NL2012518A - Medical lead and system for neurostimulation. - Google Patents

Description

Medical lead and system for neurostimulation

The present invention relates to a medical lead for neurostimulation, especially for deep brain stimulation, and a system for neurostimulation.

Implantable neurostimulation devices have been used for the past ten years to treat acute or chronic neurological conditions. Deep brain stimulation (DBS), the mild electrical stimulation of sub-cortical structures, belongs to this category of implantable devices, and has been shown to be therapeutically effective for Parkinson’s disease, Dystonia, and Tremor. New applications of DBS in the domain of psychiatric disorders (obsessive compulsive disorder, depression) are being researched and show promising results. In existing systems, the probes are connected to an implantable current pulse generator.

Currently, systems are under development with more, smaller electrodes in a technology based on thin film manufacturing. These novel systems consist of a lead made from a thin film based on thin film technology, as e.g. described in WO 2010/055453 A1. The thin film leads are fixed on a core material to form a lead. These probes will have multiple electrode areas and will enhance the precision to address the appropriate target in the brain and relax the specification of positioning. Meanwhile, undesired side effects due to undesired stimulation of neighboring areas can be minimized.

Leads that are based on thin film manufacturing are e.g. described by US 7,941,202 and have been used in research products in animal studies.

In existing systems, the DBS lead has e.g. four 1.5 mm-wide cylindrical electrodes at the distal end spaced by 0.5 mm or 1.5 mm. The diameter of the lead is 1.27 mm and the metal used for the electrodes and the interconnect wires is an alloy of platinum and iridium. The coiled interconnect wires are insulated individually by fluoropolymer coating and protected in an 80 micron urethane tubing. With such electrode design, the current distribution emanates uniformly around the circumference of the electrode, which leads to stimulation of all areas surrounding the electrode.

The lack of fine spatial control over field distributions implies that stimulation easily spreads into adjacent structures inducing adverse side-effects in about 30% of the patients. To overcome this problem, systems with high density electrode arrays are being developed, hence providing the ability to steer the stimulation field to the appropriate target.

The clinical benefit of DBS is largely dependent on the spatial distribution of the stimulation field in relation to brain anatomy. To maximize therapeutic benefits while avoiding unwanted side-effects, precise control over the stimulation field is essential.

During stimulation with existing DBS leads there is an option to use monopolar, bipolar or even tripolar stimulation. Neurostimulator devices with steering brain stimulation capabilities can have a large number of electrode contacts (n > 10) that can be connected to electrical circuits such as current sources and/or (system) ground. Stimulation may be considered monopolar when the distance between the anode and cathode is several times larger than the distance of the cathode to the stimulation target. During monopolar stimulation in homogeneous tissue the electric field is distributed roughly spherical similar to the field from a point source. When the anode is located close to the cathode the distribution of the field becomes more directed in the anode-cathode direction. As a result the field gets stronger and neurons are more likely to be activated in this area due to a higher field gradient.

The mechanisms of DBS are unknown. However, it is hypothesized that polarization (de- and/or hyperpolarization) of neural tissue is likely to play a prominent role for both suppression of clinical symptoms, as well as induction of stimulation-induced side-effects. In order to activate a neuron it has to be depolarized. Neurons are depolarized more easily close to the cathode than by the anode (about 3-7 times more depending on type of neuron, etc.).

Therefore, compared to monopolar stimulation the effect of bipolar stimulation is less spread of the electric field, a stronger electric field between the anode and cathode, and more activated neurons close to the cathode. Bipolar stimulation is therefore used to focus the field to certain areas in cases when beneficial stimulation is not obtained during monopolar stimulation.

It has been recently discovered by Coenen et al (University of Freiburg) that depression may be reduced by stimulating the supero-lateral branch of the medical forebrain bundle.

To effectively stimulate the fiber tracks in this region, the existing deep brain stimulation leads with a ring electrode design or with small circular electrodes are not optimally designed and shaped. For example, EP 2 663 361 A1 discloses such ring electrode with a ring electrode design which not optimally designed for the stimulation of fiber tracks in specific regions of the brain.

It is therefore an object of the present invention to improve a medical lead for neurostimulation, especially for deep brain stimulation, and a system for neurostimulation, especially in that a medical lead for neurostimulation and a system for neurostimulation allow an effective stimulation of regions of the brain, especially of the supero-lateral branch of the medical forebrain bundle.

This object is solved according to the present invention with a medical lead for neurostimulation with the features of claim 1. Accordingly, a medical lead for neurostimulation is provided, comprising a plurality of elongated electrodes.

The medical lead may be especially a lead for deep brain stimulation.

The elongated electrodes allow an optimal delivery of stimulation to cover the target area. The fiber tracks in the target region may be optimally stimulated. Especially fiber tracks in deep brain structures and e.g. the supero-lateral branch of the medial forebrain bundle may be stimulated.

The lead according to the present invention allows advantageously that the therapeutic effect is improved while the impact on surrounding brain tissue is minimized, which might cause unwanted side effects.

Furthermore, elongated electrodes allow good stimulation coverage in case that the target area is large. Also, elongated electrodes help to reduce the power consumption and are thus helpful to increase the battery lifetime as well as the current density, which is advantageous in terms of safety reasons.

Moreover, the plurality of electrodes allows steering of the stimulation field such that the stimulation field may be adapted and conform to the target area. In particular, stimulation steering is enabled where the electric field is shaped such that certain directions receive much less stimulation current than other adjacent tissue regions.

In a further embodiment, the lead may have a longitudinal extension and the electrodes may be not aligned perpendicular to the longitudinal extension. By this, the advantage is achieved that the electrodes may be better aligned to the fiber tracks in a target area.

The electrodes may substantially aligned to the axis of the longitudinal extension and especially parallel to the axis of the longitudinal extension. Such an electrode design is helpful during placement of the lead, since the insertion trajectory and the direction and alignment of the electrodes is parallel to each other.

Furthermore, the electrodes and the axis of the longitudinal extension may enclose an angle and the electrodes may be spirally wound around the lead. Such a design is helpful to conform to the characteristics of the target region, where fiber tracks are not straight but may have at least partially curved portions. Also, even in case of a slight difference of the intended insertion position, this design still allows good stimulation coverage due to the fact the electrodes a wound around the axis of the longitudinal extension. The angle may be an acute angle and may be chosen within a range between 0-90°, especially between 30° to 55°, preferably between 40° to 50° and especially around 45°.

The electrodes may have non-circular and stretched shapes. Such a design has been discovered as a very good shape for the interaction with long fiber bundles and is optimized with a maximum therapeutic effect with as little side-effects as possible.

In a further embodiment, the electrodes may be parallel to each other. This allows the formation of an electrode array with high density, which is advantageous for a delivery of good stimulation coverage.

Moreover, in a further exemplary embodiment the electrodes may have the same width. By this, the stimulation field part provided by each electrode is substantially equal and allows a better adjustability and predictability of the overall stimulation field.

Additionally, the lead may have a proximal end and distal end with a tip end and wherein the electrodes are arranged at the distal end of the lead. By this, the insertion of the lead is restricted to the absolutely necessary pathway and the once the tip end has reached the target region, also the electrodes are correctly positioned.

Furthermore, adjacent electrodes of different rows may be offset to each other. This increases the possibilities to steer the stimulation field provided by the electrodes and allows a more dense packing of the electrodes. Furthermore, so-called dead zones, where no or less stimulation can be provided are avoided.

In a further embodiment, the electrodes have a length that is approx. 2-10 times the width of the electrode. This design of electrodes has been identified as being advantageous for the delivery of stimulation to fiber tracks of a target region.

The lead may comprise at least 20 electrodes, especially approx. 30 to 45 electrodes, more especially approx. 40 electrodes. This number of electrodes allows the creation of stimulation field which conforms to the target region and which may be formed three-dimensionally and adapted to the target region. Only those regions that need to be stimulated may be covered by the stimulation field provided by the plurality of electrodes.

The electrodes may form a complex electrode array. This is helpful to create a stimulation field that is adapted to and conforms to the target region. A complex electrode array generally refers to an arrangement of electrodes at multiple non-planar or non-coaxial positions, in contrast to simple electrode array geometries in which the electrodes share a common plane or common axis.

An example of a simple electrode array geometry is an array of ring electrodes distributed at different axial positions along the length of the lead.

An example of a complex electrode array geometry, in accordance with this disclosure, is an array of electrodes positioned at different axial positions along the length of the lead, as well as at different angular positions about the circumference of the lead.

In a further embodiment, a further electrode may be arranged between two adjacent elongated electrodes.

The further electrode may be a non-elongated electrode.

This further electrode may be an electrode with a specific function. For example, the further electrode may be a sensing and/or recording electrode. In particular, the further electrode may be used for sensing and/or recording only and the elongated electrodes may be used for stimulation.

It is possible that the further electrode is a microelectrode. This electrode may be a dot-like electrode with e.g. a circular or oval or triangular or rectangular shape. A row of electrodes may be formed by alternating one elongated electrode and the further electrode.

In a further exemplary embodiment, a first array of elongated electrodes and a second array of non-elongated electrodes may be provided.

The first array of elongated electrodes and the second array of electrodes may form both a complex array of electrodes.

It is possible that the second array is arranged next to the tip of the lead and the first array in an area adjacent to the area of the second array, wherein the area of the first array of electrodes is more proximal than the area of the second array.

Furthermore, the elongated electrodes may be formed by electrodes with a fractal design. A fractal design of an electrode is given in cases where a part of the antenna is similar to the entire antenna itself except smaller. A fractal design is according to the present disclosure also provided by star-like designs. Two opposing portions or tips of the star-shape form together an elongated portion of the electrode so as to form at least in terms of function an elongated electrode design. A further possible fractal design can be provided by using a checked pattern design for the electrodes.

The electrodes with fractal design may be arranged in a complex array of electrodes.

Additionally, the present invention relates to a system for neurostimulation. Accordingly, a system for neurostimulation comprises at least one lead as described above.

In particular, the system may be a deep brain stimulation system.

Moreover, as a part of the present disclosure, a method for providing neurostimulation with a medical lead is disclosed. Accordingly, a medical lead for neurostimulation comprising a plurality of elongated electrodes is implanted into a target region of neural tissue.

The lead may be a lead as described above, comprising the features and advantages as disclosed above.

The neural tissue may be brain tissue.

The target region may be a deep brain structure.

For example, the target region may be the supero-lateral branch of the medial forebrain bundle.

The stimulation is provided via the electrodes to the target region. The stimulation field may be adapted such as to conform to the target region. To achieve this, the relevant electrodes are selected and switched on and strength of the electrical field provided by these electrodes is adjusted accordingly so as to form a stimulation field that is adapted such as to conform with the target region.

Further details and advantages of the present invention shall be described hereinafter with respect to the drawings. It is shown in:

Figure 1 a schematically drawing of a neurostimulation system for deep brain stimulation (DBS);

Figure 2 a further schematically drawing of a probe of a neurostimulation system for deep brain stimulation (DBS) and its components;

Figure 3 a schematically drawing of a probe system according to the present invention;

Figure 4 a schematically drawing of a distal lead portion according to the present invention in a first embodiment;

Figure 5 a schematically drawing of a distal lead portion according to the present invention in a second embodiment;

Figure 6 a schematically drawing of a distal lead portion according to the present invention in a third embodiment;

Figure 7 a schematically drawing of a distal lead portion according to the present invention in a fourth embodiment;

Figure 8 a schematically drawing of a distal lead portion according to the present invention in a fifth embodiment;

Figure 9 a schematically drawing of a distal lead portion according to the present invention in a sixth embodiment;

Figure 10 a schematically drawing of a distal lead portion according to the present invention in a seventh embodiment;

Figure 11 a schematically drawing of a distal lead portion according to the present invention in a eighth embodiment; and

Figure 12 a schematically drawing of a distal lead portion according to the present invention in a ninth embodiment. A possible embodiment of a neurostimulation system 100 for deep brain stimulation (DBS) is shown in Figure 1. The neurostimulation system 100 comprises at least a controller 110 that may be surgically implanted in the chest region of a patient 1, typically below the clavicle or in the abdominal region of a patient 1. The controller 110 can be adapted to supply the necessary voltage pulses. The typical DBS system 100 may further include an extension wire 120 connected to the controller 110 and running subcutaneously to the skull, preferably along the neck, where it terminates in a connector. A DBS lead arrangement 130 may be implanted in the brain tissue, e.g. through a burr-hole in the skull.

Figure 2 further illustrates a typical architecture for a Deep Brain Stimulation probe 130 that comprises a DBS lead 300 and an active lead can 111 comprising electronic means to address electrodes 132 on the distal end 304 of the thin film 301, which is arranged at the distal end 313 and next to the distal tip 315 of the DBS lead 300. The lead 300 comprises a carrier 302 for a thin film 301, said carrier 302 providing the mechanical configuration of the DBS lead 300 and the thin film 301. The thin film 301 may include at least one electrically conductive layer, preferably made of a biocompatible material. The thin film 301 is assembled to the carrier 302 and further processed to constitute the lead 300. The thin film 301 for a lead is preferably formed by a thin film product having a distal end 304, a cable 303 with metal tracks and a proximal end 310. The proximal end 310 of the thin film 301 arranged at the proximal end 311 of the lead 300 is electrically connected to the active lead can 111. The active lead can 111 comprises the switch matrix of the DBS steering electronics. The distal end 304 comprises the electrodes 132 for the brain stimulation. The proximal end 310 comprises the interconnect contacts 305 for each metal line in the cable 303. The cable 303 comprises metal lines (not shown) to connect each distal electrodes 132 to a designated proximal contact 305.

Figure 3 shows schematically and in greater detail an embodiment of a system 100 for brain applications, here for neurostimulation and/or neurorecording as a deep brain stimulation system 100 as shown in Figures 1 and 2. The probe system 100 comprises at least one probe 130 for brain applications with stimulation and/or recording electrodes 132, wherein e.g. 40 electrodes 132 can be provided on outer body surface at the distal end of the probe 130. By means of the extension wire 120 pulses P supplied by controller 110 can be transmitted to the active lead can 111. The controller 110 can be an IPG 110.

Figure 4 shows a schematically drawing of a distal lead portion, i.e. the distal end 313 of the medical lead 300 according to the present invention in a first embodiment.

The medical lead 300 is a lead of a system 100 for neurostimulation according to the present invention and as generally described above with respect to Figures 1 to 3. More specifically, the system shown in Figure 4 is a Deep Brain Stimulation System 100.

The lead 300 has at its distal end 313 a plurality of elongated electrodes 132.

The lead 300 has a longitudinal extension E along its longitudinal axis X and the electrodes 132 are not aligned perpendicular to the longitudinal extension E.

In particular, the electrodes 132 are substantially aligned to the axis X, i.e. longitudinal axis X of the longitudinal extension E.

According to the embodiment shown in Figure 4, the electrodes 132 are parallel to the axis X of the longitudinal extension E.

The electrodes 132 have non-circular and stretched shapes.

Furthermore, the electrodes 132 are parallel to each other.

Also, the electrodes 132 have all the same width W.

Adjacent electrodes 132 of different rows R are offset to each other.

As can be seen in Figure 4, every second row the lowermost and uppermost electrode 132’, which is the last electrode 132 before the lead tip, i.e. the distal end 304 of the medical lead 300 comprises only half of the length L, i.e. the length L1, when compared with all other electrodes.

The electrodes 132 have a length L that is approx. 2-10 times the width W of the electrode 132, here approx. 10 times the width W of the electrode 132.

The width W of the electrodes 132 and the electrodes 132’ is identical.

The lead 300 according to the embodiment of Figure 4 comprises 40 electrodes 132, which form a complex electrode array, i.e. an array of electrodes 132 that are arranged such the electrodes are arranged at multiple non-planar and non-coaxial positions. The electrodes 132 are positioned at different axial positions along the length of the lead 300, as well as at different angular positions about the circumference of the lead 300.

The function of the lead 300 and the medical system 100, here a DBS system 100 according to the present invention is as follows:

Via the electrodes 132 of the lead 300 an electrical field stimulation to a target region of the brain may be applied. The plurality of electrodes 132, here 40 electrodes 132, which are arranged in a complex electrode array, allows steering of the stimulation field such that the stimulation field may be adapted and conform with the target area or the supero-lateral branch of the medial forebrain bundle.

The stimulation field provided by the electrodes 132 is formed three-dimensionally and adapted to the target region. Only those regions that need to be stimulated are covered by the stimulation field provided by the plurality of electrodes 132.

The target region is for example a deep brain target region, e.g. a cortical structure.

By means of the complex array of stimulation electrodes 132, a stimulation field can be generated that is adapted to and conforms to the target region.

The steering of the stimulation field is improved by the fact that the electrodes 132 forming the complex array have the same width and that adjacent electrodes 132 of different rows R may be offset to each other.

Due to the parallel arrangement of the electrodes 132 an electrode array with high density of electrodes 132 is formed, which is advantageous for a delivery of good stimulation coverage to the target region.

The equal width has the function that the stimulation field part provided by each electrode is substantially equal and allows a better adjustability and predictability of the overall stimulation field.

The offset of the electrodes 132 increases the possibilities to steer the stimulation field provided by the electrodes 132 and allows a more dense packing of the electrodes 132. Thus dead zones, where no or less stimulation can be provided, are avoided.

The elongated electrodes 132 allow an optimal delivery of stimulation to cover the target area and thus the fiber tracks in the target region are optimally stimulated. Accordingly, the therapeutic effect is improved while the impact on surrounding brain tissue is minimized, which might cause in unwanted side effects.

The elongated electrodes 132 allow good stimulation coverage especially in case that the target area is large. Also, elongated electrodes 132 reduce the power consumption and are thus the battery lifetime of the IPG 110 is increased as well as the current density, which is advantageous in terms of safety reasons.

The fact that the electrodes 132 have non-circular and stretched shapes is advantageous for the interaction of the electrodes 132 with long fiber bundles of the supero-lateral branch of the medial forebrain bundle is improved by means of the circular and stretched shapes of the electrodes 132. A maximum therapeutic effect with as little side-effects as possible is provided.

Moreover, as a part of the present disclosure, a method for providing neurostimulation with a medical lead is disclosed. Accordingly, a medical lead for neurostimulation comprising a plurality of elongated electrodes is implanted through a burr hole of the skull of the patient into a target region of neural tissue, e.g. the supero-lateral branch of the medial forebrain bundle.

Due to the fact that the electrodes 132 are arranged at the distal end of the lead 300, the insertion of the lead 300 is restricted to absolutely necessary pathway and the once the tip end 315 has reached the target region also the electrodes 132 are correctly positioned.

The electrodes 132 are after correct placement of the lead 300 automatically aligned to the insertion trajectory and to the fiber tracks.

The stimulation is provided via the electrodes 132 to the target region. The stimulation field may be adapted such as to conform to the target region. To achieve this, the relevant electrodes 132 are selected and switched on and strength of the electrical field provided by these electrodes 132 is adjusted accordingly so as to form a stimulation field that is adapted such as to conform to the target region.

Figure 5 shows a schematically drawing of a distal lead portion, i.e. the distal end 304 of the medical lead 300 according to the present invention in a second embodiment.

The embodiment as shown in Figure 5 comprises the same structural and functional features as the embodiment shown in Figure 4.

The only difference is the fact that the electrodes 132, 132’ have a length L that is around half of the length L of the electrodes according to the embodiment of Figure 4, wherein the width W is the same as the width W according to the embodiment of Figure 4.

Figure 6 shows a schematically drawing of a distal lead portion, i.e. the distal end 304 of the medical lead 300 according to the present invention in a third embodiment.

The lead 300 shown in Figure 6 comprises each and every structural and functional feature and advantage as the lead 300 shown in Figure 4 and described above, except the following difference:

The electrodes 132 and the axis X of the longitudinal extension E enclose an angle a and the electrodes 132 are spirally wound around the distal end 304 of the lead 300. All electrodes 132 have the same length L and the same width W.

This design has the function to conform to the characteristics of the target region, where fiber tracks are not straight but may have at least partially curved portions. Also, even in case of a slight difference of the intended insertion position, this design still allows good stimulation coverage due to the fact the electrodes 132 a wound around the axis X of the longitudinal extension E.

Figure 7 shows a schematically drawing of a distal lead portion, i.e. the distal end 304 of the medical lead 300 according to the present invention in a fourth embodiment.

The embodiment as shown in Figure 7 comprises the same structural and functional features as the embodiment shown in Figure 6.

The only difference is the fact that the electrodes 132 have a width W that is around half of the width W of the electrodes according to the embodiment of Figure 6, wherein the length L is the same as the length L according to the embodiment of Figure 6.

Figure 8 shows a schematically drawing of a distal lead portion, i.e. the distal end 304 of the medical lead 300 according to the present invention in a fifth embodiment. The embodiment of Figure 8 is similar to the embodiment of Figure 6 and comprises the same structural and functional features as the embodiment of Figure 6.

According to this embodiment, further electrodes 134 are arranged between two adjacent elongated electrodes 132.

The further electrodes 134 are be non-elongated microelectrodes with a dot-like rounded rectangular shape. A row R of electrodes 132, 134 is formed by alternating one elongated electrode 132 and the further electrode 134.

The further electrodes 134 have a specific function. Here, the further electrodes 134 are sensing and recording electrodes. The further electrodes 134 are used for sensing and/or recording only and the elongated electrodes 132 are used for stimulation only.

Figure 9 shows a schematically drawing of a distal lead portion, i.e. the distal end 304 of the medical lead 300 according to the present invention in a sixth embodiment. The embodiment of Figure 9 is similar to the embodiment of Figure 6 and comprises the same structural and functional features as the embodiment of Figure 6.

According to this embodiment, a first array A1 of elongated electrodes 132 and a second array A2 of non-elongated electrodes 134 may be provided.

The first array A1 of elongated electrodes 132 and the second array A2 of electrodes 134 form both a complex array of electrodes.

The second array A2 is arranged next to the tip 315 of the lead 300 and the first array A2 is in an area adjacent to the area of the second array A2, wherein the area of the first array A1 of electrodes 132 is more proximal than the area of the second array A2.

Furthermore, the elongated electrodes 132 may be formed by electrodes with a fractal design as shown in Figures 10 to 12. A fractal design of an electrode is given in cases where a part of the electrode is similar to the entire electrode itself except smaller. A fractal design is according to the present disclosure also provided by star-like designs as shown in Figure 10. Two opposing tips 133 of the star-shape form together an elongated portion of the electrode 132 so as to form at least in terms of function an elongated electrode design. A further possible fractal design can be provided by using a checked pattern P design for the electrodes 132 as shown in Figures 11 and 12.

Two outermost portions 133 of the checked pattern P form together an elongated portion of the electrode 132 so as to form at least in terms of function an elongated electrode design.

The electrodes with fractal design are arranged in a complex array of electrodes in the embodiments shown in Figures 10 to 12.

These electrodes may act as antennas and the may operate with good performance in a wide range of frequencies.

Here follows the translation of the Dutch text on the next pages: 1. A medical lead (300) for neurostimulation, especially for deep brain stimulation, comprising a plurality of elongated electrodes (132). 2. A medical lead (300) according to claim 1, wherein the lead (300) has a longitudinal extension (E) and wherein the electrodes (132) are not aligned perpendicular to the longitudinal extension (E). 3. A medical lead (300) according to claim 2, wherein the electrodes (132) are substantially aligned to the axis (X) of the longitudinal extension (E) and especially parallel to the axis (X) of the longitudinal extension (E). 4. A medical lead (300) according to claim 2, wherein the electrodes (132) and the axis (X) of the longitudinal extension (E) enclose an angle (a) and wherein the electrodes (132) are spirally wound around the lead (300). 5. A medical lead (300) according to one of the preceding claims, wherein the electrodes (132) have non-circular and stretched shapes. 6. A medical lead (300) according to one of the preceding claims, wherein the electrodes (132) are parallel to each other. 7. A medical lead (300) according to one of the preceding claims, wherein the electrodes (132) have the same width (W). 8. A medical lead (300) according to one of the preceding claims, wherein the lead (300) has a proximal end (311) and distal end (313) with a tip end (315) and wherein the electrodes (132) are arranged at the distal end (315) of the lead (300). 9. A medical lead (300) according to one of the preceding claims, wherein adjacent electrodes (132) of different rows (R) are offset to each other. 10. A medical lead (300) according to one of the preceding claims, wherein the electrodes (132) have a length (L) that is approx. 2-10 times the width (W) of the electrode (132). 11. A medical lead (300) according to one of the preceding claims, wherein the lead (300) comprises at least 20 electrodes (132), especially approx. 30 to 45 electrodes (132), more especially approx. 40 electrodes (132). 12. A medical lead (300) according to one of the preceding claims, wherein the electrodes (132) form a complex electrode array. 13. A medical lead (300) according to one of the preceding claims, wherein the electrodes (132) have a fractal design. 14. A system (100) for neurostimulation comprising at least one lead (300) according to one of the preceding claims. 15. The system (100) according to claim 14, wherein the system (100) is a deep brain stimulation system.

Claims (15)

A medical guide wire (300) for neurostimulation, in particular for deep brain stimulation, comprising a plurality of elongated electrodes (132). A medical guide wire (300) according to claim 1, wherein the guide wire (300) has a longitudinal extension (E) and wherein the electrodes (132) extend non-perpendicular to the longitudinal extension (E). A medical guide wire (300) according to claim 2, wherein the electrodes (132) extend approximately parallel to the axis (X) of the longitudinal extension (E) and in particular parallel to the axis (X) of the longitudinal extension (E). A medical guide wire (300) according to claim 2, wherein the electrodes (132) and the axis (X) of the longitudinal extension (E) enclose an angle (a) and wherein the electrodes (132) are spirally wound around the guided wire (300). A medical guide wire (300) according to any one of the preceding claims, wherein the electrodes (132) have non-circular and stretched shapes. A medical guide wire (300) according to any one of the preceding claims, wherein the electrodes (132) extend parallel to each other. A medical guide wire (300) according to any one of the preceding claims, wherein the electrodes (132) have the same width (W). A medical guide wire (300) according to any one of the preceding claims, wherein the guide wire (300) has a proximal end (311) and a distal end (313) with an end portion (315) and wherein the electrodes (132) are arranged are near the distal end (313) of the guided wire (300). A medical guide wire (300) according to any one of the preceding claims, wherein adjacent electrodes (132) of different rows (R) are spaced apart. A medical guide wire (300) according to any one of the preceding claims, wherein the electrodes (132) have a length (L) that is approximately. Is 2-10 times the width (W) of the electrode (132). A medical guide wire (300) according to any one of the preceding claims, wherein the guide wire (300) comprises at least 20 electrodes (132), in particular about 30 to 45 electrodes (132), even more particularly about 40 electrodes (132). A medical guided wire (300) according to any one of the preceding claims, wherein the electrodes (132) form a complex electrode concatenation. A medical guide wire (300) according to any one of the preceding claims, wherein the electrodes (132) have a fractal shape. A neurostimulation system (100) comprising at least one guide wire (300) according to any one of the preceding claims. The system (IOO) of claim 14, wherein the system (100) is a deep brain stimulation system.