Protein Functionalized Nanodiamond Arrays
© The Author(s) 2010
Received: 22 January 2010
Accepted: 1 April 2010
Published: 14 April 2010
Various nanoscale elements are currently being explored for bio-applications, such as in bio-images, bio-detection, and bio-sensors. Among them, nanodiamonds possess remarkable features such as low bio-cytotoxicity, good optical property in fluorescent and Raman spectra, and good photostability for bio-applications. In this work, we devise techniques to position functionalized nanodiamonds on self-assembled monolayer (SAMs) arrays adsorbed on silicon and ITO substrates surface using electron beam lithography techniques. The nanodiamond arrays were functionalized with lysozyme to target a certain biomolecule or protein specifically. The optical properties of the nanodiamond-protein complex arrays were characterized by a high throughput confocal microscope. The synthesized nanodiamond-lysozyme complex arrays were found to still retain their functionality in interacting with E. coli.
KeywordsNanodiamond Biosensor Self-assembled monolayer
With recent developments in nanobioscience and nanobiotechnology, nanomaterials (e.g., carbon nanotubes, fullerenes, quantum dots, and nanodiamonds (ND)) have been receiving increased attention . Quantum dots have specifically been applied in fluorescent probes in recent years. However, there are concerns on their bio-cytotoxicity. In comparison, nanodiamonds possess remarkable features of low bio-cytotoxicity and good optical property for bio-applications. Schrand et al.  demonstrated that nanodiamonds, with and without surface modification by acid or base, are biocompatible with a variety of cells of different origins. Cells grown on ND-coated substrate show sustained viability over time. NDs are rapidly emerging as promising carriers for next-generation therapeutics and drug delivery. Therefore, it is envisaged that nanodiamonds can serve as good drug carriers, image probes, or implant coatings in biological systems [3–13]. However, developing future nanoscale devices and arrays that harness these nanoparticles will require unprecedented spatial control.
The Raman and photoluminescence properties of nanodiamonds have been intensively studied [14–17]. Core-level photoabsorption has been used to determine the sp2 and sp3 bonding content of nanocrystalline diamond thin film . Extensive Raman and FTIR studies have been reported  on nanodiamond powders. Some intrinsic Raman signals can be used as detection markers or can be employed in biological objects. The major Raman peak of diamonds is located at 1,332 cm−1 for the SP3 bonding of carbons. This diamond Raman peak is strong and isolated, so it can be used as an indicator for allocating nanodiamonds. Functionalized diamond films and nanodiamonds (carboxylation or oxidation) facilitate chemical or physical conjugation with biomolecules [18, 20–23]. For the aforementioned reasons, functionalized nanodiamonds can be used as bio-labeling materials. If techniques to single out, position, and allocate a single bio-labeled nanodiamond can be developed, the creation of a single nanodiamond that can serve as a platform for observing molecular-molecular interactions via optical means (Raman and/or photoluminescence spectroscopy techniques) can be made.
In this report, we demonstrated techniques to single out, position, and allocate nanodiamond arrays on silicon substrates. Nanodiamond arrays absorb lysozyme and form nanodiamond-lysozyme complex arrays [24, 25]. The optical properties of the nanodiamond-lysozyme complex arrays were characterized by a high throughput confocal microscope, and the functionality of the complex was tested with E. coli.
The nanodiamond powder used in this study is commercially available (GE Diamond Company), and the samples were produced under high pressure and high temperature (HPHT) conditions. The nanoparticles have an average size of about 100 nm with a size distribution within ±20%, which was confirmed by SEM. In order to well disperse the nanodiamonds, they were treated with a 5:1 mixture of concentrated H2SO4 and HNO3 solutions at 75°C for 6 h, and extensively rinsed several times with DI water. The solution was placed in an ultrasonic bath operated at a vibration frequency of 185 kHz for 30 min to prevent the formation of the nanodiamond clusters. It may be due to the acoustic cavitation effect [26, 27] so that the ultrasonic wave heats up the water and breaks the water molecules into H+ and OH− ions. The OH− ions attach onto the nanodiamond surface and induce a Coulomb repulsion force between nanoparticles. Therefore, the clustering of nanodiamonds can be avoided. A test drop of the solution is placed on a bare Si wafer and, after the solution dries out, the scanning electron microscope (SEM) and transmission electron (TEM) images are taken to examine the clustering of the nanodiamond. The concentration of the solution is continuously adjusted until the nanoparticles can be well dispersed on the template. The sediment was then collected and dried. The functional COOH groups, which are commonly used for conjugation with biomolecules, were formed on the ND surface followed by the standard chemical treatment mentioned in Ref. [28, 29]. Formation of the COOH group was further confirmed through IR absorption measurements. The oxidative acid-treated ND surfaces contain ~7% of COOH carboxyl groups. It should be noted that this amount of surface carboxyl groups is sufficient for ensuing bio-conjugation [30, 31].
A silicon wafer was first diced into 15 × 15 mm chips. A silicon oxide layer was grown on the silicon chips with a thickness of about 400 nm by using PECVD. The substrate was first cleaned with ultrasonic bath in acetone, isopropyl alcohol, and DI water solution for 5 min. Then, the ZEP520 photoresist was spin-coated on the silicon oxide substrates at a rate of 500 rpm for 10 s and 5,000 rpm for 50 s, and baked at 180°C for 2 min. The thickness of the photoresist on the Si chip was about 300 nm.
The NDs solution was prepared by adding 0.1 g of COOH functionalized NDs into 100 ml of DI water followed by an ultrasonic bath for 60 min. The patterned substrate was dipped into 3 ml of the ND solution and 3 ml of 0.1 M MES buffer [2-(N-morpholino) ethane sulfonic acid]. After which, 6 ml of 0.025 M EDC solution 1-ethyl-3-[3-(dimethylamino)propyl]carbodiimide hydrochloride, 0.025 M NHS solution (N-hydroxysuccinimide) (hereafter “EDC/NHS solution”) and 8 ml DI water were added into the reaction and allowed to stabilize for 8 h. After the reaction was completed, the substrate was washed with acetone. The entire template was then immersed into ZDMAC (dimethylacetamide) solution for 4 h to remove the photoresist. The substrate was again washed with acetone and DI water, then dried with N2. Figure 1b and 1c shows how the functionalized NDs were anchored on the patterned silicon templates and processes for the preparation of the substrates. The preparation of the lysozyme functionalized nanodiamond arrays is explained as follows.
The lysozyme protein of 0.1 g was dissolved into 10 ml PBS (phosphate-buffered saline) buffer. To ensure equilibration absorption, the nanodiamond patterned chip was dipped into the lysozyme solution mentioned earlier and mixed together with stirring for 2 h before it was washed by PBS buffer and deionized water. After which, 10 μl of E. coli suspension in 90 μl PBS medium was mixed with the nanodiamonds chip in PBS buffer. The nanodiamond chip was washed with PBS buffer and deionized water.
Results and Discussion
The bioactive lysozyme-ND complex arrays were tested to be still functional at room temperature up to 10 h after preparation. However, they complete ceased to react with bacteria after 24 h. Nevertheless, it is possible to extend lifetime of the chip up to a week if it was kept under low temperature (5°C) and humid condition.
In this study, we have demonstrated new methods and techniques to anchor bio-functionalized NDs on a patterned silicon template using e-beam lithography and SAM techniques. The lysozyme proteins bound on the NDs still retained their antibacterial activity and interacted with E. coli bacterial cells. The device demonstrated here is suitable for applications in bio-sensing chips and single biomolecule patterning and detection. It facilitates the development of new applications of different biomolecule-nanodiamond complexes that can interact with special targets, as well as the individual observation of their optical property.
This work was supported by a grant from the National Science Council, ROC (NSC 96-2112-M-009).
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