SADDOW, Stephen, E. (16602 Palm Royal Dr, Tampa, FL, 33647, US)
COLETTI, Camilla (Allmandring 24B, Stuttgart, Stuttgart, DE)
MAX-PLANCK-INSTITUTE FOR SOLID STATE RESEARCH (Heisenbergstasse 1, Stuttgart, Stuttgart, DE)
FREWIN, Christopher, Leroy (15403 Plantation Oaks Drive, Tampa, FL, 33647, US)
SADDOW, Stephen, E. (16602 Palm Royal Dr, Tampa, FL, 33647, US)
COLETTI, Camilla (Allmandring 24B, Stuttgart, Stuttgart, DE)
FREWIN,C.L.: 'the Neuron-SiC Interface: Biocompatability Study and BMI Device Development.' GRADUATE SCHOOL THESES AND DISSERTATIONS., [Online] 28 May 2009, Retrieved from the Internet:
ARISTOV,V.Y. ET AL.: 'Graphene Synthesis on Cubic SiC/Si Wafers. Perspectives for Mass Production of Graphene-Based Electronic Devices.' NANO LETTERS. vol. 10, no. 3, 08 February 2010, pages 992 - 995
|What is claimed is:
1 . An implantable neuronal prosthetic device for placement in a patient for receiving and sending electrical signals, comprising:
at least one electrode shank adapted for arrangement in said patient having at least one graphene electrode contact disposed on its surface and arranged to electrically couple with said patient, said at least one electrode shank being formed on a single crystal cubic silicon carbide.
2. An implantable neuronal prosthetic device for receiving and sending electrical signals as in claim 1 , further comprising an insulation layer of amorphous, polycrystalline, or single crystal silicon carbide disposed over said electrode shank, said insulation layer of amorphous, polycrystalline, or single crystal silicon carbide being removed from said graphene electrode contact.
3. An implantable neuronal prosthetic device for receiving and sending electrical signals as in claim 1 , wherein the graphene electrode deposited on one side of the electrode shank.
4. An implantable neuronal prosthetic device for receiving and sending electrical signals as in claim 1 , wherein the graphene electrode deposited on two sides of the electrode shank.
5. An implantable neuronal prosthetic device for receiving and sending electrical signals as in claim 1 , further comprising signal control electronics attached to said at least one electrode shank and in communication with said at least one grapheme electrode contact.
6. An implantable neuronal prosthetic device for receiving and sending electrical signals as in claim 1 , further comprising a plurality of said at least one electrode shanks being arranged into a matrix.
7. A method of manufacturing am implantable neuronal prosthetic device for placement in a patient for receiving and sending electrical signals, comprising the steps of: forming at least one electrode shank adapted for arrangement in said patient out of a single crystal cubic silicon carbide; forming a layer of graphene sheet on a surface of at least one electrode shank; and
patterning the layer of graphene sheet to at least one graphene electrode contact, said at least one electrode being arranged to electrically couple with said patient.
8. The method of claim 7, wherein step a) is achieved by heteroepitaxially growing the crystal cubic silicon carbide on a cubic lattice crystalline substrate wafer.
9. The method of claim 8, wherein the silicon carbide is grown on one side of cubic lattice crystalline substrate wafer in step a), and further comprising the step d) of removing the substrate wafer from the other side of the substrate wafer.
10. The method of claim 9, wherein removing substrate wafer is achieved by using wet or dry etching techniques.
11 . The method of claim 8, wherein silicon carbide is grown on both sides of cubic lattice crystalline substrate wafer, and further comprising the step d) of temporarily bonding the graphene electrode side to a supporting wafer, and cleaning interface defects on the other side.
12. The method of claim 1 1 , wherein cleaning the interface defects is achieved by the reactive ion etching about 6 pm microns of silicon carbide.
13. The method of Claim 7, wherein forming the layer of graphene sheet upon the
surface is achieved by high-temperature annealing in Ar ambient to realize thermal decomposition of the 3C-SiC surface.
14. The method of claim 7, wherein forming the layer of graphene sheet upon the surface is through ultra high vacuum annealing to decompose the 3C-SiC surface.
15. The method of claim 7, wherein patterning the graphene sheet into electrode contact is through common lithographic techniques and 02 plasma etching.
16. The method of claim 7, wherein at least one graphene electrode contact is formed upon the surface.
17. The method of claim 7, further comprising the steps of:
insulating said at least one electrode shank with amorphous, polycrystalline, or single crystal silicon carbide; and
removing said insulating layer of amorphous, polycrystalline, or single crystal silicon carbide from said at least one graphene electrode contacts such that said at least one electrode contacts are exposed.
18. A method of manufacturing an implantable neuronal prosthetic for placement in a patient for receiving and sending electrical signals as in claim 7, further comprising the step of attaching signal control electronics to said at least one electrode shank, said signal controls electronics being in communication with said at least one electrode contact.
19. A method of manufacturing an implantable neuronal prosthetic for placement in a patient for receiving and sending electrical signals as in claim 7, further comprising the step of arranging a plurality of said at least one electrode shanks into a matrix.
CROSS REFERENCE TO RELATED APPLICATIONS This application is a continuation of and claims priority to currently pending U.S. Provisional Patent Application 61/418,200, filed November 30, 2010, by the same inventors, which application is incorporated herein by reference.
FIELD OF THE INVENTION
This invention relates to the field of medical devices. More specifically, it relates to an implantable neuronal prosthetic and method of manufacture thereof having biocompatible graphene electrodes.
BACKGROUND OF INVENTION
One of the problems with long term, implantable biomedical devices arises from the response of the body to one or more of the materials that are used to construct the device, or the degradation of the material due to the body environment. This problem has led to advances in the materials used for mechanical devices that replace bones and joints, teeth, and coronary devices like arterial stents or artificial heart valves. Biomedical devices gained an entire new level of complexity with the advent of the microchip which adds electrical interaction with the cells to the previously utilized mechanical interaction. Unfortunately, direct long-term interaction for the microchip with the body is difficult as most of the materials used in the microchips are either chemically reactive, toxic, or both, and must be hermetically sealed to maintain a degree of biocompatibility. This separation between the electrical elements of the biomedical device requires use of a transducer, an object which transforms the interaction between the body and a specific material, the analyte, into another signal which can interact with electronics. One popular transducer for both biosensors and electrical stimulation devices is the utilization of an extremely conductive material, otherwise known as an electrode.
Like every other material utilized in long term implantation, electrodes must be made of a non- corrosive, highly conductive material that does not cause adverse body reactions, is thromboresistant, and has good material durability and strength. Noble metals like gold, platinum, and iridium have been traditionally used in many electrically-active biomedical devices. Transmission electrodes that activate action potentials in electrically active cells, like the ones used in implantable heart pacemakers, have longevity in vivo, but these same electrodes experience many problems when miniaturized for smaller microelectrode array devices. This problem is most exemplified by the generation of Faradaic reactions at the surface of the electrode that produce harmful reactive species which interact with tissue near the electrode and lead to an inflammatory response. Faradic reactions are generated either due to the electrochemical interaction between the electrode and the electrolyte, but can also be dependent on the large charge injections required for cellular membrane depolarization which pass through a small geometrical surface area (i.e., high current density). The ideal electrode would not produce Faradaic reactions and have a large geometrical surface area to allow for large charge injection. An example is the brain machine interface (BMI), it offers therapeutic options to relieve many individuals suffering from central nervous system (CNS) or peripheral nervous system (PNS) disabilities due to disease or trauma. The central component of the BMI system is the neuronal prosthetic which interacts with the body's electrophysiological signals. Implantable neuronal prosthetics have the ability to not only receive electrical signals directly from neurons or muscles, but they can deliver electrical signals to these same cells and provide a means for a closed loop BMI systems. These devices are unfortunately still regulated to experimental BMI systems due to a severe long term in vivo reliability issue. Device failure over time is thought to arise from lowered material biocompatibility which activates the immune response of the body, or failure can arise due to deterioration of the electrical interaction point due to Faradaic reactions caused by the high current densities needed for neuron action potential activation. The solution to this problem is to find materials that are physically and chemically resilient, biocompatible, and have great electrical properties.
Graphene is a two-dimensional (2D) monoatomic layer of graphite which has shown exceptional mechanical, optical, and electrical properties enabling it to perform a wide range of different applications. It is the basic building block for many popular carbon containing materials like the 0D "Bucky ball" C 60 , the popular 1 D carbon nanotube, and if layered into a 3D structure, it becomes common graphite. Graphene was originally obtained via mechanical exfoliation of graphite, the so-called 'scotch tape method', which however yields graphene flakes of limited sizes. Many different methodologies like sheet extraction from graphene dispersions to epitaxial growth on semiconductors, silicon dioxide, and metals have been used to gain large area sheets of graphene. One interesting method utilizes the sublimation of silicon (Si) from the surface of silicon carbide (SiC), which has generated large scale monolayer and few-layer epitaxial graphene sheets. Although graphene is an attractive material for the study of quantum electrodynamics, it presents an equal attraction for the generation of a new set of electronic and mechanical devices superior to Si.
SUMMARY OF INVENTION
Graphene is utilized as the electrode contacts on the implantable neuronal prosthetic due to this material's chemical resilience, extended surface area over conventionally used electrode materials, excellent electrical conductivity and specific capacitance in electrolytes, and biocompatibility. Graphene is naturally formed through the thermal decomposition of the surface of silicon carbide, thereby making this an ideal material combination. It also has the ability to be fashioned into device structures using common lithography and oxygen plasma etching.
BRIEF DESCRIPTION OF THE DRAWINGS
For a fuller understanding of the invention, reference should be made to the following detailed description, taken in connection with the accompanying drawings, in which:
Fig. 1 is an illustration of the general process for the generation of a planar 3C-SiC based graphene electrode neural prosthetic system with electrodes located on a single side of the shank; and
Fig. 2 is an illustration of the general process steps for the generation of a planar 3C-SiC based graphene electrode neural prosthetic system with electrodes on both faces of the planar system. Fig. 3 is an illustration of (a) ARPES, (b) XPS and (c) AFM characterization of a typical monolayer graphene sample used in the invention.
Fig 3(a) Dispersion of the π-bands measured with UV excited ARPES (hv = 40.8 eV) with a display analyzer oriented for momentum scans perpendicular to the ΓΚ-direction of the graphene Brillouin zone. Fig 3(b) C1 s XPS spectrum measured using a non-monochromatic Mg Ka source, hv = 1253.6 eV, plotted as a black line and fitted components.
Fig 3(c) AFM micrograph of epitaxial graphene on 6H-SiC (0001 ). Scan area 20 μηι x 20 m. Scale -10 nm to 8 nm. FIG. 4 is a depiction of fluorescent micrographs of HaCaTs after 72 hour on a) graphene (A), b) graphene (B), c) 6H-SiC(0001 ), and after 120 hrs on d) 6H-SiC(0001 ) and e) graphene (B).
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT
In the following detailed description of the preferred embodiments, reference is made to the accompanying drawings, which form a part hereof, and within which are shown by way of illustration specific embodiments by which the invention may be practiced. It is to be understood that other embodiments may be utilized and structural changes may be made without departing from the scope of the invention.
The present invention provides a long term implantable neuronal prosthetic device including graphene electrodes on a planar 3C-SiC. Graphene is mechanically and chemically resilient. Single layer graphene has excellent conduction properties due to its zero band-gap and large, uniform sheets are ideal for the production of multiple, large scale uniform electrodes. Additionally, the band-gap of graphene can be tuned using the underlying substrate, the addition of multiple graphitic layers, and even the geometry of the devices. Graphene performs superiorly as an electrochemical double layer capacitive electrode, displaying specific capacitances of 135 and 99 F/g in aqueous and organic electrolytes. With a surface area of 2630 m2g-1 , graphene has double the surface area of carbon nanotubes and 200 times that of graphite, therefore reducing the chance of electrochemical reaction and subsequent damage from capacitive charge transfer to an irreversible Faradaic reaction because of small geometric area to charge transfer relationship. Graphene has shown markers of biocompatibility. Graphene obtained from the decomposition of SiC allows access to all of these previously mentioned features as well as widening the number of options in device construction with the addition of the powerful semiconductor. Compared with other conventional electrodes, graphene electrodes have the ability to produce the appropriate threshold charge densities required for neuron and muscle stimulation.
In one embodiment, the method of manufacture of graphene electrodes on a single side of a planar 3C-SiC implantable neuronal prosthetic is shown in Figure 1 (a)-1 (h). The process begin with heteroepitaxially growing 3C-SiC on a cubic lattice crystalline substrate, like silicon, to a thickness of 15 to 20 pm, as shown in Figure 1 (a) and 1 (b). Figure 1 (b) shows that graphene can be generated on the surface of the 3C-SiC using thermal decomposition of the 3C-SiC surface which is possible on any crystalline orientation of 3C-SiC through thermal annealing in Ar ambient gas and temperatures greater than 1000 C . Common lithographic techniques, such as, but not limited to the utilization of ultraviolet or electron beam exposure of photoresist are used to pattern electrodes on the graphene, and an 02 plasma will etch any exposed graphene as shown in Figure 1 (d). The electrodes can be smaller than conventional electrodes due to the larger electrolytic specific capacitance of graphene as well as a greater surface area, allowing for less invasive shanks and more electrodes per shank resulting in higher connectivity to the neurons in the brain. The surface of the graphene/ 3C-SiC layer is coated in highly insulating amorphous, polycrystalline, or single crystal 3C-SiC and lithography is used to open windows over the electrode ends, as exemplified in Figure 1 (e). The substrate wafer is removed from the backside of the device using wet or dry etching techniques. Figure (f) shows the open windows over the freestanding electronic device. A final mask for the physical shank assembly, as shown in Figure 1 (g), is used to mold the final device shown in Figure 1 (h). In this embodiment, a single sided, planar shank contacts in planar neuronal prosthetics is produced.
In an alternative embodiment, the method of manufacture of graphene electrodes on a two- sided planar 3C-SiC implantable neuronal prosthetic is shown in Figure 2(a)-2(j). The steps outlined in Figure 2(a)-2(d) are performed exactly as detailed above for the one sided shank contacting device. After the generation of the graphene electrodes on the surface of the 3C- SiC epitaxial film, Figure 2(e) shows that a thin coat of photoresist is applied and the front side of the wafer is temporarily bonded to a Si wafer to provide mechanical support for further processing. The silicon substrate is removed using wet or dry chemical etching, which results in a freestanding 3C-SiC structure, deep reactive ion etching (DRIE) about 6 micros of silicon carbide of the 3C-SiC interface surface will remove damage formed during epitaxial growth from either the lattice mismatch or Si evaporation voids. The graphene is then formed on the 3C-SiC surface as outlined above and patterned using lithography and 02 plasma etching. Interfacial defects caused by the lattice mismatch between Si and SiC as well as Si evaporation are reduced through etching back the 3C-SiC backside surface. 3C-SiC interface defects are mainly generated through heteroepitaxial growth due to thermal coefficient and lattice mismatch, but are also due to atomic layer stacking faults and twining. It is well known that many of these defects annihilate themselves as the crystal grows in thickness. The damage can be eliminated through this etch so as to make the final product more structurally and electrically sound. Figure 2(f) shows that graphene electrodes are created on the backside of the device through plasma degeneration. Figure 2(g) indicates that the backside electrodes are isolated by applying insulating amorphous, polycrystalline, or single crystal 3C- SiC on top of the shanks prior to graphene formation, and following lithography and DRIE processing to etch open windows over the electrode ends. Next, the Si handle wafer is removed, the front side is coated in the same insulating SiC material, and windows are opened over the electrodes as shown in Figure 2(h). Figure 2(i) shows that the shanks are patterned using photoresist and subsequent etching of the unwanted material between the shanks, leaving freestanding neuronal prosthetic electrodes. Figure 2(j) shows the final neuronal prosthetic device.
The completed shank devices are attached to electronics to facilitate signal transmission and recording. A fully-implantable device would require electronics for conditioning and amplifying received signals via amplifiers, filters, etc., signal generation to excite an action potential from neurons or muscles (transmission), a control system to manage the signals, wireless communication, and finally power management.. Power for the device can be either delivered with rechargeable batteries and/ or inductive generation. Although electronics can be generated in 3C-SiC, they can more easily be realized in Si. The latter method implies that Si electronics are realized separately and then attached (both electrically and physically) to the 3C-SiC device structure through standard semiconductor die bonding techniques. The vulnerable Si electronics are then hermetically sealed with a chemically resistive, biocompatible material, like amorphous silicon carbide, to protect it from attacks from the body's immune system. An alternative method to facilitate the onboard electronics requires that a part of the Si substrate upon which the 3C-SiC was grown upon is preserved for electronics implementation. The required electronics are realized in the preserved silicon tab portion of the shanks and connected to the 3C-SiC and graphene through interconnections made using standard microelectronic processing (metal traces, insulation, conductive via connections, etc.). Either final device, consisting of signal and power electronics and at least one implantable shank with at least one electrode, can be used as the main interface component of a brain machine interface (BMI) device.
Biocompatability of grapheme on SiC
The interaction of HaCaT (human keratinocyte) cells on epitaxial graphene was compared with that of bare 6H-SiC(0001 ) while using polystyrene (PSt) as the control surface. Fluorescent optical microscopy and MTT [3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide] assays were used to assess the biocompatibility of these surfaces.
Cell viability and cell morphology of these surfaces was compared. Two different cleaning procedures were employed on the graphene surfaces tested. The optical inspection results after 72 hours of cell incubation showed that the ethanol sterilization step is required in order to have a more homogeneous and enhanced cell adhesion on graphene surfaces. The graphene films were epitaxially grown on 6H-SiC(0001 ) substrates. Initially, the 6H-SiC samples were H2 etched in order to remove any commercial polishing damage and to obtain a well ordered surface. Subsequently, graphitization was performed under an Ar environment at annealing temperature between 1600 and 1700°C . The quality and thickness of the grapheme films were evaluated by angle-resolved photoemission spectroscopy (ARPES) and X-ray photoelectron spectroscopy (XPS). AFM and surface water contact angle (SWCA) were used to assess the surface morphology and wettability of SiC and graphene. The surface topography analysis was done using an XE-100 Advanced Scanning Microscope from Park Systems. The SWCA data were obtained from the average of three 10 μΙ droplets deposited on different areas of the sample. The images of the liquid droplets were obtained using a KSV CAM101 system from KSV Instruments and the contact angle (Θ) was estimated by measuring the angles between the baseline of the droplet and the tangent at the droplet boundary.
Prior to cell seeding the graphene surfaces were cleaned of possible air contamination by performing thermal annealing under an Ar atmosphere at 700°C in a chemical vapor deposition (CVD) reactor. While for one set of samples (A) cell seeding was performed without any further surface treatment, for another set of samples (B) an additional sterilization step via immersion in ethanol was performed. The different surface treatment methods were considered for graphene with the intention of learning if the final ethanol dip (typically used to prevent bacteria formation prior to cell seeding) would change the cell morphology and proliferation. The 6H-SiC surfaces were first HF dipped to remove the native oxide, then annealed as with the graphene samples in Ar atmosphere at 700°C and finally ethanol dipped.
For the cell morphology analysis and viability assays, the HaCaT cells were counted and plated on the PSt controls, 6H-SiC and epitaxial graphene samples at a density of 30,000 cells/cm2 in Dulbecco's Modified Eagle's Medium (DMEM) supplemented with 10% FBS and incubated for 72 hours. In addition cell morphology inspection analysis was performed after 120 hours on extra samples from group B and on 6H-SiC. A 5 μΜ solution of CMFDA (5- chloromethylfluoresceindiacetate) cell tracker dye was used to perform the cell morphology analysis via fluorescent microscopy.
Characterization of both the epitaxial graphene and 6H-SiC surfaces was performed to assess the surface properties prior to cell seeding. Fig 3a shows the dispersion of the π- bands around the K-point of the graphene Brillouin zone measured via ARPES.
The TT-bands linear dispersion and the displacement of the Fermi level above the Dirac point of circa 0.42 eV are characteristic features of monolayer graphene epitaxially grown on SiC(0001 ). Also the C1 s XPS spectrum shown in Fig. 3b confirms the monolayer nature of the adopted grapheme films. The analysis of the graphene surface topography with AFM (Fig 3c) showed indication of large continuous terraces, on average 3.6 2 pm long with a step height of 6.3 3.6 nm, which is larger than the original H2 etched 6H-SiC substrate terraces. The SWCA measured for graphene cleaned by methods A and B were 87.3° ± 9.5° and 94.9°± 3.2°, respectively. These results confirm the well-known hydrophobicity of graphene and 832 Silicon Carbide and Related Materials 2010 demonstrate that the sterilization in ethanol did not change the affinity of the surface to water in a statistically significant way. For 6H-SiC the SWCAs was 47°.2±3°. hereby confirming the hydrophilic character of the surface even though partially reduced with respect to what was reported in  (i.e., SWCA ~ 25° for a Piranha and hydrofluoric acid (HF) treated 6H-SiC(0001 ) surface) by the thermal annealing step.
Figure 4 shows after 72 hours, for both graphene and 6H-SiC, the morphology of the HaCaT cells was similar to that on the PSt control with signs of cell-cell interaction and cell-substrate interaction.. For the graphene substrates from group A, as seen in Fig 4a, small islands of cells were observed compared to the monolayer that started forming on the graphene surface cleaned by method B shown in Fig 4b. The 6H-SiC samples also showed via optical inspection clear signs of an initial formation of a cell monolayer (Fig 4c). It is apparent from the comparison of Figures 4a and 4b that the ethanol dip step favors a more homogeneous cell adhesion and for this reason subsequent experiments whose results are reported below were performed only on samples cleaned by using method B.
HaCaTs tend to form groups of cells such as islands, and with time they start growing tighter and closer to each other and eventually form a conformal layer of cells. Consequently at a time of 120 hours optical inspection of cells plated graphene and 6H-SiC samples was performed with the intent of checking whether the cells would grow to confluence. The 120 hrs optical inspection data showed a homogeneous monolayer of cells formed on both graphene and 6H-SiC, shown in Figure 4d and 4e.
The MTT assays provided an average value of cell viability after 72 hrs of incubation and with respect to the PSt control. The results were 17 ± 0.07 (std deviation of the mean) for graphene and 58 ± 0.05 for 6H-SiC. After 120 hrs of incubation, the formation of a cell monolayer on graphene substrates in a similar to 6H-SiC, as shown in Figures 2d and 2e.
[1 ] V. Y. Aristov, et al., "Graphene Synthesis on Cubic SiC/Si Wafers. Perspectives for Mass Production of Graphene-Based Electronic Devices," Nano Letters, 10, (2010) 992-995.
 KV Emtsev, A Bostwick, K Horn, et al. Nature Materials 8 (2009) 203-207.  C Coletti, M Jaroszeski, A. Pallaoro, AM Hoff, S lannotta and SE Saddow, IEEE EMBS proc. (2007), 5850-5853. It will be seen that the advantages set forth above, and those made apparent from the foregoing description, are efficiently attained and since certain changes may be made in the above construction without departing from the scope of the invention, it is intended that all matters contained in the foregoing description or shown in the accompanying drawings shall be interpreted as illustrative and not in a limiting sense.
It is also to be understood that the following claims are intended to cover all of the generic and specific features of the invention herein described, and all statements of the scope of the invention which, as a matter of language, might be said to fall there between.
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