaging), and simultaneously assesses the degree of cerebral edema based on the magnitude of the impedance decrease; the more significant the impedance decrease, the more severe the extracellular fluid increase caused by cerebral edema. Based on this, the control module 25 further integrates real-time EEG characteristics and real-time impedance characteristics, comprehensively assessing the epilepsy level from two dimensions: the degree of electrical activity abnormality (discharge frequency, amplitude) and the degree of physiological disorder (impedance change rate, range of change).

[0054] In the intervention decision-making stage, the control module 25 generates a targeted electrical stimulation plan based on the above assessment results: First, it determines the electrical stimulation signal parameters by combining the degree of cerebral edema and the epilepsy level. If the cerebral edema is severe and the epilepsy level is high, the current intensity of the electrical stimulation will be appropriately increased or the stimulation time will be extended. Second, it selects a suitable electrical stimulation electrode pair from the ring-shaped common electrode 26 according to the lesion location.

[0055] More importantly, the control module 25 also has dynamic adjustment capabilities: before the epileptic seizure time (usually a 20-second window after impedance decrease and before the appearance of EEG abnormalities), the control gating switch switches the shared electrode from the acquisition state to the stimulation state, and at the same time instructs the electrical stimulation module 24 to apply electrical stimulation that meets the parameter requirements to the selected electrode pair; during the stimulation process, the control module 25 continuously receives real-time signals from the impedance acquisition unit 22 and the EEG acquisition unit 23. If an increase in discharge frequency or amplitude is detected (indicating increased epileptic activity), the current intensity of the electrical stimulation is increased or the stimulation time is extended in a timely manner; if an increase in the rate of impedance change is observed (indicating worsening cerebral edema), the stimulation frequency is increased; if the EEG rhythm is monitored to return to normal and the impedance returns to the normal range, the stimulation intensity is gradually reduced or stimulation is stopped. Through this closed-loop mechanism of "monitoring-analysis-adjustment", the side effects of overstimulation are minimized while ensuring the therapeutic effect.

[0056] In the above embodiments, the coordinated use of the ring-shaped shared electrode 26 and the multimodal signal acquisition module 21 achieves efficient acquisition and functional multiplexing of impedance signals and EEG signals in epilepsy monitoring, solving the problems of single signal and hardware redundancy in traditional monitoring equipment. The control module 25 identifies the epileptic pre-seizure time in advance based on real-time impedance characteristics (EIT is extremely sensitive to changes in cerebral blood volume, and the conductivity of blood flow is much higher than that of brain tissue. Before an epileptic seizure, an increase in cerebral blood flow in the lesion area can often be observed. This is because the activity of abnormally discharging neurons is intensified, oxygen consumption and glucose metabolism rate increase, and the brain automatically increases blood supply to meet energy needs through the neurovascular coupling mechanism. According to experimental data, impedance decreases about 20 seconds earlier than EEG abnormalities), accurately locates the lesion site, and assesses the brain. The degree of edema, combined with bimodal features, comprehensively assesses the epilepsy level, overcoming the limitations of traditional EEG's low spatial resolution and inability to intuitively present physiological changes in the brain (EIT's data acquisition rate can reach tens of frames per second, sufficient to track rapid physiological dynamics before an epileptic seizure). Simultaneously, based on the assessment results, appropriate electrical stimulation signal parameters are generated and electrode pairs are precisely selected. Electrical stimulation is initiated before the expected seizure time, and parameters are dynamically adjusted through real-time signal feedback, achieving a shift from passive monitoring to active pre-intervention. This effectively suppresses the severity of epileptic seizures, shortens seizure duration, and visualizes the lesions, edema areas, and dynamic changes throughout the entire epileptic cycle, providing precise data support for clinical diagnosis and treatment, and significantly improving the timeliness, accuracy, and safety of epilepsy monitoring and treatment.

[0057] In some embodiments, when the stimulation mode of the electrical stimulation module is configured as a transcranial alternating current stimulation mode, the control module is also used to select, based on the lesion site, an electrode pair that can pass through the lesion site from the common electrodes as the electrical stimulation electrode pair.

[0058] Specifically, when the stimulation mode of the electrical stimulation module is configured as transcranial alternating current stimulation (tACS), the control module further combines the real-time impedance characteristics obtained by the impedance acquisition unit through the shared electrodes to accurately locate the specific location of the epileptic focus in the brain (such as the right temporal region, posterior occipital region, etc.). Based on the fixed positions of the 16 ring-shaped shared electrodes, electrode pairs whose electrode connections can directly pass through the brain region corresponding to the lesion site are selected as electrical stimulation electrode pairs. Figure 3 As shown, if EIT imaging shows the lesion is located on the right side (corresponding to the coverage area of ​​electrodes 0, 1, 2, 3, 4, 12, 13, 14, 15), the control module will select electrode pairs from the above electrodes, such as electrodes 1 and 12, or electrodes 4 and 14, whose lines can pass through the right-side lesion. If EIT imaging shows the lesion is located on the left side (corresponding to the coverage area of ​​electrodes 4, 5, 6, 7, 8, 9, 10, 11, 12), the control module will select electrode pairs from the above electrodes, such as electrodes 7 and 12, or electrodes 4 and 10, whose lines can pass through the left-side lesion. Figure 4 As shown, if EIT imaging shows the lesion is located on the anterior side (corresponding to the coverage area of ​​electrodes 0, 1, 2, 3, 5, 6, 7, 8), the control module will select electrode pairs such as electrodes 3 and 8, or electrodes 1 and 6, whose lines can pass through the anterior lesion. If EIT imaging shows the lesion is located on the posterior side (corresponding to the coverage area of ​​electrodes 8, 9, 10, 11, 12, 13, 14, 15, 0), the control module will select electrode pairs such as electrodes 9 and 14, or electrodes 10 and 15, whose lines can pass through the posterior lesion. This ensures that the weak AC power applied in tACS mode, which is adapted to the abnormal brain rhythm frequency, is accurately applied to the lesion area. Through rhythm entrainment or phase interference mechanisms, it effectively regulates abnormal brain electrical activity, maximizes the inhibitory effect of electrical stimulation on epileptic seizures, and avoids unnecessary stimulation of normal brain tissue around the lesion.

[0059] In the above embodiments, by using a shared circular electrode distribution and EIT imaging to locate the lesion area, the weak AC energy in the transcranial alternating current stimulation (tACS) mode is ensured to be precisely applied to the lesion, avoiding stimulation of normal brain tissue. At the same time, the electrode pairs passing through the lesion allow the stimulation signal to directly cover the abnormally discharging neuronal area, more efficiently regulating brain electrical activity through rhythm entrainment (pulling abnormal brain electrical rhythms back to normal) or phase interference (desynchronizing abnormal rhythms) mechanisms, maximizing the inhibitory effect of electrical stimulation on epileptic seizures, further improving the precision and effectiveness of electrical stimulation intervention, and reducing unnecessary stimulation side effects.

[0060] In some embodiments, when the stimulation mode of the electrical stimulation module is configured as a transcranial direct current stimulation mode, the control module is further configured to select, based on the lesion site, an electrode closer to the lesion site as a cathode electrode and an electrode farther from the lesion site as an anode electrode among the common electrodes, and use the electrode pair consisting of the cathode electrode and the anode electrode as an electrical stimulation electrode pair, wherein the line connecting the cathode electrode and the anode electrode must pass through the brain region corresponding to the lesion site.

[0061] Specifically, when the stimulation mode of the electrical stimulation module is configured as transcranial direct current stimulation (tDCS), the control module first locates the specific brain region of the epileptic focus (such as the left temporal region, anterior frontal region, etc., represented by low-impedance red areas in the imaging) based on the real-time impedance characteristics obtained by the impedance acquisition unit through the shared electrode, combined with EIT dynamic imaging technology. Then, based on the corresponding position of the lesion site within the ring coverage area of ​​the shared electrode, the electrode closest to the lesion site is precisely selected from 16 shared electrodes as the cathode electrode (based on the core anti-epileptic mechanism of tDCS cathode inhibiting neuronal excitability, ensuring that the cathode can directly act on the lesion to reduce abnormal discharge activity). At the same time, the electrode far from the lesion site and not on the lesion diffusion path is selected as the anode electrode (to avoid the anode's effect of increasing neuronal excitability from adversely affecting the lesion). The selected cathode electrode and anode electrode form an electrical stimulation electrode pair, and it is strictly ensured that the connection of this electrode pair passes through the brain region corresponding to the lesion site. Figure 5 As shown, if EIT imaging shows the lesion is located on the right side (corresponding to the coverage area of ​​electrodes 0, 1, 2, 4, 6, 8, 10, 12, 14, 15), the control module will select electrode 15 (closer to the right lesion) as the cathode and electrode 6 (away from the right lesion) as the anode, ensuring that the line connecting electrodes 15 and 6 passes through the right lesion; if EIT imaging shows the lesion is located on the left side (corresponding to the coverage area of ​​electrodes 0, 2, 4, 6, 7, 8, 9, 10, 12, 14), the control module will select electrode 7 (closer to the left lesion) as the cathode and electrode 14 (away from the left lesion) as the anode, ensuring that the line connecting electrodes 7 and 14 passes through the left lesion; Figure 6As shown, if EIT imaging shows the lesion is located on the anterior side (corresponding to the coverage area of ​​electrodes 0, 2, 3, 4, 5, 6, 8, 10, 12, 14), the control module will select electrode 4 (closer to the anterior lesion) as the cathode and electrode 12 (far from the anterior lesion) as the anode, ensuring that the line connecting electrodes 4 and 12 passes through the anterior lesion. If EIT imaging shows the lesion is located on the posterior side (corresponding to the coverage area of ​​electrodes 0, 2, 4, 6, 8, 10, 11, 12, 13, 14), the control module will select electrode 13 (closer to the posterior lesion) as the cathode and electrode 6 (far from the posterior lesion) as the anode, ensuring that the line connecting electrodes 13 and 6 passes through the left lesion. This allows the constant direct current in tDCS mode to be precisely applied to the lesion area. Through the synergistic effect of the cathode inhibiting the excitability of the lesion and the anode not interfering with the lesion, the inhibitory effect of transcranial direct current stimulation on epileptic seizures is maximized, while reducing stimulation of surrounding normal brain tissue.

[0062] In the above embodiments, on the one hand, through the core mechanism of tDCS—"cathode reduces neuronal excitability, anode increases neuronal excitability"—the cathode is precisely placed near the lesion, which can directly inhibit the activity of abnormally discharging neurons in the lesion area through hyperpolarized cell membranes. At the same time, selecting an anode far from the lesion can avoid its excitatory effect from interfering with the lesion or causing abnormal activity in the surrounding brain tissue, thus ensuring the targeted nature of the anti-epileptic effect from a mechanistic perspective. On the other hand, strictly requiring the connection between the cathode and anode to pass through the brain region corresponding to the lesion can ensure that the electric field formed by the constant direct current in tDCS mode can accurately cover the core area of ​​the lesion, maximizing the efficiency of the current in regulating the excitability of neurons in the lesion, reducing energy loss and side effects caused by the current spreading to unrelated brain regions. At the same time, combined with the fixed distribution of 16 ring-shaped shared electrodes, the accuracy of electrode selection is further improved, ultimately achieving efficient and targeted inhibition of epileptic lesions, which not only enhances the therapeutic effect of tDCS stimulation but also reduces the impact on normal brain tissue.

[0063] In some embodiments, real-time EEG characteristics include discharge frequency, discharge amplitude, discharge distribution, and diffusion velocity; real-time impedance characteristics include impedance change rate and impedance change spatial range.

[0064] Specifically, real-time EEG characteristics encompass discharge frequency, discharge amplitude, discharge distribution, and diffusion velocity, each corresponding to different dimensions of abnormal brain activity. Discharge frequency refers to the number of epileptiform discharges (such as spikes and sharp waves) per unit time, directly reflecting the instability of cortical excitability; discharge amplitude refers to the voltage level of abnormal electrical activity, its magnitude being positively correlated with the intensity of abnormal neuronal synchronization; discharge distribution defines the spatial extent of abnormal discharges, distinguishing between focal (limited to a single brain region), multifocal (involving multiple independent brain regions), or diffuse (covering the entire brain) discharges, serving as a key basis for determining the type of epileptic seizure; diffusion velocity reflects the rate at which abnormal electrical activity spreads from the lesion area to surrounding brain tissue, providing early warning of the risk of seizure spread; and real-time impedance... The features focus on the dynamic changes in the brain's physiological state, specifically including the rate of change of impedance and the spatial range of impedance changes. The rate of change of impedance refers to the decrease in impedance value of the lesion area compared to the normal baseline (impedance decreases due to lesion congestion before an epileptic seizure and cerebral edema after an epileptic seizure). The more significant the decrease, the more severe the blood flow metabolic disorder or cerebral edema. The spatial range of impedance changes is presented through EIT dynamic imaging, which refers to the coverage area of ​​the low impedance area in the whole brain. It can intuitively reflect the size of the lesion and the affected area. Together, they provide core physiological data support for assessing the time of epileptic seizure prognosis, lesion localization, and the degree of cerebral edema.

[0065] In some embodiments, the system further includes a gating switch; the control module is also configured to switch the common electrode to the stimulation electrode via the gating switch before the epileptic pre-seizure time and when the impedance change rate drops to a preset range, and to control the electrical stimulation module to apply electrical stimulation to the electrical stimulation electrode pair in accordance with the electrical stimulation signal parameters.

[0066] Specifically, the system also includes a key hardware component called a gating switch. One end of the gating switch is connected to 16 ring-shaped common electrodes, and the other end is connected to the multimodal signal acquisition module and the electrical stimulation module, respectively. This gating switch is responsible for the core function of switching the working state of the electrodes. After the control module calculates the epileptic pre-seizure time based on the real-time impedance characteristics obtained by the impedance acquisition unit, it continuously monitors the impedance change rate in the real-time impedance characteristics. When the impedance change rate drops to a preset range (this preset range is set based on clinical trial data and is usually 5%-15% of the normal baseline impedance value of the lesion area, corresponding to the key physiological stage of lesion congestion before epileptic seizure), it immediately sends a switching command to the gating switch. The common electrodes that were originally in the first acquisition state (EIT signal acquisition) or the second acquisition state (EEG signal acquisition) are quickly switched to the electrical stimulation state through the gating switch. At the same time, the electrical stimulation electrode pairs determined based on the lesion location and the electrical stimulation signal parameters generated based on the degree of cerebral edema and the epilepsy grade are called up to control the electrical stimulation module to apply electrical stimulation that conforms to the parameters to the switched electrical stimulation electrode pairs.

[0067] In the above embodiments, the addition of the gating switch enables efficient switching between the shared electrode signal acquisition and electrical stimulation states, avoiding hardware redundancy caused by separately setting acquisition and stimulation electrodes, simplifying the system structure and reducing costs. The control module uses the pre-seizure time (estimated based on impedance drop occurring approximately 20 seconds before EEG abnormality) and impedance change rate reaching a preset range (corresponding to the critical stage of lesion congestion) as dual triggering conditions. This ensures that stimulation is initiated within the golden intervention window before the epileptic seizure, avoiding premature stimulation that wastes resources or delayed stimulation that misses the inhibition opportunity. It also eliminates interference from non-pathological impedance fluctuations through precise threshold judgment of impedance change rate, reducing the risk of false stimulation. At the same time, the shared electrode after switching directly serves as the stimulation electrode. Combined with the previously determined electrode pairs and parameters, electrical stimulation can be applied to the lesion quickly, maximizing the inhibitory effect of electrical stimulation on epileptic seizures, and balancing the timeliness, accuracy, and practicality of intervention.

[0068] In some embodiments, the control module is also used to assess the epilepsy grade based on the discharge frequency, discharge amplitude, and impedance change rate.

[0069] Specifically, when assessing epilepsy severity based on discharge frequency, discharge amplitude, and impedance change rate, the control module combines the advantages of EEG (electroencephalography) and EIT (electrophysiological imaging). EEG provides indicators of the frequency and amplitude of electrical activity during seizures, reflecting the degree of abnormal discharge activity at the brain level; EIT provides indicators of the magnitude of impedance decrease during seizures, reflecting physiological changes in the lesion area caused by changes in blood flow or cerebral edema. The control module integrates these indicators, and when the electrical activity is intense (high discharge frequency and large amplitude) and accompanied by a sudden drop in impedance (drastic changes in blood flow / edema), the severity of epilepsy is determined to be high.

[0070] In the above embodiments, the integrated evaluation of multiple indicators overcomes the limitations of single EEG or EIT evaluation, and can more comprehensively and accurately reflect the comprehensive changes in brain electrical and physiological states during epileptic seizures. This provides a more reliable basis for the accurate adaptation of subsequent electrical stimulation parameters, improves the effectiveness and pertinence of epilepsy intervention, and reduces the risk of inappropriate intervention due to one-sided evaluation.

[0071] In some embodiments, the control module is also used to assess the epilepsy grade based on discharge distribution, diffusion rate, and the spatial range of impedance changes.

[0072] Specifically, when assessing epilepsy severity based on discharge distribution, diffusion velocity, and the spatial range of impedance changes, the control module combines multi-dimensional information from electroencephalography (EEG) and electrical impedance imaging (EIA). Discharge distribution and diffusion velocity reflect the spatial spread of EEG abnormalities, while the spatial range of impedance changes reflects the spatial coverage of physiological disturbances. A high degree of epilepsy severity is indicated when both the electrical diffusion range (wide discharge distribution and rapid diffusion velocity) and the spatial range of impedance changes (wide range of physiological disturbances) are present. Furthermore, the control module can also assess epilepsy severity based on the degree and duration of post-ictal background activity suppression provided by EEG, and the speed at which impedance returns to baseline provided by EIT. Persistent EEG background suppression and slow impedance recovery indicate poor recovery ability and high epilepsy severity.

[0073] In the above embodiments, the multi-indicator fusion assessment method breaks through the limitations of single-modality assessment, and can more comprehensively and accurately grasp the spatial breadth of epileptic seizures in terms of EEG abnormalities and physiological disorders. This provides a more reliable basis for subsequent precise targeted intervention of electrical stimulation, effectively improves the pertinence and effectiveness of epilepsy intervention, and reduces the risk of intervention deviation caused by incomplete assessment.

[0074] In some embodiments, when the stimulation mode of the electrical stimulation module is configured as a transcranial direct current stimulation mode, the control module is further configured to increase the current intensity of the electrical stimulation signal parameters and / or prolong the stimulation time of the electrical stimulation signal parameters when the discharge frequency increases and / or the discharge amplitude increases.

[0075] The control module is also used to increase the stimulation frequency of the electrical stimulation signal parameters when the impedance change rate increases.

[0076] Specifically, when the stimulation mode of the electrical stimulation module is configured as transcranial direct current stimulation (tDCS), the control module dynamically adjusts the electrical stimulation signal parameters based on the real-time characteristics of EEG and impedance. Once an increase in discharge frequency is detected, indicating an increase in the frequency of abnormal electrical activity in the brain and increased seizure activity, and / or an increase in discharge amplitude, indicating a greater intensity of abnormal electrical activity and more severe neuronal synchronization abnormalities, the control module increases the current intensity of the electrical stimulation signal parameters (e.g., from 1.5mA to 2.0mA) to suppress the excitability of abnormal neurons with a stronger current. It also extends the stimulation time (e.g., from 20min to 25min) to make the inhibitory effect more persistent, thus more effectively combating the worsening trend of seizures. Furthermore, when the impedance change rate increases, reflecting a deepening of physiological disturbances (such as changes in blood flow and edema) in the lesion area caused by epilepsy, the control module increases the stimulation frequency of the electrical stimulation signal parameters (e.g., from once daily to twice daily) to intervene in the deteriorating physiological state in a timely manner through more frequent stimulation, preventing further development of epilepsy. In addition, the control module will adjust the electrode montage (such as increasing the size of the cathode electrode, using a multi-cathode array, or moving the anode from the extra area to the contralateral shoulder) when the abnormal spatial range spreads, so that the inhibition range covers a larger abnormal brain area; the control module will also reduce the current intensity and reduce the stimulation frequency (such as from once a day to once every other day) when the severity decreases, and find the lowest effective dose under good control to reduce tolerance and unnecessary stimulation.

[0077] In the above embodiments, by using a dynamic parameter adjustment mechanism based on multimodal real-time characteristics, the principle of "cathode inhibition and anodic excitation" of tDCS is fully utilized to achieve precise matching between electrical stimulation and the epileptic seizure process. This not only enhances the inhibitory effect on abnormal electrical activity in epilepsy, but also strengthens intervention in a timely manner according to changes in the physiological state of the lesion. This effectively improves the timeliness and effectiveness of epilepsy intervention and reduces the problems of insufficient intervention or overstimulation caused by fixed parameters, providing strong support for personalized and dynamic treatment of epilepsy.

[0078] In some embodiments, when the stimulation mode of the electrical stimulation module is configured as a transcranial alternating current stimulation mode, the control module is further configured to adjust the stimulation frequency of the electrical stimulation signal parameters when a specific abnormal rhythm appears in the real-time EEG characteristics.

[0079] Specifically, when the stimulation mode of the electrical stimulation module is configured to transcranial alternating current stimulation (tACS), the control module adjusts the stimulation frequency of the electrical stimulation signal parameters when specific abnormal rhythms such as focal theta rhythms and spike rhythms appear in real-time EEG characteristics. Two parameter adjustment strategies can be employed: one is same-frequency interference, using the same frequency as the abnormal rhythm to desynchronize it through phase interference, thus disrupting its abnormal synchronicity; the other is different-frequency adjustment, selecting frequencies that can induce inhibition, such as sensorimotor rhythms (SMR, 12-15Hz), to suppress the abnormal rhythm. In addition, the control module will also attempt to use extremely high-frequency tACS (e.g., ≥250Hz) when high-frequency oscillations (HFOs) increase; immediately trigger a short, strong stimulation pulse when EIT shows a sharp drop in impedance (indicating the onset of a seizure); and use alpha frequency (approximately 10Hz) tACS when background activity diffusely slows down.

[0080] In the above embodiments, by dynamically adjusting the stimulation frequency based on specific abnormal rhythms of real-time EEG, the frequency-dependent entrainment characteristics of tACS can be fully utilized to precisely intervene in abnormal EEG rhythms related to epilepsy, effectively breaking the synchronization of abnormal rhythms, inhibiting abnormal EEG activity related to epileptic seizures, improving the intervention effect of electrical stimulation on epilepsy, providing strong support for personalized and precise treatment of epilepsy, and reducing the poor intervention effect caused by fixed stimulation frequency.

[0081] This embodiment also provides an electrical stimulation method for epilepsy monitoring. Figure 7 This is a flowchart of an epilepsy monitoring electrical stimulation method according to an embodiment of this application, such as... Figure 7 As shown, the process includes the following steps:

[0082] Step S701: Obtain real-time impedance characteristics and real-time EEG characteristics during the epileptic pre-seizure period; the real-time impedance characteristics are obtained by a shared electrode in the first acquisition state, and the real-time EEG characteristics are obtained by a shared electrode in the second acquisition state; wherein, a set of shared electrodes is distributed in a ring on the human head.

[0083] Step S702: Based on real-time impedance characteristics, assess the epileptic pre-seizure time, lesion location, and degree of cerebral edema; based on real-time EEG characteristics and real-time impedance characteristics, assess the epilepsy grade.

[0084] Step S703: Based on the degree of cerebral edema and the epilepsy grade, obtain the electrical stimulation signal parameters; based on the lesion location, determine the electrical stimulation electrode pair from the shared electrodes.

[0085] Step S704: Before the epileptic seizure time, apply electrical stimulation to the electrical stimulation electrode pair that conforms to the electrical stimulation signal parameters, and adjust the electrical stimulation signal parameters based on real-time impedance characteristics and real-time EEG characteristics.

[0086] Specifically, firstly, using a set of shared electrodes distributed in a ring around the human head (16 electrodes deployed in fixed positions: No. 1 above the right ear, No. 5 in the middle of the forehead, No. 9 above the left ear, No. 13 below the occipital protuberance, and the remaining electrodes filling the space at equal angles), key signals are acquired by switching states. When the shared electrodes are configured in the first acquisition state, the impedance acquisition unit captures real-time impedance characteristics (such as the rate of change of impedance in the lesion area and the spatial range of impedance change); when configured in the second acquisition state, the electroencephalogram (EEG) acquisition unit extracts real-time EEG characteristics (such as discharge frequency, amplitude, and distribution), and focuses on the golden intervention window of the epileptic pre-seizure period to complete signal acquisition. Next, a multi-dimensional assessment was conducted based on real-time impedance characteristics: the epileptic seizure onset time was estimated based on the pattern that "epilepsy congestion leads to impedance decrease (approximately 20 seconds earlier than EEG abnormalities)". The lesion site was located using the low-impedance red area in EIT imaging, and the degree of cerebral edema was determined based on the magnitude of the impedance decrease. Simultaneously, real-time EEG and impedance characteristics were integrated to comprehensively assess the epilepsy grade from two dimensions: the degree of electrical activity abnormality (discharge frequency, amplitude) and the degree of physiological disorder (impedance change rate, range). Subsequently, an intervention plan was generated based on the assessment results: the electrical stimulation signal parameters were determined by combining the degree of cerebral edema (e.g., stronger intervention is required for more severe edema) and the epilepsy grade (e.g., higher stimulation intensity is required for severe seizures). Suitable electrode pairs were selected from shared electrodes based on the lesion site. Finally, electrical stimulation was initiated before the epileptic seizure onset time, applying stimulation to the selected electrode pairs with parameters consistent with the parameters. Real-time impedance and EEG characteristics were continuously monitored during stimulation, and parameters were adjusted promptly to ensure the intervention always adapted to changes in the epileptic state, achieving precise and dynamic epilepsy suppression.

[0087] Through the above steps, on the one hand, the dual-state acquisition using shared electrodes avoids the need for additional dedicated acquisition electrodes, simplifying the system structure. Simultaneously, the ring-shaped electrode distribution provides more comprehensive coverage of the head region, improving the completeness and accuracy of feature acquisition. On the other hand, based on multi-dimensional feature evaluation and dynamic adjustment of electrical stimulation parameters, targeted intervention on the lesion can be performed during the critical window before an epileptic seizure. This improves the timeliness and effectiveness of epilepsy intervention and allows for optimization of the stimulation protocol based on real-time changes in the patient's condition, reducing unnecessary stimulation or insufficient intervention. This provides strong support for precise and personalized treatment of epilepsy.

[0088] Figure 8 This is a functional flowchart of an epilepsy monitoring electrical stimulation method according to an embodiment of this application, such as... Figure 8 As shown, the process includes the following steps:

[0089] Step S801: Impedance monitoring and EEG monitoring. During the pre-seizure period of epilepsy, the system simultaneously initiates brain impedance monitoring and EEG monitoring via 16 ring-distributed shared electrodes. The shared electrodes switch their operating states via a selector switch: in the first acquisition state, the impedance acquisition unit acquires real-time impedance characteristics; in the second acquisition state, the EEG acquisition unit acquires real-time EEG characteristics, providing bimodal raw data for subsequent evaluation.

[0090] Step S802: Extraction of impedance and EEG features during the pre-seizure period of epilepsy. From the impedance features, identify the impedance decrease trend in the lesion area due to congestion (experimental data show that this decrease occurs approximately 20 seconds earlier than the EEG abnormality); from the EEG features, capture early signals of interictal epileptiform discharges (such as spikes and sharp waves); simultaneously, convert the impedance features into visual images using EIT dynamic imaging to preliminarily locate potential lesion sites corresponding to low impedance (red areas), completing the preliminary screening and analysis of pre-seizure features.

[0091] Step S803, Seizure Identification. Seizure identification is completed by combining preset judgment rules. For example, when the impedance characteristics meet the condition that the impedance change rate decreases to a preset range, and the EEG characteristics show typical signals of the seizure phase, the system determines that a seizure is about to occur or has already occurred. Simultaneously, it identifies the area where impedance continues to decrease as the specific lesion site, providing a precise target for subsequent intervention.

[0092] Step S804: Evaluate the severity of epilepsy and the location of the lesion using impedance data and EEG data. A multi-dimensional assessment is conducted based on real-time impedance and EEG characteristics. From an electrical activity perspective, the degree of EEG abnormality is determined by discharge frequency (number of spikes per unit time) and discharge amplitude (abnormal electrical activity voltage). From a physiological disturbance perspective, the degree of cerebral edema and the extent of lesion influence are assessed through impedance change rate (impedance decrease amplitude) and impedance change spatial range (area covered by low impedance regions). The severity of epilepsy is determined by combining both factors (e.g., mild: focal discharge + mild impedance decrease; severe: diffuse discharge + significant impedance decrease). Simultaneously, EIT imaging is used to precisely locate the specific region of the lesion in the brain (e.g., right temporal region, anterior frontal region).

[0093] Step S805, Focused Electrical Stimulation. First, electrode pairs are selected from 16 shared electrodes based on the location of the lesion; second, electrical stimulation parameters are determined by combining the epilepsy grade and the degree of cerebral edema; finally, the gating switch is controlled to switch the shared electrodes to the stimulation state, and before the epileptic pre-seizure time (within the 20-second window after impedance decrease), the electrical stimulation module is controlled to apply electrical stimulation that meets the parameters to the electrode pairs, so as to achieve precise intervention on the lesion.

[0094] Step S806: Monitoring and Adjusting the Effect of Electrical Stimulation. During the electrical stimulation process, impedance and EEG characteristics are acquired in real time to assess the stimulation effect. Based on the assessment results, it is determined whether to continue applying electrical stimulation. If real-time data shows a decrease in abnormal EEG discharges, a return of impedance to the normal range, and a reduction in the red area on EIT imaging, the stimulation is considered effective, and the stimulation intensity can be reduced or the stimulation can be stopped. If data shows no improvement in discharges, a continued decrease in impedance, and an expansion of the lesion area, it is determined that stimulation needs to continue and the electrical stimulation parameters need to be adjusted. If there is no significant change in whole-brain impedance after stimulation, or if the local area remains red, indicating poor efficacy, the system will prompt that the stimulation mode needs to be changed or the intervention intensity increased to ensure the effectiveness and safety of the intervention.

[0095] Step S807: Storage of impedance data, electrical stimulation parameters, etc. When the system determines that electrical stimulation is no longer necessary, it first stops the electrical stimulation module and controls the gating switch to switch the shared electrode back to the acquisition state, continuously monitoring the recovery of impedance and EEG signals in the lesion area; secondly, it automatically stores all the data from this monitoring and intervention, including impedance characteristics, EEG characteristics, electrical stimulation parameters, and stimulation effect evaluation results at each stage.

[0096] EEG / EIT assessment of epileptic severity to adjust tDCS / tACS parameters represents a shift from "blind bombardment" to "precision guidance." Furthermore, impedance imaging allows users to visually observe cerebral edema in the patient's brain; areas with severe edema require focused attention. The most typical characteristic of cerebral edema caused by epileptic activity on EIT is a focal, persistent decrease in brain impedance, reflecting the pathological process of extracellular fluid increase following blood-brain barrier disruption. Therefore, combining EIT with EEG not only allows for early detection of epileptic electrical activity (via EEG) but also real-time monitoring of subsequent pathophysiological changes in brain tissue (such as edema, via EIT), providing a crucial real-time bedside monitoring window for assessing the severity of epilepsy, particularly the risk of brain injury in status epilepticus. This is of great significance for achieving "early suppression" and preventing irreversible brain damage.

[0097] From the perspective of impedance characteristics, after an epileptic seizure, due to blood abnormalities, edema will occur around the lesion. This will cause the lesion location to show a continuous decrease in impedance on EIT imaging, and the area will appear red in the image. From the perspective of EEG characteristics, the earliest clear change in the EEG during the seizure is in the onset phase. Its main signal characteristics include four types: rhythmic fast activity (most common in focal seizures, manifested as low amplitude β fast activity >13Hz with gradually increasing amplitude and possibly gradually decreasing frequency), rhythmic spike / wave activity (common in generalized seizures (such as 3Hz spike-wave syndrome in absence seizures)), electrodecrement (manifested as a sudden and significant suppression and flattening of background activity, often accompanied by rhythmic fast activity), and rhythmic slow activity belonging to the θ or δ frequency band with gradually increasing amplitude.

[0098] EIT presents the difference between the current impedance distribution and the reference frame through dynamic imaging, such as Figure 9 As shown, in the imaging, blue represents areas with impedance greater than the reference frame, and red represents areas with impedance less than the reference frame. The color scale indicates the intensity of impedance change; the darker the color, the greater the impedance change. Regarding the correlation between cerebral edema and impedance, if cerebral edema leads to an increase in extracellular fluid, impedance will decrease; if brain dehydration leads to a decrease in extracellular fluid, impedance will increase. In the initial stage of the EIT imaging system, the image is transparent (defaulting to a normal brain state). After an epileptic seizure, due to abnormal blood flow, edema occurs around the lesion, resulting in a sustained decrease in impedance at the lesion location in the image, which is displayed in red. Impedance imaging can show changes in impedance throughout the brain. The system continuously performs electrical stimulation based on the abnormal signal frequency of the EEG, while the software records and times the events. Over time, four different results will appear:

[0099] Result 1: Increased blood flow at the lesion site and development of cerebral edema around the lesion site, decreased impedance and the corresponding area appeared red in impedance imaging. After electrical stimulation, the impedance at the lesion site increased and the impedance value returned to normal level. The result was eventually maintained at the normal level and the imaging remained transparent, indicating that the electrical stimulation was effective and the human brain recovered well.

[0100] Result 2: Increased blood flow at the lesion site and development of cerebral edema around the lesion site, decreased impedance and the corresponding area appeared red in impedance imaging. After electrical stimulation, the impedance at the lesion site and the surrounding area increased and the impedance value returned to normal level. After the electrical stimulation stopped, the result eventually returned to the impedance value before stimulation, and the imaging returned to the red color of the lesion site. This indicates that the electrical stimulation was effective, but the brain tissue recovery effect was not good and a longer period of electrical stimulation was required to maintain it.

[0101] Result 3: Increased blood flow at the lesion site and development of cerebral edema around the lesion, decreased impedance and red impedance imaging of the corresponding area, no significant increase in whole brain impedance or local brain impedance after electrical stimulation, indicating that the condition is relatively serious and the effect of electrical stimulation is not good.

[0102] Result 4: Increased blood flow at the lesion site and development of cerebral edema around the lesion site, decreased impedance and the corresponding area of ​​impedance imaging was red. After electrical stimulation, the impedance of most of the lesion site increased and most of it was colorless. The local imaging of the lesion site was still red, indicating that the effect of electrical stimulation was not good.

[0103] In addition, in conjunction with the epilepsy monitoring electrical stimulation method in the above embodiments, this application embodiment can provide a storage medium for implementation. The storage medium stores a computer program; when executed by a processor, the computer program implements any of the epilepsy monitoring electrical stimulation methods in the above embodiments.

[0104] It should be noted that the user information (including but not limited to user device information, user personal information, etc.) and data (including but not limited to data used for analysis, data stored, data displayed, etc.) involved in this application are all information and data authorized by the user or fully authorized by all parties.

[0105] Those skilled in the art will understand that all or part of the processes in the above embodiments can be implemented by a computer program instructing related hardware. The computer program can be stored in a non-volatile computer-readable storage medium. When executed, the computer program can include the processes of the embodiments described above. Any references to memory, databases, or other media used in the embodiments provided in this application can include at least one of non-volatile and volatile memory. Non-volatile memory can include read-only memory (ROM), magnetic tape, floppy disk, flash memory, optical memory, high-density embedded non-volatile memory, resistive random access memory (ReRAM), magnetic random access memory (MRAM), ferroelectric random access memory (FRAM), phase change memory (PCM), graphene memory, etc. Volatile memory can include random access memory (RAM) or external cache memory, etc. By way of illustration and not limitation, RAM can take many forms, such as Static Random Access Memory (SRAM) or Dynamic Random Access Memory (DRAM). The databases involved in the embodiments provided in this application may include at least one type of relational database and non-relational database. Non-relational databases may include, but are not limited to, blockchain-based distributed databases. The processors involved in the embodiments provided in this application may be general-purpose processors, central processing units, graphics processing units, digital signal processors, programmable logic devices, quantum computing-based data processing logic devices, etc., and are not limited to these.

[0106] Those skilled in the art should understand that the technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments have been described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0107] The embodiments described above are merely illustrative of several implementation methods of this application, and while the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the invention patent. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the protection scope of this application. Therefore, the protection scope of this patent application should be determined by the appended claims.

Claims

1. An epilepsy monitoring electrical stimulation system, characterized in that, The system includes: a multimodal signal acquisition module, an electrical stimulation module, a control module, a gating switch, and a set of shared electrodes distributed in a ring around the human head; The multimodal signal acquisition module includes an electrical impedance acquisition unit and an electroencephalogram (EEG) acquisition unit; The impedance acquisition unit is used to acquire the real-time impedance characteristics transmitted by the common electrode in the first acquisition state when the working state of the common electrode is configured in the first acquisition state. The EEG acquisition unit is used to acquire real-time EEG features transmitted by the common electrode in the second acquisition state when the working state of the common electrode is configured in the second acquisition state. The control module is used to assess the epileptic pre-seizure time, lesion location, and degree of cerebral edema based on the real-time impedance characteristics; and to assess the epilepsy grade based on the real-time EEG characteristics and the real-time impedance characteristics. The control module is also used to obtain electrical stimulation signal parameters based on the degree of cerebral edema and the epilepsy level; The control module is further configured to determine an electrical stimulation electrode pair from a set of common electrodes based on the lesion site; and, before the epileptic pre-seizure time and when the impedance change rate in the real-time impedance characteristics drops to a preset range, switch the common electrode to a stimulation electrode via the gating switch, and control the electrical stimulation module to apply electrical stimulation to the electrical stimulation electrode pair that conforms to the electrical stimulation signal parameters. The control module is also used to adjust the electrical stimulation signal parameters based on the real-time impedance characteristics and the real-time EEG characteristics during the application of electrical stimulation.

2. The epilepsy monitoring electrical stimulation system according to claim 1, characterized in that, When the stimulation mode of the electrical stimulation module is configured as transcranial alternating current stimulation mode, the control module is also used to select, based on the lesion site, an electrode pair that can pass through the lesion site from the common electrodes as the electrical stimulation electrode pair.

3. The epilepsy monitoring electrical stimulation system according to claim 1, characterized in that, When the stimulation mode of the electrical stimulation module is configured as transcranial direct current stimulation mode, the control module is further configured to select, based on the lesion site, an electrode closer to the lesion site as the cathode electrode and an electrode farther away from the lesion site as the anode electrode among the common electrodes, and use the electrode pair consisting of the cathode electrode and the anode electrode as the electrical stimulation electrode pair, and the line connecting the cathode electrode and the anode electrode must pass through the brain region corresponding to the lesion site.

4. The epilepsy monitoring electrical stimulation system according to claim 1, characterized in that, The real-time EEG characteristics include discharge frequency, discharge amplitude, discharge distribution, and diffusion velocity; the real-time impedance characteristics include impedance change rate and impedance change spatial range.

5. The epilepsy monitoring electrical stimulation system according to claim 4, characterized in that, The control module is also used to assess the epilepsy level based on the discharge frequency, the discharge amplitude, and the impedance change rate.

6. The epilepsy monitoring electrical stimulation system according to claim 4, characterized in that, The control module is also used to assess the epilepsy level based on the discharge distribution, the diffusion rate, and the spatial range of impedance changes.

7. The epilepsy monitoring electrical stimulation system according to claim 4, characterized in that, When the stimulation mode of the electrical stimulation module is configured as transcranial direct current stimulation mode, the control module is further configured to increase the current intensity of the electrical stimulation signal parameter and / or prolong the stimulation time of the electrical stimulation signal parameter when the discharge frequency increases and / or the discharge amplitude increases. The control module is also used to increase the stimulation frequency of the electrical stimulation signal parameters when the impedance change rate increases.

8. The epilepsy monitoring electrical stimulation system according to claim 4, characterized in that, When the stimulation mode of the electrical stimulation module is configured as transcranial alternating current stimulation mode, the control module is also used to adjust the stimulation frequency of the electrical stimulation signal parameters when the real-time EEG features show a specific abnormal rhythm.

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