A system for biodetection applications (Machine-translation by Google Translate, not legally binding

专利摘要:
A system for biosensing applications. The present invention relates to a system for biosensing applications comprising two basic elements, a substrate with a functionalized surface and a nanoparticle, the system being able to enhance the plasmonic effect of the nanoparticle. The invention also relates to a biosensor that incorporates such a system, in addition to the method for detecting and quantifying a target analyte selected in a sample using such a system. Finally, the invention relates to a device that can detect the enhanced optoplasmonic effect of the nanoparticles by means of the system of the invention or combine the detection of such optoplasmonic effect with the analysis of the changes in the mechanical characteristics in the substrate. (Machine-translation by Google Translate, not legally binding)
公开号:ES2553027A1
申请号:ES201430846
申请日:2014-06-03
公开日:2015-12-03
发明作者:Francisco Javier Tamayo De Miguel；Priscila Monteiro Kosaka；Valerio Pini；Montserrat Calleja Gomez；Jose Jaime RUZ MARTINEZ；Daniel RAMOS VEGA；Maria Ujue GONZÁLEZ SAGARDOY
申请人:Consejo Superior de Investigaciones Cientificas CSIC；
IPC主号:

专利说明:

5
10
fifteen
twenty
25
30
35
40
Four. Five
A system for biodetection applications FIELD OF THE INVENTION
The present invention belongs to the field of biosensors. More particularly, the present invention relates to a system for biodetection applications comprising two basic elements, a substrate with a functionalized surface and a nanoparticle, the system being able to enhance the plasmonic effect of the nanoparticle. The invention also relates to a biosensor that incorporates such a system, in addition to the method for detecting and quantifying a selected target analyte in a sample using such a system. Finally, the invention relates to a device that can detect the enhanced optoplasmonic effect of the nanoparticles by means of the system of the invention or combine the detection of such an optoplasmonic effect with the analysis of changes in the mechanical characteristics of the substrate.
BACKGROUND OF THE INVENTION Biosensors
A biosensor measures the physical changes that a biological recognition layer attached to a solid transducer undergoes when it interacts with a sample containing the molecules chosen as the target. Thus, it employs the ability of some biomolecules (receptors) to specifically bind (recognize) complementary biomolecules (ligands). The most typical interactions are complementary nucleic acid hybridization and antibody / antigen binding. Biosensors are increasingly in demand in fundamental biological studies, health sciences research, drug discovery and clinical diagnosis13. Depending on the physical change measured, the biosensors can be classified as optical, electrical and mechanical.
Optical biosensors can be divided mainly into mark-based detection and mark-free detection. The most commonly used brand-based biosensors are based on fluorescence-based detection, target molecules or biorecognition molecules are labeled with fluorescent labels, such as dyes; The intensity of the fluorescence signal indicates the amount of molecules chosen as the target. While fluorescence-based detection is extremely sensitive, it suffers from laborious marking procedures that can also interfere with the function of the biomolecule. In contrast, in unlabeled detection, the molecules chosen as the target are not labeled or altered, and are detected in their natural forms. A significant part of the unmarked optical sensors measures the change in the refractive index close to the sensor surface by exciting an evanescent field that decreases exponentially in bulk solution with a characteristic length between tens to hundreds of nanometers4. The surface plasmon resonance procedure (SPR) and the localized surface plasmon resonance procedures (LSPR) are the most popular among unbranded optical biosensors.
Among electric biosensors, electrochemical devices have traditionally received most of the attention57. These devices normally couple enzymes that produce or consume electrons after recognition of substrates to an electrode transducer. Many of these enzymes specifically catalyze the reactions of clinically important analytes such as glucose, lactate, cholesterol, amino acids, urate, pyruvate, glutamate, alcohol, hydroxybutyrate, to name a few. Advances in nanotechnology are also providing nanometer-scale electrical biosensors based on nanowires and semiconductor nanotubes, in which electrochemical opening occurs from a change in local surface potential due to target binding8'10.
5
10
fifteen
twenty
25
30
35
40
Four. Five
fifty
Among mechanical biosensors, the quartz crystal microbalance has become one of the most established techniques11'13. These devices are based on quartz crystal resonators (such as those used in watches), which are piezoelectric and thus allow direct measurement of crystal deformation by electrical procedures. In these devices, the resonance frequency is measured and related to the change in mass induced by the binding of the analyte to the recognition layer immobilized on the crystalline surface. A subclass of mechanical biosensors is called nanomechanical biosensors, which make the most of the nanometer scale size of at least one of its dimensions14-20.
Among the existing procedures, the most satisfactory biosensors in the biomedical field include endpoint detection bioassays such as ELISA. ELISAs are essential tools in the biomedical field due to their good sensitivity, simplicity of the assay, reliability and high performance.
On the other hand, devices such as lateral flow tests are of the utmost importance in the short time required for analysis and have been satisfactorily miniaturized and simplified to the point that even home testing is possible. However, the lowest analyte concentration they can detect is commonly up to 0.1jM, which is not good enough to detect many targets of biological importance. By comparison, ELISA requires a much longer analysis time (~ 1 h), but offers much better concentration sensitivity (~ 1 pM).
The biodetection technique that can combine excellent sensitivity and specificity with short analysis time, together with miniaturization potential, is still under investigation. In particular, there is a high demand for techniques that can be integrated into a point of care device that is worthy of sensitivity, quantification capacity and good dynamic range. To date, no technique has been demonstrated to provide this. The ability to be integrated into a point of care (POC) device means that detection protocols must be simple, use small sample volumes and do not require complicated preparation or / or complex chemical washing steps to prepare samples and / or detection devices. A low cost for complete analyzes and long storage stability is also a requirement to obtain a commercially viable product.
Biosensors based on nanoparticles
There are approaches in the prior art that have been successful in many, but not all, of the challenges cited for POC devices. The use of nanoparticles (NP) has taken its part in this success. Particularly, gold and other noble metal nanoparticles have been used in the detection of analytes. The localized surface plasmon resonance (LSPR) in gold NP shifts when the surrounding dielectric constant changes, so that shifts in the spectral peak of LSPR facilitated by the binding of biomolecules provide a procedure for the detection of analytes in samples clinics Different detection approaches that make use of this phenomenon on a nanometric scale are reviewed in reference 21.
In a satisfactory approach, called plasmonic ELISA, the localized plasmon resonance shift facilitated by the aggregation of gold nanoparticles is used to color the detection mark of very low concentrations of an analyte of interest. In reference 22, both PSA and the p24 antigen of the HIV1 capsid are detected at concentrations of only 1 x 10-18 g / ml. In this procedure, the biocatalytic cycle of an enzyme generates colored NP solutions due to the fact that when the concentration of hydrogen peroxide decreases aggregate NPs are formed. The binding of the analyte promotes the aggregation of NP which in turn gives the solution a blue color. This color change is used as a detection signal that can even be followed with the naked eye and thus provides a
3
5
10
fifteen
twenty
25
30
35
40
Four. Five
fifty
low cost detection approach.
In another relevant methodology, the labeling of NP with various DNA sequences provides the multiplexing capability that metallic NPs would not have alone, since they lack a range of color marks to mark each specific reaction. The so-called bar biocode procedure has not only been used for DNA detection, but has also successfully treated protein detection. Later, the bar biocode is based on magnetic microparticle probes with antibodies that specifically bind to a target of interest, for example, a clinically relevant protein as a specific prosthetic antigen (PSA) (see reference 23) and nanoparticle probes which are encoded with DNA that is unique to the target protein of interest and antibodies that can match the target captured by the microparticle probes. The magnetic separation of the complexed and target probes, followed by the dehybridization of the oligonucleotides on the surface of the nanoparticle probe, allows the determination of the presence of the target protein that identifies the oligonucleotide sequence released from the nanoparticle probe. Because the nanoparticle probe carries a large number of oligonucleotides for the protein binding event, there is substantial signal amplification and the target protein can be detected at low concentrations (atomolar concentration). Alternatively, a polymerase chain reaction (PCR) in oligonucleotide barcodes can enhance sensitivity to 3 atomolar. Comparable clinically accepted conventional trials have sensitivity limits of 3 picomolar, six orders of magnitude less sensitive to that observed with this procedure23. A limitation of this technique is the required analysis time, up to 100 minutes, given the need to separate the complex and target probes from the sample solution and subsequent identification of the DNA tags. With this procedure quantification is also possible. One approach is to perform a PCR and / or gel electrophoresis, but these are procedures not suitable for point of care applications and exclude rapid analysis as discussed in reference 25.
An alternative detection procedure is based on the spectral change in the scattered light when at least two NPs get close to each other26,27. The color change is due to a shift in the surface plasmon resonance of the Au nanoparticles when at least two NPs get close to each other. This produces a color shift and a change in the intensity of collected light that can be measured optically. NP probe complexes always comprise two or more nanoparticles bound to a specific target analyte, this has been called a light scattering complex. This has the advantage that only NP aggregates, which contain the analyte, are detected. Non-aggregated particles, which include those that do not contain the target analyte, are not detected in this procedure. This allows the detection of NP aggregates in the presence of a significant excess of non-aggregated particles. This procedure has demonstrated excellent sensitivity, better than 10 femtomols of an oligonucleotide. Within this procedure, the use of evanescent lighting by means of a support waveguide and dispersion-based colorimetric detection has proven to be 4 orders of magnitude better than the absorbance-based spot tests (EP1639370).
One way to eliminate the need for PCR amplification while maintaining a good multiplexing capacity is to hybridize the GNP dispersion complexes on a solid support functionalized with known sequences at defined positions, as is done in fluorescent matrices. The subsequent scan of the scattered light serves as a biosensor signal and the multiplexing capacity is obtained by the predefined positions of the known immobilized sequences. Normally, a way to amplify this optical signal is needed. A procedure for scaling the scattered light signal of the NP marks is the reduction of silver promoted by nanoparticles28 or colorimetric response by enzymatic catalysis on optically coated silicon substrates29. This procedure is used to amplify the optical signal and also allows quantifying the amount
4
5
10
fifteen
twenty
25
30
35
40
Four. Five
fifty
of analyte in the sample 30.
Biosensors based on nanomechanical resonators
Nanomechanical resonators have demonstrated unprecedented detection limits in the detection of masses of atoms and molecules under vacuum. The mass detection limits have recently been pushed to the range of yoctograms, that is, the mass of a single proton can be measured. Two components are essential to achieve mass sensitivity: devices with nanometric scale dimensions and high quality factors (1000-100000) that involve vacuum measurements. However, the detection of biomolecules should ideally be carried out in aqueous solutions, the natural environment in which biological processes occur. Nanomechanical resonators in liquids have a very low quality factor (1-10) as a result of viscous damping. In addition, the liquid is dragged along with the nanomechanical resonator, increases its effective mass and thus reduces sensitivity. The miniaturization of devices at the nanometric scale does not improve these limitations. And, more importantly, biological detection requires many repetitive measurements that can only be achieved with disposable and cost-effective devices that can be both easily manipulated and measured. These requirements are satisfied by micro-lever matrices that are commercially available, but not by nanometer-scale mechanical resonators of the state of the matter that are still manufactured at low speed by nanofabrication techniques and are highly irreproducible in dimensions and mechanical response. In addition, the measurement of the resonant frequency of these devices in liquid is scientifically and technically demanding. These limitations have limited the success of nanomechanical resonators as biological sensors.
Nanomechanical resonators with mass marks.
Nanomechanical resonators have made use of NP to amplify the signal, here, the greater mass bonding provided by the marks increases the mechanical response of the sensor. Here, a reduction in the resonance frequency is related to the added mass of the analyte-NP complex that binds to the resonator. Although dynamic nanomechanical sensors have shown good performance without marks; marking greatly improves specificity and can reduce the detection limit. It has been shown that the marking of samples for nanomechanical detection is advantageous in endpoint tests. Craighead et al. Demonstrated in reference 31 that the labeling of a monoclonal antibody with nanoparticles in a sandwich immunoassay could improve the detection limit by three orders of magnitude to reach 2 ng / ml in the detection of prion proteins and even detect the presence 50 fg / ml PSA enriched in a background noise of fetal bovine serum. The technique is also quantitative, since the authors found a clear linear dependence of the frequency response on the PSA concentration. The ability to detect fM concentrations of a target protein in realistic background noise puts the marked resonant lever sensors in an excellent position to compete with all the innovative techniques mentioned, in addition to the most established technologies. Still, nanomechanical resonators are not yet widely used in the clinic. This is because they lack the necessary robustness in the response. The few studies that show a statistically significant number of tests show that the number of false positives and negatives is still too high. The frequency offset commonly used as a detection signal in these sensors depends largely on the non-specific adsorption on the surface of the device.
A key limitation of nanomechanical resonators is non-specific adsorption. The definitive detection limits predicted by theoretical approaches may be far from the actual detection limits when nanomechanical biosensors functionalized with bioreceptors are immersed in complex solutions, such as serum, to detect the presence of biomarkers in real time or ex-situ. In this situation, other molecules to
5
10
fifteen
twenty
25
30
35
40
Four. Five
fifty
much higher concentration, even billions of times greater, are present in the solution. Although these molecules have much lower affinity for sensors grafted receptors, their high concentration imposes the actual detection limit. For example, cancer biomarkers are in blood plasma at a concentration in the range of 1 ng / ml, while the concentration of unwanted proteins is approximately 70 mg / ml. The sensitivity to achieve the detection of cancer biomarkers is satisfied by most nanomechanical biosensors. However, the selectivity that determines the rate of false positives and false negatives has received little attention. The detection of cancer biomarkers in complex media such as serum requires selectivity greater than 1 part per million.
Theoretical predictions indicate that the selectivity required for the detection of biomarkers in complex media can be achieved by functionalizing the sensors with a high surface density of receptors32. This prediction is in agreement with the findings in nanomechanical biosensors based on surface tension, in which the best results are obtained at high densities of receptor packaging. A second theoretical prediction is that the stage of additional intermediate surface passivation by small inert molecules after the incubation of the receptor could significantly reduce the bioincrustation and help to achieve better selectivity. Interestingly, the size and geometry of the blocking molecule used to refill the gaps in the sensor surface plays a critical role. This is in agreement with the results of recent statistical analyzes of the effect of immunoreactions on the response of nanomechanical biosensors in static mode33. The study included 1012 levers with different antibody surface densities, two blocking strategies based on polyethylene glycol (PEG) and bovine serum albumin (BSA), rigorous controls with non-specific antibodies and small proteins such as lysozymes. The study revealed that the assay performance critically depends on both the surface density of antibodies and blocking strategies. They found that optimal conditions involve surface densities of antibodies close to, but lower, than saturation and blocking with PEG.
In addition, other practical approaches have been proposed to minimize non-specific adsorption and enhance selectivity. The use of nanomechanical element matrices with an internal reference helps to reject common noise sources, which include non-specific adsorption. Another approach is the implementation of the sandwich assays traditionally used in ELISA. In this assay, the nanomechanical system is functionalized with a specific molecular receptor for the biomarker of interest. After exposure of the nanomechanical system to the sample, the device is incubated with secondary receptors attached to a molecule or a material that acts as a signal amplifier, such as a nanoparticle to increase the effect of the mass. The use of two different receivers greatly enhances sensitivity and specificity. This approach was applied to detect prion proteins with nanomechanical resonator, which in conformationally altered forms are known to produce neurodegenerative diseases in animals, in addition to humans34. The resonance frequency was detected ex-situ in high vacuum. For direct incubation of the nanomechanical resonators functionalized with a primary antibody against the prion protein, the detection limit was approximately 20 pg / ml. When the resonators were subjected to a subsequent incubation step with secondary antibodies that bind, the detection limit was potentiated 3 orders of magnitude, being approximately 2 ng / ml.
A second promising strategy that maintains the unmarked characteristic of nanomechanical biosensors is to implement microfluidics for purification and preconcentration of samples. The potential of this approach has been demonstrated with non-branded nanowire nanosensors. In this work, a microfluidic purification chip simultaneously captures multiple biomarkers of blood samples and releases them, after washing, in purified buffer for detection by nanosensors8. This two-stage approach isolates the detector from the complex whole blood environment, and reduces its sensitivity
6
5
10
fifteen
twenty
25
30
35
40
Four. Five
Minimum required to effectively pre-concentrate biomarkers. The authors demonstrated quantitative and specific detection of two model cancer antigens from a 10 ml sample of whole blood in less than 20 min.
Although nanotechnology has provided biosensors with unpredictable levels of sensitivity without the need for marking, nanosensors have also shown significant difficulties in issues related to specificity and reproducibility, and hence are not yet ready for the selection of biomarkers in blood . This arises from the extreme difficulty of ‘finding’ low-abundance protein biomarkers in a ‘haystack of plasma proteins, some of them at concentrations at least seven orders of magnitude higher (approx. 40 mg / ml albumin). Thus, the situation is that the high biological noise set by non-specific interactions greatly exceeds the intrinsic noise of most existing nanosensors. In short, the problem is not sensitivity, but:
• Specificity; to discriminate traces of biomarkers in the complex mixture of blood proteins.
• Reliability, to minimize painful false positives and false negatives in the diagnosis of patients.
Now, the authors of the present invention have found a system for biodetection applications that allows ultra-low detection limits as it discriminates concentrations at the edge of 10 ag / ml. In addition, the system allows the detection of target analytes in complex biological background noises such as blood samples, without the need for any purification stage. The invention is based on a sandwich-type optical test that takes advantage of the surprising and unexpected enhancement of the plasmonic effect caused in the nanoparticles by the combination of the particular nature and design of the substrate used in the biosensor and the particular nature and dimensions of the nano particle. . This system can be adapted in a nanomechanical device in order to analyze both optoplasmonic and mechanical signals so as to improve detection reliability. The robustness of this dual biosensor leads to an extremely low false positive and false negative rate, «2 x 10" 4 at an ultra low concentration of 100 ag / ml, thus providing an excellent solution to be integrated into a POC device.
DESCRIPTION OF THE INVENTION
The following definitions are intended to help in the understanding and interpretation of the present invention:
Biosensor: Analytical device comprising a biological recognition element (for example, enzyme, receptor, DNA, antibody, or microorganism) in intimate contact with a transducer of electrochemical, mechanical, optical, thermal, acoustic or other physical signals that together allow the analysis of chemical properties or detection or quantification of target analytes.
Dielectric material: A dielectric material is an electrical insulator that can be polarized by an applied electric field.
Functionalized surface or surface functionalization: A procedure or technique to introduce chemical functional groups into a surface. This is used in biosensors to immobilize a recognition element on a surface, in the present invention on the surface of the substrate.
Recognition element: It is the element of the immobilized system that functionalizes the surface of the substrate that can specifically recognize and bind to the target analyte. The recognition element may be selected from, but not limited to, an antibody, a receptor, a peptide, a protein, a carbohydrate, a nucleic acid, a cell, a
7
5
10
fifteen
twenty
25
30
35
40
microorganism or a part thereof.
Detection element: It is the element of the system attached to the nanoparticle and that can specifically recognize and bind to the target analyte. The detection element together with the nanoparticle allow the detection of the target analyte when it is present in the sample.
Target analyte: It is the element sought for detection and / or quantification. It can be of any nature such as organic or inorganic molecules (drugs, hormones, cholesterol, etc.), biological molecules (peptides or proteins, nucleic acid molecules, growth factors, biomarkers etc.), cells (protozoic cells, bacterial cells , fungal cell, eukaryotic cells) or cell fragments (bacterial walls, cellular organelles such as mitochondria, cell vesicles, etc.) or viruses.
Extinction coefficient: The extinction coefficient is the imaginary part of the complex index of refraction.
Refractive index: The refractive index of a substance (optical medium) is a dimensionless number that describes how light, or any other radiation, propagates through that medium.
Surrounding material: It is the material underlying both surfaces of the substrate in the system of the invention. The refractive index of the surrounding material is relevant in achieving the enhanced plasmonic effect.
Plasmonic effect: It is the phenomenon produced in nanoparticles that have plasmonic properties when irradiated with an appropriate electromagnetic radiation. The plasmonic effect is produced by the oscillations of free electrons induced in a metal by an electromagnetic wave.
Antibody: A Y-shaped protein (immunoglobulin) on the surface of B lymphocytes that is secreted in the blood or lymph in response to an antigenic stimulus, such as a bacterium, virus, parasite or transplanted organ, and that neutralizes the antigen by binding specifically to him. The detection of antibody-antigen pair formation can be followed by several procedures and is the basis of many biosensors.
Receiver: It is a biological structure that can detect chemical stimuli from its surroundings. Receptors are normally present on the cell surface and are adapted to detect a particular type of molecule that is responsible for inducing a response in the cell once in contact with the receptor.
Peptide: Short chains of amino acid monomers linked by peptide bonds.
Carbohydrate: Refers in the context of the invention to complex oligosaccharide or polysaccharide molecules that have the ability to bind specific targets. As an example, lipopolysaccharide can be cited.
Nucleic acid: Any polymeric or oligomeric molecule that has a skeleton that contains a sequence of nitrogen bases - adenine (A), thymine (T), cytosine (C) and guanine (G). In the context of the present invention, nucleic acid molecules include, among others, DNA molecules, RNA molecules, aptamers or PNA molecules.
Plasmonic metamaterial nanoparticle: It is a nanoparticle made of an artificial material manipulated to manifest plasmonic properties.
Transmittance: Transmittance is the fraction of incident light (electromagnetic radiation) at a specified wavelength that passes through a sample.
5
10
fifteen
twenty
25
30
35
40
Reflectance: Reflectivity or reflectance is the fraction of incident electromagnetic power that is reflected from a separation surface.
Detection: It is the action of identifying the presence or absence of the target analyte in the sample.
Quantification: It is the action of determining the concentration of a target analyte within the sample.
Sample: A preparation of a biological fluid that is normally to be analyzed in liquid form although it is also possible as a solid form to be resolved in a liquid or reconstitutable form.
Electromagnetic radiation: Electromagnetic radiation is a fundamental phenomenon of electromagnetism, behaving like waves that propagate through space and carry radiant energy. An electromagnetic wave has both electric and magnetic field components, which oscillate in a fixed relationship with each other, perpendicular to each other and perpendicular to the direction of energy and wave propagation.
Dispersion of light: The dispersion of light is a type of interaction between matter and an electromagnetic wave. When a wave that propagates is incident on a surface, the reflected wave is normally concentrated in the specular direction as determined by the well-known laws of reflection. In addition to specular reflection there is also a diffuse component that is irradiated over a wide range of angles centered on the specular beam that is commonly known as light scattering. The dispersion processes can be produced from the non-zero roughness of the surface or by the presence of small particles deposited on it.
Absorption: The absorption of electromagnetic radiation is the way in which the energy of an electromagnetic radiation is collected by matter, usually the electrons of an atom. Thus, electromagnetic energy is transformed into internal energy of the absorber, for example, thermal energy.
Extinction signal: The term "extinction" means the loss of light in a transmitted optical beam when it passes through a medium or object. Two different mechanisms contribute to extinction: absorption and dispersion.
A first objective of the invention is a system for biodetection applications comprising:
to. a substrate of dielectric material having at least one functionalized surface with a recognition element that can specifically bind to a target analyte and
b. at least one nanoparticle with plasmonic properties comprising at least one detection element attached thereto and which can be specifically bound to the target analyte in a sandwich type arrangement,
characterized in that:
- the substrate of dielectric material has a thickness between 0.1 pm and 5 pm and an extinction coefficient of less than 0.3,
- the nanoparticle has at least one of its dimensions with a size of 2 nm to 300 nm and
- because the ratio between the refractive index of the dielectric material and the surrounding material is greater than 1.1.
5
10
fifteen
twenty
25
30
35
40
Four. Five
fifty
The system of the invention is adapted for sandwich detection and quantification procedures (see, for example, Figure 1). The use of a recognition element and a detection element is a first aspect that greatly improves the sensitivity and specificity of the system. However, the most surprising and advantageous aspect of the system of the invention derives from the potentiated plasmonic effect that can be achieved in optoplasmonic detections. This particular effect allows ultra-low detection limits. The effect is a hybrid plasmonic mode that results from the combination of the particular nature and design of elements that make up the system, specifically the substrate and the nanoparticle.
The substrate has to be a dielectric material so that the phenomenon of surface plasmon resonance can take place. Any dielectric material in the electromagnetic spectral range of interest is suitable in the system of the invention. The only condition is that its extinction coefficient must be less than 0.3. In a particular embodiment, the dielectric material is quartz, silicon, silicon nitride, silicon carbide, graphene, polymers such as photoresist, for example SU8, and hydrogels such as mixtures of PEG and PLA or DEXTRANO and PEG. The most preferred dielectric materials are silicon or silicon nitride.
Another important aspect of the system of the invention is the design of the substrate. There are two key points in the design of the substrate that have to be fulfilled in order to achieve the enhanced plasmonic effect at the site of the nanoparticle.
The first is that the thickness of the substrate should be between 0.1 pm and 5 pm, more preferably between 0.25 pm and 2 pm. For larger thicknesses, the incident electromagnetic radiation is refracted and cannot produce a multireflector effect within the substrate cavity, which is the physical phenomenon that ultimately contributes to the potentiation of the plasmonic effect (see Figure 2a). In practice, the potentiation of the plasmonic effect is a hybrid mode that results from the coupling of the surface plasmon mode located on the nanoparticles and the optical cavity mode. When the nanoparticle is on the substrate, in addition to backward scattering, multiple pathways help enhance dispersion by a single nanoparticle. One route involves the amplification of direct dispersion by the nanoparticle by multiple reflections. In this mechanism, the coupling between the dipole plasmon resonance of the nanoparticle and the resonances of the optical substrate cavities creates a hybrid mode that reinforces the dispersion signal at the nanoparticle site. In a second route, the non-scattered light undergoes multiple reflections in the optical cavity of the substrate, producing a cascade of scattering interactions at neighboring nanoparticle sites that lead to a higher bulk density of nanoparticles in, for example, a field image Dark.
The relevance of the thickness in the dispersion signal is clearly demonstrated by a particular embodiment of the invention in which the substrate is in the form of a lever with a thickness design between 0.1 pm and 5 pm. A clear difference in the intensity of the dispersion signal can be observed between the chip region in which the thickness is greater than 5 pm and the lever region in which the thickness is between 0.1 pm and 5 pm (see Figure 6a).
The second key point to consider in the design of the system is that the ratio between the refractive index of the dielectric material (substrate) and the surrounding material must be greater than 1.1. This aspect is also essential in achieving the multireflector effect in the substrate cavity. The presence of materials surrounding the substrate that have a different refractive index in the particular ratio greater than 1.1, makes the opposite surfaces of the substrate as mirrors, which allows multireflection within the cavity. The surrounding material may be both in the solution itself in which the substrate is submerged for detection as any surrounding fluid or gases, or a particular surrounding solid material with the sole condition that the refractive index of the surrounding material differs from index of refraction of the substrate.
5
10
fifteen
twenty
25
30
35
40
Four. Five
The system of the invention can in principle be used in any type of biosensor conformation of mechanical resonators. In particular, in the system of the invention, the substrate can be in the form of a micro lever, a micropile, a rope, a trampoline, a rectangular lever, a triangular lever, a pyramid lever, a shovel lever, a membrane, a plate, a bridge, a hollow tube or a nanowire (see, for example, Figure 11).
The target analyte is the element to be detected from the sample, especially from biological samples. The target analyte can be of any nature such as organic or inorganic molecules (drugs, hormones, cholesterol, etc.), biological molecules (peptides or proteins, nucleic acid molecules, growth factors, biomarkers etc.), cells (protozoic cells , bacterial cells, fungal cell, eukaryotic cells) or cell fragments (bacterial walls, cellular organelles such as mitochondria, cell vesicles, etc.) or viruses.
An advantage of the system of the invention is that it allows detecting and quantifying analyses within complex samples, such as, for example, blood or urine samples, without the need for any purification stage or separation stage. This makes the manipulation simpler and reduces the time for detection, which makes the present system very suitable for implementation in POC devices.
The recognition element that functionalizes the surface of the substrate can be any element that can recognize and specifically bind a target analyte. In this sense, the recognition element may be an antibody (a polyclonal or monoclonal antibody), a receptor (a cell surface receptor such as an opioid receptor), a peptide (such as an opioid peptide), a protein (such as lectins), a carbohydrate (such as lipopolysaccharide O antigen), a nucleic acid (a DNA or RNA sequence), a cell (protozoic cells, bacterial cells, fungal cell, eukaryotic cells), a microorganism or a part thereof (such as bacterial walls, cell organelles such as mitochondria, cell vesicles etc.). In a preferred embodiment of the invention, the recognition element is an antibody, more preferably a monoclonal antibody.
The other essential feature of the system, apart from the functionalized substrate, is the nanoparticle. Of course, the nanoparticle must have plasmonic properties. In principle, any type of nanoparticle with plasmonic properties can be used. Thus, the nanoparticle can be, for example, a gold, silver or plasmonic metamaterial nanoparticle such as, but not limited to, titanium nitride and non-stoichiometric oxides such as vanadium, titanium and aluminum.
In addition, the nanoparticle can take a multitude of forms or structures such as, for example, nanospheres, nanovarillas, sharp nanovarillas, nanovainas, nanojaulas / frames, hollow nanospheres, tetrahedra, octahedra, cubes, icosahedrons, rhombic dodecahedrons, concave nanocubes, tetrahexahedrons, bipyramids obtuse triangular, trisohectahedra and nanoprisms (see Figure 12), but it is essential that at least one of its dimensions has a size of 2 nm to 300 nm, preferably 5 nm to 150 nm, because the peak of plasmonic resonance is highly dependent on the size of the nanoparticle.
The nanoparticle comprises at least one detection element attached to it that can specifically bind to the target analyte. The detection element can be any type of element that can be attached to the target analyte, thus, in principle its nature may be the same or similar to that of the recognition element. However, in a preferred embodiment, the detection element is selected from both an antibody and a nucleic acid molecule. The detection element has the function of detecting the presence of the target analyte captured by the recognition element immobilized on the surface of the substrate. Thus, the nanoparticle will only be attached to the substrate by the detection element attached to it if the
5
10
fifteen
twenty
25
30
35
40
Four. Five
target analyte is present in the analyzed sample. In such a case, the recognition element can be attached to the target analyte which is then detected by the detection element in a sandwich arrangement. The absence of the target analyte in the sample has the consequence that the recognition element will not bind to the target analyte and thus no detection by the detection element will occur.
In summary, if the target analyte is present in the sample, even at ultra low concentrations, it can be detected and quantified based on the dispersion intensity or extinction intensity (depending on the measured parameters) produced by the nanoparticles. If the target analyte is not present in the sample, no detectable plasmonic effect will take place on the substrate since no nanoparticles will be present.
The detection and quantification can be done by measuring the intensity of dispersion produced by the nanoparticles when the system is irradiated with electromagnetic radiation. A detectable plasmonic effect will take place by irradiation at any wavelength of the white light spectrum thanks to the amplification of the signal provided by the substrate that meets the design parameters.
If the type of signal measured is the dispersion signal, the measurement is made in reflectance and, in this case, the substrate reflectance index ranges between 0.01 and 1.
Alternatively, detection and quantification can be carried out by measuring the extinction signal of the irradiated nanoparticles with electromagnetic radiation. If the extinction signal is measured, the measurement is made in transmittance and, in such case, the transmittance index of the substrate comprises between 0.01 and 1.
The visualization of the nanoparticles in the system of the invention can be performed by optical means such as a dark field microscope or a cross polarization microscope.
A further aspect of the invention is a biosensor comprising a system according to the invention. The system of the invention is in principle applicable to any type of biosensor on which the system can be arranged.
In a particularly preferred embodiment, the system is arranged in a micro or nanomechanical biosensor so that optomecanoplasmonic signals can be detected and analyzed. This particular type of dual biosensor allows superior reliability, since the biosensor response is only considered positive when both plasmonic and mechanical signals give a positive result. Although the dual biosensor does not improve the detection limit of the optoplasmonic system of the invention alone, it clearly improves the specificity of the assay, thus improving its reliability.
For example, in a particular embodiment, of a dual signal biosensor based on a substrate in the form of a mbro-lever, in which both plasmonic and mechanical signals were measured, it was observed that the error rate for the lower concentrations was smaller in optoplasmonic transduction. For concentrations greater than 1 fg / ml, the error rate of both mechanical and optoplasmonic transduction became comparable, but positively, the combination of mechanical and optoplasmonic signals (optomechanolamic signal) significantly enhanced the confidence of the test that leads to a positive rate. false and negative false extremely low, approximately 2 x 104 at an ultra low concentration of 100 ag / ml of the target analyte (Figure 10).
In a particular embodiment, the biosensor is arranged in the form of a matrix comprising multiple systems according to the invention, each system comprising a substrate designed to detect a different target analyte or different concentrations of the same analyte.
5
10
fifteen
twenty
25
30
35
40
Four. Five
Another aspect of the invention is a method for detecting and / or quantifying a selected target analyte in a sample comprising:
a) contacting a sample with a substrate of dielectric material having a functionalized surface with a recognition element that can be specifically bound to the target analyte, the substrate of dielectric material having a thickness between 0.1 pm and 5 pm and a coefficient of extinction less than 0.3 and the ratio between the refractive index of the dielectric material and the surrounding material being greater than 1.1
b) add to the substrate resulting from a) at least one nanoparticle with plasmonic properties and having at least one of its dimensions with a size of 2 nm to 300 nm, comprising at least one detection element attached thereto and which can be attached specifically to the target analyte, in order to detect the presence of the target analyte bound to the recognition element
c) irradiating the resulting substrate of b) with an electromagnetic radiation in which the presence of the target analyte in the sample produces a plasmonic effect on the nanoparticles amplified by the presence of the substrate that can be detected by optical means,
d) measure the light scattering or intensity of the extinction signal so that it detects the presence or absence of the target analyte in the sample and for quantification thereof.
The process of the invention is based on the use of the sandwich detection system of the invention as explained above.
Stage a) is the recognition stage, in which the sample is contacted with the functionalized surface of the substrate. The substrate surface is designed to detect a particular type of target analyte. Thus, after a suitable incubation time so that the reaction can take place if the target analyte is present in the sample, it will be attached to the recognition element and thus immobilized on the surface.
As explained above, the dielectric material used in the process can be any dielectric material as long as it has an extinction coefficient of less than 0.3. In a particular embodiment, the dielectric material is quartz, silicon, silicon nitride, silicon carbide, graphene, polymers such as photoresists such as SU8 and hydrogels such as mixtures of PEG and PLA or DEXTRANO and PEG. The most preferred dielectric materials are silicon or silicon nitride.
Also as explained above, the recognition element used in the process of the invention can be any element that can specifically recognize and bind to a desired target analyte. In this sense, in a particular embodiment, the recognition element may be an antibody (a polyclonal or monoclonal antibody), a receptor (a cell surface receptor such as an opioid receptor), a peptide (such as a peptide of opiodes), a protein (such as lectins), a carbohydrate (such as lipopolysaccharide O antigen), a nucleic acid (a DNA or RNA sequence), a cell (protozoic cells, bacterial cells, fungal cell, cells eukaryotes), a microorganism or a part thereof (such as bacterial walls, cell organelles such as mitochondria, cell vesicles, etc.). In a preferred embodiment of the invention, the recognition element is an antibody, more preferably a monoclonal antibody.
Step b) of the process of the invention comprises the detection stage. The nanoparticle that acts as a brand for detection and quantification is attached to a detection element that can specifically bind to the target analyte in a position or area
5
10
fifteen
twenty
25
30
35
40
Four. Five
different from the recognition element. If the target analyte is present in the sample, the structure resulting from step a) will be detected by the detection element after a suitable incubation time. Once the detection reaction has taken place, the nanoparticles are immobilized on the surface of the substrate and are in a condition to be detected and / or quantified based on their plasmonic properties.
The detection element attached to the nanoparticle used in the context of the process can be any type of element that can bind to the target analyte, thus, in principle its nature may be the same or similar to that of the recognition element. However, in a preferred embodiment, the detection element is selected from both an antibody and a nucleic acid molecule.
Also as explained above, the type of nanoparticle used in the process of the invention can be any nanoparticle that has plasmonic properties. In this sense, the nanoparticle can be a nanoparticle of gold, silver or plasmonic metamaterial. With respect to the shape, the nanoparticle can adopt any structure such as nanospheres, nanovarillas, sharp nanovarillas, nanovainas, nanojaulas / frames, hollow nanospheres, tetrahedra, octahedra, cubes, icosahedrons, rhombic dodecahedrons, concave nanocubes, tetrahexahedrons, obtuse triangular bipyramids trisohectahedrons and nanoprisms as long as one of its dimensions is 2 nm to 300 nm in size.
Step c) comprises irradiation of the substrate surface with electromagnetic radiation so as to reveal the presence or absence of the nanoparticle in the substrate. The electromagnetic radiation incident on the substrate resulting from step b) will reveal whether or not the sample contains the target analyte. If the target analyte is present in the sample, the incident electromagnetic radiation will produce a plasmonic effect on the nanoparticle that will be greatly enhanced by the particular phenomena that take place within the substrate cavity due to its particular design. As explained above, the enhanced plasmonic effect produced when the nanoparticles are present in the substrate is a hybrid mode that results from the coupling of the surface plasmon mode located on the nanoparticles and the optical cavity mode.
The last stage of the process of the invention, step d), comprises measuring the light scattering or intensity of the extinction signal so that the presence or absence of the target analyte in the sample is detected and for quantification thereof. Measurements can be made by optical devices or means adapted for such a task as a dark field microscope or a cross polarization microscope.
Quantification can be done based on the intensity of the light scattering signal or the intensity of the light extinction signal. The intensity of the measured signal can be related to an unknown analyte concentration by comparison with a calibration curve obtained from samples with previously known concentrations of an analyte.
The process of the invention can be designed to measure the enhanced plasmonic effect on nanoparticles in reflectance or transmittance.
If the measurement is made in reflectance, then the intensity of the dispersion signal is measured and thus the substrate of dielectric material must have a reflectance index between 0.01 and 1.
Alternatively, if the measurement is made in transmittance, then the intensity of the extinction signal is measured and thus the substrate of dielectric material must have a transmittance index between 0.01 and 1.
The process of the present invention allows ultra-low detection limits as it discriminates concentrations at the edge of 10 ag / ml and has the advantage that it allows detection
14
5
10
fifteen
twenty
25
30
35
40
Four. Five
of target analytes in complex biological samples such as blood or urine samples without the need for any prior preparation or purification of the sample.
In a particularly preferred embodiment, the process of the invention is performed in a micromechanical system whereby the substrate of dielectric material is arranged as a mechanical element that can undergo a change in at least one mechanical characteristic when the target analyte is present in the sample, and when the following additional steps are performed:
e) measure the at least one mechanical characteristic in the mechanical element so that it detects the presence or absence of the target analyte in the sample,
f) combine the optical data obtained in stage d) with mechanical data of stage e) in order to improve the reliability of the detection procedure.
The inventors have found that in this particularly preferred embodiment, the process of the invention, although it does not improve the detection limit dramatically, improves the reliability of the procedure when compared to the procedure based solely on the optoplasmonic effect. The process of the invention in this particularly preferred embodiment leads to a very low rate of false positives and false negatives. The superior reliability is explained because the result of the procedure is only considered when both the plasmonic and the mechanical signals give a positive result.
In this particular embodiment, the substrate of dielectric material that is essential in the present invention due to its optical properties is also arranged to act as a mechanical element that can undergo a change in at least one mechanical characteristic when the target analyte is present in the sample. . This change in a mechanical characteristic can be measured so that a mechanical signal is obtained, in addition to the optoplasmonic signal. The presence of the nanoparticle when the target analyte is present in the sample also produces an amplified mechanical signal due to the greater mass provided by the nanoparticle.
The mechanical element may be in the form of a micro lever, a micropile, a string resonator, a trampoline resonator, a rectangular lever, a triangular lever, a pyramid lever, a blade lever, a membrane resonator, a plate resonator , a bridge, a hollow lever or a nanowire. In a particularly preferred embodiment, the substrate is arranged to act as a mechanical element in the form of a micro lever.
In addition, a change of any mechanical characteristic of the mechanical element can be measured in order to detect the presence of the target analyte in the sample. The change in the detected mechanical characteristic can be selected, but not limited to, the position of a portion of the mechanical element, the vibration characteristic of the mechanical element, such as the vibration phase of the mechanical element, the frequency of the vibration of the element. mechanical, the amplitude of the vibration of the mechanical element or the surface tension on a portion of the mechanical element or the dissipation changes of the mechanical element.
The combination of the optical data obtained in step d) with the mechanical data of step e) of the present process provides improved process reliability.
Finally, another object of the invention is a device that can detect the enhanced optoplasmonic effect of the nanoparticles by means of the system of the invention or combine the detection of such an optoplasmonic effect with the analysis of changes in the mechanical characteristics in the substrate.
More precisely, the device for surface inspection arranged to detect the effect
5
10
fifteen
twenty
25
30
35
40
Four. Five
Optoplasmonic in at least one nanoparticle of a system according to steps c) and d) of the process of the invention comprises:
- a source of electromagnetic radiation arranged to generate at least one beam of electromagnetic radiation;
- a first sensitive detector such as a dark field microscope or a cross polarization microscope arranged to receive electromagnetic radiation when reflected or transmitted through the substrate to produce at least a first output signal in response to dispersion and / or the extinction of said electromagnetic radiation;
- an electronic control system;
Additionally, in order to perform steps e) and f) of the process of the invention, in which changes in mechanical characteristics are measured when the target analyte is present in the sample, the device also comprises:
- a subsystem for detecting a change in a mechanical characteristic in the substrate, said subsystem comprising a second sensitive detector arranged to detect a mechanical change in the substrate to produce at least a second signal in response to said mechanical change, namely:
or a lighting light or laser beam and a linear position sensitive photodetector (PSD) to record the change in the mechanical characteristic on the substrate
or an electronic control system;
or scanning means for the relative displacement of said light or laser beam with respect to the substrate so that the substrate is swept with the light beam following instructions of the electronic control system.
Y
- means for producing a final output signal based on the combination of the first and second output signals of the first and second sensitive detectors.
BRIEF DESCRIPTION OF THE FIGURES
Figure 1: Schematic representation of the sandwich assay on the substrate in the form of a lever, (a) The lever is functionalized with capture antibodies. The functionalization comprises silanization, antibody binding on the upper surface of the lever and blocking with polyethylene glycol to minimize non-specific interactions on the lower surface of the lever and gaps between the antibodies, (b) The lever is then immersed in the serum sample to bind the biomarker protein, if present, by immunoreaction with the capture antibodies (recognition element), (c) Finally, the immunoreactions are revealed by exposing the lever to a primary antibody (detection element) that is bound to a 100 nm diameter gold nanoparticle that recognizes a specific free region of the captured biomarker.
Figure 2: Plasmonic detection of the CEA protein biomarker on the optical microcavity of the lever, (a) Schemes illustrating the different routes for the generation of the optical signal on the lever by multiple internal reflections, (b) Dispersion spectra of the assay of sandwich in the chip and lever regions for the CEA detection test The dispersion is normalized to that of the silicon chip. The coupling between the dipole plasmonic modes and the individual modes of the lever microcavity leads to a double effect, first the plasmon-assisted dispersion is enhanced by the optical lever cavity by almost an order of magnitude, and second, the spectrum Plasmon nanoparticles are discretized by the modes of optical cavity of the lever.
5
10
fifteen
twenty
25
30
35
40
Four. Five
fifty
Figure 3: Schemes of the optical beam deflection procedure to measure the vibration of the lever. A laser beam focuses on the region of the free end of the lever. The deflection of the reflected beam due to the vibration of the lever is measured by a linear position sensitive photodetector (PSD). A frequency generator sweeps the frequency by exciting a piezoelectric actuator located below the base of the lever matrix. The amplitude of vibration versus frequency is adjusted to the harmonic oscillator model to derive the resonance frequency and the quality factor of the lever.
Figure 4: Scanning electron microscope (SEM) images of a region of the lever that meets the design that leads to the enhanced plasmonic effect (surface of the micro lever) and chip that has dimensions that do not lead to the enhanced plasmonic effect, both after sandwich assay in a control experiment as in a 1 pg / ml detection assay of serum CEA. The surface of the lever and the surface of the chip show the same average amount of nanoparticles.
Figure 5: Density of nanoparticles on the micro-levers and chip in buffer measured with a scanning electron microscope and using a signal-based contrast algorithm implemented in Matlab software.
Figure 6: Plasmonic detection of the CEA protein biomarker (a) Darkfield optical images of the lever after the recognition stage with the antibodies bound to the nanoparticles for a rigorous control experiment and for the CEA detection assay with a 1 pg / ml sample in phosphate buffered saline. The dispersion signal is insignificant in the control experiment, while it is significantly higher in the micro lever region in the detection assay. The micro lever acts as an optical cavity while the dispersion in the chip's pre-pinning region is low, and cannot be used to discriminate the presence of CEA in the sample, (b) Medium dispersion signal in the micro lever and the chip in front of the CEA concentration in buffer and serum. The signal is obtained from a quick inspection of the levers with a simple commercial optical microscope and dark field objective with low magnification. The lever data is compared with the chip data to evaluate the effect of the optical lever cavity. The dispersion for the control experiments in the lever and chip regions are represented as discontinuous regions representing the standard deviation of the data.
Figure 7: (a) Dispersion spectra of the effect of the nanoparticles that join on the chip that have dimensions that do not lead to the enhanced plasmonic effect, and lever regions that meet the design that leads to the enhanced plasmonic effect. The dispersion is normalized to that of a raw silicon chip. The box illustrates the different routes for generating the signal scattered on the lever by means of multiple internal reflections (also represented in Figure 2.) (b) Schemes of the effect of nanoparticle mass loading on the lever's resonance frequency . The resulting reduction in the resonance frequency is proportional to the mass increase.
Figure 8: Resonance of nanoparticle plasmons and optical lever cavity, (a) The gold nanoparticles used in the sandwich assay characterize plasmon resonances associated with collective electron oscillations in the nanoparticle. These resonances give rise to enhanced dispersion and absorption close to the optical resonance frequency, (b) Dark field optical image of a single 100 nm diameter nanoparticle after performing a sandwich test on a silicon substrate. The gold nanoparticle presents the well-known Airy pattern due to the diffraction of light.
(c) Dispersion spectra collected from an area of 20 x 20 pm2 with a single nanoparticle.
(d) Scanning electron microscopy image showing the border between the chip, 6 pm thick, and the lever, 1 pm thick. The thickness of the lever means that the light can bounce effectively multiple times between the opposite sides of the lever that lead to an enhancement of the optical reflectivity at wavelengths at which they occur
5
10
fifteen
twenty
25
30
35
40
Four. Five
fifty
constructive interference and, instead, a suppression of reflectivity for wavelengths in which destructive interference occurs. (e) Bright-field images of the lever and chip regions showing the modulation of the reflectivity of the lever with the illumination wavelength in the region of the visible spectrum. The modulation of the reflectivity of the chip is insignificant. (f) Relative reflectivity in the lever with respect to the chip.
Figure 9: Biomarker of the CEA protein for mechanical detection. (a) Frequency of mechanical resonance of a silicon lever before and after the recognition stage with antibodies bound to nanoparticles for a control experiment and for a CEA detection assay (1 pg / ml in PBS). The measurements were carried out in air at room temperature. The fundamental resonance frequency and the quality factors of the uncoated levers were 4.8 ± 0.5 kHz and 5.5 ± 0.5, respectively. (b) Relative displacement of the resonance frequency of the fundamental vibration mode versus the biomarker concentration in buffer and serum samples (red symbols). The lines are a guide for the eyes. The frequency shifts measured in buffer solution are compared with the predicted theoretical frequency shift of the nanoparticle distribution on the lever obtained by scanning electron microscopy. The good agreement confirms that the frequency shift occurs from the mass loading of nanoparticles. The frequency offset for control experiments is represented as a discontinuous region that represents the standard deviation of the data.
Figure 10: (a) DET curves for a concentration of 10 fg / ml using nanomechanical and plasmonic signals and an optimal linear combination of them. (b) False negative rate versus false positive rate for each transduction mechanism and for a hybrid procedure that uses an optimal linear combination of scattering and mechanical resonance frequency offset signals. The colors indicate the target concentration.
Figure 11: Examples of different forms for the substrate of the system (a) commercial micro-levers, (b) micropilar resonators, (c) chord resonator, (d) trampoline resonators, (e) rectangular, triangular and blade levers, (f) membrane resonators, (g) plate resonators, (h) SEM image of a hollow lever and schematic representation, (i) nano-wire.
Figure 12: Gold nanoparticles of different size and shape useful in the system of the invention. Small (a) and large (b) nanospheres, (c) nanovarillas, (d) sharp nanovarillas,
(e) nanovains, (f) nanocages / frames, (g) hollow nanospheres, (h) tetrahedra / octahedra / cubes / icosahedra, (i) rhombic dodecahedra, (j) octahedra, (k) concave nanocubes, (l) tetrahexahedrons , (m) rhombic dodecahedra, (n) obtuse triangular bipyramids, (or) trisoctahedra and (p) nanoprisms.
DESCRIPTION OF A PREFERRED EMBODIMENT OF THE INVENTION
As a proof of concept experiment to support the invention, a sandwich immunoassay was performed for the detection of a cancer biomarker. Carcinoembryonic antigen (CEA) detection was chosen as the model. First, a biofunctionalization procedure was applied to levers with optimum recognition efficiency and ultra-low embedding capacity33 (see Figure 1a). The silicon levers were 500 gm long, 100 gm wide and 1 gm thick. This biofunctionalization occurs to immobilize the receptor layer that recognizes and traps the cancer biomarker. After that, the biofunctionalized lever was immersed in the liquid sample for a certain period of time and fixed temperature to allow binding of the biomarker chosen as target to the capture antibodies immobilized on the surface of the lever (see Figure 1b) . After rigorous rinsing, the lever was exposed to a solution containing the detection antibody bound to the nanoparticle that it recognized and bound to a region
18
5
10
fifteen
twenty
25
30
35
40
Four. Five
specific for the surface captured biomarker (see Figure 1c); here also the ideal time and temperature for the second recognition was determined. Basically, a sandwich test was carried out that involves two stages of recognition to enhance selectivity and amplify the sensor response. The detection antibody was bound to a 100 nm diameter gold nanoparticle that converted and amplified the biorecognition product into two detectable physical signals: (i) an increase in mass and (ii) an increase in light scattering due to the plasmonic properties of the nanoparticle (see Figure 7a and 7b).
For these experiments, the detailed protocol for immobilization of the capture antibody, biomarker detection and the sandwich assay was applied as described below.
Antibody conjugation with spherical gold nanoparticles of carboxyl polymer
The primary antibody, mouse monoclonal anti-carcinoembryonic antigen 3C1 (MAb3C1), was immobilized on the surface of spherical gold nanoparticles of 100 nm diameter carboxyl polymer following the procedure provided by Nanopartz ™. The sample was stored in the refrigerator at 4 ° C until use.
Functionalization of the lever and activation of the carboxyl groups on the surface
Before surface functionalization, the lever matrices were cleaned with piranha solution (3H2S04: 1 H202) (be careful: the piranha solution is extremely corrosive, reactive and potentially explosive) for 15 minutes at room temperature (TA). The levers were rinsed three times with Milli-Q water and dried under a stream of nitrogen. The levers were immersed in a 0.2% solution of (3-glycidyloxypropyl) trimethoxysilane in dry toluene overnight at room temperature. After that, the samples were washed with toluene, Milli-Q water and dried under N2. A solution of 100 mM NTA in 50 mM carbonate buffer at pH 9.5 was prepared and the levers were incubated overnight at 25 ° C under gentle agitation. Then, the levers were rinsed with 50 mM carbonate buffer at pH 9.5, Milli-Q water and dried under N2. The carboxyl groups on the lever surface were activated by immersion in a mixed solution of 100 mM EDC and 150 mM sulfo-NHS, both dissolved in 10 mM MES at pH 5.5. The levers were incubated for 45 minutes at 37 ° C under gentle agitation. The samples were rinsed thoroughly with 10 mM MONTH.
Covalent and oriented immobilization of the capture and control antibodies on the lever
Just after the surface activation stage, the immobilization of the antibody was performed only on the upper side of the levers. A 50pg / ml solution of the capture antibody, mouse monoclonal anti-carcinoembryonic antigen 3C6 (MAb3C6), was prepared in 10 µM MES at pH 5.5. The levers were incubated for 2 hours at 37 ° C. After that, the samples were washed with 10 mM MES at pH 5.5 and incubated for 45 minutes at 37 ° C with 10mMapH8.0 sodium phosphate buffer with 0.3 M NaCI to desorb antibodies that were not covalently bound to the surface. For control experiments, rabbit-produced anti-peroxidase antibody (anti-HRP) was immobilized on the upper side of the lever surface instead of MAb3C6. For the control samples the same antibody concentration and procedure applied to the covalent and oriented immobilization of MAb3C6 were used. Before immobilization of the control antibody on the levers, 1 ml of a 4 mg / ml solution of anti-HRP in Milli-Q water was dialyzed overnight at 4 ° C. The concentration of the antibody solution after dialysis was determined using the Bradford assay [M. M. Bradford, M. M. Analytical Biochemistry, 1976, 72, 248-254], A calibration curve was made using bovine serum albumin (BSA) as a protein standard. The linear range of the assay was 5 pg / ml to 2500 pg / ml.
After immobilization of capture (MAb3C6) and control (anti-HRP) antibodies in a
5
10
fifteen
twenty
25
30
35
40
Four. Five
Covalent and oriented mode and desorption of antibodies that do not covalently bind to the surface, the lever surface was locked to prevent nonspecific adsorption. The levers were immersed in 1 mg / ml of (aminoethyl) polyethylene glycol (PEG), overnight at 4 ° C. After that, the samples were washed with MES at pH 5.5 with 0.05% Tween® 20 (pH 5.5).
Biomarker Recognition and Sandwich Assay
The levers were incubated for 1 hour at 37 ° C in CEA solutions with concentrations ranging from 1 pg / ml to 1 ag / ml in PBS solution with 0.05% Tween® 20 at pH 7.4 (PBST) . In order to have rigorous control experiments, the concentration of CEA in solution used for these samples was 1 pg / ml. To simulate a real sample, CEA solutions were prepared with a concentration ranging from 100 fg / ml to 10 ag / ml in SBF and for the rigorous control experiments in SBF the concentration of CEA was maintained at 1 pg / ml. Right after, the levers were washed twice with PBST and once with PBS at pH 7.4. After that, the samples were rinsed with Milli-Q water and dried under a stream of N2.
For the sandwich assay, the levers were immersed in 1 pg / ml of spherical gold nanoparticles solution functionalized with the detection antibody (GNPs-MAb3C1) prepared in 10 mM MES with 0.05% Tween® 20 pH 5, 5. The samples were incubated at 37 ° C for 1 hour under gentle agitation, washed three times with MES with Tween, twice with MES, rinsed thoroughly with Milli-Q water and dried under a stream of N2.
The efficiency of the biom archer recognition can be affected by the bioreceptor layer immobilized on the lever and also by the experimental conditions at which the recognition reaction takes place such as temperature, pH and time. Strategies to immobilize the bioreceptor layer must be optimized for each case; they can include the orientation and density of the receptors on the surface, and blocking strategies to avoid non-specific interactions. For example, if the detection biomarker is a small protein, the strategy to immobilize the antibodies on the surface of the micro lever, such as its density and orientation, and the chosen blocking molecule will not be the same if the biosensor is now revealed for detection of a bacterial cell, which is greater. Even when working with antibodies alone conditions can change; Ideal conditions such as concentration, pH, time and temperature to be used should be determined and optimized. The immobilization and experimental conditions for the recognition of analytes have to be customized each case; but the principle of the procedure presented here, based on dual detection, remains the same.
Optical measurements were made using a commercial optical microscope in a dark-field reflective mode (Axioskop 2 MAT equipped with AxioCam MRc 5 and bright-field / dark-field EC Epiplan Neofluor® lenses from Zeiss 50x from Zeiss - Oberkochen, Germany). The chip and lever surfaces were observed after the CEA recognition stage on the lever and after the sandwich assay (binding of the functionalized nanoparticles with the detection antibody).
The resonant frequency was obtained from the activated vibration of the lever that is detected optically by means of the simple optical lever procedure35 (see Figure 3). The resonance frequency of the fundamental vibration mode of the lever is measured in air before and after exposure of the lever to the gold nanoparticles functionalized with the primary antibody.
The samples used in the proof of concept experiments were analyzed by scanning electron microscopy (SEM) as illustrated in Figure 4. At least 100 images on the lever and chip were taken for each concentration of CEA detected and
5
10
fifteen
twenty
25
30
35
40
Four. Five
fifty
both surfaces had the same density of nanoparticles (Figure 5). The information obtained from the SEM images will be used to support the results of the optical and mechanical measurements.
Figure 6a shows the dark field images of the chip region for a control experiment and for a detection experiment with 1 pg / ml CEA in PBS. The dispersion signal is negligible in the control experiment. In the case of the CEA detection test, a negligible increase in the dispersion is observed in the chip region, the chip region has dimensions outside the design rules for the substrate in the invention, thus not leading to the enhanced plasmonic effect. , while the attached nanoparticles make the area of the lever shine, since the lever complies with the design that leads to the enhanced plasmonic effect.
The mean dispersion signal obtained from the dark field images is represented in Figure 6b as a function of the concentration of CEA in buffer or serum. The detection limit found for the experiments performed in buffer medium is 0.1 fg / ml. The scatter signal on the lever is approximately 6 times the signal on the chip, showing increases in the optical signal by the designed substrate. The resonant enhancement of the dispersion signal plays a role in determining CEA at ultra low serum concentrations. Thus, the dispersion signal in the chip is based on the region obtained in the control experiments for CEA concentrations of 0.1 fg / ml to 100 fg / ml. Impressively, the boost induced by the dispersion signal lever cavity allows discrimination of concentrations of only 0.1 fg / ml.
The bright aspect of the lever is related to its effect as an optical cavity, as outlined in Figure 7a. If the light interacts with a nanoparticle on the lever chip (a support that does not meet the design rules of the object of the invention), the scattered light collected is only given by the backward dispersion of the dispersion from the surface of separation between the environment and the raw substrate. If the nanoparticle is on the lever, in addition to the backward dispersion observed in the raw support chip, multiple routes help enhance the dispersion by a single nanoparticle that dramatically boosts the measured backward scatter signal. One route involves the amplification of the light scattered by the nanoparticle towards the lever by multiple reflections, producing multiple dispersion procedures. A second route encloses procedures in which the light that strikes in the regions of the lever between nanoparticles undergo multiple reflections in the cavity of the optical lever, producing a cascade of dispersion interactions at the site of nanoparticles.
In order to determine the coupling between the optical cavity and the plasmon response, the spectral response of the dispersion in the lever and the support chip was analyzed. The spectra showed the resonant enhancement of plasmon-assisted dispersion of the optical lever cavity by almost an order of magnitude. Multiple reflection procedures in the lever cavity result in the modulation of the dispersion signal with the wavelength, reminiscent of the reflectivity modulation shown in Figure 8.
Figure 9 shows the mechanical frequency response of the lever due to the added mass given by antibody-coated nanoparticles that bind. Mechanical resonance was measured by an instrument with a laser beam deflection procedure as depicted in Figure 3 for reading. Figure 9a shows the peak mechanical resonance frequency before and after the nanoparticle recognition step in buffer media for the control experiment and during 1 pg / ml CEA. The mechanical resonance peaks before and after the exposure of the control lever to the solution contained in the CEA biomarkers show negligible differences. A significant shift of the mechanical resonance peak at lower frequencies is observed in the CEA detection test. Shifts in mechanical resonance frequency versus
5
10
fifteen
twenty
25
30
35
40
Four. Five
fifty
The concentration of CEA is shown in Figure 9b for purified buffer (left) and serum solutions (right). The mechanical resonance shifts in buffer solution are shown in Figure 9b (left) together with the biological base noise determined in the control assays. The experimental data show an excellent coincidence with the theoretical prediction based on the mass of the nanoparticles attached to the lever that the present inventors have evaluated by SEM. The limit of detection in these calibration curves is 0.1 fg / ml. The limit of detection increases an order of magnitude when the tests are carried out in serum due to the enormous amount of non-specific interactions of competition between plasma biomolecules and the lever surface.
The fact that the optical technique reaches a higher detection limit than that obtained with mechanical measurement does not indicate that it is a better biosensor. A statistical analysis of the reliability of pure optical and mechanical sensors indicates that both biosensors have similar performances, but the combination of the two transduction mechanisms led to a dual biosensor with improved performance as can be seen in Figure 10.
Statistical study of the reliability of the optomecanoplasmonic sensor (hybrid signal)
The sensitivity and specificity of a diagnostic test are a function of a chosen threshold value. Changing the threshold value so that sensitivity increases will decrease specificity, and vice versa. The receiver operating characteristic (ROC) curve is a graph of all the sensitivity / specificity pairs resulting from continuously varying the decision threshold with respect to the complex range of observed results. This is a graph of the rate of true positives (or sensitivity) on the y-axis and the rate of true negatives (specificity 1) on the x-axis. The true positive rate (TPR) is the probability that a disease case is classified correctly and the true negative rate (TNR) is the probability that a true normal case is correctly classified. The ROC curve can also be used to compare the performance of two or more diagnostic tests78. An alternative to the ROC curve is the graph of the detection error compensation (DET), which represents the false negative rate (lost detections) versus the false positive rate (false alarms) on the x-axis and logarithmic. This alternative spends more graphic area in the region of interest, that is, the region with a minimum false rate. The DET plot is made assuming a normal distribution determined by the experimentally obtained mean value and standard deviation. Figure 10a shows the DET curves for a concentration of 10 fg / ml by the plasmonic and nanomechanical transduction procedures. The dashed-line corresponds to a random parameter. Both transduction procedures provide DET curves well below this non-discrimination curve. The optimal value of the threshold signal is that which gives a minimum in the distance between the DET curve and the origin. The case is now considered in which the signal of the present inventors is a combination of the dispersion intensity and the displacement of the mechanical resonance frequency7. The linear combination is optimized by minimizing the minimum distance between the DET curve and the origin. In this way, thanks to the dual signal, the false detection rate of the present inventors is always enhanced as shown in Figure 10a. The enhancement in reliability is modest for the lower concentrations as can be seen in Figure 10b, in which the plasmonic transduction is clearly superior to the nanomechanical transduction. However, as the concentration increases, the reliability of both transduction procedures becomes comparable, and the optimization by linear combination of both signals is clearly advantageous (see the sphere symbols in Figure 10b).
REFERENCES
1. D'Orazio, P. Biosensors in clinical chemistry-2011 update. Chimica Clinic Acta 412, 1749-1761 (2011).
5
10
fifteen
twenty
25
30
35
40
2. Tothill, I. E. 55-62 (Elsevier).
3. Justino, C. I. L., Rocha-Santos, T. A & Duarte, A C. Review of analytical figures of merit of sensors and biosensors in clinical applications. TrAC Trends In Analytical Chemistry 29, 1172-1183 (2010).
4. Fan, X. et al. Sensitive optical biosensors for unlabeled targets: A review. Analytical chimica acta 620, 8-26 (2008).
5. Wang, J. Carbon-nanotube based electrochemical biosensors: A review. Electroanalysis 17, 7-14 (2005).
6. Wang, J. Electrochemical biosensors: Towards point-of-care cancer diagnosics. Biosensors and Bioelectronics 21,1887-1892 (2006).
7. Wang, J. Amperometric biosensors for clinical and therapeutic drug monitoring: a review. Journal of pharmaceutical and biomedical analysis 19, 47-53 (1999).
8. Stem, E. et al. Label-free biomarker detection from whole blood. Nature nanotechnology 5, 138-142 (2009).
9. Duan, X. et al. Quantification of the affinities and kinetics of protein interactions using Silicon nanowire biosensors. Nature nanotechnology 7, 401-407 (2012).
10. Zheng, G., Gao, X. P. A & Lieber, C. M. Frequency domain detection of biomolecules using Silicon nanowire biosensors. Nano Letters 10, 3179-3183 (2010).
11. Dixon, M. C. Quartz crystal microbalance with dissipation monitoring: enabling real-time characterization of biological materials and their interactions. Journal of biomolecular techniques: JBT19, 151 (2008).
12. Lange, K., Rapp, B. E. & Rapp, M. Surface acoustic wave biosensors: a review. Analytical and bioanalytical chemistry 391, 1509-1519 (2008).
13. O'sullivan, C. & Guilbault, G. Commercial quartz crystal microbalances-theory and applications. Biosensors and Bioelectronics 14, 663-670 (1999).
14. Arlett, J., Myers, E. & Roukes, M. Comparative advantages of mechanical biosensors. Nature nanotechnology 6, 203-215 (2011).
15. Boisen, A & Thundat, T. Design & fabrication of cantilever array biosensors. Materials Today 12, 32-38 (2009).
16. Datar, R. et al. Cantilever sensors: nanomechanical tools for diagnostics. MRS bulletin 34, 449.454 (2009).
17. Boisen, A, Dohn, S., Keller, S. S., Schmid, S. & Tenje, M. Cantilever-like micromechanical sensors. Reports on Progress in Physics 74, 036101 (2011).
18. Fritz, J. Cantilever biosensors. Analyst 133, 855-863 (2008).
19. Raiteri, R., Grattarola, M., Butt, H. J. & Skladal, P. Micromechanical cantilever-based biosensors. Sensors and Actuators B: Chemical 79, 115-126 (2001).
20. Wagoner, P. S. & Craighead, H. G. Micro-and nanomechanical sensors for environmental, Chemical, and biological detection. Lab Chip 7, 1238-1255 (2007).
21. Kathryn M. Mayer, Jason H. Hafner, Localized Surface Plasmon Resonance Sensors, Chemical Reviews 111, 3828-3857 (2011)
22. Roberto de la Rica, Molly M. Stevens, Plasmonic ELISA for the ultrasensitive detection of disease biomarkers with the naked eye, Nature Nanotechnology 7, 821-824 (2012)
23. Jwa-Min Nam, C. Shad Thaxton, Chad A. Mirkin, Nanoparticle-Based Bio-Bar Codes for the Ultrasensitive Detection of Proteins, Science 301, 1884-1886 (2003)
5 25. Dong et al., Two types of nanoparticle-based bio-barcode amplification assays to detect
HIV-1 p24 antigen, Virology Journal 9, 180 (2012)
26. Elghanian R, Storhoff JJ, Mucic RC, Letsinger RL, Mirkin CA Selective colorimetric detection of polynucleotides based on the distance-dependent optical properties of gold nanoparticles, Science 277, 1078-81 (1997)
10 27. James J. Storhoff, Robert Elghanian, Robert C. Mucic, Chad A Mirkin, Robert L.
Letsinger, One-Pot Colorimetric Differentiation of Polynucleotides with Single Base Imperfections Using Gold Nanoparticle Probes, J. Am. Chem. Soc., 120, 1959-1964 (1998)
28. T. Andrew Taton, Chad A Mirkin, Robert L. Letsinger, Scanometric DNA Array Detection with Nanoparticle Probes, Science 289, 1757-1760 (2000)
15 29. Robert Jenison, Shao Yang, Ayla Haeberli, Barry Polisky, Interference-based detection of
nucleic acid targets on optically coated Silicon, Nature Biotechnology 19, 62-65 (2001)
30. Goluch ED1, Nam JM, Georganopoulou DG, Chiesl TN, Shaikh KA Ryu KS, Barron AE, Mirkin CA, Liu C., A bio-barcode assay for on-chip attomolar-sensitivity protein detection, Lab Chip. 6, 1293-9 (2006)
20 31. Wagoner, P. S., Varshney, M. & Craighead, H. G. Detection of prostate specific antigen
with nanomechanical resonators. Lab Chip 9, 3095-3099 (2009).
32. Nair, P. R. & Aam, M. A. Theory of “Selectivity” of label-free nanobiosensors: Ageometro-physical perspective. Journal of applied physics 107, 064701-064701-064706 (2010).
33. Priscilla M. Kosaka, Javier Tamayo, José J. Ruz, Sara Puertas, Ester Polo, Valeria Grazu, 25 Jesús M. de la Fuente and Montserrat Calleja. Tackling Reproducibility in Microcantilever
Biosensors: A Statistical Approach for Sensitive and Specific End-point detection of Immunoreactions, Analyst 138, 863-872 (2013).
34. Varshney M, Wagoner PS, Tan CP, Aubin K, Montagna RA Craighead HG., Prion protein detection using nanomechanical resonator arrays and secondary mass labeling, Anal Chem.
30 80.2141-8 (2008).
35. Javier Tamayo, Valerio Pini, Prisicila Kosaka, Nicolás F Martínez, Oscar Ahumada, Montserrat Calleja, Imaging the surface stress and vibration modes of a microcantilever by laser beam deflection microscopy, Nanotechnology, 23, 315501 (2012)

权利要求:
Claims (24)
[1]
5
10
fifteen
twenty
25
30
35
40
1. A system for biodetection applications comprising:
to. a substrate of dielectric material having at least one functionalized surface with a recognition element that can specifically bind to a target analyte and
b. at least one nanoparticle with plasmonic properties comprising at least one detection element attached thereto and which can be specifically bound to the target analyte in a sandwich type arrangement,
characterized in that:
- the substrate of dielectric material has a thickness between 0.1 pm and 5 pm and an extinction coefficient of less than 0.3,
- the nanoparticle has at least one of its dimensions with a size of 2 nm to 300 nm and
- because the ratio between the refractive index of the dielectric material and the surrounding material is greater than 1.1.
[2]
2. A system according to claim 1, wherein the dielectric material is selected from quartz, silicon, silicon nitride, silicon carbide, graphene, polymers and hydrogels.
[3]
3. A system according to any one of claims 1 or 2, wherein the substrate is in the form of a micro lever, a micropile, a string resonator, a trampoline resonator, a rectangular lever, a triangular lever, a pyramid lever, a blade lever, a membrane resonator, a plate resonator, a bridge, a hollow lever or a nanowire.
[4]
4. A system according to any one of claims 1 to 3, wherein the substrate is functionalized with a recognition element selected from an antibody, a receptor, a peptide, a protein a carbohydrate, a nucleic acid, a cell, a microorganism or a part thereof.
[5]
5. A system according to any one of claims 1 to 4, wherein the detection element is selected from an antibody or a nucleic acid molecule.
[6]
6. A system according to claim 1 to 5, wherein the nanoparticle is a nanoparticle of gold, silver or plasmonic metamaterial.
[7]
7. A system according to claim 1 to 5, wherein the nanoparticle has a structure selected from the group of nanospheres, nanovarillas, sharp nanovarillas, nanovainas, nanojaulas / m arcs, hollow nanospheres, tetrahedra, octahedra, cubes, icosahedra, rhombic dodecahedrons , concave nanocubes, tetrahexahedrons, obtuse triangular bipyramids, trisohectahedra and nanoprisms.
[8]
A system according to any one of claims 1 to 7, wherein the substrate has a transmittance index between 0.01 and 1 and / or a reflectance index between 0.01 and 1.
[9]
9. A biosensor comprising a system according to any one of claims 1 to 8.
[10]
10. A biosensor arranged in the form of a matrix comprising multiple systems according to any one of claims 1 to 8, each system comprising a substrate designed to detect a different target analyte or different concentrations of the same analyte.
5
10
fifteen
twenty
25
30
35
40
[11]
11. A method for detecting and / or quantifying a selected target analyte in a sample comprising:
a) contacting a sample with a substrate of dielectric material having a functionalized surface with a recognition element that can be specifically bound to the target analyte, the substrate of dielectric material having a thickness between 0.1 pm and 5 pm and a coefficient of extinction less than 0.3 and the ratio between the refractive index of the dielectric material and the surrounding material being greater than 1.1
b) add to the substrate resulting from a) at least one nanoparticle with plasmonic properties and having at least one of its dimensions with a size of 2 nm to 300 nm, comprising at least one detection element attached thereto and which can be attached specifically to the target analyte, in order to detect the presence of the target analyte bound to the recognition element
c) irradiating the resulting substrate of b) with an electromagnetic radiation in which the presence of the target analyte in the sample produces a plasmonic effect on the nanoparticles amplified by the presence of the substrate that can be detected by optical means,
d) measure the light scattering or intensity of the extinction signal so that it detects the presence or absence of the target analyte in the sample and for quantification thereof.
[12]
12. A process according to claim 11, wherein the dielectric material is selected from quartz, silicon, silicon nitride, silicon carbide, polymers, hydrogels or graphene.
[13]
13. A method according to any of claims 11 to 12, wherein the recognition element is selected from an antibody, a receptor, a peptide, a carbohydrate, a nucleic acid, a cell and a microorganism or a part of the same.
[14]
14. A method according to any of claims 11 to 13, wherein the detection element is selected from an antibody or a nucleic acid molecule.
[15]
15. A method according to any of claims 11 to 14, wherein the nanoparticle is a gold, silver or a plasmonic metamaterial nanoparticle.
[16]
16. A method according to any of claims 11 to 15, wherein the nanoparticle has a structure selected from the group of nanospheres, nanovarillas, sharp nanovarillas, nanovainas, nanojaulas / frames, hollow nanospheres, tetrahedra, octahedra, cubes, icosahedra, dodecahedra rhombic, concave nanocubes, tetrahexahedrons, obtuse triangular bipyramids, trisohectahedra and nanoprisms.
[17]
17. A method according to any of claims 11 to 16, wherein the optical medium comprises a dark field microscope or a cross polarization microscope.
[18]
18. A method according to any of claims 11 to 17, wherein:
• the substrate of dielectric material has a reflectance index between 0.01 and 1 when the dispersion intensity signal is measured or
• The substrate of dielectric material has a transmittance index between 0.01 and 1 when the extinction intensity signal is measured.
[19]
19. A method according to any of claims 11 to 18, wherein the process is performed in a microelectromechanical system by which the substrate of dielectric material is arranged as a mechanical element that can undergo a change in at least one
5
10
fifteen
twenty
25
30
35
40
mechanical characteristic when the target analyte is present in the sample, and, in which the following additional steps are performed:
e) measure at least one mechanical characteristic in the mechanical element so that it detects the presence or absence of the target analyte in the sample,
f) combine the optical data obtained in stage d) with mechanical data of stage e) in order to improve the reliability of the detection procedure.
[20]
20. A method according to claim 19, wherein the mechanical element may be in the form of a micro lever, a micropile, a string resonator, a trampoline resonator, a rectangular lever, a triangular lever, a pyramid lever, a lever shovel, a membrane resonator, a plate resonator, a bridge, a hollow lever or a nanowire.
[21]
21. A method according to any of claims 19-20, wherein the at least one mechanical characteristic can be selected from: the position of a portion of the mechanical element, the vibration characteristic of the mechanical element, such as the vibration phase of the mechanical element, the frequency of the vibration of the mechanical element, the amplitude of the vibration of the mechanical element or the surface tension on a portion of the mechanical element or the dissipation changes of the mechanical element.
[22]
22. Device for surface inspection arranged to detect an optoplasmonic effect in at least one nanoparticle of a system according to claim 1, said device comprising:
- a source of electromagnetic radiation arranged to generate at least one beam of electromagnetic radiation;
- a first sensitive detector arranged to receive electromagnetic radiation when it is reflected or transmitted through the substrate to produce at least a first output signal in response to the dispersion and / or extinction of said electromagnetic radiation;
- an electronic control system;
[23]
23. A device according to claim 22, wherein the device further comprises:
- a subsystem for detecting a change in a mechanical characteristic in the substrate, said subsystem comprising a second sensitive detector arranged to detect a mechanical change in the substrate to produce at least a second signal in response to said mechanical change; Y
- means for producing a final output signal based on the combination of first and second output signals of the first and second sensitive detectors.
[24]
24. A device according to claim 23, wherein said detection subsystem comprises:
- a light of illumination or laser beam and a sensitive photodetector of linear position to record the change in the mechanical characteristic on the substrate
- an electronic control system;
- scanning means for the relative displacement of said light or laser beam with respect to the substrate so that they sweep the substrate with the light beam following instructions of the electronic control system.

类似技术:

---

公开号 | 公开日 | 专利标题

---

ES2684794T3|2018-10-04|System for biodetection applications

---

Tokel et al.2014|Advances in plasmonic technologies for point of care applications

---

Couture et al.2013|Modern surface plasmon resonance for bioanalytics and biophysics

---

Li et al.2019|Plasmonic-based platforms for diagnosis of infectious diseases at the point-of-care

---

Feuz et al.2010|Improving the limit of detection of nanoscale sensors by directed binding to high-sensitivity areas

---

Li et al.2015|Antibody modified gold nano-mushroom arrays for rapid detection of alpha-fetoprotein

---

Munawar et al.2019|Nanosensors for diagnosis with optical, electric and mechanical transducers

---

Zhang et al.2019|Immunosensor-based label-free and multiplex detection of influenza viruses: State of the art

---

Fu et al.2019|Recent advances in biosensors for nucleic acid and exosome detection

---

Gopinath et al.2008|Influence of nanometric holes on the sensitivity of a waveguide-mode sensor: Label-free nanosensor for the analysis of RNA aptamer− ligand interactions

---

Omar et al.2017|Recent development of SPR spectroscopy as potential method for diagnosis of dengue virus E-protein

---

Upasham et al.2018|Cardiac troponin biosensors: where are we now

---

Ong et al.2018|Diagnosing human blood clotting deficiency

---

JP2009150708A|2009-07-09|Detection method and inspection kit of target substance

---

Arshavsky Graham et al.2020|Mass transfer limitations of porous silicon-based biosensors for protein detection

---

Darwish et al.2018|Immunofluorescence–based biosensor for the determination of dengue virus NS1 in clinical samples

---

Lifson et al.2014|Enhancing the detection limit of nanoscale biosensors via topographically selective functionalization

---

EP3350117B1|2019-08-28|End-cap suitable for optical fiber devices and nanoplasmonic sensors

---

Vaish et al.2011|Thin gold film-assisted fluorescence spectroscopy for biomolecule sensing

---

Kim et al.2015|Label-free C-reactive protein SERS detection with silver nanoparticle aggregates

---

US7829349B2|2010-11-09|Base carrier for detecting target substance, element for detecting target substance, method for detecting target substance using the element, and kit for detecting target substance

---

Xu et al.2014|Label-free microcantilever-based immunosensors for highly sensitive determination of avian influenza virus H9

---

CN102150033A|2011-08-10|Improved wire grid substrate structure and method for manufacturing such a substrate

---

Lee et al.2014|Selective fluorescence and fluorescence-free detection of single biomolecules on nanobiochips

---

Tamayo de Miguel et al.2018|System for biodetection applications

同族专利:

---

公开号 | 公开日

---

US20200072829A1|2020-03-05|

---

US10502734B2|2019-12-10|

---

PL3153844T3|2019-03-29|

---

EP3153844A1|2017-04-12|

---

PT3153844T|2018-10-19|

---

ES2684794T3|2018-10-04|

---

US20170205405A1|2017-07-20|

---

WO2015185778A1|2015-12-10|

---

ES2553027B1|2016-09-13|

---

EP3153844B1|2018-05-23|

---

HUE040582T2|2019-03-28|

---

DK3153844T3|2018-08-27|

引用文献:

---

公开号 | 申请日 | 公开日 | 申请人 | 专利标题

---

WO2014016465A1|2012-07-26|2014-01-30|Universidad De Zaragoza|Biosensor comprising metal nanoparticles|

---

ES2584553T3|1999-10-06|2016-09-28|Becton Dickinson And Company|Spectroscopically active surface-enhanced compound nanoparticles|

---

EP1639370B1|2003-05-30|2009-09-02|Nanosphere, Inc.|Method for detecting analytes based on evanescent illumination and scatter-based detection of nanoparticle probe complexes|

---

US7884930B2|2007-06-14|2011-02-08|Hrl Laboratories, Llc|Integrated quartz biological sensor and method|

---

US20100053598A1|2008-08-27|2010-03-04|Sunghoon Kwon|Surface deformation detection|

---

US9921165B2|2010-11-05|2018-03-20|Genalyte, Inc.|Optical analyte detection systems and methods of use|US20170328912A1|2016-05-10|2017-11-16|Regents Of The University Of Minnesota|Glycopolymer capture matrix for use with surface-enhanced raman spectroscopy detection and related systems and methods|

---

WO2019031514A1|2017-08-10|2019-02-14|株式会社Ｊｖｃケンウッド|Analysis method and analysis device|

---

US11041187B2|2017-10-26|2021-06-22|The Board Of Trustees Of The University Of Illinois|Photonic resonator absorption microscopyfor digital resolution biomolecular diagnostics|

---

EP3575784B1|2018-05-28|2021-01-27|Consejo Superior de Investigaciones Cientificas |Method and system for the analysis of analytes through mechanical resonance transduction|

---

CN108956743B|2018-07-24|2021-01-08|哈尔滨工程大学|Detection method of field effect transistor biosensor enhanced by AuNPs|

---

CN109030455B|2018-07-27|2020-11-10|天津大学|Preparation and detection method of surface Raman enhanced substrate based on microchip|

---

EP3719477A1|2019-04-03|2020-10-07|Mecwins, S.A.|Method for optically detecting biomarkers|

---

EP3719461A1|2019-04-03|2020-10-07|Mecwins, S.A.|Biosensor platform and method for the simultaneous, multiplexed, ultra-sensitive and high throughput optical detection of biomarkers|

---

CN110243800B|2019-04-18|2020-05-29|华中科技大学|Method and device for detecting quality and yield of biochar|

法律状态:
2016-09-13| FG2A| Definitive protection|Ref document number: 2553027 Country of ref document: ES Kind code of ref document: B1 Effective date: 20160913 |

优先权:

---

申请号 | 申请日 | 专利标题

---

ES201430846A|ES2553027B1|2014-06-03|2014-06-03|A SYSTEM FOR BIODETECTION APPLICATIONS|ES201430846A| ES2553027B1|2014-06-03|2014-06-03|A SYSTEM FOR BIODETECTION APPLICATIONS|

---

EP15742334.4A| EP3153844B1|2014-06-03|2015-06-02|System for biodetection applications|

---

PL15742334T| PL3153844T3|2014-06-03|2015-06-02|System for biodetection applications|

---

PCT/ES2015/070434| WO2015185778A1|2014-06-03|2015-06-02|System for biodetection applications|

---

ES15742334.4T| ES2684794T3|2014-06-03|2015-06-02|System for biodetection applications|

---

DK15742334.4T| DK3153844T3|2014-06-03|2015-06-02|System for bio-detection applications|

---

US15/315,029| US10502734B2|2014-06-03|2015-06-02|System for biodetection applications|

---

HUE15742334A| HUE040582T2|2014-06-03|2015-06-02|System for biodetection applications|

---

PT15742334T| PT3153844T|2014-06-03|2015-06-02|System for biodetection applications|

---

US16/668,005| US20200072829A1|2014-06-03|2019-10-30|System for biodetection applications|