Electrode, electrode system and electroosmosis delivery system

Abstract

The invention relates to the technical field of medical instruments, and particularly discloses an electrode, an electrode system and an electroosmosis delivery system.The electrode comprises an electrode body made of a cobalt-based alloy material; the conductive contact part is arranged at one end of the electrode main body and is connected with an external power supply; the stimulation part is arranged at the other end of the electrode main body and is used for being in contact with the biological tissue and applying electrical stimulation; by adopting the arrangement of the cobalt-based alloy electrode and the accurate insulating layer exposure area, the electrode main body has excellent biocompatibility and stable conductivity, and meanwhile, the local exposure design of the insulating layer at the stimulation part ensures accurate focusing of an electric field; therefore, the effect of remarkably improving the spatial resolution of electroosmosis treatment while reducing the risk of tissue damage is achieved, and the effect of flexibly adapting to different focus forms and depths and achieving brain tissue global coverage type electroosmosis treatment is achieved through the arrangement that a net-shaped or helmet-type supporting structure is matched with a multi-electrode array capable of being independently adjusted.

Description

Technical Field

[0001] The present invention belongs to the technical field of medical devices, and in particular relates to an electrode, an electrode system and an electroosmotic delivery system. Background Art

[0002] In the field of medical device technology, especially in the intersection of neuroscience and bioelectric medicine, electrical stimulation technology, as a non-invasive or minimally invasive treatment method, has been widely used in the treatment and rehabilitation of neurological diseases. With the rapid development of materials science, electronic engineering and biomedical engineering, the design and application of electrical stimulation electrodes have continuously made new breakthroughs. Traditional electrical stimulation electrodes, such as the rubber electrodes in the transcranial direct current stimulation (tDCS) system, can regulate nerve excitability and improve nerve function to a certain extent, but their treatment accuracy and effect are often limited by the electrode material, size, installation method and stimulation mode.

[0003] Specifically, traditional tDCS electrodes use large-area rubber electrode sheets covered with saline sponges and fixed to the scalp via a headband. Although this design is simple and easy to use, it has obvious limitations. First, due to the large electrode area and lack of precise positioning capability, the current can only act on the superficial cortex and cannot penetrate into the deep brain tissue, thereby limiting its treatment range and effect. Secondly, the traditional tDCS system uses constant direct current stimulation, lacks waveform modulation function, and the electrode polarity is fixed, and cannot be dynamically switched according to treatment needs, resulting in a single treatment effect and difficulty in achieving personalized treatment. More importantly, the traditional tDCS system lacks a real-time biofeedback mechanism and cannot dynamically adjust the stimulation parameters according to changes in tissue state during treatment, thereby increasing safety risks such as skin burns, so staff need to improve it. Summary of the Invention

[0004] The object of the present invention is to provide an electrode, an electrode system and an electroosmotic delivery system to solve the problems raised in the above background technology.

[0005] To achieve the above object, the present invention provides the following technical solutions:

[0006] An electrode comprising:

[0007] The electrode body is made of cobalt-based alloy material;

[0008] A conductive contact portion, provided at one end of the electrode body, for connecting to an external power source;

[0009] a stimulation portion, disposed at the other end of the electrode body, for contacting biological tissue and applying electrical stimulation;

[0010] The insulating layer covers a portion of the surface of the electrode body, and the insulating layer is provided with an exposed area at the stimulation part so that the stimulation part can electrically communicate with the biological tissue.

[0011] Preferably, the electrode body is one of a needle-shaped and a sheet-shaped structure, with a length of 1-10 cm and a diameter of 0.1-2 mm.

[0012] An electrode system comprising:

[0013] Multiple electrodes;

[0014] a support structure, for fixing the positions of the plurality of electrodes, wherein the support structure is in one of a mesh, a cap, and a helmet shape, and is adapted to fit the patient's head;

[0015] The multiple electrodes are arranged at intervals on the support structure, and the position of each electrode is independently adjusted according to treatment requirements.

[0016] Preferably, the support structure is provided with at least 10 electrodes and at most 100 electrodes, and each electrode is independently configured as either an anode or a cathode.

[0017] Preferably, it also includes:

[0018] A detection module for real-time monitoring of electrical signals and fluid transmission responses between the electrode and biological tissue;

[0019] The feedback module dynamically adjusts the electrode potential and current parameters according to the data from the detection module;

[0020] A heating detection module is used to detect temperature changes in contact with biological tissue during electrical stimulation;

[0021] The control module automatically disconnects the stimulation output when the detected potential, current or current density exceeds the set threshold.

[0022] An electroosmotic delivery system comprising:

[0023] Electrode system;

[0024] A control unit, configured to control the potential and current of each electrode in the electrode system;

[0025] A computer program module configured to:

[0026] receiving medical image data of a patient;

[0027] Generate a patient-specific 3D head model based on medical image data;

[0028] Based on the three-dimensional head model, simulating the effects of electrode positions and potential and current parameters on fluid transport;

[0029] Output optimized electrode configuration and treatment parameters to the control unit.

[0030] Preferably, the control unit can independently control the potential and current of each electrode, and the output current is one of direct current and alternating current, the direct current waveform is ideal direct current, square wave, triangle wave, etc., the alternating current waveform is sine wave, triangle wave, square wave, etc., the frequency is 0-100Hz, and the current amplitude is 0.1-200mA.

[0031] Preferably, the computer program module is further configured to:

[0032] Select the target tissue area as the fluid drainage area, mainly the location of edema caused by brain trauma, cerebral infarction, brain tumor and other diseases;

[0033] Select the receiving area as the fluid target location, mainly the adjacent area of ​​cerebrospinal fluid circulation and cerebrospinal fluid discharge site, superior sagittal sinus, etc.

[0034] The anode and cathode configurations of the electrodes were determined based on the simulation results to guide the directional transport of fluid from the discharge area to the receiving area.

[0035] Preferably, it also includes:

[0036] The drug delivery module is used to synchronously release drugs during electroosmotic delivery, wherein the drugs are guided to the target tissue area through the electroosmotic effect.

[0037] Preferably, the medical image data includes at least one of computed tomography, magnetic resonance imaging, positron emission tomography and diffusion tensor imaging.

[0038] Compared with the prior art, the present invention has the following beneficial effects:

[0039] (1) By adopting the cobalt-based alloy electrode and the precise insulation layer exposure area, the electrode body has excellent biocompatibility and stable conductivity. At the same time, the local exposure design of the insulation layer at the stimulation part ensures the precise focusing of the electric field, thereby achieving the effect of significantly improving the spatial resolution of electroosmotic treatment while reducing the risk of tissue damage.

[0040] (2) Through the use of a mesh or helmet-like support structure combined with an independently adjustable multi-electrode array, the electrode system can dynamically adjust the electrode position and polarity according to the patient's individualized head model, thereby achieving the effect of flexible adaptation to different lesion morphologies and depths and achieving full-area electroosmotic treatment of brain tissue.

[0041] (3) By combining computer program modules with medical imaging data to establish an individualized three-dimensional model, the system can simulate the electric field distribution and fluid transmission rules under different electrode configurations and automatically optimize treatment parameters, thereby achieving the effect of accurately guiding the directional migration of cerebrospinal fluid or drugs and avoiding unnecessary interference with healthy brain areas.

[0042] (4) By integrating a feedback control module with real-time impedance and temperature sensors, the system can dynamically monitor the tissue status during treatment and automatically adjust the current intensity and waveform, thereby achieving a safety guarantee effect of minimizing tissue overheating or electrochemical damage while ensuring treatment efficiency. BRIEF DESCRIPTION OF THE DRAWINGS

[0043] Figure 1 is a system flow chart of the present invention;

[0044] Figure 2 A flow chart for electrode design of the present invention;

[0045] Figure 3 Constructing a flow chart for the electrode system of the present invention;

[0046] Figure 4 This is a flow chart of the operation of the electroosmotic delivery system of the present invention. DETAILED DESCRIPTION

[0047] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of the present invention.

[0048] Example 1:

[0049] See also Figures 1 to 4 As shown, the specific structure of the electrode (corresponding to claims 1-2)

[0050] The electrode is made of a cobalt-based alloy (such as cobalt-chromium or cobalt-nickel) to improve biocompatibility and conductivity. The main electrode is a needle-shaped structure, and femtosecond laser electrocuting and inert gas welding are used to improve the precision of the electrode tip. It is 5 cm long and 0.5 mm in diameter, suitable for intracranial or scalp implantation.

[0051] Conductive contact part: Located at the proximal end of the electrode, it is gold-plated and used to connect to the external power wire to ensure low-resistance contact.

[0052] Stimulation part: Located at the distal end of the electrode, it is an exposed metal tip (about 0.3 mm in diameter) used to directly contact the scalp, skull or dura mater of brain tissue and apply electrical stimulation.

[0053] Insulation layer: The electrode body is covered with polyimide (PI) or polytetrafluoroethylene (PTFE) material, leaving only a 1 mm exposed area at the stimulation site to prevent current leakage and improve stimulation accuracy.

[0054] The electrode system uses an adjustable helmet structure made of a flexible polymer (such as silicone or polyurethane) with 32 electrodes embedded inside, arranged in a grid pattern (with a spacing of approximately 2 cm).

[0055] Support structure: The inside of the helmet is equipped with an adjustable elastic strap to accommodate different patient head circumferences (50-65 cm). Each electrode is fixed to the helmet via a micro-guide rail and can be moved radially by ±1 cm to adapt to individualized treatment needs.

[0056] Detection module: Integrates impedance sensors, pressure sensors, and temperature sensors to monitor the contact status and electrical signal changes of the electrode-tissue interface in real time;

[0057] Regional ion concentration detection (optional): biosafety-grade ion-sensitive field-effect transistors are implanted in the receiving area, the middle area of ​​liquid flow, etc., using semiconductor field effects to detect changes in regional ion concentration at a specific location and time. After a set time (such as stimulation for 30 minutes), the stimulation current can be automatically cut off and the detection module can be started to perform regional ion concentration detection. After the detection is completed, stimulation output will be performed again.

[0058] Feedback module: Based on the detection data, it automatically adjusts the current intensity (0.5-5mA) or polarity (anode / cathode switching) of the electrode to ensure a stable electroosmotic effect.

[0059] How the electroosmotic delivery system works

[0060] Data input and modeling: Patients underwent MRI and CT scans to obtain high-resolution brain images (1 mm slice thickness).

[0061] The computer program module (running on a GPU-accelerated workstation) performs the following steps:

[0062] A 3D reconstruction algorithm (such as Marching Cubes) is used to generate a personalized finite element model of the patient's brain, including the skin, skull, brain tissue gray matter, white matter, cerebrospinal fluid distribution, and lesion areas (such as edema or tumors).

[0063] The electric field distribution and fluid transport rate under different electrode configurations (such as the anode located behind the lesion area and the cathode located near the superior sagittal sinus) were simulated in the model.

[0064] Treatment parameter optimization: The system selects the optimal electrode combination based on simulation results (for example, activating electrodes 8, 15, and 22 as anodes and electrodes 3 and 10 as cathodes).

[0065] The control unit outputs pulsed direct current (waveform: square wave, frequency 1 Hz, amplitude 2 mA, duty cycle 50%) for 20 minutes.

[0066] Individualized brain tissue electroosmotic-fluid coupling model

[0067] Objective: To establish a three-dimensional finite element model of patient brain tissue and simulate the electric field distribution and fluid transport rate.

[0068] Formula design:

[0069]

[0070] Parameter explanation:

[0071] Ψ(r,t) is the quantitative index of the electroosmotic-fluid coupling effect at position r and time t (unit: mm 3 / s, the range is [0,+∞), the larger the value, the higher the efficiency of fluid transport driven by electroosmosis;

[0072] σ(r) is the tissue conductivity tensor (unit: S / m), reconstructed from MRI-DTI data;

[0073] φ(r,t) is the electric potential distribution (unit: V), which is solved by Poisson's equation ▽·(σ▽φ)=0;

[0074] r0 is the coordinate of the electrode center, k is the Gaussian attenuation coefficient (unit: mm), which controls the local focusing of the electric field;

[0075] C i (r,t) is the concentration of the i-th fluid (such as cerebrospinal fluid, edema fluid) (unit: mol / m 3 );

[0076] erf(·) is the error function used to filter out the invalid low electric field area (threshold E th =0.3V / cm);

[0077] λ is the electroosmotic-diffusion coupling coefficient (unit: m 2 / V·s), calibrated by in vitro experiments.

[0078] Electrode configuration optimization objective function

[0079] Goal: Select the optimal electrode combination to maximize fluid clearance from the target area.

[0080] Formula design:

[0081]

[0082] Parameter explanation:

[0083] F(E) is the optimization score of the electrode configuration E (dimensionless), with a range of (-∞, +∞), where positive values ​​indicate that the benefits of treatment outweigh the risks;

[0084] Ψ target is the integral of the Ψ value of the lesion area (unit: mm 3 );

[0085] E j is the coordinate of the jth electrode, E safe A safe distance (e.g., avoiding the sagittal sinus by 3 mm);

[0086] γ is the distance penalty coefficient (unit: mm), α and β are weight factors (fitted by clinical data);

[0087] cubic term Strengthen security boundary constraints.

[0088] Dynamic electrical stimulation parameter control

[0089] Goal: Adjust current waveform parameters based on real-time feedback.

[0090] Formula design:

[0091]

[0092] Parameter explanation:

[0093] I(t) is the time-varying current amplitude (unit: mA), with a range of [0, 2I0], where I0 = 2 mA is the base current;

[0094] η is the adaptive gain (dimensionless), which is updated in real time by the impedance sensor;

[0095] τ is the time constant (unit: s), which controls the current rise rate;

[0096] The sinc(·) function suppresses high-frequency noise, with f = 1 Hz as the fundamental frequency;

[0097] H(·) is a Heaviside step function that cuts off the output when (minimum flow rate threshold).

[0098] Data collection and calculation:

[0099] σ(r) is the anisotropic conductivity of white matter obtained by DTI-MRI.

[0100] Real-time measurements by fluorescent particle tracking microscopy.

[0101] All the above formulas can be solved numerically by custom finite element codes.

[0102] Drug co-delivery (optional): If the therapeutic goal is to clear amyloid protein in Alzheimer's disease, the system can be activated by electroosmosis and then inject drug-loaded nanoparticles (such as liposomes loaded with Aβ antibodies) into the scalp via a micropump.

[0103] The electric field drives the drug to migrate directionally along a simulated path (such as from the brain parenchyma to the subarachnoid space), thereby increasing the local drug concentration.

[0104] Application scenarios:

[0105] Treatment of cerebral edema: The anode is placed behind the edema area and the cathode is placed in the superior sagittal sinus to drive the edema fluid into the cerebrospinal fluid circulation system.

[0106] Parkinson's disease drug delivery: the anode is close to the substantia nigra, the cathode is placed in the motor cortex, and levodopa nanoformulation is delivered simultaneously.

[0107] Key parameter verification:

[0108] Electric field strength: The model predicts that it needs to reach 0.5-3 V / cm to induce effective electroosmotic flow.

[0109] Fluid flow rate: verified by fluorescent tracer imaging, the error between actual flow rate and simulation is <15%.

[0110] Example 2:

[0111] The electrode adopts a flexible three-dimensional mesh electrode array, which is suitable for direct implantation into the brain parenchyma during craniotomy.

[0112] Electrode body: Made of platinum-iridium alloy wire (80 μm in diameter) woven into a 3D porous structure (porosity 70%), the surface is coated with poly (3,4-ethylenedioxythiophene) (PEDOT) to reduce the interfacial impedance.

[0113] Stimulation part: Each intersection node is an exposed spherical contact (diameter 200μm), with a spacing of 1.5mm, for a total of 256 stimulation points.

[0114] Insulation layer: The wire is wrapped with bioresorbable polylactic acid (PLA), which gradually degrades 3 months after surgery to reduce long-term foreign body reactions.

[0115] Special design: A micro pH sensor (accuracy 0.01) is integrated at the end of the electrode to monitor the risk of tissue acidosis in real time.

[0116] Electrode system architecture:

[0117] Implant module: 4×4×4mm 3 Titanium alloy base, containing:

[0118] 32-channel wireless power supply chip (operating frequency 13.56MHz);

[0119] Adaptive impedance matching circuit (dynamic range 50Ω-10kΩ).

[0120] External controller: A wearable belt device that transmits energy and data via near-field communication (NFC) with a maximum output power of 500mW.

[0121] Workflow:

[0122] Intraoperative positioning: Based on preoperative DTI images, the electrode array was implanted 2 mm below the motor cortex using a neuronavigation robot.

[0123] Postoperative calibration: A test current (0.1 mA, 100 Hz square wave) was applied, and the electrode-tissue coupling status was verified by electrocortical evoked potential (ECoG).

[0124] Establish an individualized current-flow rate response matrix:

[0125]

[0126] v i Where is the flow velocity at the i-th node (μm / s), I j is the j-th channel current (mA).

[0127] Electroosmotic delivery system:

[0128] Multimodal data fusion modeling

[0129] Input data:

[0130] Intraoperative optical coherence tomography (OCT) was used to obtain the three-dimensional morphology of the electrode-brain tissue interface (resolution 5 μm);

[0131] Postoperatively, 7T fMRI was used to monitor changes in blood oxygenation level-dependent (BOLD) signals.

[0132] Model construction:

[0133]

[0134] Where ⊕ represents channel splicing, ∈ = 0.7 is the diffusion tensor D DTI The weight coefficient of .

[0135] Closed-loop treatment control

[0136] Real-time optimization algorithm:

[0137]

[0138] Ttarget is the target velocity distribution (predicted by the model);

[0139] ζ = 15s is the tissue memory time constant;

[0140] μ = 0.3 is a sparsification penalty term that reduces the number of activated electrodes.

[0141] Output waveform:

[0142] Carrier: 2kHz sine wave (to avoid electrolytic damage);

[0143] Modulation wave: dynamic amplitude modulation pulse (AM index 0.8), the envelope is updated in real time according to the optimization results.

[0144] Drug synergy case

[0145] When treating Parkinson's disease:

[0146] Magnetic nanoparticles (50 nm in diameter) encapsulating GDNF were released through the central micropores of the array;

[0147] A rotating magnetic field (10 mT, 5 Hz) was applied to drive the diffusion of nanoparticles;

[0148] Synchronously activate the peripheral electrode (cathode) to form electroosmotic flow and enhance drug targeting:

[0149] F total =q(E+v×B)-6πηrv;

[0150] q: nanoparticle surface charge (-25 mV);

[0151] E: local electric field strength (0.8 V / cm);

[0152] B: Magnetic field strength.

[0153] Security monitoring mechanism

[0154] Overheat protection: Each electrode is integrated with a micro-thermocouple (response time 10ms), which is triggered when the temperature is >39°C:

[0155]

[0156] Bleeding detection: Analyzes impedance spectrum phase angle mutation (5°@1kHz) and automatically pauses treatment.

[0157] Typical treatment parameters:

[0158] parameter Numerical range Monitoring methods Single point current density <![CDATA[15-50μA / mm 2 ]]> Potentiostat + lock-in amplifier Fluid directional velocity 8-22μm / s Ultrasound Particle Imaging (UPI) Drug enrichment ratio (lesion area / normal area) 6.8:1 PET-CT quantitative

[0159] Comparative Example:

[0160] The transcranial direct current stimulation (tDCS) system currently used in clinical practice adopts the following design:

[0161] electrode:

[0162] Material: rubber electrode (surface covered with saline sponge);

[0163] Size: 5×7cm 2 Large area contact;

[0164] Installation method: Fixed to the scalp via a headband, no precise positioning capability.

[0165] Stimulation Mode:

[0166] Output constant DC (1-2mA), no waveform modulation function;

[0167] The electrode polarity is fixed (anode / cathode, either one) and cannot be switched dynamically. Treatment limitations:

[0168] The current can only act on the superficial cortex (depth <1 cm);

[0169] Targeted delivery of cerebrospinal fluid or drugs cannot be achieved;

[0170] There is a lack of real-time biofeedback and a risk of skin burns.

[0171] Comparative Example 1 (Non-invasive Electroosmosis System):

[0172] Comparison Item Existing technology (tDCS) Example 1 Electrode accuracy Centimeter-level large-area stimulation Millimeter-scale grid electrodes (2cm spacing) Depth of action Cortex only Can target deep lesions (such as the lateral ventricles) Dynamic Control Fixed current output Real-time optimization of electrode combination and current parameters based on MRI model Treatment effect Only regulates neural excitability Simultaneous electroosmotic flow drive + targeted drug delivery Security Skin burn rate > 5% Integrated temperature / impedance feedback, burn rate <0.1%

[0173] Comparison of typical cases:

[0174] Treatment of cerebral edema:

[0175] tDCS: can only temporarily relieve symptoms and cannot remove edema fluid;

[0176] Example 1: Edema volume reduced by 42% within 24 hours (CT verification). Comparative Example 2 (implantable electroosmotic system):

[0177]

[0178] Comparison of surgical results:

[0179] Parkinson's disease treatment:

[0180] tDCS: Symptom improvement rate is approximately 20% (UPDRS score);

[0181] Example 2: The bradykinesia score was reduced by 58%, and the drug dosage was reduced by 70%.

[0182] Existing technologies can only achieve rough regulation, but this application achieves precise intervention at the cellular scale through high-density electrodes.

[0183] Traditional tDCS is open-loop stimulation, and this application introduces real-time biofeedback and adaptive optimization.

[0184] This application breaks through the limitations of single electrical stimulation and integrates multimodal treatments such as electroosmosis, drug delivery, and magnetic field regulation.

[0185] While embodiments of the present invention have been shown and described, it will be appreciated by those skilled in the art that various changes, modifications, substitutions, and variations may be made to these embodiments without departing from the principles and spirit of the invention, and that the scope of the invention is defined by the appended claims and their equivalents.

Claims

1. An electrode, characterized in that: include: The electrode body is made of cobalt-based alloy material; A conductive contact portion, provided at one end of the electrode body, for connecting to an external power source; a stimulation portion, disposed at the other end of the electrode body, for contacting biological tissue and applying electrical stimulation; The insulating layer covers a portion of the surface of the electrode body, and the insulating layer is provided with an exposed area at the stimulation part so that the stimulation part can electrically communicate with the biological tissue.

2. An electrode according to claim 1, characterized in that: The electrode body is a needle-shaped or sheet-shaped structure, with a length of 1-10 cm and a diameter of 0.1-2 mm.

3. An electrode system, suitable for an electrode according to any one of claims 1 to 2, characterized in that: include: Multiple electrodes; a support structure, for fixing the positions of the plurality of electrodes, wherein the support structure is in one of a mesh, a cap, and a helmet shape, and is adapted to fit the patient's head; The multiple electrodes are arranged at intervals on the support structure, and the position of each electrode is independently adjusted according to treatment requirements.

4. An electrode system according to claim 3, characterized in that: The support structure is provided with at least 10 electrodes and at most 100 electrodes, and each electrode is independently configured as either an anode or a cathode.

5. An electrode system according to claim 3, characterized in that: Also includes: A detection module for real-time monitoring of electrical signals and fluid transmission responses between the electrode and biological tissue; The feedback module dynamically adjusts the electrode potential and current parameters according to the data from the detection module; A heating detection module is used to detect temperature changes in contact with biological tissue during electrical stimulation; The control module automatically disconnects the stimulation output when the detected potential, current or current density exceeds the set threshold.

6. An electroosmotic delivery system, suitable for an electrode system according to any one of claims 3 to 5, characterized in that: include: Electrode system; A control unit, configured to control the potential and current of each electrode in the electrode system; A computer program module configured to: receiving medical image data of a patient; Generate a patient-specific 3D head model based on medical image data; Based on the three-dimensional head model, simulating the effect of the three-dimensional electrical stimulation vector field generated by electrode positions and potential and current parameters on fluid transport; Output optimized electrode configuration and treatment parameters to the control unit.

7. The electroosmotic delivery system according to claim 6, characterized in that: The control unit can independently control the potential and current of each electrode, and the output current is one of direct current and alternating current. The direct current waveform is ideal direct current, square wave, triangle wave, etc., and the alternating current waveform is sine wave, triangle wave, square wave, etc. The frequency is 0-100Hz and the current amplitude is 0.1-200mA.

8. The electroosmotic delivery system according to claim 6, characterized in that: The computer program modules are further configured to: selecting a target tissue region as a fluid drainage area; Selecting a receiving area as the fluid target location; The anode and cathode configurations of the electrodes were determined based on the simulation results to guide the directional transport of fluid from the discharge area to the receiving area.

9. An electroosmotic delivery system according to claim 6, characterized in that: Also includes: The drug delivery module is used to synchronously release drugs during electroosmotic delivery, wherein the drugs are guided to the target tissue area through the electroosmotic effect.

10. The electroosmotic delivery system according to claim 6, characterized in that: The medical image data includes at least one of computed tomography, magnetic resonance imaging, positron emission tomography, and diffusion tensor imaging.

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