AU2004254295B2

AU2004254295B2 - Improvements in sensor chips

Info

Publication number: AU2004254295B2
Application number: AU2004254295A
Authority: AU
Inventors: Daniel Luke Johnson; Lisandra Lorraine Martin
Original assignee: Tacnia Pty Ltd
Current assignee: Tacnia Pty Ltd
Priority date: 2003-07-08
Filing date: 2004-07-08
Publication date: 2010-05-27
Anticipated expiration: 2024-07-08
Also published as: AU2004254295A1

Description

WO 2005/003383 PCT/AU2004/000923 IMPROVEMENTS IN SENSOR CHIPS Field of the Invention 5 The present invention relates to sensor chips of the type that have a monolayer of molecules immobilised on a substrate surface. The sensor chips may be used to investigate interactions between the immobilised molecules and other molecules or to investigate interactions between the immobilised molecules and the substrate surface. 10 Background of the Invention The investigation and/or analysis of ligand-molecule interactions and/or the electrochemical behaviour of biomolecules are fundamentally important in many 15 fields, including biology, immunology, chemistry and pharmacology. A number of analytical techniques can be used to investigate ligand-molecule interactions. For example, biological analytes can be detected or quantified based on ligand-specific binding between a ligand and a receptor. Common 20 ligand/receptor binding pairs include antigen-antibody, hormone-receptor, drug receptor, cell surface antigen-lectin, biotin-avidin, substrate-enzyme, and complementary nucleic acid strands. The analyte to be detected may be either member of the binding pair; alternatively, the analyte may be a ligand analogue that competes with the ligand for binding to the receptor. 25 Other analytical techniques utilise the oxidation or reduction of a molecule on the surface of a solid support. For example, glucose sensors may include an enzyme, such as glucose oxidase, which converts glucose into reaction products including hydrogen peroxide. A suitable electrode can then measure 30 the formation of hydrogen peroxide as an electrical signal. The signal is produced following the transfer of electrons from the peroxide to the electrode, and under suitable conditions the enzyme catalysed flow of current is WO 2005/003383 PCT/AU2004/000923 -2 proportional to the glucose concentration in a sample. Alternatively, an electrode surface may be used in combination with current or impedance measuring elements for detecting a change in current or impedance in response to the presence of a ligand-receptor binding event. 5 Many of the aforementioned analytical techniques involve immobilising a molecule on a solid support. Other than immobilising the molecules, the solid support may play no role in subsequent chemical or biological investigations of the immobilised molecules. Alternatively, the solid support may interact with the 10 immobilised molecule, such as when the solid support is an electrode which is used to investigate the electrochemistry of the molecule. A common technique for the immobilisation of molecules on the surface of a solid support is to covalently attach molecules onto a surface of a solid support 15 that has previously been modified with an alkanethiol. Covalent attachment of the molecules to the surface prohibits diffusion of the molecules away from the solid support and also typically results in the formation of a film of molecules that is limited to a single monolayer, thereby limiting the required sample volume. The formation of self-assembled monolayers ("SAMs") of molecules in 20 this way has enabled the design of new interfaces for the study of ligand molecule binding interactions as well as specific redox-active analytes. For example, monolayers have been formed via alkanethiol-gold linkage and related linkages between carboxylates and phosphonates and metal oxide surfaces. Monolayers formed on gold surfaces are particularly suited for studying 25 biomolecular recognition at surfaces because the well-defined structures are amenable to detailed characterisation at a molecular level by using, for example, scanning tunneling microscopy, atomic force microscopy as well as other optical and electrochemical bioanalytical techniques. 30 Solid supports having a monolayer of immobilised molecules are commonly referred to as "chips" or "sensor chips". The sensor chips are routinely used in biosensor instruments where one or more properties of the immobilised WO 2005/003383 PCT/AU2004/000923 -3 molecules may be measured. A representative class of biosensor instrumentation is sold by Biacore AB (Uppsala, Sweden) under the trade name BlAcoreTM(hereinafter referred to as "the BlAcore instrument"). The BlAcore instrument includes a light emitting diode, a sensor chip covered with a thin gold 5 film, an integrated fluid cartridge and a photodetector. Molecules that are receptors of an analyte of interest are immobilised on the surface of the sensor chip and the chip is contacted with a flow of sample containing the analyte of interest. Any change in the surface optical characteristics of the sensor chip arising from the binding of the analyte of interest are then measured by 10 detecting any intensity loss or "dip" in light that is reflected from the gold film on the surface of the sensor chip. Numerous devices for determination of analytes that are based on the use of sensor chips are now available. However, many of the available sensor chips 15 have some limitation with respect to sensitivity, test sample volume, reproducibility, speed of response, number of effective uses, or the range of detection. In the clinical setting, it is a goal to maximize the data obtainable from relatively small test sample volumes during analysis of fluids. 20 The discussion of the background to the invention herein is included to explain the context of the invention. This is not to be taken as an admission that any of the material referred to was published, known or part of the common general knowledge in any country. Further, throughout this specification reference may be made to documents for the purpose of describing various aspects of the 25 invention. However, no admission is made that any document cited in this specification forms part of the common general knowledge in the art in any country. 30 -4 Summary of the Invention The present invention arises out of studies conducted by the inventors that have shown that by uniformly orienting molecules on the surface of a solid substrate 5 so that the active site is uniformly orientated on the surface it is possible to increase the efficiency of any interaction of the immobilised molecule with a solution phase or with the solid support. If the active sites or recognition domains of every immobilised molecule are facing an appropriate solution phase, then each molecule is capable of interacting with an appropriate 10 substrate and contributing to the overall biosensor response. An optimised detection layer can be expected to display increased sensitivity and reliability, potentially enhancing the range of suitable applications and reducing manufacturing costs. 15 The present invention provides a method for selectively orienting and immobilising molecules on a surface of a solid support, the method including the steps of: - attaching a linker molecule to the surface of the solid support, the linker molecule including a head group that is capable of binding to 20 the solid support, and a tail group that is capable of chelating to a metal ion, wherein the tail group of the linker molecule is a cyclic ligand containing three or more atoms that are capable of coordinating to the metal ion; - treating the solid support with a solution containing the metal ion so 25 that the metal ion is chelated to the tail group; - attaching a metal ion chelating tag to the molecules to form tagged molecules; and - capturing the tagged molecules on the solid support by contacting it with the tagged molecules to form a monolayer of molecules on the 30 surface of the solid support in which a majority of the molecules are held in the same orientation with respect to the surface. -Maname' -5 Also described herein is a sensor chip including a monolayer of immobilised molecules captured on a surface of a solid support, wherein a majority of the immobilised molecules are in the same orientation with respect to the surface. 5 The present invention also provides a sensor chip including: -a solid support having a noble metal surface; -a linker molecule attached to the surface of a solid support, the linker molecule including a head group that is bound to the solid support, and a tetradentate macrocycle tail group that is chelated to a metal ion; 10 -a monolayer of immobilised molecules on the surface of the solid support, wherein each molecule contains a metal ion chelating tag and is held on the surface of the solid support by co-ordination of the tag with the metal ion such that a majority of the molecules are held in the same orientation with respect to the surface. 15 To determine whether or not "a majority of the molecules are held in the same orientation with respect to the surface" it is possible to compare the redox response for molecules oriented on a solid support using the method of the present invention and measuring the electrochemical response over increasing 20 scan rates. The molecules are taken to be oriented if an improved electrochemical reversibility is observed. Preferably, the tail group of the linker molecule is a cyclic ligand containing three or more atoms that are capable of coordinating to the metal ion. More 25 preferably, the tail group is a tetradentate macrocycle that is capable of chelating with the metal ion. Also described herein is a method for selectively orienting and immobilising molecules on a surface of a solid support, the method including the steps of: 30 - attaching a linker molecule to a gold surface on the solid support, the linker molecule including a head group that is capable of binding to the gold surface, a tetradentate macrocycle tail group that is capable Ofienams- -6 of chelating to a metal ion and a spacer extending between the head group and the tail group; - contacting the solid support with a solution containing the metal ion so that the metal ion is coordinated with the macrocycle; 5 - attaching a 6*his tag that is capable of coordinating with the metal to the molecules to form tagged molecules; and - capturing the 6*his tagged molecules on the solid support by contacting it with the tagged molecules such that the 6*his tag is coordinated with the metal ion to form a monolayer of molecules on 10 the surface of the solid support in which a majority of the molecules are held in the same orientation with respect to the surface. As a result of the macrocyclic effect, the use of a macrocycle tail group may provide for tighter binding of the metal ion to thereby reduce leakage of metal 15 ions from the support. The term "macrocyclic effect" refers to the greater thermodynamic stability of a complex with a cyclic polydentate ligand when compared to the complex formed by a comparable non-cyclic ligand. The present invention also provides a biosensor device including: 20 - a sensor chip of the present invention; and - a transducer for detecting a change in a parameter in the immobilised molecules on the sensor chip. Also described herein is a method for increasing the sensitivity of measurement 25 of a parameter of a molecule that is immobilised on a solid support, the method including the step of orienting the molecule on the solid support using the method described herein. The present invention also provides a method for increasing the reproducibility 30 and/or sensitivity of measurement of an electrochemical parameter of a redox active molecule that is immobilised on a solid support electrode, the method including the steps of: ',rdeme -7 - attaching a linker molecule to a surface on the solid support electrode, the linker molecule including a head group that is capable of binding to the solid support, a tail group that is capable of chelating to a metal ion, and an alkyl chain of more than two atoms in length 5 between the head group and the tail group; - treating the solid support with a solution containing the metal ion so that the metal ion is chelated to the tail group; - attaching a metal ion chelating tag to the redox active molecules to form tagged molecules; and 10 - capturing the tagged redox active molecules on the solid support by contacting it with the tagged molecules to form an immobilised monolayer of redox active molecules on the surface of the solid support in which a majority of the molecules are held in the same orientation with respect to the surface. 15 The present invention also provides a method of determining the presence of an analyte in a sample, the method including the steps of: - providing a self-assembled monolayer on a surface of a solid support, said monolayer comprising linker molecules having head groups that 20 are bound to the surface of the solid support, and tail groups that are chelated to a metal ion, wherein the tail groups of the linker molecules are cyclic ligands containing three or more atoms that are capable of coordinating to the metal ion; and analyte binding molecules having a tag that is bound to the metal ion, said analyte binding molecules 25 oriented uniformly with respect to the surface of the solid support; - contacting the self-assembled monolayer having the analyte binding molecule immobilised thereon with a sample suspected of containing a target analyte; and - detecting binding of the target analyte with the analyte binding 30 molecule to thereby determine the presence or absence of the target analyte.

7a The present invention also provides a method for selectively orienting and immobilizing molecules on a solid support having a gold surface, the method including the steps of: - treating the gold surface with a mercaptopropionic acid to form a 5 mercaptopropionic acid self-assembled monolayer; - treating the mercaptopropionic acid self-assembled monolayer with a tetradentate derivative of 1,4,7-triazacyclononane to form a macrocyle modified mercaptopropionic self-assembled monolayer; - treating the macrocyle modified mercaptopropionic self-assembled 10 monolayer with a metal desirous of octahedral coordination to form a metallo macrocyle modified mercaptopropionic self-assembled monolayer; and - treating the metallo macrocyle modified mercaptopropionic self assembled monolayer with a solution containing a 6*his tagged 15 molecule to form a highly orientated monolayer of immobilized molecules.

WO 2005/003383 PCT/AU2004/000923 -8 Brief Description of the Figures Figure 1 is a schematic flow diagram showing a procedure for producing SAMs according to the methods of the present invention. 5 Figure 2 shows a plot of wavenumber vs absorbance for a Diffuse Reflectance Infrared Fourier Transform (DRIFT) spectroscopy study on the surface chemistry of SAMs that were formed according to the methods of the present invention. 10 Figure 3 shows typical cyclic voltammograms of histidine tagged thioredoxin obtained at a AcBztacn modified gold electrode (5, solid line) compared with those obtained when the protein is covalently bound to the electrode via surface lysine residues at stage 2 (dashed line). The one-electron reduction of the 15 oxidised thioredoxin to the radical anion is shown. Scan rates are (a) 0.2 mV/s (b) 1.0 mV/s and (c) 10 mV/s. Current responses are indicated for each scan rate in 20 mM phosphate buffer (pH 7.4). Figure 4 shows a cyclic voltammogram for histidine tagged plastocyanin (a) at 20 AcBztacn modified gold/Zn electrode in 0.1 M phosphate buffer, with a scan rate of 20 mV/s (vs NHE) and histidine tagged bovine cytochrome P450c17 (b) at AcBztacn modified gold/Zn electrode in 0.1 M phosphate buffer, and the surfactant DDAB (didodecylammonium bromide), with a scan rate of 5 mV/s vs NHE. 25 Figure 5 shows binding of His-tagged thioredoxin, plastocyanin and green fluorescent protein to Acbztacn- and NTA-modified surfaces. Protein concentration is 30 pgmL-1 in 10 mM HEPES, 150 mM NaCl, pH 7.4. 30 WO 2005/003383 PCT/AU2004/000923 -9 General Description of the Invention Before proceeding with a general description of the present invention, some of the terms that will be used throughout this specification will now be defined. 5 The term "molecule" as used throughout the specification is to be understood to mean any carbon-based molecule for which a chemical and/or physical parameters or characteristics can be measured or determined by capturing the molecule on a solid support surface. The molecule could be any protein, 10 peptide, nucleic acid, carbohydrate, lipid or synthetic molecule. The term "orientation" when used in the specification in relation to the placement of a molecule with respect to the surface of a solid support is to be understood to mean the position and attitude of the molecule with respect to the 15 solid support surface. The term "immobilised" when used in the specification in relation to molecules on the surface of a solid support is to be understood to mean that the molecules are bound to the solid support under conditions in which the solid support is 20 intended to be used. Under such conditions, the molecules are not able to migrate from the surface of the solid support. However, it is to be understood that the molecules may be reversibly bound so that they can be removed from the solid support under specific conditions. 25 As previously discussed, the present invention provides a method for immobilising and selectively orienting molecules on a surface of a solid support. The method includes the steps of: - attaching a linker molecule to the surface of the solid support, the linker molecule including a head group that is capable of binding to 30 the solid support, and a tail group that is capable of chelating to a metal ion; WO 2005/003383 PCT/AU2004/000923 - 10 - treating the solid support with a solution containing the metal ion so that the metal ion is chelated to the tail group; - attaching a metal ion chelating tag to the molecules to form tagged molecules; and 5 - capturing the tagged molecules on the solid support by contacting it with the tagged molecules to form a monolayer of molecules on the surface of the solid support in which a majority of the molecules are held in the same orientation with respect to the surface. 10 By selectively orienting the molecules on the surface of the solid support it may be possible to increase the sensitivity of an analytical determination that is being made when compared to existing methods because most of the molecules are oriented with an active site in a position suitable for reaction. In the case of proteins, using existing methods control over protein orientation is 15 limited, since any surface amines can provide a point of attachment of the protein to the linker molecule. Consequently, two adjacent protein molecules may well be up to 1800 with respect to each other, since the monolayer forms by random coupling events. In order to analyse for a specific substrate, specific region(s) on the protein surface must be available to optimise sensor 20 performance. Under the random coupling scenario, as much as half of the protein monolayer may be in an orientation unsuitable for substrate conversion. The tag in the tagged molecule is preferably covalently bound to the molecule at a position on the molecule that is separated from the active site (or recognition 25 region) of the molecule. It will be appreciated that the active site of the molecule is that portion of the molecule that is involved in the chemical and/or physical transformation that is being investigated whist the molecule is captured on the solid support. For example, in the case of a polypeptide or protein, the tag may be covalently bound anywhere on the protein, as long as the protein 30 activity is not affected. In this way the protein is attached to the solid support at a modified portion of the protein and not a native portion of the protein. In the case of a small organic molecule the tag may be attached to the small organic WO 2005/003383 PCT/AU2004/000923 - 11 molecule via a flexible linker chain that acts to separate the tag from the active site of the molecule. The linker chain may be a functionalised alkyl chain for example. 5 The tag is preferably a small peptide chain containing chelate forming amino acids. Suitable chelate forming amino acids include cysteine, lysine, histidine, arginine. More preferably, the tag is a peptide containing a minimum of two but preferably four to six consecutive histidine residues. Most preferably the tag is a peptide containing six consecutive histidine residues herein referred to as a 10 "6*his" tag. The 6*his tag has been found to be particularly suitable for binding to a chelating metal ion. The solid support onto which the linker molecule is attached is preferably a noble metal. Suitable noble metals include silver, gold, platinum and palladium. 15 In addition, graphite-based materials, TiO 2 , IrO 2 , SnO 2 , Si-based surfaces or clays may also be used as a solid support. The solid support may be a chip having a surface that is formed from one of the aforementioned materials. The chip itself may be formed from any suitable material including but not limited to glass, plastic or ceramic material. Most preferably, the solid support includes a 20 gold surface. The linker molecule may be attached to the solid support either directly or indirectly. For example, the head of the linker molecule may be bonded to a noble metal surface on the solid support. Alternatively, the solid support may 25 have a coating, such as a dextran coating, onto which the linker molecule is attached. The linker molecule comprises the head group, the tail group, and a spacer group between the head group and tail group. The spacer group is covalently 30 attached to the head and tail groups and one function of the spacer group is to locate the tail group away from the surface of the solid support. Preferably the spacer a carbon-based chain between the head and tail groups. Preferably, the WO 2005/003383 PCT/AU2004/000923 - 12 carbon-based chain is an alkyl chain or an alkyl chain containing heteroatoms such as 0, N or S. The carbon-based chain is preferably two to six atoms in length and most preferably three atoms in length between the tail group and the head group. 5 Preferably, the head group is a heteroatom that has a relatively high affinity for the noble metal surface. Sulfur and selenium are particularly preferred head groups for noble metal substrates, however, any atom or group that can react with the surfaces listed above may be used. 10 In a particularly preferred form of the invention the tail group is a cyclic ligand containing three or more atoms that are capable or coordinating to the metal ion. Tetradentate macrocycles containing heterodonor atoms including 0, S, Se, N, P, As or any atom that can act as a Lewis base are particularly preferred. 15 The macrocycle is preferably a derivative of 1,4,7-triazacyclononane. More preferably, the derivative of 1,4,7-triazacyclononane contains a heterodonor atom that is pendant from the triazacyclononane ring. For example, the heterodonor atom may be the oxygen atom of a carbonyl group (ester, carboxylic acid, ketone, aldehyde, amide etc.). Most preferably the macrocycle 20 is 1-acetato-4-benzyl-1,4,7-triazacyclononane. The metal ion can be any ion that is capable of chelating with heteroatoms such as N, S, 0 and the like. Preferably, the metal ion is capable of octahedral coordination. Suitable metal ions include zinc, copper, cobalt and nickel. 25 In one preferred form of the invention the solid support is an electrode. In this way the solid support can form part of an electrochemical array so that the redox activity of the molecules immobilised on the surface can be determined. More specifically, the method of the present invention may be particularly 30 suitable for direct electrochemical measurements of redox active proteins, such as thioredoxin and other proteins having a redox active site, including metalloproteins, or those containing organic cofactors. In this way it is possible WO 2005/003383 PCT/AU2004/000923 -13 to measure directly the redox 'signature' of a protein of interest. In a preferred form of the present invention the linker molecule is three atoms in length and thus bound protein is held relatively close to the electrode. Close proximity to the electrode is associated with strong and reproducible signals for electrode 5 sensors. Alternatively, the solid support may form part of a chip, the surface of which is formed from a suitable material according to the present invention, for example a noble metal surface. The chip may be formed from glass, plastic, ceramic or 10 the like. In this case, the immobilised molecules may be used to capture a specific analyte in a sample suspected of containing the analyte. In particularly preferred embodiments of the present invention, the method involves: (i) the formation of a self assembled monolayer of mercaptopropionic 15 acid ("MPA") on gold; (ii) the activation of the carboxylic acid groups to reaction with a nitrogen nucleophile; (iii) treatment of the activated substrate with a suitable derivative of 1,4,7-triazacyclononane; (iv) treatment of the subsequent reaction product with a solution containing the chelating metal ion Zn 2 ; and (v) formation of a self assembled monolayer of protein (or other) molecules by 20 treating the product from (iv) with 6*his tagged molecules. Advantageously, the sensor chip of the present invention can be regenerated to bind the same or different molecules by washing the surface of the solid support with imadazole, acidic pH or addition of any ligand which is a Lewis base. In 25 addition, the metal ion can be changed using EDTA or another known metal chelating ligands. The present invention also provides a biosensor device including a sensor chip as hereinbefore described. The biosensor also includes a transducer for 30 detecting a change in a parameter in the immobilised molecules on the sensor chip. The transducer may measure an electrical parameter, such as in a WO 2005/003383 PCT/AU2004/000923 - 14 glucose biosensor, an optical parameter, such as in a Biacore instrument, or any other suitable parameter. The skilled person will appreciate that the sensor chip of the present invention 5 may be used in existing apparatus for measuring one or more parameters of the molecules immobilised on the surface of the sensor chip and/or molecules that bind to the molecules immobilised on the surface of the sensor chip. The apparatus typically include a reaction substrate and a separate reader or detector device, such as a scintillation counter or spectrophotometer. Assays 10 based on surface plasmon resonance (SPR) effects, such as the BlAcoreTM instrument and methodology, for example. These assays exploit the shift in SPR surface reflection angle that occurs with perturbations, e.g., binding events, at the SPR gold-glass interface. Applications include direct electrochemistry, including bioelectrochemistry, fluorescence or luminescence 15 studies between interacting species or functional groups, and applications involving immunological interactions, such as antibody-antigen interactions. It will also be appreciated that included within the scope of the present invention is the use of the layer of molecules held in the same orientation with respect to 20 the surface for applications that do not involve measuring a parameter of molecules immobilised on the surface, but rather use the uniform orientation of the immobilised molecules as a scaffold. In this case, the uniform orientation of the immobilised molecules may be used as a scaffold, for example, for other molecules, molecular complexes, or cells. 25 Accordingly, in another form the present invention provides a solid support including a monolayer of immobilised molecules captured on the surface of the solid support, wherein a majority of the immobilised molecules are in the same orientation with respect to the surface, and further including one or more 30 molecules attached or captured by the immobilised molecules on the surface of the solid support.

WO 2005/003383 PCT/AU2004/000923 - 15 In addition, the methods of selectively orienting and immobilising molecules on the surface of a solid support may include a further step of attaching or capturing one or more secondary molecules to the tagged molecules. 5 It will also be appreciated that included within the scope of the present invention is the use of the layer of molecules held in the same orientation with respect to the surface for applications in which the properties of the immobilised molecules are assessed without interaction with an analyte. For example, direct electrochemistry provides the ability to measure properties of a protein by 10 electron exchange. Accordingly, the present invention also provides a sensor device for measuring a parameter of an immobilised molecule on the surface of the sensor device. 15 Therefore, the present invention also provides a sensor device including a sensor chip of the present invention and a transducer for measuring a parameter in the immobilised molecules on the sensor chip. Description of Embodiments of the Invention 20 Preferred embodiments of the invention will now be described by way of the following non-limiting examples. Example 1 - Preparation of self assembled monolayers (SAMs) 25 Self assembled monolayers of molecules of interest were formed on a gold surface. The immobilisation protocol is outlined in Figure 1. A clean gold surface was modified with a mercaptopropionic acid (MPA) SAM, 30 designated 1 and the monolayer was subsequently modified with EDC/NHS to create the NHS intermediate 2. Specifically, a gold sheet was placed in a 5 mM solution of MPA (75:25 w/w Ethanol:H 2 0) overnight. The surface was then WO 2005/003383 PCT/AU2004/000923 -16 washed with ethanol to remove unbound MPA, and dried under a stream of N 2 . The dried gold sheet was placed into an aqueous solution containing 75 mM EDC and 25 mM NHS for 30 minutes, washed with water and used immediately. 5 The modified macrocyclic amine, 1-acetato-4 benzyl-1,4,7 triazacyclononane 3, was synthesized according to the method described in Warden et al. (Org. Lett. (2001) 3(18) 2855-2858). The gold sheet that had been modified to 2 was then placed into an aqueous solution containing 20 nM 1-acetato-4-benzyl-1,4,7 10 triazacyclononane 3 for 3 days. The gold was then washed exhaustively with water and used immediately. Addition of a metal desirous of octahedral coordination (pictured is Zn 2 ) gives the coordination sites 5. Specifically, the gold sheet that had been modified to 4 15 was placed into a 20 mM solution of ZnCl 2 for 20 minutes. The gold was washed thoroughly with water, and then immersed in a dilute solution containing 6*his tagged molecules to afford the highly orientated protein monolayer 6. For example, the modified gold surface may be placed in an aqueous solution containing 6*his tagged thioredoxin (0.2 mg of protein / mL in 10 mM phosphate 20 buffer, pH 6.0) at 40C overnight, washed in 10 mM phosphate buffer, pH 6.0 and used immediately. Example 2 -_Analysis of SAMs 25 The SAMs prepared according to Example 1 were examined using electrochemical cell and surface characterization techniques that are described in the literature (D.L. Johnson, J. Thompson, S.M. Brinkmann, K.L. Schuller & L.L. Martin, Electrochemical Characterisation of purified Rhus vernicifera laccase - voltametric evidence for a sequential 4-electron transfer, Biochemistry 30 2003, 42:10229-10237 and references therein).

WO 2005/003383 PCT/AU2004/000923 -17 DRIFT (Figure 2) and XPS experiments (not shown) were consistent with the proposed surface chemistry. DRIFT analysis was performed on fine silver powder modified according to Figure 1. DRIFT analysis of the preparatory stages 1, 2, and 4 are shown in Figure 2. Successful surface modification can 5 be clearly seen in the C-H and C=O stretching regions. 1 displays one C=O stretching vibration resulting from the COOH functionality, 2 displays two distinct C=O stretching vibrations resulting from the -COON- species and from the carbonyl groups on the succinimide, and 4 displays two different C=O stretching vibrations from the amide and from the COOH group on the 10 macrocyclic amine. XPS measurements concur, with significant variation in the

N

1 and 01, binding regions. Example 3 - Electrochemical behaviour of immobilised thioredoxin: comparison of oriented and non-oriented monolayers 15 The self assembled monolayer was studied using direct electrochemistry on histidine-tagged E. coli thioredoxin. Thioredoxin is the simplest member of a growing superfamily which regulate redox operation through a disulfide bond(s). The highly conserved active site contains two cysteine residues with the 20 sequence Cys-XXX-XXX-Cys. The oxidized form contains a disulfide bond, and the reduced form, generated by the sequential addition of two electrons, contains two thiol groups. The thioredoxin used in this study was expressed in E. coli using the Novagen 25 expression plasmid vector pET-32a(+) containing the coding region of E. coli thioredoxin gene and six codons for additional histidine residues at the C terminus. The histidine-tagged thioredoxin was then purified to homogeneity as assessed by a single band on SDS-PAGE using a nickel affinity (Ni/NTA) column (QIAGEN). The sample was concentrated to 5 mg/mL and stored in 30 potassium phosphate buffer (pH 7.4) at -80 0C before use.

WO 2005/003383 PCT/AU2004/000923 -18 Macrocycle modified electrodes were prepared by placing a gold electrode in a 5 mM solution of mercaptopropionic acid (MPA) (75:25 v/v ethanol/water) overnight. The electrode surface was then washed with ethanol to remove unbound MPA, and dried under a stream of nitrogen gas. The dried gold 5 electrode was placed into an aqueous solution containing 75 mM 1-ethyl-3-(3 dimethylaminopropyl) carbodiimide (EDC) and 25 mM N-hydroxysuccinimide (NHS) for 30 minutes, washed with water and used immediately. The SAM modified electrode was placed into an aqueous solution containing 20 mM 1 acetato-4-benzyl-1,4,7-triazacyclononane at pH 8 for - 30 h. The gold electrode 10 was then washed with water and used immediately. Metal ions were incorporated into the macrocycle by placing the modified electrode into a 20 mM solution of ZnC1 2 for 20 minutes. The electrode was washed thoroughly with water, placed into an aqueous solution of thioredoxin (0.2 mg of histidine tagged thioredoxin/mL in 10 mM phosphate buffer, pH 7.4) at 4 *C for between 30 min 15 and 3 h, then washed in the same buffer and used immediately. Alternatively, His-tagged cytochrome P450c17 and plastocyanin were immobilised overnight at 4 0 C using a 20 mM protein solution in 10 mM phosphate buffer, pH 7.4. Covalent attachment of the thioredoxin directly to the electrode for comparison was done following the same procedure but without addition of the macrocyclic 20 moiety, thereby resulting in its attachment to a surface amine on the thioredoxin protein. All electrochemical measurements were obtained using a BAS 100B electrochemical analyser (Bioanalytical Systems Inc., Lafayette, USA) at room 25 temperature. A conventional electrochemical set-up was employed, involving an Ag/AgCI (3 M KCI) reference electrode, a platinum auxiliary electrode and a gold electrode either in the form of a button electrode (from BAS) or a gold sheet. Potentials were corrected to the normal hydrogen electrode (NHE). 30 We compared the electrochemical behaviour of E. coli thioredoxin specifically captured via a histidine-tag using the methods of the present invention with thioredoxin covalently immobilized on a SAM with random orientation. Figure 3 illustrates typical cyclic voltammograms obtained at a gold electrode. The solid WO 2005/003383 PCT/AU2004/000923 - 19 line represents an electrode modified using the procedure described in Example 1, leading to an oriented monolayer; the dashed line represents an electrode modified by coupling surface amines on the protein to the electrode, leading to a randomly oriented monolayer. The scan rates shown are a) 200 pV/s, b) 1 5 mV/s and c) 10 mV/s. 20 mM phosphate buffer, pH 7.0. We observed a superior electrochemical response using the oriented protein layer, with a faster electron transfer rate constant (more reversible redox signal) and an improved signal to background ratio. 10 Example 4 - Surface plasmon resonance (SPR) analysis of a gold chip modified according to the present invention compared with a commercial BlAcore NTA chip Other histidine tagged proteins that were immobilised included bovine 15 cytochrome P450c17, Synechocystis plastocyanin and Montipora efflorescens green fluorescent protein (GFP). BlAcore spectra were obtained on a BlAcore X analytical system using modified J1 (J1 is a plain gold surface) and NTA sensor chips (BlAcore AB, Uppsala, 20 Sweden). The J1 chip was modified according to the methods described in Example 1, resulting in a 1-acetato-4-benzyl-1,4,7-triazacyclononane ("AcBztacn") chip, and the NTA chip was used as purchased. The running buffer was 10 mM HEPES, 150 mM NaCl, the activation buffer was 500 pM NiCl 2 , 10 mM HEPES, 150 mM NaCl, the sample buffer was 30 pg/mL 25 thioredoxin in 10 mM HEPES, 150 mM NaCl and the regeneration buffer was 350 mM EDTA, 10 mM HEPES, 150 mM NaCl (all at pH 7.4). All solutions were freshly prepared, degassed and filtered through a 0.2 pm Millipore filter. Oriented binding was evaluated by charging the chip with activating buffer (30 p.L/min for 1 min) followed by sample buffer (30 pL/min for 1 min). The stability 30 of the protein-chip interaction was monitored by passing running buffer (20 p.L/min) over the surface and monitoring the sensorgram over time. The dissociation rate was determined as the percentage of original binding lost per WO 2005/003383 PCT/AU2004/000923 - 20 minute across a period of between 2 and 14 h, assuming a linear decay. Non specific protein binding was evaluated by injecting sample buffer before Ni activation, thus comparing the weakly attached protein material prior to activation of the chips by metal ions. 5 Protein binding to the chip was assessed using SPR, as shown in Figure 5. We compared our AcBztacn electrode with the commercially available NTA chip from BlAcore for two proteins histidine-tagged thioredoxin and Montipora efflorescens green fluorescent protein (GFP (Table 1). In particular, we 10 examined the relative binding magnitude, stability (as assessed by protein dissociation) and the degree of non-specific binding of histidine-tagged thioredoxin and Montipora efflorescens green fluorescent protein (GFP). Despite a lower surface coverage, the AcBztacn modified surface displayed greater than five-fold increase in binding magnitude (Table 1) as assessed by 15 the amount of bound protein to Ni-treated surface. The stability of the protein-Ni interaction was assessed by the rate of decay of the initial binding strength, as determined by the amount of protein dissociation after protein loading and expressed as the percentage of dissociation per minute. The AcBztacn-Ni protein complex is eight times more stable than NTA-Ni-protein (Table 1). The 20 AcBztacn electrode therefore has potential applications for long term biosensor use, with 50% of bound protein dissociated from the NTA chip in less than 40 min, compared with a loss of only 40% of total protein even after 15 h for the AcBztacn electrode (shown by a comparison of the dissociation rates in Table 1). Binding of protein prior to Ni ion activation was an order of magnitude 25 greater for NTA, indicating that a component of non-specific binding occurs in the NTA chips. The increased binding of protein, improved stability and a reduction in non-specific binding indicates that the AcBztacn surface of the sensor chips of the present invention has superior qualities to this commercially available system. 30 WO 2005/003383 PCT/AU2004/000923 - 21 Table 1 Thioredoxin Ni-NTA Ni-AcBztacn Improvement Factor Immobilized protein (RU) 828 4504 5.4 Dissociation rate 1.7 0.2 8.5 (% of initial RU lost per min) Non-specific protein binding 46.7 5.0 9.2 (%) Green Fluorescent Protein Immobilized protein (RU) 376 2325 6.2 Dissociation rate 7.6 0.9 8.4 (% of initial RU lost per min) Non-specific protein binding 38 4 9.5 (%) 5 Finally, it is to be understood that various other modifications and/or alterations may be made without departing from the spirit of the present invention as outlined herein.

Claims

1. A method for selectively orienting and immobilising molecules on a surface of a solid support, the method including the steps of: - attaching a linker molecule to the surface of the solid support, the linker molecule including a head group that is capable of binding to the solid support, and a tail group that is capable of chelating to a metal ion, wherein the tail group of the linker molecule is a cyclic ligand containing three or more atoms that are capable of coordinating to the metal ion; - treating the solid support with a solution containing the metal ion so that the metal ion is chelated to the tail group; - attaching a metal ion chelating tag to the molecules to form tagged molecules; and - capturing the tagged molecules on the solid support by contacting it with the tagged molecules to form a monolayer of molecules on the surface of the solid support in which a majority of the molecules are held in the same orientation with respect to the surface.

2. A method as in claim 1, wherein the tail group of the linker molecule is a macrocycle that is capable of chelating with the metal ion.

3. A method as in claim 2, wherein the macrocycle is a tetradentate macrocycle.

4. A sensor chip including: - a solid support having a noble metal surface; - a linker molecule attached to the surface of the solid support, the linker molecule including a head group that is bound to the solid support, and a tetradentate macrocyle tail group that is chelated to a metal ion; - 23 - a monolayer of immobilised molecules on the surface of the solid support, wherein each molecule contains a metal ion chelating tag and is held on the surface of the solid support by co-ordination of the tag with the metal ion such that a majority of the molecules are held in the same orientation with respect to the surface.

5. A method as in claim 3 or a sensor chip as in claim 4, wherein the macrocycle is a derivative of 1,4,7-triazacyclononane.

6. A method or a sensor chip as in claim 5, wherein the macrocycle is 1 acetato-4-benzyl-1,4,7-triazacyclononane.

7. A method as in any one of claims 1 to 6 or a sensor chip as in any one of claims 4 to 6, wherein the metal ion is capable of octahedral coordination.

8. A method or a sensor chip as in claim 7, wherein the metal ion is selected from the group consisting of zinc, copper, cobalt and nickel.

9. A method as in any one of claims 1 to 8 or a sensor chip as in any one of claims 4 to 8, wherein the tag is a peptide chain containing chelate forming amino acids.

10. A method or a sensor chip as in claim 9, wherein the chelate forming amino acids are selected from one or more of the group consisting of cysteine, lysine, histidine, arginine.

11. A method as in any one of claims 1 to 10 or a sensor chip as in any one of claims 4 to 10, wherein the tag is a peptide containing four to six consecutive histidine residues.

12. A method or sensor chip as in claim 11, wherein the tag is a peptide containing six consecutive histidine residues. -24

13. A method as in any one of claims 1 to 12, wherein the solid support onto which the linker molecule is attached is a noble metal.

14. A method as in claim 13 or a sensor chip as in any one of claims 4 to 12, wherein the noble metal is selected from the group consisting of silver, gold, platinum and palladium.

15. A method as in any one of claims 1 to 12, wherein the solid substrate includes a gold surface onto which the head group of the linker molecule binds.

16. A method as in any one of claims 1 to 15 or a sensor chip as in any one of claims 4 to 12 and 14, wherein the linker molecule includes a spacer between the head and tail groups.

17. A method or sensor chip as in claim 16, wherein the spacer is a carbon based chain between the head and tail groups.

18. A method or sensor chip as in claim 17, wherein the carbon-based chain is an alkyl chain.

19. A method or sensor chip as in claim 18, wherein the carbon-based chain is two to six atoms in length.

20. A method or sensor chip as in claim 19, wherein the carbon-based chain is three atoms in length between the tail group and the head group.

21. A method as in any one of claims 1 to 20 or a sensor chip as in any one of claims 4 to 12, 14 and 16 to 20, wherein the head group is a heteroatom that has a relatively high affinity for the noble metal surface.

22. A method or sensor chip as in claim 21, wherein the head group is sulfur or selenium. -25

23. A method or sensor chip as in claim 22, wherein the immobilised molecule is a protein.

24. A method or sensor chip as in claim 23, wherein the tag in the tagged molecule is covalently bound to the protein at a position on the protein that is separated from the active site or recognition region of the protein.

25. A method or sensor chip as in claim 24, wherein the solid support is an electrode.

26. A sensor chip that is modified according to the method of any one of claims 1 to 25.

27. A biosensor device including: - a sensor chip according to any one of claims 4 to 12, 14 and 16 to 25; and - a transducer for detecting a change in a parameter in the immobilised molecules on the sensor chip.

28. A method of determining the presence of an analyte in a sample, the method including the steps of: - providing a self-assembled monolayer on a surface of a solid support, said monolayer comprising linker molecules having head groups that are bound to the surface of the solid support, and tail groups that are chelated to a metal ion, wherein the tail groups of the linker molecules are cyclic ligands containing three or more atoms that are capable of coordinating to the metal ion; and analyte binding molecules having a tag that is bound to the metal ion, said analyte binding molecules oriented uniformly with respect to the surface of the solid support; - contacting the self-assembled monolayer having the analyte binding molecule immobilised thereon with a sample suspected of containing a target analyte; and -26 - detecting binding of the target analyte with the analyte binding molecule to thereby determine the presence or absence of the target analyte.

29. A method for selectively orienting and immobilising molecules on a solid support having a gold surface, the method including the steps of: - treating the gold surface with a mercaptopropionic acid to form a mercaptopropionic acid self-assembled monolayer; - treating the mercaptopropionic acid self-assembled monolayer with a tetradentate derivative of 1,4,7-triazacyclononane to form a macrocyle modified mercaptopropionic self-assembled monolayer; - treating the macrocyle modified mercaptopropionic self-assembled monolayer with a metal desirous of octahedral coordination to form a metallo macrocyle modified mercaptopropionic self-assembled monolayer; and - treating the metallo macrocyle modified mercaptopropionic self assembled monolayer with a solution containing a 6*his tagged molecule to form a highly orientated monolayer of immobilized molecules.

30. A method as in any one of claims 1, 28 and 29, substantially as herein described with reference to the accompanying examples and drawings.

31. A sensor chip as in claim 4, substantially as herein described with reference to the accompanying examples and drawings.