Deep brain stimulation electrode and stimulation system

Abstract

The invention relates to the field of medical equipment, in particular to a deep brain stimulation electrode and a stimulation system, the electrode penetrates through or is inserted into one or more intracerebral functional targets and is used for outputting one or more electrical stimulation signals to the intracerebral functional targets, the electrode comprises a plurality of contact sets, each contact set comprises a plurality of contacts, and the contacts are arranged in the contact sets. Each contact can independently output or not output an electrical stimulation signal, at least one contact group is provided with two groups, each group comprises two contacts, and the number of the contacts of the contact group is greater than that of the corresponding target spots, so that the contact group can cover the corresponding target spots; allowance is provided for adjustment of implantation positions of other contact groups, stimulation requirements of different patients on different intracerebral functional targets are met, and multi-target joint precise stimulation in a long stimulation area is realized.

Description

Technical Field

[0001] This invention relates to the field of medical devices, and more particularly to a deep brain stimulation electrode and stimulation system. Background Technology

[0002] Deep brain stimulation (DBS) therapy uses stereotactic precision to implant electrodes into specific nuclei deep within the brain. Under the control of a pulse generator, electrical pulses are emitted through the electrodes to stimulate the target area. Specific stimulation parameters are then provided by an externally programmed device to alter the excitability of these nuclei, thereby modulating neural function. With the development of neurostimulation technology, DBS has proven effective for an increasing number of symptoms. Symptoms of various limb and mental disorders, including Parkinson's disease, essential tremor or Parkinsonian tremor, dystonia, epilepsy, and obsessive-compulsive disorder, have shown significant improvement after using this therapy.

[0003] In clinical treatment, when faced with complex conditions such as mental illness and movement disorders, medical teams typically choose to stimulate different functional targets in the brain. However, because different functional targets have different shapes (irregular bodies), the orientation of each target relative to the electrode varies after the electrode is implanted deep in the brain. Furthermore, over a long period of implantation, the electrode may shift relative to the target, making existing electrodes unable to meet the clinical requirements for high-precision combined stimulation of multiple targets within a long stimulation area. Summary of the Invention

[0004] In view of this, the present invention provides a deep brain stimulation electrode and stimulation system.

[0005] In a first aspect, the present invention provides a deep brain stimulation electrode, wherein when the electrode is directionally implanted into the brain, the electrode passes through or is inserted into one or more functional target points in the brain, for outputting one or more electrical stimulation signals to the functional target points in the brain.

[0006] The distal portion of the electrode is provided with a contact assembly, which includes multiple contact groups arranged along the length of the distal portion. Each contact group includes multiple contacts spaced apart along the length of the electrode, and each contact group is used for a different functional target point in the brain. The contacts are either ring contacts or directional contacts, and the directional contacts are arranged in a ring in the form of directional contact groups. Each contact can be individually configured to output or not output the electrical stimulation signal.

[0007] Wherein, at least one of the contact groups is provided with two groups along the distal length direction, and each group includes at least one directional contact group.

[0008] In a second aspect, the present invention provides a stimulation system comprising a pulse generator and the aforementioned electrodes, wherein the electrodes are electrically connected to the pulse generator, and the pulse generator is configured to output one or more electrical stimulation signals to each of the contact groups.

[0009] The beneficial effects of this invention include:

[0010] 1. It has a wider stimulation range, enabling stimulation of one or more target points, and outputting one or more electrical stimulation signals to the functional target points in the brain, thereby improving the accuracy of stimulation and the therapeutic effect, and reducing the occurrence of side effects.

[0011] 2. By adopting a margin design for at least one contact group, two groups are set up, each group including two contacts. The number of contacts in the contact group exceeds the corresponding target point. During electrode implantation, it is ensured that the contact group can cover its corresponding target point, providing a margin for position adjustment of the remaining contact groups. This adapts to the different brain functional target stimulation needs of different patients and achieves precise stimulation of multiple targets in a long stimulation area.

[0012] 3. Each contact group corresponds to different functional targets in the brain. Each contact can be set to output or not output electrical stimulation signals independently, which provides support for the innovation of multi-target combined stimulation therapy in clinical practice, makes it easier for doctors to try more target combination stimulation methods, and helps to further improve the accuracy and therapeutic effect of electrical stimulation. Attached Figure Description

[0013] The above and other objects, features and advantages of the present invention will become clearer from the following description of embodiments of the invention with reference to the accompanying drawings, in which:

[0014] Figure 1 This is a schematic diagram of the structure of the pulse generator implanted in the skull in Embodiment 1 of the present invention.

[0015] Figure 2 This is a schematic diagram of the pulse generator implanted in the chest in Embodiment 2 of the present invention.

[0016] Figure 3 This is a schematic diagram of the electrode structure in Embodiment 3 of the present invention.

[0017] Figure 4 This is a schematic diagram of the arrangement structure of the conduit and wire in Embodiment 3 of the present invention.

[0018] Figure 5 This is a schematic diagram of the arrangement structure of the conduit and wire in Embodiment 4 of the present invention.

[0019] Figure 6 This is a schematic diagram of the arrangement structure of the conduit and wire in Embodiment 5 of the present invention.

[0020] Figure 7 This is a schematic diagram of the electrode structure in Embodiment 6 of the present invention.

[0021] Figure 8This is a schematic diagram of three distribution structures of directional contacts in the circumferential direction in this invention.

[0022] Figure 9 This is a schematic diagram of the electrode structure in Embodiment 7 of the present invention.

[0023] Figure 10 This is a schematic diagram of the electrode structure in Embodiment 8 of the present invention.

[0024] Figure 11 This is a schematic diagram of the combined stimulation of three target points by the electrode in Embodiment 3 of the present invention.

[0025] Explanation of reference numerals in the attached figures:

[0026] 10 - Pulse generator; 20 - Electrode; 30 - Extension wire;

[0027] 21, 21a, 21b - catheter; 22 - guidewire; 23 - first contact group; 24 - second contact group; 25 - third contact group; 26 - positioning ring; 27 - connecting ring; 28 - annular contact; 29, 29a, 29b - directional contact group;

[0028] 211 - distal end; 212 - proximal end; 213, 213a, 213b - central cavity; 214, 214a - peripheral cavity; 215 - bifurcated structure; 216 - outer tube; 217 - inner tube;

[0029] 241 - Group 1; 242 - Group 2;

[0030] 261-Protrusion. Detailed Implementation

[0031] The present invention will now be described in further detail with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the invention and not intended to limit it. Furthermore, it should be noted that, for ease of description, the accompanying drawings show only the parts relevant to the present invention, and not all of the structures.

[0032] In the description of this invention, unless otherwise explicitly specified and limited, the terms "connected," "linked," and "fixed" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components. Those skilled in the art can understand the specific meaning of the above terms in this invention based on the specific circumstances.

[0033] In the description of this embodiment, the terms "upper," "lower," "right," etc., refer to the orientation or positional relationship shown in the accompanying drawings. They are used only for ease of description and simplification of operation, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on the present invention. In addition, the terms "first" and "second" are used only for distinction in description and have no special meaning.

[0034] This invention proposes a deep brain stimulation electrode and stimulation system. The stimulation system includes a pulse generator and electrodes, with the pulse generator and electrodes being detachably electrically connected. In this embodiment, the pulse generator can be any type of implantable pulse generator (IPG) in the prior art, which can be implanted in the patient's body, such as in the chest, brain, or other body parts.

[0035] Example 1

[0036] Figure 1 This is a schematic diagram of the structure of the pulse generator 10 implanted in the skull in Embodiment 1 of the present invention.

[0037] like Figure 1 As shown, this embodiment provides a neurostimulation system, including a pulse generator 10 and electrodes 20. The pulse generator 10 is implanted in the patient's head and fixed to the skull, while the electrodes 20 are implanted deep within the patient's brain. The specific implantation location can be determined by constructing a three-dimensional model of the patient's skull preoperatively and selecting the implantation location based on the skull thickness at various points in the three-dimensional model. Then, a groove is cut into the patient's skull according to the selected location, and the pulse generator 10 is installed within the skull groove. Depending on the thickness of the pulse generator 10, the skull thickness, etc., the pulse generator 10 can be completely embedded inside the skull or partially protruding from the skull surface.

[0038] Example 2

[0039] Figure 2 This is a schematic diagram of the pulse generator 10 implanted in the chest in Embodiment 2 of the present invention.

[0040] like Figure 2 As shown, this embodiment provides a nerve stimulation system, including a pulse generator 10 and an electrode 20. The pulse generator 10 can also be implanted in a location away from the head, such as under the skin of the patient's chest, and the electrode 20 passes under the skin of the neck. An extension lead 30 extends from the chest to the neck, and the electrode 20 is connected to the pulse generator 10 through the extension lead 30.

[0041] In this invention, the pulse generator 10 sends an electrical stimulation signal to the electrode 20 according to a combination of electrical stimulation parameters, and the electrode 20 transmits the electrical stimulation signal to the target point through contacts. The aforementioned combination of electrical stimulation parameters may include one or more of the following parameters:

[0042] Frequency, such as the number of electrical stimulation pulses per second, is measured in Hz.

[0043] Pulse width, the duration of each pulse, in μs;

[0044] Amplitude, usually expressed as voltage or current, is the intensity of each pulse, measured in V or I.

[0045] Timing can be either continuous or clustered, with clustered behavior referring to non-continuous temporal behavior consisting of multiple processes.

[0046] Stimulation modes include one or more of the following: current mode, voltage mode, timed stimulation mode, and cyclic stimulation mode;

[0047] The doctor's control limits are the upper and lower limits (the range that the doctor can adjust) and the patient's control limits are the upper and lower limits (the range that the patient can adjust independently).

[0048] Example 3

[0049] Figure 3 This is a schematic diagram of electrode 20 in Embodiment 3 of the present invention.

[0050] This embodiment provides a deep brain stimulation electrode, one end of which ( Figure 3 The left end is defined as the distal 211, which extends deep into the brain; the other end ( Figure 3 The right end is defined as the proximal end 212, which is usually located outside or near the outside of the body.

[0051] The deep brain stimulation electrode 20 of this invention passes through or is inserted into one or more functional target points in the brain, and is used to output one or more electrical stimulation signals to the functional target points in the brain. Its distal end 211 is provided with a contact assembly, which includes multiple contact groups arranged along the length of the distal end 211. Each contact group includes multiple contacts, and each contact group corresponds to a different functional target point in the brain. Each contact can be individually set to output or not output an electrical stimulation signal. The contacts are either ring contacts or directional contacts, with directional contacts arranged in a ring in the form of directional contact groups.

[0052] At least one contact group is provided with two groups along the length direction of the distal end 211, each group including multiple contacts, and each group including at least one directional contact group 29, the directional contact group 29 including multiple directional contacts. For example... Figure 3As shown, the contact assembly includes a first contact group 23, a second contact group 24, and a third contact group 25. The first contact group 23 is located near the proximal end 212, the third contact group 25 is located near the distal end 211, and the second contact group 24 is located between the first contact group 24 and the third contact group 25. The first contact group 23 and the third contact group 25 each include two annular contacts 28, which are used to form an annular electric field around the circumference of the electrode 20, thereby achieving omnidirectional stimulation of the surrounding tissue around the contact. Each group of the second contact group 24 includes two directional contact groups 29 spaced apart along the length direction. Each directional contact group 29 includes three directional contacts, which are used to provide directional stimulation in the directional direction of the electrode 20 around its circumference.

[0053] In this embodiment, the group closer to the first contact group 23 is defined as the first group 241, and the other is defined as the second group 242. When stimulating one or more different functional targets in the brain in combination, the second contact group 24 serves as a margin design contact group, with more contacts than the corresponding targets. During electrode implantation, this ensures that the second contact group 24 covers its corresponding target, while providing leeway for adjusting the implantation position of other contact groups. This facilitates precise combined stimulation of multiple targets within a long stimulation region. Each contact can be set to output one of multiple electrical stimulation signals, and each contact can be individually set to output or not output an electrical stimulation signal. This supports innovation in multi-target combined stimulation therapy in clinical practice, allowing doctors to try more target combination stimulation methods, and helps to further improve the accuracy and therapeutic effect of electrical stimulation.

[0054] Electrode 20 also includes a conduit 21 and a wire disposed within the conduit 21. One end of the conduit 21 is designated as the distal end 211, and the other end of the conduit 21 is designated as the proximal end 212. The proximal end 212 is provided with connecting rings 27. The number of connecting rings 27 is equal to the total number of annular contacts 28 and directional contacts. The annular contacts 28 and directional contacts are respectively connected to different connecting rings 27 one-to-one through wires. Figure 3 In the example, there are sixteen connecting rings 27, four annular contacts 28, and four groups of directional contacts 29, each group including three directional contacts arranged in a ring, for a total of twelve directional contacts.

[0055] In this invention, polyurethane is used between adjacent contacts to prevent short circuits. Other materials and structures of insulating materials can also be used. Silicone rubber can be injected between the annular contact 28 and the conduit 21 as a filler to improve the structural stability of the annular contact 28 and increase the stiffness and structural strength of the distal end 211.

[0056] Along the length of electrode 20, the interval between two adjacent contact groups is greater than or equal to 0.5 mm, and the interval between two adjacent contacts within a contact group is greater than or equal to 0.5 mm. The annular contact 28 can be formed by rolling sheet material or by cutting tubing into segments of a predetermined length. The length of the annular contact 28 is between 1 mm and 3 mm, preferably 1 mm or 1.5 mm. The material of the annular contact 28 is a biocompatible metallic material, such as platinum, platinum alloy, iridium, iridium alloy, titanium, titanium alloy, stainless steel, nickel-titanium alloy, or cobalt-based alloy, or one or more of these. The directional contact is made of the same material as the annular contact 28. The directional contact can be circular, elliptical, rectangular, or rhomboid in shape, and is bent along the circumference of the conduit 21. The maximum dimension of the directional contact in the length direction of its distal end 211 is 0.5 mm to 3 mm, preferably 1.5 mm. If the size of the directional contact point is too small, its contact area with the target point will be small, resulting in poor conductivity and affecting the stimulation effect; if the length is too large, it will result in a large stimulation range, which may easily stimulate surrounding tissues and produce side effects.

[0057] It should be noted that after electrode 20 is implanted in the brain, the doctor can set the stimulation program of pulse generator 10 using an external programming device. The pulse generator is used to output one or more electrical stimulation signals to each contact group. The pulse generator controls whether each contact can output an electrical stimulation signal or not through an internal switching circuit. All directional contacts in a directional contact group 29 simultaneously provide the same stimulation output, and the stimulation range and effect are comparable to the stimulation output of the ring contact 28.

[0058] refer to Figure 3 and Figure 11 As shown, electrodes are inserted into multiple functional target points in the brain. Target points P1, P2, and P3 are three target points with different functions in the brain. The first contact group 23 corresponds to target point P1 and provides omnidirectional stimulation. The second contact group 24 corresponds to target point P2 and provides directional stimulation. The third target group 25 corresponds to target point P3 and provides omnidirectional stimulation. The second contact group 24 employs a margin design, setting up two groups, each group including two directional contact groups 29. The number of contacts in the second contact group 24 exceeds the corresponding target points, ensuring that the contact group can pass through or insert into the predetermined target points. When there is a misalignment between the second contact group 24 and the target point, directional stimulation can be applied to the target point by selecting a suitable directional contact, achieving precise combined stimulation of multiple target points within a long stimulation region. In this example, target point P1 is the caudal undefined zone (Czi), target point P2 is the subthalamic nucleus (STN), and target point P3 is the substantia nigra reticularis (SNr). During stimulation therapy, the first contact group 23 can be selected to correspond to the caudal indeterminate zone Czi; and / or the second contact group 24 can correspond to the subthalamic nucleus STN; and / or the third contact group 25 can correspond to the substantia nigra reticularis SNr.

[0059] Electrode 20 also includes a positioning ring 26 capable of being visualized under X-rays. The positioning ring 26 is located at the distal end 211 and on the side of the contact assembly near the proximal end 212. The positioning ring 26 has an extension 261 extending along the circumferential direction of electrode 20. The extension length of the extension 261 is at least 0.5 mm, and the extension 261 is used to position the direction of the contact. The positioning ring 26 is made of a metal material with lower X-ray permeability than the conduit, such as platinum-iridium alloy or tantalum.

[0060] In some embodiments of the present invention, electrode 20 further includes a metal mesh sleeve (not shown), which is sleeved on the outside of catheter 21, located between proximal end 212 and distal end 211. The metal mesh sleeve is made of one or more of the following biocompatible materials: platinum, platinum alloy, iridium, iridium alloy, titanium, titanium alloy, stainless steel, nickel-titanium alloy, and chromium-tungsten (molybdenum) alloy. In the high-frequency RF magnetic field of MRI, the metal mesh sleeve, as a flexible conductive layer, can shield the wires inside electrode 20, shunt the induced current on the wires, thereby reducing the current density at the contact point, suppressing contact heating, and improving the safety of the stimulation system in magnetic resonance imaging.

[0061] Figure 4 This is a schematic diagram of the arrangement structure of the conduit and wire in Embodiment 3 of the present invention.

[0062] like Figure 3-4 As shown, the catheter 21 has a central cavity 213 and one or more peripheral cavities 214 surrounding the central cavity 213. The axis of the central cavity 213 coincides with the axis of the catheter 21, while the peripheral cavities 214 are spaced apart from and independently arranged from the central cavity 213. Multiple peripheral cavities 214 extend spirally around the central cavity 213 for at least a certain length of 20-3000 mm (e.g., 300 mm, 500 mm, 1000 mm, 2000 mm, etc.) from the middle of the catheter 21 to both ends. The central cavity 213 is used to thread metal wires to provide sufficient rigidity during the implantation of the electrode 20 into the brain, facilitating the implantation of the electrode 20.

[0063] In this invention, the conductor includes multiple guide wires 22, the number of which is the same as the number of connecting rings 26 at the proximal end 212. The guide wires 22 are made of materials such as nickel-cobalt alloy. An insulating coating is provided on the surface of the guide wires 22, and the insulating coating material is any one of PFA, ETFE, PTFE, and PI. The guide wires 22 extend from one end of the catheter 21 to the other end of the catheter 21 through peripheral cavities 214, and one or more guide wires 22 can be disposed in each peripheral cavity 214. Figure 4 In the example, eight peripheral cavities 214 are provided, and two guide wires 22 are provided in each peripheral cavity 214.

[0064] Example 4

[0065] Figure 5This is a schematic diagram of the arrangement structure of the conduit and wire in Embodiment 4 of the present invention.

[0066] This invention provides a deep brain stimulation electrode, which differs from the electrode in Embodiment 3 in the arrangement of the conduit and lead wires. For example... Figure 5 As shown, the catheter 21a structure includes an inner tube 217 and an outer tube 216. The inner tube 217 is nested inside the outer tube 216, and their axes coincide. The inner tube 217 has a central cavity 213a, and the outer diameter of the inner tube 217 is smaller than the inner diameter of the outer tube 216, thus forming an annular peripheral cavity 214a between the outer tube 216 and the inner tube 217. The wire is disposed within the peripheral cavity 214a, and the multi-strand guide wire 22 of the wire extends spirally around the inner tube 217. The cavity of the inner tube 217 is the central cavity 213a for threading the metal wire. Compared to Figure 4 The structure of catheter 21, Figure 5 The example replaces multiple independent peripheral cavities 214 with a single annular peripheral cavity 214a.

[0067] Example 5

[0068] This invention provides a deep brain stimulation electrode, which differs from the electrode in Embodiment 3 in the arrangement of the conduit and lead wires. For example... Figure 6 As shown, catheter 21b only has a central cavity 213b, and the multi-strand guidewire 22 of the catheter is arranged around the inner wall of the central cavity 213b. Compared to Figure 4 and Figure 5 The outer cavities 214 and 214a were eliminated, and the remaining space in the central cavity 213b, after removing the space occupied by the wires, was used to thread metal wires.

[0069] In this invention, regardless of the structure of the conduits 21, 21a, and 21b selected, the wire extends in a spiral shape at least in the middle section of the conduits 21, 21a, and 21b, thereby improving the elasticity of the electrode 20 and reducing the probability of wire breakage. The conduits 21, 21a, and 21b are made of polyurethane, and their outer diameter is any value between 1mm and 2mm, such as 1mm, 1.2mm, 1.5mm, 1.8mm, 2mm, etc.

[0070] Example 6

[0071] This embodiment of the invention provides a deep brain stimulation electrode, which differs from Embodiment 3 in the structure of the proximal end 212 of the electrode 20. In this embodiment, the proximal end 212 may be provided with one, two, or more connecting segments, which are used to connect to a pulse generator. Figure 7As shown, the conduit 21 has a bifurcation structure 215 with a bifurcation angle between 30° and 60°. Two connecting segments of equal length are provided through the bifurcation structure 215. The total number of connecting rings 27 in the two connecting segments is equal to the total number of annular contacts 28 and directional contacts. There are a total of sixteen annular contacts 28 and directional contacts. Specifically, there are four annular contacts 28 and four directional contact groups 29. The first group 241 and the second group 242 each include two directional contact groups 29, for a total of twelve directional contacts. Each connecting segment has eight connecting rings 27, connecting two annular contacts 28 and six directional contacts within the same group.

[0072] Figure 8 This is a schematic diagram of three distribution structures of the directional contact points in the circumferential direction according to the present invention.

[0073] like Figure 8 As shown, in this invention, the distal end of the electrode 20 may be provided with two, three, four or more directional contacts arranged in a ring to form a directional contact group. Directional contact group 29a includes two directional contacts and is capable of outputting stimulation in two directions; directional contact group 29 includes three directional contacts and is capable of outputting stimulation in three directions; directional contact group 29b includes four directional contacts and is capable of outputting stimulation in four directions.

[0074] Example 7

[0075] Figure 9 This is a schematic diagram of the electrode structure in Embodiment 7 of the present invention.

[0076] This embodiment provides a deep brain stimulation electrode, which differs from Embodiment 3 in the contact structure within the contact group. In this invention, the contact group structure refers to whether the contacts are directional or annular. For example... Figure 9 As shown, the first contact group 23 and the third contact group 25 have the same structure, each including an annular contact 28 and a directional contact group 29. The second contact group 24 includes a first group 241 and a second group 242, each including an annular contact 28 and a directional contact group 29. Along the length of the electrode, the contacts at the distal end 211 are arranged in an alternating pattern of annular contacts 28 and directional contact groups 29, with the annular contact 28 on the proximal side of each contact group. This design allows for the selection of each contact group and group to use either annular contacts 28 or directional contacts for stimulation output when stimulating multiple different functional targets; that is, each contact group can select either omnidirectional or directional stimulation targets.

[0077] Example 8

[0078] Figure 10 This is a schematic diagram of the electrode structure in Embodiment 8 of the present invention.

[0079] This embodiment provides a deep brain stimulation electrode. Figure 10 and Figure 9 The difference is that: along the length of electrode 20, the contacts of the distal end 211 are arranged in an alternating form of ring contacts 28 and directional contact groups 29, with each contact group having a directional contact group 29 on the proximal side.

[0080] In other embodiments of the present invention, each of the two groups includes a ring contact 28 and a directional contact group 29, and adjacent contacts of the two groups are either ring contacts 28 or directional contacts. The contact structures between the two groups can also differ. For example, the second contact group 24 may have three ring contacts 28 and one directional contact group 29, with one group consisting of two ring contacts 28 and the other consisting of one ring contact 28 and one directional contact 29. Alternatively, the second contact group 24 may consist of three directional contact groups 29 and one ring contact 28. The variations in the contact structure of the second contact group 24 are designed to adapt to different clinical stimulation needs, providing support for innovation in multi-target combined stimulation therapy in clinical practice. This facilitates doctors in trying more contact combination stimulation output methods, and helps to further improve the accuracy and therapeutic effect of electrical stimulation.

[0081] Example 9

[0082] This embodiment provides a method for fabricating an electrode, used to fabricate the aforementioned deep brain stimulation electrode 20.

[0083] A certain length is selected from one end of the catheter 21 and set as the proximal end 212.

[0084] At the proximal end 212, a wire is crimped or soldered to a connecting ring 27. The wire comprises multiple strands of guide wire 22, each strand of guide wire 22 connected to a connecting ring 27. The other end of the guide wire 22 is inserted into a conduit 21 and exits at the distal end 211. The connecting ring 27 is fixed to the proximal end 212. Glue or other fillers can be injected between the connecting ring 27 and the conduit 21 to increase rigidity. The end of the proximal end 212 is chamfered.

[0085] In some other embodiments, the outer skin of the conduit 21 at the proximal end 212 can be removed to reduce the diameter, and then the connecting rings 27 are spaced out on the part of the proximal end 212 where the outer skin has been removed. A polyurethane insulator is provided between adjacent connecting rings 27 to prevent short circuits between adjacent connecting rings 27.

[0086] A certain length is selected from the other end of the catheter 21 and set as the distal end 211.

[0087] The positioning ring is assembled onto the conduit at the distal end 211, with the protrusion 261 of the positioning ring 26 corresponding to a directional contact. Each annular contact 28 and directional contact is connected to a guide wire 22 (e.g., by welding or crimping). The annular contacts 28 and directional contacts are connected to the conduit 21, with the directional contacts arranged in a ring in the form of a directional contact group. Glue can be injected between the contacts and the conduit 21 as a filler. Finally, a closed plug is made at the end of the distal end 211 to seal the conduit 21 at the end.

[0088] Obviously, the above embodiments of the present invention are merely examples for clearly illustrating the present invention, and are not intended to limit the implementation of the present invention. Those skilled in the art will be able to make various obvious changes, readjustments, and substitutions without departing from the scope of protection of the present invention. It is neither necessary nor possible to exhaustively describe all embodiments here. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of the present invention should be included within the scope of protection of the claims of the present invention.

Claims

1. A deep brain stimulation electrode, characterized in that, When the electrode is implanted into the brain, it passes through or is inserted into one or more functional targets in the brain to output one or more electrical stimulation signals to the functional targets in the brain. The distal portion of the electrode is provided with a contact assembly, which includes multiple contact groups arranged along the length of the distal portion. Each contact group includes multiple contacts spaced apart along the length of the electrode, and each contact group corresponds to a different functional target point in the brain. The contacts are either ring contacts or directional contacts, and the directional contacts are arranged in a ring in the form of directional contact groups. Each contact can be individually configured to output or not output the electrical stimulation signal. Wherein, at least one of the contact groups is provided with two groups along the distal length direction, and each group includes at least one directional contact group.

2. The electrode according to claim 1, characterized in that, The contact assembly includes a first contact group, a second contact group, and a third contact group, with the second contact group located between the first contact group and the third contact group, and the second contact group having two subgroups. Each of the aforementioned contact point groups corresponds to a functional target point in the brain.

3. The electrode according to claim 2, characterized in that, The first contact point group corresponds to the intracranial functional target point in the caudal indeterminate zone (Czi); and / or The second set of contact points corresponds to the subthalamic nucleus (STN) as the brain's functional target point; and / or The brain functional target point corresponding to the third contact point group is the substantia nigra reticularis (SNr).

4. The electrode according to claim 2, characterized in that, The first contact group and the third contact group each include two of the ring contacts.

5. The electrode according to claim 2, characterized in that, The first contact group and the third contact group each include one annular contact and one directional contact group.

6. The electrode according to claim 1, characterized in that, Each of the contacts can be configured to output one of the plurality of electrical stimulation signals.

7. The electrode according to claim 1, characterized in that, The length of the contact point is between 1mm and 3mm; the distance between two adjacent contact point groups is ≥0.5mm.

8. The electrode according to claim 1, characterized in that, Each group includes the annular contact and the directional contact group, with multiple contacts of the two groups arranged alternately in annular contact and directional contact group.

9. The electrode according to claim 1, characterized in that, Each group comprises two directional contact groups.

10. A stimulation system, characterized in that, It includes a pulse generator and an electrode as described in any one of claims 1-9, wherein the electrode is electrically connected to the pulse generator, and the pulse generator is used to output one or more electrical stimulation signals to each of the contact groups.

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