Electrode assembly and system for precise positioning of deep brain lesion targets

Abstract

The application provides an electrode assembly and system for accurate positioning of a deep brain lesion target. The electrode assembly comprises a first catheter and an electrode probe. The first catheter comprises a penetration end, an exit end and a catheter body, and the exit end is provided with at least one blocking part. The electrode probe comprises a proximal end and a distal end, and the distal end is arranged in the first catheter and is arranged offset relative to the central axis of the first catheter; wherein the electrode probe can rotate around the central axis in the first catheter to adjust the offset position of the distal end in the first catheter, so that the distal end can avoid the blocking part or be blocked by the blocking part to bend relative to the central axis of the first catheter during the process of penetrating out of the first catheter. By adjusting the rotation of the electrode probe in the first catheter, the distal end can select different penetration paths, and a large range of electrophysiological signal collection is realized, which is helpful for accurately positioning the position relationship between the stimulating electrode and the target nucleus.

Description

Technical Field

[0001] This application relates to the field of medical devices, specifically to electrode assemblies and systems for precise localization of deep brain lesions. Background Technology

[0002] Deep brain stimulation (DBS), as an important neuromodulation technique, is widely used in the treatment of diseases such as Parkinson's disease and refractory epilepsy. Clinically, doctors often determine the target lesion by observing the cellular firing patterns of specific nuclei in the brain, thereby planning the implantation path and depth of the stimulation electrodes. Currently, microelectrodes are typically implanted deep into the brain using an electrophysiological system to collect local electrophysiological signals to assist in target localization.

[0003] In existing technologies, some electrophysiological systems simultaneously implant a central microelectrode and multiple peripheral microelectrodes at the same brain location to achieve electrophysiological signal acquisition over a larger area. For example, CN 118490162A discloses a three-dimensional multi-directional microelectrode and deep brain stimulation electrode implantation system for precise localization of deep brain lesion targets. This system advances the central recording electrode and peripheral recording electrodes through a linear movement mechanism and simultaneously detects target signals.

[0004] However, this design requires extremely thin microelectrodes, resulting in insufficient rigidity and making them prone to bending or breakage, posing significant safety hazards. Furthermore, the slender electrodes are prone to shifting during penetration of brain tissue, affecting signal acquisition accuracy.

[0005] Another design involves implanting multiple electrode catheters in different brain locations, and then re-implanting the microelectrodes after the electrodes have acquired signals. While this design reduces the number of microelectrodes implanted at a single location and maintains a certain degree of electrode rigidity, it still causes significant damage to brain tissue during the implantation of electrode catheters in different brain locations, increasing intraoperative risks and postoperative recovery time.

[0006] Therefore, there is still a need for a microelectrode implantation system that has good rigidity and flexible orientation capabilities, and causes less damage to brain tissue, in order to improve the accuracy and safety of target localization. Summary of the Invention

[0007] In view of this, this application provides an electrode assembly and system for precise localization of target points in deep brain lesions, in order to solve the technical problems of poor microelectrode rigidity and large brain tissue damage caused by the positional relationship between the stimulation electrode and the target nucleus in existing electrophysiological systems in order to achieve precise and complete localization of the stimulation electrode.

[0008] To achieve the above-mentioned objectives, the present application may adopt the following technical solutions.

[0009] This application provides an electrode assembly for precise localization of target points in deep brain lesions, comprising:

[0010] A first catheter includes an inlet end, an outlet end, and a catheter body connecting the inlet end and the outlet end, wherein the outlet end is provided with at least one blocking portion; an electrode probe includes a proximal end and a distal end, wherein the distal end is inserted into the first catheter and is offset relative to the central axis of the first catheter; wherein the electrode probe is rotatable within the first catheter about the central axis to adjust the offset position of the distal end within the first catheter, so that the distal end can avoid the blocking portion or be blocked by the blocking portion and bend relative to the central axis of the first catheter during its exit from the first catheter.

[0011] In at least one embodiment, the blocking portion extends axially outward from the exit end along the catheter body and has a tapered apex structure aligned with the direction of the exit end; the blocking portion is used to cover a portion of the port of the exit end, and the blocking portion has an arcuate curved surface on its covering side facing the port to guide the distal end to bend during the exit process.

[0012] In at least one embodiment, the electrode assembly includes a second conduit sleeved outside the first conduit, the first conduit being rotatable about an axis within the second conduit, and the blocking portion being located outside the second conduit.

[0013] In at least one embodiment, the electrode probe includes a body portion located between the proximal end portion and the distal end portion, and radially offset from the distal end portion.

[0014] In at least one embodiment, the inner surface of the distal end is provided with a data acquisition contact for acquiring electrophysiological signals from deep brain tissue.

[0015] In at least one embodiment, the insertion end of the first catheter is provided with a first fixing part, and the second catheter is provided with a plurality of second fixing parts in the circumferential direction for connecting with the first fixing part, so as to achieve fixing of the first catheter and the second catheter at different angles.

[0016] In at least one embodiment, the first fixing part is provided as a plurality of parts, wherein at least one of the first fixing parts has a different length in the radial direction than the other first fixing parts in the radial direction, for marking the orientation of the blocking part.

[0017] In at least one embodiment, the proximal end of the electrode probe is provided with at least one marking group, the marking group including a first marking structure and a second marking structure arranged axially spaced apart;

[0018] The first marking structure is used to indicate the insertion position when the distal end extends out of the first catheter in a straight line, and the second marking structure is used to indicate the insertion position when the distal end extends out of the first catheter in a bent state.

[0019] In at least one embodiment, the first marking structure and the second marking structure are spaced apart by a distance H. This distance is used to compensate for the difference in the extension length required to achieve the same sampling depth when the distal end extends out in a bent or straight manner.

[0020] This application provides a system for precise localization of target points in deep brain lesions, which includes the aforementioned electrode assembly, as well as an electrophysiological host and an implantable drive mechanism.

[0021] The electrophysiology host is electrically connected to the implantation drive mechanism and the electrode assembly, respectively, and is used to control the positioning and signal acquisition of the electrode assembly; the implantation drive mechanism is connected to the electrode assembly and, under the control of the electrophysiology host, adjusts the implantation depth of the electrode assembly.

[0022] By adopting the above technical solution, this application provides an electrode assembly for precise target localization of deep brain lesions. In this electrode assembly, the distal end of the electrode probe is offset relative to the central axis within a first conduit, and different exit paths can be selected by adjusting the rotation of the electrode probe within the first conduit. Thus, this application achieves large-area electrophysiological signal acquisition by implanting one electrode probe at a single location, which helps to accurately locate the positional relationship between the stimulating electrode and the target nucleus. This solves the problems of small microelectrode diameter and poor rigidity caused by implanting multiple microelectrodes at the same location in existing electrophysiological systems, as well as the technical problem of significant brain tissue damage caused by implanting microelectrodes at multiple locations. Attached Figure Description

[0023] Figure 1 This is a schematic diagram of an electrode assembly for precise localization of deep brain lesions according to an embodiment of this application;

[0024] Figure 2 This is a schematic diagram of an electrode assembly for precise target localization of deep brain lesions according to an embodiment of this application from another perspective.

[0025] Figure 3 This is a side view schematic diagram of an electrode assembly for precise target localization of deep brain lesions according to an embodiment of this application;

[0026] Figure 4 This is a schematic diagram of an electrode assembly for precise localization of deep brain lesions according to an embodiment of this application, wherein the electrode probe extends from a first catheter in a straight line.

[0027] Figure 5 for Figure 4 A cross-sectional view taken along the central axis AA of the electrode probe;

[0028] Figure 6 This is a schematic diagram of an electrode assembly for precise localization of deep brain lesions according to an embodiment of this application, wherein the electrode probe extends from a first catheter in a bent state.

[0029] Figure 7 for Figure 6 A cross-sectional view taken along the central axis BB of the electrode probe;

[0030] Figure 8A , Figure 8B , Figure 8C These are schematic diagrams of the structure of an electrode probe according to an embodiment of this application;

[0031] Figure 9A , Figure 9B These are schematic diagrams of structures used in this application to acquire electrophysiological signals from nuclei;

[0032] Figure 10A , Figure 10B The images are schematic diagrams of the structures used to acquire nucleus electrophysiological signals using the electrode assembly of this application. Figure 10A The blocking part has an arc-shaped surface with a small curvature.

[0033] Explanation of reference numerals in the attached figures

[0034] 1. First catheter;

[0035] 11 Insertion end; 12 Exit end; 13 Conduit body; 14 Blocking part; 141 Curved surface; 15 First fixing part;

[0036] 2. Second catheter;

[0037] 21. Second fixing part;

[0038] 3. Electrode probes;

[0039] 31 Main body; 32 Distal end; 33 Data acquisition contact; 34 First identification structure; 35 Second identification structure; 36 Third identification structure Detailed Implementation

[0040] Exemplary embodiments of this application are described below with reference to the accompanying drawings. It should be understood that these specific descriptions are for teaching those skilled in the art how to implement this application only, and are not intended to exhaust all possible methods of this application, nor to limit the scope of this application.

[0041] Embodiments of this application provide an electrode assembly (hereinafter, sometimes simply referred to as "electrode assembly") for precise localization of deep brain lesion targets.

[0042] In this application, "distal end" refers to the end furthest from the operator, "axial" refers to the direction parallel to the central axis of the electrode assembly, and "radial" refers to the direction perpendicular to the axial direction. It is important to note that "proximal end" and "distal end" are not the tip, endpoint, or end wall, but rather a portion extending axially and / or radially from the tip, endpoint, or end wall on the element to which it belongs. The above definitions are for convenience only and should not be construed as limiting this application.

[0043] In this application, the electrode assembly may have various shapes, including but not limited to straight lines, curves, or any other geometric shapes. For the sake of simplicity and ease of understanding, the illustrations in this application show the electrode assembly in a straight line. However, this representation of a straight line does not imply a limitation on the shape of the electrode assembly; in fact, the shape of the electrode assembly can be designed and adjusted according to the actual application requirements.

[0044] Furthermore, in the accompanying drawings of this application, certain portions of the first catheter 1, the second catheter 2, and the electrode probe 3 are omitted to simplify the view and highlight key features. These omitted portions are indicated by break lines (e.g., Figure 1 The two parallel dotted lines in the diagram indicate that the actual length of these components exceeds the range shown.

[0045] like Figure 1 and Figure 2 As shown, embodiments of this application provide an electrode assembly for precise localization of deep brain lesions, which may include a first catheter 1, a second catheter 2, and an electrode probe 3. The first catheter 1 may be fitted onto the second catheter 2, and the first catheter 1 may rotate about an axis within the second catheter 2.

[0046] See Figure 2 and Figure 5 The first catheter 1 may include an insertion end 11, an exit end 12, and a catheter body 13 connecting the insertion end 11 and the exit end 12. Further, the wall thickness of the first catheter 1 is uniform, and the central axis of its lumen coincides with the central axis of the catheter body 13. In some other embodiments, there is an acceptable deviation between the central axis of the lumen and the catheter body 13.

[0047] like Figure 8A As shown, the electrode probe 3 may include a proximal end portion, a main body portion 31, and a distal end portion 32, with the main body portion 31 located between the proximal end portion and the distal end portion 32. Furthermore, see [link to other documentation]. Figure 1 The distal end 32 may be provided with a collection contact 33 for collecting electrophysiological signals from deep brain tissue.

[0048] The distal end 32 of the electrode probe 3 can be inserted into the first conduit 1 from the insertion end 11 and exit from the exit end 12. Furthermore, the length of the electrode probe 3 can be greater than the length of the first conduit 1, so that when the distal end 32 exits from the first conduit 1, both the proximal end and the distal end 32 can be located outside the first conduit 1.

[0049] In this embodiment, the second catheter 2 can drive the first catheter 1 and the electrode probe 3 to move together, thereby moving the distal end 32 of the electrode probe 3 to the target nucleus for electrophysiological signal acquisition.

[0050] Furthermore, the first catheter 1, the second catheter 2, and the electrode probe 3 can all be made of biocompatible metal materials, and the first catheter 1 and the second catheter 2 can be electrically isolated from each other through an insulating sleeve or coating. In addition, the body of the electrode probe 3 can be coated with a biocompatible insulating material, and its distal end 32 exposes the acquisition contact 33.

[0051] When the electrode assembly is in operation, the electrophysiological host (see below for details) is connected to the insertion end 11 of the first catheter 1 and the proximal end of the electrode probe 3, respectively. At this time, the electrophysiological host, the uninsulated part of the exit end 12 of the first catheter 1, the acquisition contact 33 of the electrode probe 3, and the target brain region cell nucleus together constitute a complete signal acquisition circuit, realizing efficient acquisition of electrophysiological signals.

[0052] like Figure 2 and Figure 3 As shown, the exit end 12 of the first conduit 1 may be provided with a blocking part 14, which is used to guide the distal end 32 to bend at a certain angle relative to the central axis of the first conduit 1 and exit through the first conduit 1. The blocking part 14 may extend outside the second conduit 2, thereby preventing the electrode probe 3 from being affected by the second conduit 2 bending and exiting.

[0053] In this embodiment, the distal end portion 32 can be biased to one side of the catheter body 13 of the first catheter 1. The electrode probe 3 is rotatably disposed within the first catheter 1. By adjusting the rotation of the electrode probe 3 relative to the first catheter 1, the distal end portion 32 rotates accordingly, thereby changing its bias position within the first catheter 1.

[0054] Specifically, see Figure 4 and Figure 5 When the distal end 32 is misaligned with the blocking part 14 in the axial direction, it can avoid the blocking part 14 and pass through the first catheter 1 in a straight line, thereby collecting electrophysiological signals from the target nucleus directly in front of the exit end 12 of the first catheter 1.

[0055] See Figure 5The axial misalignment of the distal end 32 with the blocking part 14 can be understood as the radial distance between the blocking part 14 and the catheter body 13 being a small gap, so that the blocking part 14 can not block the passage of the distal end 32 (i.e., it does not cause the distal end 32 to bend).

[0056] See Figure 6 and Figure 7 When the offset position of the distal end 32 is aligned with the blocking part 14 in the axial direction, that is, when the blocking part 14 is on the exit path of the distal end 32, the distal end 32 will contact the blocking part 14 during the exit process and bend under the guidance of the blocking part 14, thereby exiting the first catheter 1 in a bent state, realizing the acquisition of electrophysiological signals of the surrounding tissues and expanding the acquisition range.

[0057] In this application, by adjusting the bias position of the electrode probe 3 in the first catheter 1, it is possible to control whether the distal end 32 passes through in a straight line by avoiding the blocking part 14 during the exit process, or passes through by contacting the blocking part 14 and being blocked by the blocking part 14 and bending relative to the central axis of the first catheter 1. This enables the acquisition of electrophysiological signals of tissues in different directions of the target area, or the acquisition of electrophysiological signals of tissues directly in front.

[0058] It is understood that when the blocking part 14 is located in the exit path of the distal end 32, the bending direction of the distal end 32 relative to the target nucleus can be adjusted by simultaneously rotating the electrode probe 3 and the first catheter 1 (while keeping their relative positions unchanged). Specifically, the rotation angle of the electrode probe 3 and the first catheter 1 can be adjusted so that the distal end 32 bends out in any direction, thereby improving the flexibility of selecting the direction of electrophysiological signal acquisition.

[0059] See Figure 5 and Figure 7 The blocking part 14 can extend outward along the axial direction of the conduit body 13 from the outlet end 12, and adopts a tapered pointed structure consistent with the direction of the outlet end 12. This structural design allows the blocking part 14 to partially block the port area of ​​the outlet end 12 in the radial direction of the first conduit 1.

[0060] Furthermore, the blocking portion 14 can extend to the catheter body 13 to form a semi-conical structure, thereby enhancing the puncture capability of the electrode assembly while reducing the risk of damage to brain tissue. When the distal end 32 is biased on the same side as the blocking portion 14, it indicates that the blocking portion 14 is at least partially located on the exit path of the distal end 32, thus enabling regulation of the exit direction of the distal end 32.

[0061] See Figure 5 and Figure 7The blocking part 14 may have an arc-shaped curved surface 141 on the blocking side facing the outlet end 12 port, which is used to guide the distal end 32 to bend during the outlet process and smoothly connect with the inner wall of the first conduit 1.

[0062] Specifically, the arc-shaped surface 141 extends along the axial direction of the first conduit 1, with its side away from the exit end 12 curving towards the conduit body 13, forming a concave guiding surface. When the electrode probe 3 exits, the distal end 32 contacts the arc-shaped surface 141 and bends under its guidance. Subsequently, when the distal end 32 disengages from the surface, due to the elasticity of the electrode probe 3, its bent portion can return to an approximately straight state, thereby allowing the distal end 32 to continue penetrating the target nucleus in a straight direction.

[0063] In this embodiment, the acquisition contact 33 can be disposed on the inner side of the distal end 32.

[0064] See Figure 8A The inner surface of the distal end 32 can be the side closest to the central axis of the electrode probe 3. In this way, when the distal end 32 contacts the curved surface 141, since the acquisition contact 33 is located on the side of the distal end 32 facing away from the blocking part 14, direct contact between the acquisition contact 33 and the blocking part 14 is avoided, reducing the risk of damage and improving system safety.

[0065] It is understood that the bending angle of the electrode probe 3 relative to the straight outward direction is in the range of 0 to 90°, and more preferably in the range of 20° to 60°. If the angle is too small, the acquisition range may be reduced; if the angle is too large, it may cause fatigue or breakage of the distal end 32 structure, thereby affecting the service life of the electrode probe 3.

[0066] In other embodiments, the exit end 12 of the first catheter 1 may be provided with multiple blocking portions 14, and each blocking portion 14 may be configured as an arc-shaped surface with different degrees of curvature. In this way, before the electrode probe 3 exits, a suitable arc-shaped surface, i.e. a specific blocking portion 14, can be selected to achieve electrophysiological signal acquisition in different ranges and directions.

[0067] See Figure 1 and Figure 3 The insertion end 11 of the first conduit 1 can be provided with a first fixing part 15, and the second conduit 2 can be provided with multiple second fixing parts 21, which are connected to the first fixing part 15 to restrict the relative rotation of the first conduit 1 and the second conduit 2, that is, to achieve fixing of the first conduit 1 and the second conduit 2 at different angles.

[0068] Specifically, since the first catheter 1 and the electrode probe 3 rotate synchronously, after the bending direction of the electrode probe 3 is adjusted, the first fixing part 15 and the second fixing part 21 can be connected to fix the first catheter 1, thereby preventing its electrophysiological signal acquisition from deviating from the predetermined position and ensuring that the acquisition direction of the electrode probe 3 is stable and accurate.

[0069] In this embodiment, see Figure 1 The second conduit 2 can be evenly distributed with four second fixing parts 21 in the circumferential direction to form a cross-shaped layout. During the rotation of the first conduit 1, it can be relatively fixed with the second conduit 2 in four specific directions (i.e., rotation of 0°, 90°, 180°, and 270°).

[0070] Specifically, when the blocking part 14 is located on the exit path of the distal end 32, the first conduit 1 and the electrode probe 3 can be rotated simultaneously. When rotated to any of the four directions, the first conduit 1 is positioned in that direction by connecting the first fixing part 15 and the second fixing part 21, thereby ensuring that the electrode probe 3 can stably bend and exit along that direction.

[0071] See Figure 1 The first fixing part 15 can be designed as a pin structure, with the pin protruding radially along the first conduit 1. Correspondingly, the second fixing part 21 can be designed as a cross-shaped slot structure.

[0072] Furthermore, the first fixing part 15 may be provided with multiple pins, wherein at least one pin has a radial length that differs from the other pins, thereby providing an orientation reference during operation and assisting in identifying the current rotation angle of the first conduit 1, i.e., the orientation of the marking blocking part 14.

[0073] In addition, the first fixing part 15 and the second fixing part 21 can also adopt other forms of mating structure, such as a knob-type structure. The first fixing part 15 can be nested outside the second fixing part 21, achieving self-locking through friction. Alternatively, the first fixing part 15 can also be provided with graphic or color markings to indicate the rotation angle and direction of the conduit in real time during rotation, assisting the operator in judging the position of the blocking part 14.

[0074] This design provides a simple and intuitive way to identify and control the rotational orientation of the first catheter 1, which helps to improve positioning efficiency and operational accuracy.

[0075] like Figure 5 and Figure 7As shown, the main body 31 and distal end 32 of the electrode probe 3 can be designed as cylindrical structures. Specifically, the diameter of the main body 31 can be equal to or close to the inner diameter of the lumen of the first conduit 1, thereby preventing the electrode probe 3 from swaying within the first conduit 1. The diameter of the distal end 32 gradually decreases from the proximal end to the distal end, forming a needle-like structure. In some other embodiments, the cross-section of the distal end 32 can also be designed as an ellipse, a rectangle, or other geometric shapes.

[0076] Referring to 8A, the main body 31 and distal end 32 of the electrode probe 3 can be radially offset. It is understood that the axial centers of the main body 31 and the distal end 32 can be located at the same position, but radially they can be at different positions. Specifically, the main body 31 and the distal end 32 can form a stepped structure at the connection point, such that the distal end 32 is offset to one side relative to the catheter body 13 within the first catheter 1.

[0077] In some other embodiments, the main body 31 and the distal end 32 may employ different structural designs. For example, Figure 8B The design shows that the main body 31 and the distal end 32 form an oblique conical structure. Figure 8C The design shows that the main body 31 and the distal end 32 have multiple bends. These different structures can all achieve the biasing effect of the distal end 32 within the first conduit 1.

[0078] like Figure 9A and Figure 9B As shown, the proximal end of the electrode probe 3 may be provided with one or more marking groups. In this embodiment, the marking group may include a first marking structure 34 and a second marking structure 35 arranged axially at intervals. The first marking structure 34 can be used to indicate the insertion position when the distal end 32 exits the first conduit 1 in a straight line, while the second marking structure 35 can be used to indicate the insertion position when the distal end 32 exits the first conduit 1 in a bent state.

[0079] Furthermore, the interval between the first identification structure 34 and the second identification structure 35 can be set to H, which is used to compensate for the difference in the extension length required for the distal end 32 to reach the same sampling depth under two different exit paths (i.e., straight exit and bent exit).

[0080] Specifically, such as Figure 9A As shown, when the electrode probe 3 extends out of the first catheter 1 in a straight line and the first marking structure 34 reaches the insertion end 11, electrophysiological signals can be collected from the nucleus N1. Figure 9B As shown, when the electrode probe 3 is bent out and the second marking structure 35 reaches the insertion end 11, the electrophysiological signal of group 2 can be collected. The acquisition positions of nucleus N1 and nucleus N2 are located on the same horizontal plane, which is perpendicular to the axis of the catheter body 13.

[0081] Furthermore, the electrode probe 3 may also be provided with a third marking structure 36 for indicating the offset position of the distal end 32 within the first conduit 1, so as to quickly determine the bending direction of the distal end 32 when it exits.

[0082] In this embodiment, the electrode assembly can also control the bending angle of the electrode probe 3 by adjusting the curvature of the arc surface 141 of the blocking part 14, thereby enabling the electrode probe 3 to bend out of the first catheter 1 at a predetermined angle and expand the acquisition range of electrophysiological signals, thus achieving the adjustability of the acquisition range.

[0083] Figure 10A and Figure 10B The guiding effect of curved surfaces 141 with different curvatures on the bending path of electrode probe 3 is shown. Figure 10A The blocking part 14 shown has an arcuate surface 141 with a small curvature.

[0084] like Figure 10A As shown, the blocking part 14 can guide the electrode probe 3 to bend at a small angle and pass through the first catheter 1. When the second marking structure 35 reaches the second catheter insertion end 11, the electrode probe 3 can collect the electrophysiological signal of the nucleus N2.

[0085] like Figure 10B As shown, the curvature of the arc-shaped surface 141 of the blocking part 14 is relatively large, and the bending angle of the guided electrode probe 3 also increases accordingly. Simultaneously, the distance between the first marking structure 34 and the second marking structure 35 is also greater than... Figure 10A The spacing H in the middle. At this time, when the second marking structure 35 reaches the second catheter insertion end 11, the electrode probe 3 can collect the electrophysiological signal of the nucleus N3 which is further away.

[0086] This application also provides a system for precise localization of target points in deep brain lesions, which may include an electrophysiological host, an implantable drive mechanism, and an electrode assembly. The electrophysiological host is electrically connected to both the implantable drive mechanism and the electrode assembly.

[0087] Furthermore, the electrophysiology host can control the operation of the implantation drive mechanism, which can be connected to the electrode assembly. This allows the electrophysiology host to adjust the implantation depth of the electrode assembly and receive and analyze the electrophysiological signals collected by the electrode assembly through the implantation drive mechanism.

[0088] Specifically, the implantation drive mechanism can connect to the second catheter 2 of the electrode assembly and control its implantation depth and speed, while driving the first catheter 1 and the electrode probe 3 to move together, thereby moving the distal end 32 of the electrode probe 3 to the target nucleus for electrophysiological signal acquisition.

[0089] This embodiment provides an electrode assembly for precise localization of deep brain lesions. The distal end of the electrode probe is offset relative to the central axis within a first catheter. By adjusting the rotation of the electrode probe within the first catheter, the distal end can avoid the obstruction during its exit and exit along the central axis of the first catheter, or the distal end can overlap with the obstruction in the axial direction, thereby contacting the obstruction during its exit and guiding the distal end to bend relative to the central axis of the first catheter as it exits.

[0090] The embodiments of this application implant an electrode probe at one location, which enables the acquisition of electrophysiological signals over a larger range. This helps to accurately locate the positional relationship between the stimulating electrode and the target nucleus, and solves the problems of small microelectrode diameter and poor rigidity caused by implanting multiple microelectrodes at the same location in existing electrophysiological systems, as well as the technical problem of greater brain tissue damage caused by implanting microelectrodes at multiple locations.

[0091] It should be understood that the above-described embodiments, examples, or examples are merely exemplary and are not intended to limit this application. Those skilled in the art can make various modifications and changes to the above-described embodiments, examples, or examples under the teachings of this application without departing from the scope of this application.

[0092] Unless otherwise expressly specified and limited, the terms "installation," "connection," "linking," and "fixing," etc., 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 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, unless otherwise expressly limited. Those skilled in the art can understand the specific meaning of the above terms in this invention according to the specific circumstances.

Claims

1. An electrode assembly for precise target localization of deep brain lesions, characterized in that, include: The first catheter (1) includes an insertion end (11), an exit end (12) and a catheter body (13) connecting the insertion end (11) and the exit end (12), wherein the exit end (12) is provided with at least one blocking part (14). The electrode probe (3) includes a proximal end and a distal end (32), the distal end (32) being inserted through the first catheter (1) and offset relative to the central axis of the first catheter (1); The electrode probe (3) is rotatable within the first conduit (1) around the central axis to adjust the offset position of the distal end (32) within the first conduit (1), so that the distal end (32) can avoid the blocking part (14) or be blocked by the blocking part (14) and bend relative to the central axis of the first conduit (1) as it exits the first conduit (1). The electrode probe (3) includes a main body (31) located between the proximal end and the distal end (32), and radially offset from the distal end (32). The main body (31) and the distal end (32) form a stepped structure or an oblique conical structure or have multiple bends at the connection.

2. The electrode assembly for precise target localization of deep brain lesions according to claim 1, characterized in that, The blocking part (14) extends outward from the protruding end (12) along the main body of the catheter (13) and has a tapered pointed structure in the same direction as the protruding end (12); The blocking part (14) is used to block a portion of the port of the protruding end (12). The blocking part (14) has an arc-shaped curved surface (141) on its blocking side facing the port, which is used to guide the distal end (32) to bend during the protrusion process.

3. The electrode assembly for precise target localization of deep brain lesions according to claim 1, characterized in that, The electrode assembly includes a second conduit (2), which is sleeved outside the first conduit (1). The first conduit (1) can rotate around an axis inside the second conduit (2), and the blocking part (14) is located outside the second conduit (2).

4. The electrode assembly for precise target localization of deep brain lesions according to any one of claims 1 to 3, characterized in that, The inner surface of the distal end (32) is provided with a collection contact (33) for collecting electrophysiological signals from deep brain tissue.

5. The electrode assembly for precise target localization of deep brain lesions according to claim 3, characterized in that, The first conduit (1) has a first fixing part (15) at its insertion end (11), and the second conduit (2) has a plurality of second fixing parts (21) arranged in the circumferential direction for connecting with the first fixing part (15) to achieve fixing at different angles between the first conduit (1) and the second conduit (2).

6. The electrode assembly for precise target localization of deep brain lesions according to claim 5, characterized in that, The first fixing part (15) is provided in multiple ways, wherein at least one of the first fixing parts (15) has a different length in the radial direction than the other first fixing parts (15) in the radial direction, for marking the orientation of the blocking part (14).

7. The electrode assembly for precise localization of deep brain lesions according to any one of claims 1 to 6, characterized in that, The proximal end of the electrode probe (3) is provided with at least one marking group, the marking group including a first marking structure (34) and a second marking structure (35) arranged axially spaced apart. The first marking structure (34) is used to indicate the insertion position when the distal end (32) passes through the first catheter (1) in a straight line, and the second marking structure (35) is used to indicate the insertion position when the distal end (32) passes through the first catheter (1) in a bent state.

8. The electrode assembly for precise target localization of deep brain lesions according to claim 7, characterized in that, The first identification structure (34) and the second identification structure (35) are spaced apart by a distance of H. The distance is used to compensate for the difference in the extension length required to achieve the same sampling depth when the distal end (32) is bent out and straight out.

9. A system for precise target localization of deep brain lesions, characterized in that, The system includes the electrode assembly as described in any one of claims 1 to 8, as well as an electrophysiological host and an implantation drive mechanism; The electrophysiology host is electrically connected to the implantation drive mechanism and the electrode assembly, respectively, and is used to control the positioning and signal acquisition of the electrode assembly; the implantation drive mechanism is connected to the electrode assembly and, under the control of the electrophysiology host, adjusts the implantation depth of the electrode assembly.

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