Nanogrid electrochemical sensor for detection of biochemical species by electrochemical impedance spectroscopy

Improved electrochemical impedance spectroscopy assays are provided by electrodepositing metallic nanoparticles onto the working electrode for electrochemical impedance spectroscopy. The metallic nanoparticles provide improved assay sensitivity. Electrodeposition of the metallic nanoparticles firmly affixes them to the working electrode, thereby making it easier to clean the working electrode from one assay to the next assay without undesirably removing the metallic nanoparticles.

FIELD OF THE INVENTION

This invention relates to assays using electrochemical impedance spectroscopy.

BACKGROUND

Assays are often used for chemical or biochemical analysis. Typically a sensor is coated with an immobilized receptor species (e.g., an antibody), and detection of target species (e.g., antigens) corresponding to the immobilized receptor is performed by sensing bound target-receptor complexes with the sensor. A wide variety of sensor and sensing technologies have been employed in such applications. One such approach is electrochemical impedance spectroscopy, where the bound target-receptor complexes alter an electrical impedance of the sensor. Characterization of this impedance change (typically vs. applied electrical frequency) provides the desired assay signal. In some cases, the sensitivity of an electrochemical impedance spectroscopy is lower than desired. Accordingly, it would be an advance in the art to provide improved electrochemical impedance spectroscopy for chemical and/or biochemical assays.

SUMMARY

In this work, electrochemical impedance spectroscopy is used as the sensing methodology. Furthermore, the sensor includes metallic nanoparticles conjugated to the antibody being used for the assay. Here nanoparticles are defined as particles with any shape having a largest dimension of less than 1 micron. These nanoparticles are bound to the working electrode for electrochemical impedance spectroscopy using an electrochemical deposition process. Here electrochemical deposition of metallic nanoparticles is defined as either 1) the deposition of metallic nanoparticles in solution (e.g. a colloidal suspension) on an electrode by application of an electric field, or 2) the direct formation of metallic nanoparticles on the working electrode from metal ions in solution by application of an electric field. The working electrode is preferably configured as a nano-grid having apertures in it on the order of 100 nm in size (prior to deposition of the nanoparticles).

This configuration provides significant advantages. 1) The resulting electrode structure advantageously provides greater control of electrode configuration than can be obtained with conventional nano-porous electrodes. 2) The metallic nanoparticles increase the sensitivity of the electrochemical impedance spectroscopy assay. 3) Deposition of the metallic nanoparticles on the working electrode via electrodeposition (as opposed to other methods such as sputtering) provides improved adhesion of the metallic nanoparticles to the working electrode. Such improved adhesion is helpful when cleaning the working electrode to prepare for an assay, because the goal of such cleaning is to remove receptors and bound target-receptor complexes while leaving the metallic nanoparticles affixed to the working electrode. The more firmly attached the metallic nanoparticles are to the working electrode, the easier such cleaning will be to perform. 4) This approach is expected to be faster and have lower cost than current methods such as ELISA (enzyme-linked immunosorbent assay) and mass spectrometry.

DETAILED DESCRIPTION

Introduction

In the following description, an exemplary design of an assay for the biological species LTB4 (leukotriene B4) according to the above described principles is considered. However, the present approach is applicable for assays of any chemical species, both biological species and non-biological species.

Research has shown that in the condition of pulmonary hypertension, macrophages produce high levels of leukotriene A4 hydrolase (LTA4H) in response to inflammation and this synthesized leukotriene B4 (LTB4). It was found that by blocking LTB4, the endothelial injury was prevented and the pulmonary hypertension was reversed. The detection of LTB4 can be used for diagnosis of pulmonary hypertension and the hypothesis of detection is based on antigen-antibody binding which would capture the LTB4 onto the sensor surface. Here the method of detection is by electrochemical impedance spectroscopy which would detect the change in impedance upon binding of LTB4. LTB4 detection (more generally, detection of any target species) can be done in samples including but not limited to: tissue biopsy samples, plasma, whole blood, serum, sweat, bronchoalveolar lavage fluids and colon fluids.

The sensor's preferred design of a nanogrid along with electrochemical impedance spectroscopy will improve detection relative to other approaches such as self assembled monolayer sensor surfaces, nanowires, plasmonic substrate chips and nanoporous substrates for detection of biomolecules by methods such as optical, mechanical and electrical sensing shown previously in literature. In one design, the grid lines have a dimensional range of 100 nm (after the electrodeposition of the metal nanoparticle-antibody conjugate, the spacing between the grid lines will decrease much further simulating a nanoporous substrate). Alternatively, the dimension of the grid lines can range from 50 nm to 500 nm. Platinum metal is used for the sensor patterning in this demonstration but other similar metals (e.g., gold, titanium, copper, or aluminum) can also be used. Additionally, the illustrated shape of the nanogrid can be modified to suit the purpose to achieve an ultrasensitive detection.

Sensor Design and Detection:

Electrochemical impedance spectroscopy is an important method to detect changes that happen from binding of biomolecules on the transducer surface. In this method, however, an amplification step is needed if the molecule that being detected is too small. In this research work, the molecule of interest, LTB4, is a small molecule in size and hence an amplification step is included and the phenomenon of binding is described as follows. Metal nanoparticles are conjugated with the LTB4 antibody. This conjugate is then selectively coated on the nanogrid by means of electrodeposition.

FIG. 1schematically shows the resulting assay. Here102is the working electrode,104are the metallic nanoparticles,106are the receptors (e.g., LTB4 antibody) conjugated to the metallic nanoparticles, LTB4 in solution is referenced at108and other species are referenced as110. Species-selective bound target-receptor complexes are shown as bound LTB4112in receptors106.

This novel means of immobilization of the antibody-metal nanoparticle conjugate will result in a strong adherence to the working electrode surface. This is because of the establishment of chemical bonding resulting from the exchange of electrons during electrodeposition and the modification of the metal nanoparticles of the conjugate. Moreover, the electrodeposition and resulting immobilization will happen on all exposed areas of the nanogrid lines which is designed in a manner conducive to the electrodeposition on top of the grid lines and the sides of the grid lines. This will narrow the spacing between the grid lines further and appear similar to the surface area of a porous substrate but in a much more controlled manner. The unbound conjugates will be washed off and the impedance before the assay with the LTB4 will be recorded.

FIG. 2shows an example of this electrode arrangement. Here working electrode102is configured as a grid having apertures202. Metallic nanoparticles104are deposited on side walls of apertures202as shown, and on top of working electrode102, also as shown.

FIG. 2Ashows an example of a nanogrid212with metallic nanoparticles216conjugated with LTB4 sensing antibody218and conjugated hydrocarbons222bound to immobilized serum albumin220. Here214shows an enlarged view of a nanogrid aperture having multiple nanoparticles in it. In this example, the gold nanoparticles can be bi-functionalized with amine and sulfhydryl groups. The nanogrid can be coated with a mono-protected dithiol spacer (S onFIG. 2A), such as 2,2′-(ethylenedioxy)diethanethiol with one sulfhydryl group protected with methoxytrityl [(4-methoxyphenyl)diphenylmethyl] (MMT). Next, the MMT protecting group can be removed by 1% trifluoroacetic acid in dimethylformamide. Antibody functionalized with maleimide can be chemically conjugated to the metallic nanoparticle surface by reacting with the sulfhydryl groups. Unconjugated sulfhydryl groups will be sequestered by N-acetyl cysteine. This is an important step to prevent serum albumin from covalently binding to the free sulfhydryl groups. Next, the amine groups can be modified with alkyl chains between 14 to 18 carbons long. Serum albumin (human or bovine, defatted) can be bound to the alkyl chains, and thereby physically adsorbed onto the nanoparticle and nanogrid, providing a protein environment around the antibody for structural and activity stabilization. Saturated fatty acids between 14 and 18 carbons long can be added to the substrate to saturate the hydrophobic binding sites within serum albumin.

The main advantages of this novel method of immobilization are that of stronger and more reliable immobilization of the conjugate compared to other existing methods such as self assembled monolayer, layer by layer techniques, entrapment in sol-gel matrix or other optical method of detection where the antibodies are in suspension in the solution. By means of this method of immobilization, it is also easier to clean the electrode of all antibodies and antigen by means of an electrochemical cleaning step so that reliability and accuracy for the subsequent measurements are increased. Moreover, the immobilization can be done by first conjugating the receptors to metal nanoparticles or alternatively by first electrodepositing the metal nanoparticles and then conjugating the receptors to the electrodeposited layer. The assay of the target to the receptor will cause change in the impedance spectroscopy measurements before and after binding of the target to its receptor. The role of the metal nanoparticles is dual: for signal amplification and for selectively coating the nanogrid as shown inFIGS. 1 and 2.

FIG. 3shows further details of a preferred electrode configuration. Here302is a platinum counter electrode,304is the nanogrid working electrode and306is a Ag/AgCl reference electrode.312,314and316are contact pads for electrodes302,304, and306respectively.FIG. 4shows an enlarged view of region308onFIG. 3. Here the nanogrids402are more apparent, and each of these nanogrids402would have metallic nanoparticles on them as onFIG. 2.FIG. 5shows an exemplary nanogrid design having 100 nm line widths and 100 nm square apertures. The squares seen in the figure will be spaces in the nanogrid after this pattern is made in a chromium mask.FIG. 6is a scanning electron microscope image of an e-beam resist pattern for this nanogrid pattern.

The fabrication of the nanogrid inFIGS. 3-5can be done by microfabrication methodologies such as photolithography, physical vapor deposition, wet etching, dry etching and other techniques such as electrodeposition and soft lithography. The dimension of the grid spacing and lines are preferably designed to be 100 nm as shown inFIG. 5. With the electrodeposition of the gold nanoparticle and antibody conjugates, the spacing is expected to reduce since the conjugate will deposit on top of the grid and the exposed side walls of the metal grid. This will give more surface area and more sensitivity.

FIGS. 7A-Fshow an exemplary fabrication sequence for a nanogrid electrode.FIG. 7Ashows an initial configuration with electrode metal704(e.g., Pt/Ti) disposed on a substrate702(e.g., quartz).FIG. 7Bshows a photoresist layer706disposed on the structure ofFIG. 7A, and a mask708.FIG. 7Cshows the result of patterning photoresist layer706to provide electrode resist pattern710. It should be noted that this electrode resist pattern will define the overall shape of the electrodes (e.g., as shown onFIG. 3), but does not define the apertures for the nanogrid.

FIG. 7Dshows the result of transferring resist pattern710to electrode metal704to provide an electrode pattern712, e.g., by wet chemical etching.FIG. 7Eshows the result of depositing e-beam resist714on the structure ofFIG. 7D.FIG. 7Fshow the result of patterning e-beam resist714, followed by ion milling to define the apertures in the nanogrid electrode, followed by removal of e-beam resist714. The resulting electrode structure includes nanogrids716(e.g., as shown on402ofFIG. 4).