Patent Description:
Modern medical technology allows for interacting with the human or animal neural system, e.g., if body functions have been lost or in case of dysfunctions of organs so as to bridge or restore the latter. For this, implantable electrodes are used that are brought into contact with the respective nerves to be stimulated or sensed. For example, micro-electrodes or multi-electrode arrays are known in prior art which comprise a plurality of such electrodes through which neural signals are supplied for stimulating nerves of a nervous tissue. Such implantable electrodes usually are flexible and are made from medical silicone, Parylene, or polyimide, and a metal foil which forms the electrode contacts to the nerves as well as the bond pads to the external wiring (connection means), and the conductor tracks between the sensor pads and the contact pads to the external wiring.

The conductor tracks which lead from contact pads contacting the respective nerves to bond pads that are connected to external wiring may be formed by means of a laser-structuring of a metal foil layer according to known technologies.

The conductor tracks are rather instable mechanically. Due to their fineness, they are very fragile and may break.

<CIT>, <CIT>, <CIT>, <CIT>, <CIT> relate to implantable devices having metal structures embedded in a layer. <CIT> relates to an implantable device relating to the features of the preamble of claim <NUM>.

It is an object of the present invention to provide an implantable electrode and a method of producing such an electrode which avoid the above described problems at least partially.

This object is solved by an implantable electrode device having the features according to claim <NUM> and by a method of producing an implantable electrode device having the features according to claim <NUM>. Preferred embodiments of the invention are defined in the respective dependent claims.

Accordingly provided is an implantable electrode device, comprising.

The at least one electrode contact is directly or indirectly exposable to the nerve. Indirectly means that there are other layers of biological tissues are in between.

That is, the conducting wire is guided to the respective electrode contact and fixed directly to the electrode contact. There is no other conductor path portion between the conducting wire and the electrode contact which is exposable to the nerve. In particular there is no elongated conductor path formed from a metal foil between the conducting wire and the electrode contact on the electrode device.

Herein, the at least one conducting wire is arranged in a core included within the first layer.

Herein, the core has the form of a channel within the first layer, extending from a first opening in the first layer to a position underneath the at least one electrode contact.

The at least one wire is guided through the channel the first opening into a cable coupling the electrode with an interface unit.

A strain relief means is arranged within the core and guided through the channel and the first opening into the cable and being fixed to the electrode and to the interface unit.

Further advantageously, the at least one electrode contact is formed as at least one contact pad.

Yet further advantageously, the at least one conducting wire is fixed to the at least one electrode contact at a point located underneath the at least one electrode contact, i.e., underneath the at least one contact pad.

Yet further advantageously, the first layer has a first surface and a second surface, wherein the second layer is arranged on the first surface, and wherein the first opening is formed in the second surface of the first layer.

Hereby, the strain relief means may be one of a suture, a string, litz wires, or other elongated, flexible, high pull-strength element.

The strain relief may be provided for the complete electrical path that is continuously through the electrode to the electrode cable up to the interface unit at the other end of the cable.

Moreover, preferably, the substrate is made of a flexible material, in particular, of Parylene, silicone, or polyimide.

The implantable electrode device may be formed as a micro-electrode array.

The core may comprise a filling material made from silicone.

The second layer may be made from a polymer, in particular from Parylene-C.

Further preferably, the core comprises a neutral fiber of the electrode device. The neutral fiber is a straight line which keeps its length constant when the device is bent along (i.e., in direction of) that line.

The implantable electrode may be formed as a micro-electrode array.

The micro-array may comprise a plurality of electrode contacts.

Thus, the inventive configuration provides an implantable electrode which consumes less space than configurations using conductor tracks known from prior art, since conductive wires are used which are guided inside the cavity provided in the second layer. Moreover, the wires are protected in the cavity which is filled with silicone and thus, is sealed. Also, the cavity provides for accommodating the strain relief means, namely, the suture inside the cavity which is guided through the entire electrode so as to uniformly and continuously ensure stress relief throughout the entire implantable electrode.

The invention further provides a method of forming an implantable electrode device, in particular according to any one of the preceding claims, the method comprising the steps:.

In the following, the invention is described by means of embodiments and the drawing in further detail. In the drawing:.

<FIG> shows a schematic perspective view of an implantable electrode <NUM> according to prior art. The electrode <NUM> comprises an electrically insulating substrate <NUM>, which here is medical silicone, in which conductor paths <NUM> are embedded so as to connect electrode contacts or contact pads <NUM> to bond pads or terminal contacts <NUM>-<NUM>, which in turn are connected to an electrode cable (not shown) connected to a power supply (not shown). The conductor paths <NUM> as well as the electrode contacts <NUM> and terminal contacts <NUM>-<NUM> may be produced by laser structuring of a metal foil, which is well known in the prior art.

<FIG> is a cross-sectional view of an implantable electrode device <NUM> according to a first embodiment of the invention illustrating the sequence of layers of the implantable electrode device <NUM>. As can be seen, the electrode device <NUM> basically is made up of a first layer <NUM>; 7a 7b, 7c, and a second layer <NUM>. The second layer <NUM> is arranged on a first surface <NUM> on top of the first layer <NUM>, 7a 7b, 7c and includes at least one electrode contact <NUM>, <NUM>'. The at least one electrode contact <NUM>, <NUM>' is exposable directly or indirectly to nervous tissue of a human or of an animal. However, other layers of biological tissues might be in between.

The implantable electrode device <NUM> further comprises a connecting means which electrically connects the at least one electrode contact <NUM>, <NUM>' to the outside of the implantable electrode device <NUM>. The connecting means is made up of at least one conducting wire <NUM>, <NUM>'. The at least one conducting wire <NUM>, <NUM>' is arranged within the first layer <NUM>; 7a, 7b, 7c and is fixed to the at least one electrode contact <NUM>, <NUM>'.

More specifically, the at least one conducting wire <NUM>, <NUM>' is guided up to the at least one contact <NUM>, <NUM>' and fixed directly to the at least one contact <NUM>, <NUM>' of the electrode device <NUM> on the backside of the at least one contact <NUM>, <NUM>'. The backside of the at least one contact <NUM>, <NUM>' is the side opposed to the side exposable to the nerve of the nervous tissue. There are no metal conductor portions on the electrode device <NUM> between the at least one contact <NUM>, <NUM>' and the at least one conducting wire <NUM>, <NUM>'. As can be seen in <FIG> and in <FIG>, the location where the conducting wires are fixed to the at least one contact <NUM>, <NUM>' is at the (temporary) second opening <NUM> of the first silicon layer <NUM>; 7b 7c. This is underneath the at least one electrode contact <NUM>, <NUM>'.

Fixation of the at least one conducting wire <NUM>, <NUM>' to the at least one contact <NUM>, <NUM>' is done e.g., by welding.

The electrode device <NUM> may further comprise a strain relief <NUM> for the at least one conducting wire <NUM>, <NUM>', which will be further described below.

The first layer <NUM> is made up of medical silicone material. The second layer <NUM> is a Parylene-C layer applied by chemical vapor deposition (CVP) on top of the first layer <NUM>, in particular, on the first surface <NUM> of the first layer <NUM>.

<FIG> is a cross-section of the implantable electrode <NUM> in an intermediate stage of production, illustrating how the at least one conducting wire <NUM>, <NUM>' is placed into the implantable electrode.

Hereto, the first layer <NUM> has a core <NUM> which is formed as a channel <NUM> extending from a first opening <NUM> formed in a second surface <NUM> of the first layer <NUM> to the location or locations of the at least one electrode contact <NUM>, <NUM>' through the electrode device <NUM>. The second surface <NUM> is opposite to the first surface <NUM>.

During production, the at least one conducting wire <NUM>, <NUM>' is placed in the core <NUM> within the implantable electrode <NUM>. The core <NUM> is a zone in the interior of the first layer <NUM>, i.e., the core <NUM> is enclosed by the first layer <NUM>. Later during the production process, the core <NUM> (i.e., the hollow space) is filled up with silicon glue, thus fixing the wires <NUM>, <NUM>'.

The optional strain relief <NUM> (described below) is also placed in the channel <NUM> through the opening <NUM>.

<FIG> illustrates the implantable electrode device <NUM> of the first embodiment of the present invention being electrically coupled with an interface unit <NUM> through the at least one conducting wire <NUM>, <NUM>'. The at least one conducting wire <NUM>, <NUM>' is guided within a cable <NUM>. The cable <NUM> is flexible and comprises a tube made from e.g., silicone.

The interface unit <NUM> may be, or comprise, a plug and/or an electronic unit which processes signals from and/or to the electrode device <NUM>. It may relay the signals from/to a remote location. The interface unit <NUM> is of course a unit physically distinct and separate from the electrode device <NUM>.

The electrode device <NUM> may further comprise a strain relief <NUM> for the at least one conducting wire <NUM>, <NUM>', which is fixed to the electrode device <NUM> and guided within the cable <NUM> to the interface unit <NUM> and fixed there. Within the electrode device <NUM>, the strain relief <NUM> is guided through the channel <NUM> comprised in the core <NUM>. The strain relief <NUM> extends through the entire channel <NUM> and thus, basically through the entire electrode device <NUM> and serves as a strain relief means, as described above.

The strain relief <NUM> is guided through the core <NUM> in a way that ensures it is straight and under slight tension. Tensile stresses applied in axial direction of the electrode array will distribute between the wires and the suture with the suture taking more tensile load compared to the wires.

The strain relief <NUM> may be a suture. Instead of a suture <NUM>, other flexible material that can withstand high pull forces (e.g., string, thread, litz wire, Kevlar filament, etc.) can be used as the strain relief means <NUM>.

The strain relief <NUM> is placed into the electrode device <NUM> at the same time during production as the at least one conducting wire <NUM>, <NUM>', refer to the description thereof above. Since the entire core <NUM> is filled with silicone, the inner space accommodating the at least one conducting wire <NUM>, <NUM>' and the strain relief <NUM> is sealed.

<FIG> illustrates a second embodiment of the invention. While the at least one conducting wire <NUM>, <NUM>' is guided in meander form within the electrode device <NUM>, the strain relief <NUM>, i.e., the suture <NUM> is guided straight within the electrode device <NUM>. This provides for the strain relief of the conducting wires <NUM>, <NUM>' within the electrode device <NUM>.

<FIG> illustrates a cross-section of the implantable electrode of <FIG> along a cut line A-A'. Preferably the core <NUM> is located around (i. e, comprises) the "neutral fiber" nf in the electrode device. The neutral fiber is a straight line which keeps its length constant when the device is bent along (i.e., in direction of) that line. On other words, the neutral fiber nf or neutral plane is the one plane within the electrode device <NUM>, along which there are no longitudinal stresses or strains when the electrode device <NUM> is bent. That is, the fiber nf keeps its length constant when the electrode device <NUM> is bent. If the core <NUM> is around the neutral fiber nf, the conducting wires <NUM>, <NUM>' placed therein keep their lengths always constant.

By the configuration described above, a space saving arrangement is achieved which moreover provides for strain relief over the entire length of the implantable electrode device <NUM>.

With reference to <FIG>, a production process for the implantable electrode device <NUM> of the present invention is described step by step.

In a first step, refer to <FIG>, an intermediate polymeric release layer <NUM> is applied onto a carrier substrate <NUM> made e.g., from ceramics. The intermediate layer <NUM> separates the carrier substrate <NUM> from the layer 7a, and allows to remove the ceramic carrier substrate <NUM> along with itself later.

A first layer 7a of medical silicone is applied by spin coating onto the intermediate layer <NUM>, refer to <FIG>.

Then, the first layer 7a is structured with a Laser to define a (future) first opening <NUM> around its center axis ca, which center axis ca is perpendicular to the surface of the first layer 7a, refer to <FIG>.

A (future) cavity for a core <NUM> will be prepared by applying sacrificial layer process making use of polyimide material, e.g., of a laser structured Kapton® band.

That is, the Kapton band as sacrificial layer sl is applied onto the structured first silicone layer 7a, refer to <FIG>.

The sacrificial layer sl is Laser-structured to define the geometry of the (future) cavity for the core <NUM>, refer to <FIG>.

The parts of the sacrificial layer sl which do not define the geometry of the (future) cavity for the core <NUM> are removed, refer to <FIG>.

The sacrificial layer sl as well as the parts of the first silicone layer 7a not-covered by the sacrificial layer sl are covered with a second silicone layer 7b by spin coating, refer to <FIG>.

In order to obtain a plane surface, the second silicone layer 7b is pressed using a PTFE foil pf placed onto the second layer 7b during curing the silicone, refer to <FIG>. The PTFE foil is removed after curing.

As a bond coat, a third silicone layer 7c is applied onto the second silicone layer 7b, refer to <FIG>, and Laser-structured to define a (future) second opening <NUM> and a (future) welding point above the second opening <NUM>, refer to <FIG>.

On the third silicone layer 7c, a metal layer <NUM>, e.g., a platinum90-iridium10 foil, is laminated, and cured under pressure, refer to <FIG>, in order to keep its surface plane.

The cured metal layer <NUM> is then Laser-structured to form electrode contacts <NUM>. Outer parts thereof not forming electrode contacts are removed, refer to <FIG>.

Silicone glue sg is applied in an annular shape around a (future) opening <NUM> for a future welding point, the opening <NUM> and welding point being underneath electrode contact <NUM>, refer to <FIG> and <FIG>.

The location above the welding point is temporarily covered by a Kapton® foil kf, refer to <FIG>.

The metal layer <NUM> in turn is covered by the second layer <NUM> which is e.g., a Parylene-C layer <NUM> applied by chemical vapor deposition (CVD), refer to <FIG>.

The Parylene-C-layer <NUM> is Laser-structured to allow re-opening the welding point <NUM>, refer to <FIG>.

The welding point <NUM> is opened by removing the parts of the Parylene layer <NUM> and Kapton foil kf covering it, refer to <FIG>.

Then, the carrier substrate <NUM> along with the intermediate polymeric release layer <NUM> is removed, thus exposing the first opening <NUM> to the sacrificial layer (sl) from the lower side, refer to <FIG>.

Then, the sacrificial layer sl and residential silicone particles are removed from the lower side, refer to <FIG>, thus forming the cavity (<NUM>) which corresponds to the future core <NUM>.

Then, conducting wires i.e., the connecting means <NUM>, <NUM>' are laid out within the cavity (corresponding to core <NUM>) and welded directly to the at least one electrode contact <NUM>, <NUM>', refer to <FIG>. The connecting means <NUM>, <NUM>' (e.g., a conducting wire) are welded to the rearward surface of the at least one electrode contact <NUM>, <NUM>', that is the side opposite to the side exposable to the nervous tissue, and at the location of the at least one electrode contact exposable to the nervous tissue.

Yet further, the strain relief, that is, the suture <NUM> is laid out within the cavity for the core <NUM>, refer to <FIG>.

The point on the metal contact <NUM> opposite to the welding point is sealed with silicone glue sg, refer to <FIG>.

Claim 1:
Implantable electrode device (<NUM>), comprising
a first layer (<NUM>; 7a 7b, 7c), and a second layer (<NUM>), the second layer (<NUM>) being on top of the first layer (<NUM>) and including at least one electrode contact (<NUM>, <NUM>'), the at least one electrode contact (<NUM>, <NUM>') being exposable to a nerve of a nervous tissue of a human or of an animal,
a connecting means which electrically connects the at least one electrode contact (<NUM>, <NUM>'), wherein
the connecting means is made up of at least one conducting wire (<NUM>, <NUM>'), the at least one conducting wire (<NUM>, <NUM>') being arranged within the first layer (<NUM>; 7a 7b, 7c) and being fixed to the at least one electrode contact (<NUM>, <NUM>'), wherein
the at least one conducting wire (<NUM>, <NUM>') is arranged in a core (<NUM>) included within the first layer (<NUM>; 7a 7b, 7c), and
wherein the core (<NUM>) has the form of a channel (<NUM>) within the first layer (<NUM>), extending from a first opening (<NUM>) in the first layer (<NUM>; 7a 7b, 7c) to a position (<NUM>) underneath the at least one electrode contact (<NUM>, <NUM>')
wherein the at least one wire (<NUM>, <NUM>') is guided through the channel (<NUM>) and the first opening (<NUM>) into a cable (<NUM>) coupling the electrode (<NUM>) with an interface unit (<NUM>).
characterized in that
a strain relief means (<NUM>) is arranged within the core (<NUM>) and guided through the channel (<NUM>) and the first opening (<NUM>) into the cable (<NUM>) and being fixed to the electrode (<NUM>) and to the interface unit (<NUM>).