Patent Application
20140277317
1. Field of Endeavor
The present application relates to microelectrode arrays and methods of fabricating microelectrode arrays, and particularly to a microelectrode array and method of fabricating a microelectrode array such as a neural interface with an integrated stiffening shank.
2. State of Technology
This section provides background information related to the present disclosure which is not necessarily prior art.
Micro-electrode neural interfaces are an essential tool in neuroscience, targeting the neuronal activity of neurons, enabling researchers and clinicians to better explore and understand neurological diseases. These interfaces use implanted neural probes to bypass damaged tissue and stimulate neural activity, thereby regaining lost communication and/or control with the affected parts of the nervous system.
The most common neural probes are thin-film micromachined probes fabricated on silicon substrates using MEMS fabrication techniques. Neuronal stimulation and recording is conducted at discrete sites (metal pads) along the probes. The metal pads are connected, via metal traces, to output leads or to other signal processing circuitry. Silicon is the most widely used substrate for this type of probe because of its unique physical/electrical characteristics. The prevalence of silicon in the microelectronics industry ensures the neural probes can be relatively easily and efficiently fabricated in large numbers utilizing common MEMS fabrication techniques. There is, however, concern regarding the suitability of these silicon-based neural probes tor long-term (i.e. chronic) studies as the silicon will corrode over time when implanted in a body. Furthermore, the continuous micro-motion of the brain can induce strain between the brain tissue and implanted electrode promoting chronic injury and glial scarring at the implant site. Therefore, there are outstanding questions regarding the long-term safety and functionality of these silicon-based neural probes.
Polymer-based neural probes are an attractive alternative. First, they are flexible, thereby minimizing strain between the brain tissue and the implanted probe. Second, they are fully biocompatible and thus suitable for chronic implantation with no loss of functionality or safety. Finally, these polymer-based neural probes can be easily fabricated in large numbers using existing microfabrication techniques.
Unfortunately, the inherent flexibility of the polymer-based neural probes means the probes also have a low mechanical stiffness causing the devices to buckle and fold during insertion. To counteract this, separate stiffening shanks are typically fabricated and then attached to individual neural probes. This procedure is very time-consuming, and in most cases, where the stiffening shanks are extremely thin (<50 μm thick), also very difficult.
Features and advantages of the disclosed apparatus, systems, and methods will become apparent from the following description. Applicant is providing this description, which includes drawings and examples of specific embodiments, to give a broad representation of the apparatus, systems, and methods. Various changes and modifications within the spirit and scope of the application will become apparent to those skilled in the art from this description and by practice of the apparatus, systems, and methods. The scope of the apparatus, systems, and methods is not intended to be limited to the particular forms disclosed and the application covers all modifications, equivalents, and alternatives falling within the spirit and scope of the apparatus, systems, and methods as defined by the claims.
The present application relates to neural interface devices and methods of fabrication of neural interface devices. The neural interface device includes a first dielectric material having at least one first opening for a first electrical conducting material; a first electrical conducting material in the first opening; at least one first interconnection trace electrical conducting material connected to the first electrical conducting material; and a stiffening shank material adjacent the first dielectric material, the first electrical conducting material, and the first interconnection trace electrical conducting material. In one embodiment the method of fabricating a neural interface includes the steps of depositing a bottom dielectric material on a substrate; etching openings in the bottom dielectric material for bottom electrodes; depositing and patterning bottom electrodes; depositing and patterning a bottom interconnection trace metal; depositing an interlayer dielectric material; depositing a stiffening shank material; depositing an interlayer dielectric material; patterning a stiffening shank from the stiffening shank material; depositing an interlayer dielectric material; depositing and patterning a top interconnection trace metal; depositing and patterning top electrodes; depositing a top dielectric material; etching openings in the top dielectric material for the top electrodes and connector openings; and releasing the device from the substrate.
The apparatus, systems, and methods are susceptible to modifications and alternative forms. Specific embodiments are shown by way of example. It is to be understood that the apparatus, systems, and methods are not limited to the particular forms disclosed. The apparatus, systems, and methods cover all modifications, equivalents, and alternatives falling within the spirit and scope of the application as defined by the claims.
The accompanying drawings, which are incorporated into and constitute a part of the specification, illustrate specific embodiments of the apparatus, systems, and methods and, together with the general description given above, and the detailed description of the specific embodiments, serve to explain the principles of the apparatus, systems, and methods.
Referring to the drawings, to the following detailed description, and to incorporated materials, detailed information about the apparatus, systems, and methods is provided including the description of specific embodiments. The detailed description serves to explain the principles of the apparatus, systems, and methods. The apparatus, systems, and methods are susceptible to modifications and alternative forms. The application is not limited to the particular forms disclosed. The application covers all modifications, equivalents, and alternatives falling within the spirit and scope of the apparatus, systems, and methods as defined by the claims.
The apparatus, systems, and methods described and claimed herein enable combining of a polymer-based neural probe with an integrated stiffening shank. With the apparatus, systems, and methods described and claimed herein polymer-based neural probes are created with a stiffened area suitable for insertion into tissue but also with a flexible cable to minimize tissue damage. Utilizing existing microfabrication techniques, large numbers of stiffened polymer-based neural probes can be created easily and efficiently. The flexible neural interface with integrated stiffening shank described and claimed herein is suitable for implantation in both humans and animals for either acute or chronic studies of various neurological disorders and as interfaces between neural tissue and prosthetics. (This assumes the materials comprising the device have been properly chosen with regards to their biocompatibility.) The neural probes described and claimed herein have a flexible, polymer-based cable, which runs the length of the probe and contains the electrodes and interconnection traces and a stiffening shank at the tip (where the electrodes are located). The stiffening shank is built into the device utilizing standard microfabrication techniques, and requires no post-fabrication attachment. There are different versions of the flexible neural interface with integrated stiffening shank for example a fully-encapsulated stiffening shank and a partially-encapsulated stiffening shank. (The partially-encapsulated stiffening shank may not be suitable for chronic studies.) These neural interfaces can be created with electrodes on the “top,” on the “bottom,” or on both the “top” and “bottom.”
In addition to being an integrated, wafer-level process, another advantage of this process is that the stiffening shank is not limited to silicon, unlike traditional non-polymer based neural interfaces. Other materials, with varying mechanical properties, can also be used, such as other semiconductors, dielectrics (e.g. glass/quartz/silicon-dioxide, sapphire), ceramics (e.g. alumina), metals (e.g. titanium, tungsten), and others (e.g. silicon-carbide, diamond). Ultimately, the mechanical properties and the thickness of the material used for the stiffening shank dictate the stiffness of the neural interface. Further, the process is not limited to vapor-deposited (e.g. sputtering, electron-beam/thermal evaporation, atomic layer deposition, chemical, vapor deposition, physical vapor deposition) materials and thicknesses. The encapsulation process allows free-standing films (e.g. metal foils) to be used.
This disclosure describes a fully-integrated fabrication process for flexible neural interfaces with integrated stiffening shanks. These neural interfaces are suitable for implantation in both humans and animals for either acute or chronic studies of various neurological disorders (e.g. Clinical Depression, Parkinson's Disease, Epilepsy) and as interfaces between neural tissue and prosthetics (e.g. Retinal Implants, Auditory implants).
In one embodiment the device disclosed in the present application is a microelectrode array, such as a neural interface, with an integrated stiffening shank having electrodes on the top or having electrodes on the bottom or having electrodes both on the top and on the bottom. In another embodiment, the present application relates to a microelectrode array fabrication method and in particular to a microelectrode neural interface fabrication method and method of fabricating a microelectrode array with an integrated, stiffening shank. Other example implementations provide a microelectrode array having an electrical conduit embedded within a simultaneously-polymerized multi-polymer precursor layer-based, single polymer film, wherein a portion of the conduit is exposed through the single polymer film.
The flexible neural interface with integrated stiffening shank described here is suitable for implantation in both humans and animals for either acute or chronic studies of various neurological disorders and as interfaces between neural tissue and prosthetics. The neural probes described here have a flexible, polymer-based cable, which runs the length of the probe and contains the electrodes and interconnection traces and a stiffening shank at the tip (where the electrodes are located). The stiffening shank is integrated into the device utilizing standard microfabrication techniques, and requires no post-fabrication attachment.
Referring now to the drawings and in particular to
A substrate 10 is shown in
A bottom polymer 12 is deposited on the substrate 10. This is shown in
An opening 14 is etched in the bottom polymer for the bottom electrodes. This is shown in
The bottom electrodes are deposited and patterned. This is shown in
Interconnection trace metal 18 is deposited and patterned. This is shown in
An interlayer polymer 20 is deposited on the bottom polymer 12. This is shown in
Stiffening shank material 22 is deposited on the interlayer polymer 20. This is shown in
An interlayer polymer 24 is deposited on the stiffening shank 22. This is shown in
The stiffening shank material 22 is patterned to produce a patterned stiffening shank 26. This is shown in
An interlayer polymer 28 is deposited on the patterned stiffening shank 26. This is shown in
Interconnection trace metal 30 is deposited and patterned. This is shown in
Patterned top electrode metal 32 is deposited and patterned. This is shown in
A top polymer 34 deposited on the top electrode metal 32. This is shown in
Openings 36 are etched in the top polymer for the top electrodes and external connections. This is shown in
The final release of the device is illustrated in
Referring now to
In the next step a bottom polymer 12 is deposited on the substrate 10.
In the next step an opening 14 is etched in the bottom polymer for the bottom electrodes.
In the next step the bottom electrodes are deposited and patterned. The material 16 for the bottom electrodes is deposited and patterned.
In the next step interconnection trace metal 18 is deposited and patterned.
In the next step an interlayer polymer 20 is deposited on the bottom polymer 12 and the interconnection trace metal 18.
In the next step a stiffening shank material 22 is deposited on the interlayer polymer 20.
In the next step an interlayer polymer 24 is deposited on the stiffening shank material 22.
Referring now to
In the next step the stiffening shank material 22 is patterned to produce a patterned stiffening shank 26.
In the next step an interlayer polymer 28 is deposited on the patterned stiffening shank 26 and interlayer polymer 20.
In the next step interconnection trace metal 30 is deposited and patterned.
In the next step patterned top electrode metal 32 is deposited and patterned.
In the next step a top polymer 34 is deposited on the top electrode metal 32 and interlayer polymer 28.
In the next step openings 36 are etched in the top polymer for the top electrodes and external connections.
The next step is the final release of the device. The substrate 10 has been removed.
The process described above (
The process is also compatible with different locations of the electrode metal, with respect to the outer polymer layers, by appropriate re-arrangement of steps. As shown in the process described above, the bottom electrodes are flush with the bottom polymer layer and the top electrodes are underneath the top polymer layer (i.e. effectively recessed from the top polymer layer). In another example implementation, the top electrodes can be on top of the top polymer layer by depositing and patterning them after the openings in the top polymer layer. In another example implementation, posts in the substrate material can be etched at the electrode locations prior to the deposition of the bottom polymer layer. This has the effect of recessing the bottom electrodes from the bottom polymer surface. In another example implementation, the bottom electrode material can be deposited before the bottom polymer layer, which has the effect of putting the bottom electrodes on the outside of the device (i.e. the bottom polymer layer). These different top and bottom electrode locations, with respect to the polymer layers, can be mixed and matched with this process to create a variety of different neural interfaces.
The process described above creates a neural interface with only two layers of interconnection trace metal (one for the top electrodes and one for the bottom electrodes). This same process can be used with multiple layers of interconnection trace metal for both the top and bottom electrodes. Each additional interconnection trace metal layer requires the use of another interlayer polymer layer (with appropriate openings between the interconnection trace metal layers). Different numbers of interconnection trace metal layers can be used for the top and bottom electrodes. One example would be a process/interface in which the top electrodes use 3 layers of interconnection trace metal and the bottom electrodes use 4 layers of interconnection trace metal.
The outlined fabrication steps are independent of the neural interface dimensions (length, width, thickness, overall shape) and the electrode properties (number, spatial arrangement, thickness, shape, material).
The fabrication process is independent of the specific type of polymer used to create the neural interface. Polymides and parylenes (poly(p-xylylene) are the two most commonly used polymers due to their biocompatibility. Other polymers can be used (provided these materials can be deposited and etched), although these other polymers may not be biocompatible and, thus, the neural interfaces created with these materials may not be suitable for chronic and/or acute implantation studies.
The fabrication process is independent of the specific materials used for the interconnection trace metals and the electrode metals. Although metals (e.g., gold, titanium, platinum, iridium) are the most common, due to their ease of deposition and patterning, any conductive material (e.g. other metals, conductive polymers, conductive inks) can be used. In addition, although it is shown that separate metal layers are used for the electrode metal and interconnection trace metal, this fabrication process allows a single material to be used for both the electrode metal and interconnection trace metal by elimination of the electrode metal deposition and patterning steps. This fabrication process does not require each metal layer (interconnection trace metal or electrode metal) to be comprised of the same material. A different conductive material can be used for each metal layer to meet the desired electrical and mechanical specifications.
The fabrication process is also independent of the specific material used for the stiffening shank. It is also independent of the dimensions (length, width, thickness, overall shape) of the stiffening shank. Any material that can be deposited and etched can be used. For Version 1 of the device (Fully-Encapsulated), the final device should be biocompatible and suitable for chronic and acute implantation studies, regardless of whether the stiffening shank material is biocompatible (provided the chosen polymer is biocompatible). For Version 2 of the device (Partially-Encapsulated), unless the stiffening shank material is biocompatible, the neural interface created may not be biocompatible and therefore may not be suitable for chronic and/or acute implantation studies.
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Although the description above contains many details and specifics, these should not be construed as limiting the scope of the application but as merely providing illustrations of some of the presently preferred embodiments of the apparatus, systems, and methods. Other implementations, enhancements and variations can be made based on what is described and illustrated in this patent document. The features of the embodiments described herein may be combined in all possible combinations of methods, apparatus, modules, systems, and computer program products. Certain features that are described in this patent document in the context of separate embodiments can also be implemented in combination in a single embodiment. Conversely, various features that are described in the context of a single embodiment can also be implemented in multiple embodiments separately or in any suitable subcombination. Moreover, although features may be described above as acting in certain combinations and even initially claimed as such, one or more features from a claimed combination can in some cases be excised from the combination, and the claimed combination may be directed to a subcombination or variation of a subcombination. Similarly, while operations are depicted in the drawings in a particular order, this should not be understood as requiring that such operations be performed in the particular order shown or in sequential order, or that all illustrated operations be performed, to achieve desirable results. Moreover, the separation of various system components in the embodiments described above should not be understood as requiring such separation in all embodiments.
Therefore, it will be appreciated that the scope of the present application fully encompasses other embodiments which may become obvious to those skilled in the art. In the claims, reference to an element in the singular is not intended to mean “one and only one” unless explicitly so stated, but rather “one or more.” All structural and functional equivalents to the elements of the above-described preferred embodiment that are known to those of ordinary skill in the art are expressly incorporated herein by reference and are intended to be encompassed by the present claims. Moreover, it is not necessary for a device to address each and every problem sought to be solved by the present apparatus, systems, and methods, for it to be encompassed by the present claims. Furthermore, no element or component in the present disclosure is intended to be dedicated to the public regardless of whether the element or component is explicitly recited in the claims. No claim element herein is to be construed under the provisions of 35 U.S.C. 112, sixth paragraph, unless the element is expressly recited using the phrase “means for.”
While the apparatus, systems, and methods may be susceptible to various modifications and alternative forms, specific embodiments have been shown by way of example in the drawings and have been described in detail herein. However, it should be understood that the application is not intended to be limited to the particular forms disclosed. Rather, the application is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the application as defined by the following appended claims.
This application claims benefit under 35 U.S.C. §119(e) of U.S. Provisional Patent Application No. 61/802,382 filed Mar. 16, 2013 entitled “Flexible Neural Interfaces with Integrated Stiffening Shank,” the disclosure of which is hereby incorporated by reference in its entirety for all purposes.
The United States Government has rights in this application pursuant to Contract No. DE-AC52-07NA27344 between the United States Department of Energy and Lawrence Livermore National Security, LLC for the operation of Lawrence Livermore National Laboratory.
| Number | Date | Country | |
|---|---|---|---|
| 61802382 | Mar 2013 | US |
