Implantable electrode assembly and system

Abstract

The utility model discloses an implantable electrode assembly and system, the implantable electrode assembly comprises an electrode lead, the electrode lead comprises a stimulation end, a connection end and a middle segment connecting the stimulation end and the connection end; the first end of the core tube is inserted into the inner hole of the connecting end of the electrode wire and is in interference fit with the inner hole wall of the connecting end of the electrode wire to realize sealing, so that tissue fluid is prevented from entering the electrode wire through a gap between the inner hole wall of the connecting end of the electrode wire and the core tube; the handle is detachably installed at the second end, opposite to the first end, of the core tube, the handle and the core tube are connected in a sealed mode, and the tissue fluid is prevented from entering the core tube. According to the implantable electrode assembly and the implantable electrode system, liquid can be prevented from permeating into the inner hole of the electrode, and the internal structure of the electrode is protected.

Description

Technical Field

[0001] This utility model relates to the field of implantable medical device technology, and in particular to an implantable electrode assembly and system. Background Technology

[0002] Neuro-electrical stimulation (NES) technology is an important therapeutic approach widely used in the rehabilitation of neurological dysfunction and nerve injuries. This technology uses an implanted pulse generator and electrode system to apply electrical stimulation to specific nerve sites to help patients regain function. In practical applications, the pulse generator is connected to the electrodes via a converter; one end of the converter is inserted into the pulse generator's channel module, and the other end is connected to the electrode leads. Typically, a single pulse generator needs to be connected to multiple electrodes (e.g., two or four) to achieve precise stimulation of different target points.

[0003] However, existing technologies have the following problems:

[0004] 1. Difficulty in electrode identification: During surgery, medical staff need to correctly connect multiple electrodes to their corresponding converter interfaces. Because the electrodes look similar and lack effective distinguishing markings, incorrect connections are easily made, affecting treatment outcomes and even causing complications.

[0005] 2. Insufficient electrode protection: Electrode leads are usually hollow structures, which are easily deformed or damaged by external forces during subcutaneous puncture. There is also a risk of fluid seepage, which may affect electrode performance or cause infection.

[0006] Currently, the common method of protection is to add a protective sleeve to the outside of the electrode. However, the protective sleeve requires additional fixation (such as sutures) and needs to be removed after surgery, increasing the number of surgical steps and time. In addition, a thin protective sleeve with insufficient rigidity is prone to breakage, while a protective sleeve of appropriate thickness can make subcutaneous cannulation difficult, affecting surgical efficiency.

[0007] To address at least one of the aforementioned technical problems, this utility model proposes an implantable electrode assembly and system. Utility Model Content

[0008] The purpose of this invention is to provide an implantable electrode assembly and system that can prevent liquid from seeping into the electrode's inner pores and protect the internal structure of the electrode.

[0009] The objective of this utility model is achieved through the following technical solution:

[0010] On the one hand, this utility model provides an implantable electrode assembly, including:

[0011] An electrode lead, comprising a stimulating end, a connecting end, and an intermediate section connecting the stimulating end and the connecting end;

[0012] The core tube has its first end inserted into the inner hole of the connection end of the electrode wire and is press-fitted with the inner hole wall of the connection end of the electrode wire to prevent tissue fluid from entering the electrode wire through the gap between the inner hole wall of the connection end of the electrode wire and the core tube.

[0013] A handle is detachably mounted to the second end of the core tube opposite to the first end, and the handle and the core tube are sealed together to prevent tissue fluid from entering the core tube.

[0014] The beneficial effects of the above solution are: the first-level seal is formed by the interference fit between the core tube and the inner hole, which effectively prevents liquid from seeping into the electrode wire and protects the internal structure of the electrode assembly; in addition, the second-level seal is achieved by connecting the handle and the core tube, which prevents tissue fluid from entering the core tube.

[0015] Furthermore, the stiffness of the core tube is greater than the stiffness of the electrode wire.

[0016] The beneficial effects of the above solution are: by enhancing the overall structural strength, this utility model avoids deformation or breakage of the lead wire due to bending caused by external force during implantation, while maintaining the flexibility of the electrode lead wire to adapt to the physiological structure.

[0017] Furthermore, the core tube extends from the end of the connection end toward the middle section, with at least a portion of the core tube extending to the middle section.

[0018] The beneficial effects of the above solution are: by expanding the support range of the core tube, this utility model reduces the local stress concentration of the electrode wire caused by muscle activity or external force in the body, thereby reducing the risk of fatigue fracture.

[0019] Furthermore, the handle is threadedly connected to the second end of the core tube.

[0020] The beneficial effects of the above solution are: the present invention provides stable mechanical fixation through threaded connection, which can ensure sealing and facilitate quick assembly or disassembly, thereby improving surgical efficiency.

[0021] Furthermore, the implantable electrode assembly also includes:

[0022] A stop body is disposed at the second end of the core tube and presses against the end face of the connection end of the electrode wire to limit the depth of the core tube inserted into the inner hole.

[0023] The beneficial effects of the above solution are: by controlling the insertion depth of the core tube, this utility model avoids excessive insertion that could damage the internal structure of the wire, while ensuring the accurate position of the sealing surface and improving assembly consistency.

[0024] Furthermore, the outer diameter of the stop body is less than or equal to the outer diameter of the connecting end of the electrode wire.

[0025] The beneficial effects of the above solution are: this utility model avoids the block body protruding from the outer diameter of the wire, causing local tissue irritation or blockage of the implantation channel, and ensures a smooth implantation process.

[0026] On the other hand, this utility model provides an implantable electrode system, including: multiple sets of electrode structures, each set of electrode structures including at least one set of electrode components, and each of the electrode components being the above-mentioned implantable electrode components.

[0027] The beneficial effects of the above solution are: This utility model achieves multi-target synchronous stimulation through modularization, meeting complex treatment needs (such as multi-segment regulation of the spinal cord), while each component is independently sealed to ensure the overall safety of the system.

[0028] Furthermore, the electrode structure includes a first electrode assembly and a second electrode assembly for stimulating different target locations, and the first electrode assembly and the second electrode assembly are provided with different markings.

[0029] The beneficial effects of the above solution are: This utility model can quickly distinguish electrodes of different target points during surgery by marking them, avoiding misconnection (such as differences in color or length), and improving the accuracy and efficiency of the surgery.

[0030] Furthermore, the core tubes of the first electrode assembly and the second electrode assembly have different lengths, and both the core tubes of the first electrode assembly and the second electrode assembly are made of opaque materials.

[0031] The beneficial effects of the above solution are: this invention can identify the first electrode assembly and the second electrode assembly through a CT scan core tube after surgery, thereby determining whether the first electrode assembly and the second electrode assembly correspond to the correct target point. Furthermore, the handles of the first electrode assembly and the second electrode assembly are different colors.

[0032] The beneficial effects of the above solution are: This utility model enables the naked eye to identify electrode components that are adapted to target points in different orientations through color differences.

[0033] Compared with the prior art, the beneficial effects of this utility model include at least the following:

[0034] This invention forms a first-level seal by interfering with the inner hole of the core tube, which effectively prevents liquid from seeping into the electrode wire and protects the internal structure of the electrode assembly. In addition, a second-level seal is achieved by connecting the handle to the core tube, which prevents tissue fluid from entering the core tube. Attached Figure Description

[0035] Figure 1This is a schematic diagram of the structure of an implantable electrode according to an embodiment of the present invention.

[0036] Figure 2 This is a schematic diagram of the structure of an electrode wire according to an embodiment of the present invention.

[0037] Figure 3 This is a schematic diagram of the structure of the inner core component according to an embodiment of the present utility model.

[0038] In the figure: 10, inner hole; 11, first electrode lead; 12, second electrode lead; 13, stimulation end; 14, middle section; 15, connecting end; 21, first inner core assembly; 211, first stop body; 212, first core tube; 213, first handle; 22, second inner core assembly; 221, second stop body; 222, second core tube; 223, second handle. Detailed Implementation

[0039] Exemplary embodiments will now be described more fully with reference to the accompanying drawings. However, these exemplary embodiments can be implemented in many forms and should not be construed as limited to the embodiments set forth herein; rather, these embodiments are provided to make the present invention more comprehensive and complete, and to fully convey the concept of the exemplary embodiments to those skilled in the art. The same reference numerals in the drawings denote the same or similar structures, and therefore repeated descriptions of them will be omitted.

[0040] The terms used to express position and direction in this invention are illustrated with the accompanying drawings, but changes can be made as needed, and all such changes are included within the scope of protection of this invention.

[0041] Below, we will first briefly describe one application area of ​​the present invention (i.e., implantable devices). An implantable neurostimulation system (an implantable medical system) mainly includes: a stimulator implanted in the patient's body and a programmed device placed outside the patient's body. Existing neuromodulation technology mainly involves implanting electrodes into specific structures (i.e., target points) within the body through stereotactic surgery, and then having the stimulator implanted in the patient's body send discharge pulses to the target points via the electrodes, thereby modulating the electrical activity and function of the corresponding neural structures and networks, thereby improving symptoms and relieving pain. The stimulator can be any one of an implantable neurostimulation device, an implantable cardiac stimulation system (also known as a pacemaker), an implantable drug delivery system (IDDS), or a lead adapter. Examples of implantable neurostimulation devices include: Deep Brain Stimulation (DBS), Cortical Nerve Stimulation (CNS), Spinal Cord Stimulation (SCS), Sacral Nerve Stimulation (SNS), and Vagus Nerve Stimulation (VNS).

[0042] In some embodiments, the stimulator may include: an implantable pulse generator (IPG), electrode leads, and an extension lead disposed between the IPG and the electrode leads, through which data interaction between the IPG and the electrode leads is achieved. The IPG is implanted within the patient's body. Responding to programmed commands from a programmable device, controllable electrical stimulation energy is provided to the body's tissues via a sealed battery and circuitry. One or two controllable electrical stimuli are delivered to specific areas of the body's tissues via the implanted extension lead and electrode leads. The extension lead, used in conjunction with the IPG, serves as a medium for transmitting electrical stimulation signals, conveying the electrical stimulation signals generated by the IPG to the electrode leads. The electrode leads deliver electrical stimulation to specific areas of the body's tissues via their electrode contacts. The stimulator has one or more electrode leads on one or both sides, and each electrode lead has multiple electrode contacts.

[0043] In other embodiments, the stimulator may consist only of an implantable pulse generator and electrode leads. The implantable pulse generator may be embedded in the patient's skull, and the electrode leads may be implanted intracranially, with the implantable pulse generator directly connected to the electrode leads, eliminating the need for extension leads.

[0044] The electrode leads can be neurostimulation electrodes, delivering electrical stimulation to specific areas of tissue within the body via multiple electrode contacts. The stimulator has one or more electrode leads on one or both sides, each with multiple electrode contacts arranged uniformly or non-uniformly around the circumference of the lead. As an example, the electrode contacts can be arranged in a 4x3 array (a total of 12 contacts) around the circumference of the lead. The electrode contacts can include stimulation contacts and / or acquisition contacts. For example, the electrode contacts can be sheet-like, ring-like, or dot-like shapes.

[0045] In some cases, the stimulated tissue can be the patient's brain tissue, and the stimulated site can be a specific area of ​​the brain tissue. The stimulated site generally differs depending on the patient's disease type, the number of stimulation contacts (single-source or multi-source), the application of one or more specific electrical stimulation signals (single-channel or multi-channel), and the stimulation parameter data. It can be assumed that using multiple stimulation contacts (multi-source, multi-channel) will generate a larger amount of data compared to using a single-source, single-channel approach.

[0046] This invention does not limit the types of diseases to which it is applicable, but can include those applicable to deep brain stimulation (DBS), spinal cord stimulation (SCS), pelvic stimulation, gastric stimulation, peripheral nerve stimulation, and functional electrical stimulation. Specifically, DBS can be used to treat or manage diseases including, but not limited to: spastic disorders (e.g., epilepsy), pain, migraines, mental illnesses (e.g., major depressive disorder (MDD)), bipolar disorder, anxiety disorders, post-traumatic stress disorder, mild depression, obsessive-compulsive disorder (OCD), behavioral disorders, mood disorders, memory disorders, mental state disorders, mobility disorders (e.g., essential tremor or Parkinson's disease), Huntington's disease, Alzheimer's disease, drug addiction, autism, or other neurological or psychiatric disorders and impairments.

[0047] Stimulation parameters may include: stimulation frequency (e.g., the number of electrical stimulation pulse width signals per unit time 1 second, in Hz), pulse width (the duration of each pulse width, in μs), current amplitude (generally expressed as voltage, i.e., the intensity of each pulse width, in V), timing (e.g., continuous or triggered), stimulation mode (including one or more of current mode, voltage mode, timed stimulation mode, and cyclic stimulation mode), physician control upper and lower limits (the range that physicians can adjust), and patient control upper and lower limits (the range that patients can adjust independently).

[0048] This utility model introduces an implantable electrode assembly and an implantable electrode system.

[0049] The implantable electrode assembly of this invention includes: an electrode lead, a core tube, and a handle. Furthermore, the implantable electrode assembly may also include: a stop body.

[0050] refer to Figure 2 The electrode lead includes a stimulation end 13, an intermediate segment 14, and a connecting end 15, with the intermediate segment 14 connecting the stimulation end 13 and the connecting end 15. Parts of the stimulation end 13 and the intermediate segment 14 are located intracranially, while the remainder is located extracranially, and the connecting end 15 is used to connect to the converter.

[0051] The first end of the core tube is inserted into the inner hole 10 of the electrode wire connection end, and is press-fitted with the inner hole 10 wall of the electrode wire connection end 15 to prevent tissue fluid from entering the electrode wire through the gap between the inner hole wall of the electrode wire connection end and the core tube, thus forming a first-level seal between the core tube and the electrode wire. Specifically, it prevents tissue fluid from entering the electrode wire through the gap between the electrode wire and the core tube. In application, the core tube extends from the end of the connection end 15 towards the middle section 14, with at least a portion of the core tube extending to the middle section 14. In practical applications, the stiffness of the core tube is greater than that of the electrode wire, and the outer diameter of the core tube is slightly larger than the inner diameter of the inner hole 10 of the electrode wire connection end 15.

[0052] The handle is detachably installed at the second end of the core tube opposite the first end. The handle and the core tube form a sealed connection, creating a second-level seal to prevent tissue fluid from entering the core tube. In application, the handle is threaded to the second end of the core tube, allowing for easy removal of the handle before use. In practical applications, a sealing structure is provided between the handle and the second end of the core tube to further improve the seal between them.

[0053] A stop body is located at the second end of the core tube and presses against the end face of the electrode wire connection end to limit the depth of the core tube insertion into the inner hole 10. In application, the stop body is located around the second end of the core tube, and the outer diameter of the stop body is less than or equal to the outer diameter of the electrode wire connection end 15. In practical applications, the stop body is made of an elastic sealing material, which can further enhance the sealing between the core tube and the electrode wire.

[0054] The implantable electrode system of this invention includes multiple sets of electrode structures, with different electrode structures used to stimulate different target nuclei.

[0055] In application, each set of electrode structures is marked with different labels to distinguish the target nuclei stimulated by different electrode structures.

[0056] In some embodiments, the electrodes are identified by color, with each group of electrode structures using a different color or color scheme. For example, electrode structures of the same color scheme are used to stimulate the same type of nucleus or nuclei with the same name. Electrode structures of different color schemes are used to stimulate different types of nuclei. When medical personnel use the electrode structures, they can accurately identify each group of electrode structures with the naked eye and determine the target nucleus corresponding to each group of electrode structures, thereby improving treatment efficiency and saving intraoperative time.

[0057] In some embodiments, the length is indicated, with each group of electrode structures having a different length. The electrode structures are made of opaque material. For example, electrode structures of the same length interval are used to stimulate the same type of nucleus or nuclei with the same name. Electrode structures of different length intervals are used to stimulate different types of nuclei. In application, n to N is divided into multiple equally spaced length intervals. In practical applications, after the electrodes are implanted intracranially, the length of the electrode structures can be identified using CT scans to distinguish the electrode structures and confirm whether the electrode structures are connected to the correct target nucleus.

[0058] In some embodiments, the markings are called patterns, and each group of electrode structures has different patterns, but each group of electrode structures has the same series of patterns. The electrode structures are made of opaque material. For example, electrode structures with the same series of patterns are used to stimulate the same type of nucleus or nuclei with the same name. Electrode structures with different series of patterns are used to stimulate different types of nuclei. In application, after the electrodes are implanted intracranially, the patterns of the electrode structures can be identified using CT scans to distinguish the electrode structures and confirm whether the electrode structures are connected to the correct target nuclei.

[0059] Each electrode structure of this invention includes at least one set of electrode components, with different electrode components used to stimulate different regions of the target nucleus.

[0060] Each electrode structure includes a first electrode assembly and a second electrode assembly, both of which are implantable electrode assemblies as described above. The first and second electrode assemblies are used to stimulate different target locations.

[0061] refer to Figure 1 and 3 The first electrode assembly of this utility model includes a first electrode wire 11, a first core tube 212, a first handle 213, and a first stop body 211.

[0062] The first electrode lead 11 includes a stimulation end 13, an intermediate segment 14, and a connecting end 15, with the intermediate segment 14 connecting the stimulation end 13 and the connecting end 15. Parts of the stimulation end 13 and the intermediate segment 14 are located intracranially, while the rest are located extracranially. The connecting end 15 is used to connect to the transducer, and the stimulation end 13 is used to stimulate the nuclei on the left side of the brain region.

[0063] In application, the outer diameter of the first stop body 211 is larger than the inner diameter of the inner hole 10 of the connecting end 15 of the first electrode wire 11. Preferably, the diameter of the first stop body 211 is equal to or slightly smaller than the outer diameter of the connecting end 15 of the first electrode wire 11. This ensures that the first stop body 211 can effectively press against the connecting end 15 to limit the position of the first core tube 212, while also avoiding increasing the overall outer diameter of the system, which would make subcutaneous cannulation difficult.

[0064] In practical applications, the diameter of the first core tube 212 is smaller than the diameter of the first stop body 211, and slightly larger than the inner diameter of the inner hole 10 of the connecting end 15 of the first electrode wire 11. Specifically, one end of the first core tube 212 is connected to the first side of the first stop body 211, and the other end of the first core tube 212 is inserted into the inner hole 10 of the connecting end 15 of the first electrode wire 11, and is interference-fitted with the inner hole 10 of the connecting end 15 of the first electrode wire 11. Furthermore, the stiffness of the first core tube 212 is greater than the stiffness of the first electrode wire 11, which can increase the overall stiffness of the device to a certain extent.

[0065] During implementation, the first handle 213 is detachably connected to the first core tube 212. The first handle 213 facilitates gripping and placement. Before using the electrode, the first handle 213 is removed. Preferably, the first handle 213 is threadedly connected to the first core tube 212.

[0066] refer to Figure 1 and 3 The second electrode assembly of this utility model includes a second electrode wire 12, a second core tube 222, a second handle 223, and a second stop body 221.

[0067] The second electrode lead 12 includes a stimulation end 13, an intermediate segment 14, and a connecting end 15, with the intermediate segment 14 connecting the stimulation end 13 and the connecting end 15. Parts of the stimulation end 13 and the intermediate segment 14 are located intracranially, while the remainder is located extracranially. The connecting end 15 is used to connect to the transducer, and the stimulation end 13 is used to stimulate the nuclei on the right side of the brain region.

[0068] In application, the outer diameter of the second stop body 221 is larger than the inner diameter of the inner hole 10 of the connecting end 15 of the second electrode wire 12. Preferably, the diameter of the second stop body 221 is equal to or slightly smaller than the outer diameter of the connecting end 15 of the second electrode wire 12. This ensures that the second stop body 221 can effectively press against the connecting end 15 to limit the position of the second core tube 222, while also avoiding increasing the overall outer diameter of the system, which would make subcutaneous cannulation difficult.

[0069] In practical applications, the diameter of the second core tube 222 is smaller than the diameter of the second stop body 221, and slightly larger than the inner diameter of the inner hole 10 of the connecting end 15 of the second electrode wire 12. Specifically, one end of the second core tube 222 is connected to the first side of the second stop body 221, and the other end of the second core tube 222 is inserted into the inner hole 10 of the connecting end 15 of the second electrode wire 12, and is interference-fitted with the inner hole 10 of the connecting end 15 of the second electrode wire 12. Furthermore, the stiffness of the second core tube 222 is greater than the stiffness of the second electrode wire 12, which can increase the overall stiffness of the device to a certain extent.

[0070] During implementation, the second handle 223 is detachably connected to the second core tube 222, which not only facilitates gripping and placement but also allows the second handle 223 to be removed before using the electrode. Preferably, the second handle 223 is threadedly connected to the second core tube 222.

[0071] The first electrode assembly and the second electrode assembly of this invention are marked with different symbols to distinguish them. The first electrode assembly is used to stimulate nuclei on the left side of the brain region, and the second electrode assembly is used to stimulate nuclei on the right side of the brain region.

[0072] In some embodiments, the first electrode assembly and the second electrode assembly are identified by different colors. Preferably, the first stop body 211 and the second stop body 221 are different colors within the same color family, and the first handle 213 and the second handle 223 are different colors within the same color family. When medical personnel use the electrode assemblies, they can accurately identify the first electrode assembly to which the first electrode lead 11 belongs, and the second electrode lead 12 to which the first electrode assembly and the second electrode assembly belong, by visual inspection. By identifying the first electrode assembly and the second electrode assembly, it can be determined that the first electrode lead 11 of the first electrode assembly is used to stimulate nuclei on the left side of the brain region, and the second electrode lead 12 of the second electrode assembly is used to stimulate nuclei on the right side of the brain region, thereby improving treatment efficiency and saving intraoperative time.

[0073] In some embodiments, the length of the first electrode assembly and the second electrode assembly is different, and each electrode assembly is made of an opaque material. Preferably, within a certain length range, the lengths of the first core tube 212 and the second core tube 222 are different, that is, the length difference between the first core tube 212 and the second core tube 222 is less than a length threshold, and both the first core tube 212 and the second core tube 222 are made of opaque material. In application, after the electrodes are implanted into the cranium, the lengths of the first inner core assembly 21 and the second inner core assembly 22 can be identified by CT scan to distinguish the first electrode assembly to which the first electrode lead 11 belongs and the second electrode assembly to which the second electrode lead 12 belongs, confirming whether the first electrode lead 11 of the first electrode assembly is connected to the target nucleus on the left side of the brain region, and whether the second electrode lead 12 of the second electrode assembly is connected to the target nucleus on the right side of the brain region.

[0074] In some embodiments, the markings are different on the first electrode assembly and the second electrode assembly, and each electrode assembly is made of an opaque material. Preferably, the first electrode assembly and the second electrode assembly have the same series of markings. For example, the first core tube 212 and the second core tube 222 have different markings from the same series, and both the first core tube 212 and the second core tube 222 are made of opaque material. In application, after the electrodes are implanted into the cranium, the lengths of the first inner core assembly 21 and the second inner core assembly 22 can be used to distinguish the first electrode assembly to which the first electrode lead 11 belongs and the second electrode assembly to which the second electrode lead 12 belongs, thus confirming whether the first electrode lead 11 of the first electrode assembly connects to the target nucleus on the left side of the brain region, and whether the second electrode lead 12 of the second electrode assembly connects to the target nucleus on the right side of the brain region.

[0075] Although embodiments of the present invention have been shown and described above, it is understood that the above embodiments are exemplary and should not be construed as limiting the present invention. Those skilled in the art can make changes, modifications, substitutions and alterations to the above embodiments within the scope of the present invention without departing from the principles and spirit of the present invention, and all such changes should fall within the protection scope of the claims of the present invention.

Claims

1. An implantable electrode assembly, characterized in that, include: An electrode lead, the electrode lead including a stimulating end, a connecting end, and an intermediate section connecting the stimulating end and the connecting end; The core tube has its first end inserted into the inner hole of the connection end of the electrode wire and is press-fitted with the inner hole wall of the connection end of the electrode wire to achieve a seal, thereby preventing tissue fluid from entering the interior of the electrode wire through the gap between the inner hole wall of the connection end of the electrode wire and the core tube. A handle is detachably mounted to the second end of the core tube opposite to the first end, and the handle and the core tube are sealed together to prevent tissue fluid from entering the core tube.

2. The implantable electrode assembly according to claim 1, characterized in that, The stiffness of the core tube is greater than the stiffness of the electrode wire.

3. The implantable electrode assembly according to claim 1, characterized in that, The core tube extends from the end of the connection end toward the middle section, and at least a portion of the core tube extends to the middle section.

4. The implantable electrode assembly according to claim 1, characterized in that, The handle is threadedly connected to the second end of the core tube.

5. The implantable electrode assembly according to claim 1, characterized in that, Also includes: A stop body is disposed at the second end of the core tube and presses against the end face of the connection end of the electrode wire to limit the depth of the core tube inserted into the inner hole.

6. The implantable electrode assembly according to claim 5, characterized in that, The outer diameter of the stop body is less than or equal to the outer diameter of the connecting end of the electrode wire.

7. An implantable electrode system, characterized in that, include: Multiple sets of electrode structures, each set of electrode structures including at least one set of electrode components, each of the electrode components being an implantable electrode component as described in any one of claims 1 to 6.

8. The implantable electrode system according to claim 7, characterized in that, The electrode structure includes a first electrode assembly and a second electrode assembly for stimulating different target locations, and the first electrode assembly and the second electrode assembly are provided with different markings.

9. The implantable electrode system according to claim 8, characterized in that, The core tubes of the first electrode assembly and the second electrode assembly have different lengths, and both the core tubes of the first electrode assembly and the second electrode assembly are made of opaque materials.

10. The implantable electrode system according to claim 8, characterized in that, The handle of the first electrode assembly is a different color than the handle of the second electrode assembly.

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