The present invention concerns a nanopored silicon nitride chip for the analysis of gene expression profiles and related \ biosensors. More particularly, the present invention concerns a nanopored silicon nitride chip and related biosensor to be used for diagnosis and prophylaxis in medical, botanical, zoo-technical and zoo-prophylactic field.

The Human Genome project allows new genes and expressed sequences to be identified, this project will allow the human genome complete de-codification (http://www.oml.gov/hgmis/). At the same time new technologies for genome analysis, in particular the microarray technology, allowing tens of thousands of genes in a single experiment to be analysed, have been developed. Microarray technology is based on the following principle: single strand D A molecules are fixed to a solid support, such probes are suitable to hybridize to complementary DNA sequences . Such microarray devices are used for the characterization of gene expression profiles, in order to identify point mutations and polymorphisms of single nucleotides, in order deleted or inserted chromosome regions to be identified [1] .

Recently [2] , for the genome analysis the nanopore technology has been developed. The use of nanopores for the detection and analysis of single molecules, is derived from Coulter counter principle

[3] : a small channel separating two reservoirs filled with an electrolytic solution wherein target particles are dissolved. By application a voltage difference within the channel, the particles are forced to cross the same and passage thereof is evidenced by a current drop. Current decrease magnitude is directly correlated to particle volume. This analytical technique therefore allows the concentration and size distribution of dispersed particles to be determined.

The results reported in [2] demonstrate the pos sibility to scale down this behaviour to nanometric size using pores of -hemolysin, a protein produced by Staphilococcus aureo s, able to self -assembling within double lipid layer of biological membranes, forming a pore with a diameter of 1.4 nm.

A successive step in this direction has been made according to [4] by identification of DNA strands with a single base resolution using "engineered nanopores" . This object has been reached by covalenty binding DNA- oligonucleotides (probes) near the entrance of pore lumen, in this way the pore is partially obstructed and ionic conductivity thereof is reduced. When a short com lementary oligonucleotide (target) is forced through the pore lumen by the applied voltage, said oligonucleotide forms a double strand D A with the probe, resulting in a characteristic current reduction. A not complementary oligonucleotide is pushed quickly through pore under the voltage application, producing a marked reduction of the current thus evidencing the translocation without double strand formation. In this way the device with biological engineered nanopore is used to evidence a codon in a single DNA molecule [4] , or to evidence a difference between molecules at single nucleotide level [5] .

Although it has been proved that biological pores are useful in a large number of applications, the same also show remarkable disadvantages correlated mainly to fixed size and limited stability thereof. For this reason various research teams are involved in the possible production of nanopores from solid state materials, resulting in many advantages, as: 1) high stability, 2) control of channel diameter and length, 3) adjustable surface properties and 4) possibility for nanopores to be integrated in devices and arrays [6,7] . As to the production of solid state nanopores as described for example in [6] and [7] the same show, in turn, some disadvantages, as for example the need controlled ionic sputtering process (ref [6] ) or electron beam scanning (ref [7] ) to be used in order to reduce the final size of the pore initially created using ionic focused beams.

In the light of above it is therefore apparent the need to provide for new devices for the detection of nucleotide sequences thus overcoming the disadvantages of known prior art .

The authors of the present invention previously have prepared solid state nanopores, functionalized, activated with known sequence DNA molecules, obtained using ionic beams within a suspended thin silicon nitride membrane (Si ₃ N ₄ ) [8] . It has been therefore demonstrated that solid state nanopores can be stably functional!zed with DNA molecules. However, the parameters of previously prepared biosensors have not been displayed effective for the detection of oligonucleotide molecule passage, even proved to be quite incompatible with the measure of translocation thereof .

The Authors of the present invention have now provided for solid state nanopores allowing the stable use thereof as selective biosensors suitable to recognize specific nucleotide sequences within unknown DNA molecule to be carried out . According to the present invention it is therefore pos sible solid state nanopores to be functionalized effectively with DNA, thus to be made the same more stable and less sensitive to environmental conditions than biological ones. The term "to functionalize effectively" means not so much to find chemical procedures aiming DNA to be bound to Si ₃ N ₄ , which is original but not completely new, as to be suitable to calibrate in a correct way the characteristic parameters of the problem, as the relationship of the length of DNA chosen molecules and the nanopore geometric dimensions, the concentrations of DNA molecules and ionic solution used for the measures of current through the nanopore and so on. In comparison to other procedures for DNA adhesion to nanopore surface, herein disclosed one does not involve the local pre-deposition on nanometric areas of material (gold, platinum, oxide etc) , said pre-deposition requiring complex and expensive processes of lithographic type thus increasing times, costs and failure risks during the chip preparation, to be carried out.

Secondly nanopore initial size (higher than 30 n ) allows FIB alternative lithographic production techniques to be provided, that is at remarkably reduced costs .

Moreover the same procedure for chemical functionalization can be used independently from the sequence of oligonucleotide probe. Therefore, a single chip according to invention can be used as an array of nanopores, each thereof being differently functionalized in order a specific sequence to be recognised. A device of this type represents a very powerful diagnostic tool. Said device in fact, also being similar, as to *hybridization" operation principle, to a micro-array, involves an extremely quick and simple reading, that is a current measure rather than an optical type measure.

In comparison to same type biosensor consisting of biological nanopore, the inventive one displays advantages with respect to stability, modifiability, suitability to be integrated in more complex devices, re-usability. Moreover, the biosensor according to the invention can operate at extreme temperatures and pH ranges and are easily stored.

The silicon nitride based nanopore device functionalized with oligonucleotide probes according to the invention can be advantageously used for the analysis of expression profiles for research, diagnostic and prognostic purposes. The device according to the invention allows, in various pathologies (cancerous and not) , the profiles of gene expres sion from various origin biological (bioptic material, peripheral or medullary blood etc) samples to be analysed. Such application allows molecular markers with prognostic meaning to be evaluated and/or a better patient staging within the risk categories and the consequent therapy personalization to be carried out. Particularly, the device allows SNP to be identified in biological samples relating to various pathologies (cancerous and not) . Being known that SNPs are associated to susceptibility of some diseases and different response to pharmacological therapies, such an analysis will allow a patient fingerprinting to be carried out aiming the pathology predisposition and drug response to be estimated. Moreover, the device according to the invention can be used for applications in botanical, zoo-technical and zoo-prophylactic fields, for example for the identification of OGM in foods or growing crops or virus characterization.

It is therefore a specific object of the present invention a chip comprising or consisting of a nanopored silicon nitride membrane, wherein nanopores have an effective diameter from 20 to 50 nm and the thickness of the membrane is from 10 nm to 50 nm and more preferably from 10 to 20 nm. Said nanopores can be produced by means of focused ion beams, for example by means of the use of ultra-high resolution field emission scanning electron microscope with focused ion beam.

The present invention further concerns a biosensor comprising or consisting of as defined chip, wherein at least one nanopore is functionalized with an oligonucleotide having a length from 13.6 nra to 18.7 run, preferably 15.3 nm. The nanopores can be f nctionalized with the same or different oligonucleotides. The effective diameter of functionalized nanopores of the biosensor can vary from 3 to 20 nm, preferably from 4 to 10 nm, still more preferably from 4 to 6 nm.

It is a further object of the invention a proces s for the preparation of as above described biosensor comprising or consisting of the following steps: a) deposition of a solution of oligonucleotide having a length from 40 to 55 bases, preferably 45 bases, said solution having a concentration from 10 to 200 nM, preferably 100 nM, in bi-distilled water or SSC 2X that is a sodium chloride 0.3 M solution, 0.03 M sodium citrate at pH 7.1; b) deactivation of the biosensor surface. The deactivation of the biosensor surface can be carried out by means of washings with 28% ammonia solution and successive washings with bi-distilled water .

The present invention concerns moreover a device for the detection of oligonucleotide sequences comprising chip or biosensor as above defined. The device can further comprise two ionic solution containing reservoirs communicating through the nanopores and two electrodes for voltage application and current detection.

The use of chip or biosensor or device as above defined for oligonucleotide molecule detection in medical, botanical, zoo-technical or zoo-prophylactic fields is a further object of the present invention.

The present invention now will be described by an illustrative, but not limitative way, according to preferred embodiments thereof, with particular reference to enclosed drawings wherein:

Figure 1 shows a cell scheme according to A J Storm, J H Chen, H W Zandbergen, and C Dekker, Translocation of double-strand dna through a silicon oxide nanopore. Physical Review, 71:051903, 2005 [9].

Figure 2 shows the cell of figure 1 located on antivibrating table inside of a Faraday double cage.

Figure 3 shows a current ramp detected by applying different voltages to the measuring cell containing nanopored chip (figure 3A) and the voltage- current curve extrapolated from current ramp with dotted line outlined linear fit in order R nanopore resistance to be estimated (the figure 3B) .

Figure 4 shows a nanopore scheme wherein r is the radius and 1 the length.

Figure 5 shows on the left (A) a schematic representation of experimental conditions. In the lower part the nanopored chip with attached oligonucleotide probe is represented. Moreover DNA target molecules which tend to the translocation into the pore under the action of applied voltage are represented. On the right (b) a schematic representation of ionic current signal which is likely to be expected is reported.

Figure 6 shows a picture according to S.Howorka, S. Cheley, and H.Bayley, Sequence-specific detection of individual DNA strands using engineered nanopores, Nature Biotechnology, 19 (2001) 636-639 [4J . On the left the configuration of perfect complementarines s between nanopore attached DNA probe (in gray) and trans-locating target DNA (in black) ,- on the right translocation in the presence of two filament mismatch. In the lower part, in the picture, respective measured ionic current signals are represented. Figure 7 shows a scheme according to S. M. Iqbal, D. Akin, and R.Bashir, Nature Nanotechnology, 2:243- 248, 2007 [10] . The oxide layer to be deposited on nanochannel Si in order the surface functionalization with 'hairpin* DNA molecules to be carried out. Moreover pas sing target DNA is shown.

Figure 8 shows a scheme according to M. Wanunu and A. Meller, Chemically modified solid-state nanopores, Nano Letters, 7 (6) : 1580-1585 , 2007 [11]. Functzonalization organic molecules are represented.

Figure 9 shows a schematic representation of starting Si/Si ₃ N ₄ chip.

Figure 10 shows the current ramp obtained on a nanopored chip in range 0-55 mV.

Figure 11 shows the linear Fit of the measure reported in figure 8, from which it results R = 6.91 ΜΩ.

Figure 12 shows GAPDH housekeeping Gene (SEQ ID NO: 2). In gray colour sequence (SEQ ID NO: 1) of functionalization molecule probe is reported.

Figure 13 shows the linear Fit of current measures before (black squares) and after (gray circles) the functionalization with oligonucleotide probe .

Figure 14 shows pictures obtained using a scanning electron microscope (SEM) of a nanopored chip before (on the left) and after (on the right) the functionalization with oligonucleotide probe.

Figure 15 shows the scheme of oligonucleotide molecule not functionalized (A) and functionalized nanopore .

Figure 16 shows the microfluid cell for the measures of nanopore current .

Figure 17 shows the chip section dipped within ionic solution. Oligonucleotide probes are fixed to the chip. In the cis reservoir, λ-DNA target molecules directed to pore under the application of voltage V are dipped .

Figure 18 shows the measured ionic current during the experiment of molecular translocation described in the "material and methods" section. B and C: Successive magnifications of A plot shown in order to appreciate single current spikes associated to the passage through nanopore of λ-DNA molecules. In figure C average translocation duration is indicated, equal to approximately 1.36 ras when 120 mV voltage is applied and cis and trans reservoirs are filled with KC1 2 M and 0.01 M, respectively.

EXAMPLE 1 : Preparation and operation of the biosensor according to the invention

According to preferred embodiments, the fundamental components of the measure apparatus are a cell consisting of two reservoirs containing ionic solution (typically KC1 1 M) , in communication only through the nanopore, and two electrodes (chlorinated silver wire Ag/AgCl) for the voltage application and current detection (figure 1) .

The cell, made of polymer (PDMS) or plexiglass, is located on an antivibrating table inside of a double Faraday cage so as to reduce the electrical and mechanical noise (figure 2) .

The measures of ionic current therefore are carried out inserting the nanopored chip in the measure cell and applying a voltage difference between the two solution dipped electrodes. Particularly voltage ramps are applied and current ramps are recorded (figure 3A) in order voltage-current curves to be plotted. Prom the latter, with a linear fit to delineate (figure 3B) it is possible to have an evaluation of nanopore R resistance .

By using system exemplification hypotheses, from nanopore R resistance R an evaluation of diameter thereof can be obtained. If we assume that nanopore is substantially a cylindrical channel with length 1 equal to the thickness of the membrane whereon the pore is made it is obtained (Figure 4) :

R= 1/σΚΓ ²

where σ is the conductivity of the ionic solution and R is the radius of cylindrical pore that therefore can be evaluated directly by the measure of R.

Nanopored chip can be functional!zed for the realization of a biosensor suitable to experiments for gene expres sion analysis. The nanopore is functional!zed by fixing known sequence "probe" oligonucleotides, to surface thereof, thus it can be used as biosensor in applications of gene expression profiling, SNP search or mutations. Target unknown DNA molecules are inserted in the reservoir wherein the negative electrode is dipped and, due to negative charge thereof, will tend to cross the nanopore, after the application of a voltage difference between two sides of the nanopored chip (figure 5A) . During the nanopore crossing the target molecules cause a partial clogging of the pore, that is a reduction of the level of measured ionic current. If probe and target filaments are complementary during the crossing the molecules will be slowed, staying longer in the channel and therefore causing a longer lasting clogging (figure 5B) .

Analogous measures have been already carried out with biological nanopores (see figure 6) , and various techniques have been already developed in order Si0 ₂ and Si ₃ N« made solid state nanopores to be functionalized with "DNA hairpin" (figure 7) and aminosilanes , respectively (figure 8) .

Chips according to the invention consist of a silicon substrate whereon, in succession, thin films of silicon oxide and silicon nitride, the latter being 20 nm thick, are coated. Using a chemical etching process the chip is excavated from the bottom in order the suspended silicon nitride membrane to be exposed resulting in an approximately 80 x 80 μχ wide window. On the upper part of the chip it is pos sible, but not neces sary, to carry out metal coatings to be used as local electrodes.

The chips can be nanopored using an Ultra High Resolution Field Emis sion Scanning Electron Microscope (UHR-FE-SEM) with Focused Ion Beam (FIB) allowing, using ionic sputtering, nanopores of diameter from 30 nm to 50 nm on a suspended thin silicon nitride membrane (Si ₃ N ₄ ) to be produced. For the measure of ionic current the nanopore is inserted in a microfluid cell made of plexiglas s and inserted in a double Faraday cage on an antivibrating table. The reservoirs of the measurement chamber are filled with a KC1 1M HEPES 10 mM buffered solution at pH 8. The measure is carried out using two Ag/AgCl electrodes used both for the voltage application and current detection by means of patch-clamp amplifier (Axopatch 200B, Axon Instruments) .

Figure 10 reports the standard measure carried out on a nanopored chip. From the measure it is pos sible to obtain, as above said, an evaluation of nanopore R electric resistance by a linear fit (figure From the R value it is deduced, based on (1) , an evaluation of d _eff nanopore effective diameter, approximated to a cylindrical channel with length 1 (1 = 20 ran) equal to the thicknes s of silicon nitride membrane and conductivity σ equal to that of KC1 1M solution (10 S/m) :

At this point the chemical functionalization of nanopored chips with known sequence oligonucleotide can involve the application of the following protocol:

1. Substrate pre-treatment :

- Substrate washing with ddH ₂ 0;

Treatment of the substrate with amino propyl triethoxy-silane (20% solution of ddH ₂ 0) 1 hour at room temp. ;

2. Substrate activation:

Treatment of the substrate with 1 , 4-phenylene- diisothiocyanate (5% solution of dimethylsulfoxide) 5 hours at room temp . ;

- Substrate washing with dimethylsulfoxide (2 times) ;

- Substrate washing with ddH ₂ 0 (2 times) ; - Air substrate drying at room temp. ;

3. DNA adhesion:

- Manual deposition of 100 nM oligonucleotide (45mer) solution of ddH20;

- Incubation at 37°C 0/N in humid box.

4. Substrate deactivation

- Surface washing with 28% ammonia (2 times 30 minutes each) Surface washing with ddH20 (2 times 15 minutes each)

5. Chip storage

- Vacuum and refrigerator stored at 5°C.

The above described protocol can be diagrammatically represented as below:

3 -amminopropiltrietos sisilano= 3-amino propyltriethoxyeilane, amino-modified oligo DNA

By the application of functionalization protocol therefore a nanopore with known sequence probe DNA molecules fixed to the active surface can be obtained. Particularly we used an oligo D A extracted (SEQ ID NO:

1) from GAPDH "housekeeping" gene (Homo sapiens glyceraldehyde-3 -phosphate dehydrogenase) (SEQ ID NO:

2) , expressed by all the cells. It is the sequence of 45 bases (15.3 run long filaments) gray coloured in figure 12.

The successful functionalization can be checked using ellipsometric fluorescence based techniques or verifying that the functionalization results in nanopore size narrowing, that is a reduction of the effective diameter resulting in an increase of electric resistance. Figure 13 shows in gray colour (circles) the current value obtained for nanopore as compared with that (black squares) obtained before the functionalization and also reported in figure 11.

Therefore the functionalization with 15.3 nm long probe molecules results in a reduction of pore diameter of approximately 25.5 nm (32 - 6.5 nm) , that is approximately 13 nm of radius obstruction (probe molecules do not assume a completely flat configuration) .

The presence of probe molecules after the functionalization has been also verified by SEM images (figure 14) . Also from SEM images it is possible to evaluate a lateral obstruction by functionalization organic layer of approximately 11 nm. It is an obstruction that results in a reduction of nanopore effective diameter from 30-40 nm to 8-18 run, that is an average value allowing the final hybridization tests of probe molecules with pore translocating target DNA molecules to be effectively carried out (where "effectively* means the occurrence of a detectable reduction of ionic current average level during the translocation) . The current measure calibrated functionalization protocol represents the first step (the most important) for the production of a biosensor for target sequences.

In summary the patent idea is correlated with the possibility of taking advantage of the functionalization its-self in order to not only make the nanopore selective for the specific analyzed probe- target interaction, but also in order to reduce the size of the same pore up to a value compatible with the obstruction of individual target molecules in solution.

This means to be in a contest as schematized in figure 15A, that is as a pore with much greater size than analyzed DNA molecules and therefore insensitive to the pas sage of bio-molecules and obtain, by means of functionalization, the result as reported in 15B, i.e. a pore with a reduced final effective diameter up to a value compatible with individual molecule analysis. A thus realized device allows *to see" pas sing DNA molecules as current reduction transient events.

The signal to noise ratio of the device, that is the relationship between the amplitude of current modulation due to the passage of molecules, ΔΙ ("Event amplitude" in figure IB) , and average ionic current I, depends on the ratio of target molecule section, ΔΑ, to pore effective section, A, according the relation:

The latter, based on the Ohm law (V = R I) , can be written, as:

where σ is the conductivity of used ionic solution, V is the applied voltage and L the membrane thickness (that is the length of nanochannel) .

Therefore the occurrence of molecule pas sage is detectable at sufficiently high voltage and conductivities and sufficiently low membrane thickness . Particularly, given the intrinsic noise level of the device based on silicon nitride nanopores (amplitude of the order of 300 pA) , our results show that, in normal conditions, the passage of molecules is detectable as a recognizable event from noise background only for membrane thicknes s lower than 50 run. As a demonstration in example 2 the result of a check experiment for single molecule sensitivity of functionalized nanopore is reported.

EXAMPLE 2 : Experimental examination of single molecule sensibility of nanopore device functionalized according to the invention

Materials and methods

Si/Si ₃ N ₄ chip as represented in figure 9 consisting of silicon support 300 μτη thick and coated with ~ 10 run thick silicon nitride (Si ₃ N ₄ ) film. The silicon support has been subjected to anisotropic etching in order 80x80 μπι ² Si ₃ N ₄ wide area to be exposed. On this area, constituting a suspended membrane, a single nanopore with nm effective diameter has been produced. Then the nanopore has been subjected to functionalization procedure as described in example 1 protocol, using 45-mer oligonucleotides. Particularly 5' -amino modified 45-mer oligonucleotides (M G Biotech, Germany) corresponding to 5'-GCC AAA AGG GTC ATC ATC TCT GCC CCC TCT GCT GAT GCC CCC ATG- 3 ' (SEQ ID N0:1) sequence of GAPDH (glyceraldehyde- 3 -phosphate dehydrogenase) gene have been used.

Chip containing the functionalized nanopore has been as sembled in a microfluid cell for ionic current measurements. Figure 16 represent the plexiglass made cell and consisting of two ionic solution reservoirs faced at chip chamber and equipped with channels for inlet and outlet of ionic solution and pores for Ag/AgCl electrode positioning. The chip chamber is equipped with two rubber seals.

The silver/silver chloride electrodes are connected to a patch-clamp amplifier (Axopatch 200B, Axon Instruments) for voltage (120 mV) application and nanopore current detection. The current detection is carried out with 200khz sampling rate and using a 2 ^nd order Bes sel filter at 10 khz. For the measurements a potassium chloride solution, KC1, at 2 M concentration in cis reservoir, i.e. wherein initially target molecules have been dispersed and at 0.01 M concentration in trans reservoir (see figure 17) .

Experiment target molecules are double strand ~ 48 kbp λ-DNA molecules.

Results

Given the background noise level of device based on silicon nitride nanopores (amplitude of the order of 300 pA) , our results show that, under normal conditions, the molecule pas sage is detectable as background noise recognizable event only for membrane thicknesses lower than 50 nra. As a demonstration in figure 18 results of molecular translocation experiment carried out under conditions illustrated in above reported material and methods section are reported: on the current plot spikes as sociated to the passage of single D A target molecules not found using nanopores not functionalized or functionalized by means of membranes having thickness equal or lower than 50 run, appear. In figure (18 C) are also reported the average translocation durations, equal to approximately 1.36 ms . This value is directly related to the length of target molecule and interaction level of target with probe molecules. References

[1] M. Schena, Microarray biochip technology. Eaton Publishing, 2000.

[2] J. J. Kasianowicz, E. Brandin, D. Branton, D.W. Deamer, Procl. Natl. Acad. Sci. USA 93 (1996) 13770- 13773.

[3] WH. Coulter, Proceedings of the National

Electronics Conference (1957) 1034-1042.

[4] S. Howorka, S. Cheley, H. Bayley, Nature Biotechnology 19 (2001) 636-639.

[5] S. Winters-Hilt, M. Landry, M. Akeson, M. Tanase,

I. Amin, A. Coombs, E. Morales, J. Millet, C.

Baribault, S. Sendamangalam, Cheminformatics BMC

Bioinformatics 7 (2006) S22.

[6] J. Li, D. Stein, C. McMullan, D. Branton, M. J. Aziz, J. A. Golovchenko. Nature 412 (2001) 166-169.

[7] C. J. Lo, T. Aref, A. Bezryadin, Nanotechnology 17

(2006) 3264-3

[8] Mussi et al . , Superlatticee and Microetructures , vol. 46, no. 1-2, 10 October 2008, pages 59-63.

[9] A J Storm, J H Chen, H W Zandbergen, and C Dekker. Physical Review E , 71:051903, 2005. [10] S. M. Iqbal, D. Akin, and R.Bashir, Nature Nanotechnology, 2:243-248, 2007

[11] M. Wanunu and A. Meller, Nano Letters, 7(6):1580- 1585, 2007.