Aptamers, aptamer-based sensors and methods for the detection of neurofilament light

Abstract

The present invention relates to aptamers that bind to neurofilament light, biosensors, uses of the aptamers, and methods for detecting neurofilament light.

Description

[0001] The present invention relates to aptamer molecules that bind selectively and with high affinity to neurofilament light, sensors for the detection of neurofilament light, methods for determining neurofilament light, and corresponding uses and applications. State of the art:

[0002] Currently, biomarkers for diagnosing dementia, such as Alzheimer's disease, are determined using antibodies. These biomarkers are primarily measured in cerebrospinal fluid (CSF), a procedure that requires a lumbar puncture and is invasive for the patient. The tests are typically performed using enzyme-linked immunosorbent assay (ELISA). In some cases, positron emission tomography (PET) is also used to detect biomarkers in affected tissue. PET scans are very expensive and also invasive. These methods are used when there is already an indication for the disease and not for screening without prior symptomatic indications. Furthermore, ELISA tests are expensive, require long testing times, and demand experienced personnel. The antibodies used are sensitive to degradation, exhibit variations in binding characteristics, and their development requires animal testing.Current biomarker tests, due to their high cost and invasiveness, are generally only performed after cognitive impairment has already been detected in patients, in order to confirm the diagnosis. The later the diagnosis is made, the fewer intervention options are available and their chances of success decrease. Typically, the molecular processes of neurodegeneration that lead to Alzheimer's disease begin years before cognitive impairments appear.

[0003] Neurofilament light (NF-L or NFL) is a biomarker for the diagnosis of dementia, particularly Alzheimer's disease. Neurofilament light (NF-L) is a protein found in the axonal neurites of neurons that leaks into the interstitial fluid as a result of neuronal degradation or injury. NFL concentrations are elevated in patients with neurodegenerative diseases, even in the presymptomatic phase without quantifiable cognitive impairment. Therefore, the detection of elevated NFL levels in body fluids can support the diagnosis of neurodegenerative diseases in early stages, when treatment has a higher probability of success. Task:

[0004] The object of the present invention was to provide methods and measuring devices for the determination of biomarkers for Alzheimer's disease, in particular neurofilament light (NFL), in samples, preferably body fluids, especially serum, blood, and cerebrospinal fluid (CSF), to support the diagnosis of Alzheimer's disease (AD). The determination should be as selective as possible and with the highest possible affinity. Furthermore, the methods and measuring devices to be provided should be usable at the point of care, inexpensive to manufacture, highly stable, easy to use, and exhibit high test accuracy.

[0005] Further tasks arise for the expert when considering the following description and the requirements. Solution:

[0006] These and other problems that become apparent to the person skilled in the art when considering the present description are solved by the items described in the independent claims.

[0007] Particularly advantageous and preferred items will be evident from the dependent claims and the following description.

[0008] Preferred embodiments result from the dependent claims and / or the following description. Detailed description:

[0009] Within the scope of the present invention, room temperature means a temperature of 293.15 Kelvin, i.e. 20°C.

[0010] Unless otherwise stated, all reactions and procedures are performed at atmospheric pressure (1013 mbar). absolut ) and room temperature.

[0011] Within the scope of the present invention, the terms "sensor" and "biosensor" are used synonymously.

[0012] Within the scope of the present invention, nano-objects or nanoparticles are objects with at least one spatial dimension smaller than 100 nm, measured by scanning electron microscopy.

[0013] Within the scope of the present invention, the term “Neurofilament Light” includes “Neurofilament Light chain”, “Neurofilament Light Polypeptide” and “Neurofilament Light”.

[0014] The present invention relates in a first subject matter in particular to aptamers, especially DNA aptamers, which bind to neurofilament light and are selected from the group consisting of a) comprising or consisting of an aptamer, a nucleic acid sequence selected from the group consisting of SEQ ID NO: 1, 2 and 3, b) an aptamer whose nucleic acid sequence has a similarity of at least 50%, 60%, 65%, 70%, 75%, 80%, 85%, 90%, 95% or 98% with the nucleic acid sequence of an aptamer from a), c) an aptamer in which, compared to an aptamer from a), up to 19 nucleotides, in particular 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18 or 19 nucleotides, are removed, substituted and / or extended in the sequence with SEQ ID NO: 1, 2 or 3.

[0015] In the prior art, the general term "aptamers" refers to short, single-stranded nucleic acid oligomers, also known as oligonucleotides, that can bind specifically to a target structure or molecule, also referred to as a target, such as a protein, low-molecular-weight compounds like organic substances, amino acids and antibiotics, nucleic acids, virus particles, or (micro)organisms. Aptamer-target binding occurs, for example, via structural compatibility, so-called "stacking interactions" in aromatic ring structures (stacking forces through electron interaction with neighboring bases), electrostatic interactions (e.g., van der Waals forces, ionic forces, dipole forces), and hydrogen bonds.

[0016] Aptamers with peptide structures are also known, but the present invention relates exclusively to nucleic acid aptamers. Therefore, the term "aptamers" hereafter refers to nucleic acid aptamers. Nucleic acid aptamers are classified, for example, as DNA aptamers, formed from single-stranded DNA (ssDNA), and RNA aptamers. Aptamers are characterized by the formation of a specific three-dimensional structure that depends on the nucleic acid sequence. This structure enables aptamers to bind precisely to target structures, analogous to an antigen-antibody bond. A specific nucleic acid sequence of an aptamer can, under defined conditions, exhibit a three-dimensional structure that is specific for a defined target structure. The three-dimensional structure of an aptamer arises, among other things, from intramolecular base pairing according to Watson and Crick and via Hoogsteen base pairing (quadruplex).

[0017] In preferred embodiments of the present invention, the aptamers of the present invention are modified by binding, in particular covalent binding, to a probe molecule, preferably selected from the group consisting of fluorophores, nanomaterials, enzymes, redox molecules or mixtures or combinations thereof, in particular a fluorophore, particularly at the 3' end, in order to enable or enhance signal conversion.

[0018] In alternative preferred embodiments of the present invention, the aptamers of the present invention are modified by binding, in particular covalent binding, to a probe molecule, preferably selected from the group consisting of fluorophores, nanomaterials, enzymes, redox molecules or mixtures or combinations thereof, in particular a fluorophore, particularly at the 3' end, to enable or enhance signal conversion, and additionally modified at its other end by binding, in particular covalent binding, to a binding group.

[0019] Another object of the present invention relates to aptamer probes for the detection of neurofilament light comprising one or more different aptamers according to the invention, as described above or below, and a labeling agent.

[0020] Another object of the present invention is biosensors comprising one or more different aptamers according to the invention, as described above or below, or aptamer probes according to the invention.

[0021] Another object of the present invention is biosensors based on electrochemical, thermal, optical, electrical, magnetic, gravimetric principles or other transducer principles, in particular electrochemical, optical or electrical principles, especially for determining neurofilament light in body fluids, preferably blood, serum or CSF, and comprising - an aptamer or several such aptamers binding to neurofilament light, preferably based on single-stranded deoxyribonucleic acid, particularly preferably one or more different aptamers according to the invention, as described above or below, where the aptamers either a) be freely present in a sample solution, or b) immobilized on a solid phase, preferably on an electrode, a transistor electrode, in particular a gate electrode or the transistor channel, a microbalance such as oscillating crystals and spring arms, para- or ferromagnetic materials, optical components such as coated and uncoated prisms, mirrors, gratings, fiber optics, polarizers, etc., transparent substrates, nanomaterials, micro- or nanostructured materials, metal-organic frameworks (MOFs) or another signal converter.

[0022] In preferred embodiments of the biosensors of the present invention, the aptamer used is modified by binding, in particular covalent binding, to a probe molecule, preferably selected from the group consisting of fluorophores, nanomaterials, enzymes, redox molecules or mixtures or combinations thereof, in particular a fluorophore, especially at the 3' end, in order to enable or enhance signal conversion.

[0023] In alternative preferred embodiments of the biosensors of the present invention, the aptamer used is modified by binding, in particular covalently, to a probe molecule, preferably selected from the group consisting of fluorophores, nanomaterials, enzymes, redox molecules or combinations thereof, in particular a fluorophore, especially at the 3' end, in order to enable or enhance signal transduction. Additionally or alternatively, the aptamer used can be modified at its other end by binding, in particular covalently, to a binding group.

[0024] In embodiments of the present invention, it is preferred if additional molecules which suppress the non-specific binding of components of the sample are immobilized on the solid phase.

[0025] Another object of the present invention is a solid phase, preferably an electrode, transistor electrode, in particular a gate electrode, microbalance, or another signal converter on or at which one or more aptamers or modified aptamers of the present invention as described above or below are immobilized, preferably for the detection, enrichment, separation or isolation of neurofilament light, in particular the detection of neurofilament light.

[0026] Another object of the present invention is test strips, for example for use in lateral flow assays, comprising one or more aptamers or modified aptamers of the present invention as described above or below.

[0027] A further object of the present invention is a kit comprising one or more aptamers or modified aptamers of the present invention as described above or below, and optionally further analytical material, preferably pipettes, biosensor chips, portable readers, chemicals, preparation tubes (Eppendorf tubes), cuvettes, a light source, a fluorescence detector, and the like. With regard to the term "kit," it should be noted that this kit does not necessarily have to be pocket-sized.

[0028] Another object of the present invention is a method for determining neurofilament light in body fluids, preferably serum, blood or CSF, in particular blood, comprising the steps of: a) Providing one or more aptamers binding to neurofilament light, preferably based on single-stranded deoxyribonucleic acid, particularly preferably one or more aptamers or modified aptamers of the present invention as described above or below; b) Contacting the aptamer or aptamers with a sample of body fluid, preferably blood, serum or CSF, in particular blood; c) Detecting the binding of neurofilament light to the aptamer or aptamers.

[0029] In preferred embodiments of the method according to the invention, the aptamer is provided in the form of a biosensor according to the invention, as described above or below.

[0030] In further preferred embodiments of the inventive method, detection is carried out by means of - optical methods, preferably by detection of fluorescence light, or colorimetrically by color change, e.g. in lateral flow assays or - electrical methods, preferably measuring voltage changes using a transistor, in particular an OECT (organic electrochemical transistor), or - electrochemical methods, preferably by measuring sample currents or resistances using electrodes, in particular electrochemical impedance spectroscopy.

[0031] The method according to the invention can, for example, also be carried out in the form of a competitive assay or a sandwich assay.

[0032] Another object of the invention is a method for producing the biosensors according to the invention, as described above or below, comprising the steps - Providing one or more aptamers binding to neurofilament light, preferably based on single-stranded deoxyribonucleic acid, particularly preferably one or more aptamers or modified aptamers of the present invention as described above or below; - optionally, and in many embodiments of the present invention preferred, modifying the aptamer or aptamers as described above or below; - Providing an electrode, a transistor electrode, in particular a gate electrode, a microbalance, or another signal converter; - Immobilizing the aptamer on the electrode, microbalance or other signal transducer, preferably via bonding groups, particularly preferably via a group containing thiol groups, especially an HS-(CH2)6 group; - optionally, and preferred in many embodiments of the present invention, immobilizing blocking molecules on the electrode, the microbalance or the other signal transducer.

[0033] Furthermore, another object of the present invention is the use of the aptamers according to the invention as described above or below, the aptamer probes according to the invention, the biosensors according to the invention as described above or below, and the first method according to the invention as described above or below. - for the detection of neurofilament light in samples, preferably body fluids, especially preferably blood, serum or CSF, particularly blood; - for the enrichment, separation and / or isolation of neurofilament light from samples; - for potentially preventive and decentralized testing, especially of broad population groups.

[0034] Finally, the present invention relates to the use of the aptamers according to the invention as described above or below as therapeutics, as affinity tags, as reagents, for labeling systems containing neurofilament light, for or in biosensors, and for quality control.

[0035] The electrodes used in the biosensors according to the invention can be based on gold or other metals, in particular precious metals (among other reasons, because these are ideally polarizable), semiconductors, carbon, or conductive polymers. Gold is a particularly preferred electrode material within the scope of the present invention. Furthermore, in other preferred embodiments, the electrodes can have coatings, preferably made of nanomaterials, polymer films, or molecules that functionalize the surface of the electrodes, e.g., increase the number of binding sites (nanomaterials such as nanoporous gold, platinum black, nanostructured gold, MOFs, dendritic molecules, polyvalent molecules), reduce the impedance (nanomaterials such as nanoporous gold, platinum black, nanostructured gold, conductive polymers such as poly-3,4-ethylenedioxythiophene / polystyrenesulfonic acid (PEDOT / PSS)), or modify the chemical properties of the electrodes (hydrophobic molecules, e.g.,Alkanethiols, protein-aversive molecules (e.g., ethylene glycols), hydrophilic molecules (e.g., polycations or polyanions), monomeric, oligomeric, or polymeric sugars, or other substances.

[0036] If transistors are used instead of simple electrodes, a configuration is preferably employed within the scope of the present invention in which the gate electrode and the transistor channel are connected to each other via a liquid (also referred to as a liquid gate). In these, the channel can consist of semiconducting polymer layers (e.g., poly(3-hexylthiophene) - P3HT, polyparaphenylene, polypyrrole, polyaniline), semiconductors (Si, Ge, GaAs and others), carbon (graphene, reduced graphene oxide, carbon nanotubes, fullerenes and others), molecules with a conjugated pi system (perylene, 3,4,9,10-perylenetetracarboxylic acid dianhydride - PTCDA and its derivatives, naphthalene derivatives, hexabenzocorons and others), or conductive biomolecules such as proteins (native and recombinant proteins, e.g., from bacteria such as cable bacteria).The gate electrode, which is the electrode onto which the aptamers are applied, can be located next to the channel, on the channel, or in the sample liquid. Furthermore, an extended-gate configuration can be used, in which the gate is located in the sample liquid, but the channel is not. Within the scope of the present invention, organic electrochemical transistors (OECTs) are preferably used, the channel material of which consists of conductive polymers, with PEDOT / PSS being particularly preferred as the channel material. The aptamers can also be applied to or incorporated into the channel material.

[0037] The electrodes of the biosensors according to the invention can vary in their dimensions and spacing, the latter being particularly relevant for transistors, without compromising their functionality for biomarker detection. Within the scope of the present invention, the electrodes are not limited in their precise design but can have conventional, known configurations. The electrode itself can be a simple metal surface, or, for example, a conductive trace etched onto or from a substrate, or a wire. The area of ​​the electrode to which the aptamers are bound can have various structures; it is only necessary that the resulting surface area of ​​this electrode region is sufficient to bind the desired or necessary amount of aptamer.

[0038] Within the scope of the present invention, the method described above and below, in which electrodes are incubated with the various aptamer solutions, is not the only way to immobilize different aptamers. In other preferred embodiments, this can be achieved by many other methods, such as, in particular, electrochemical molecular stripping, printing, spotting, or lithography.

[0039] The aptamers according to the invention are preferably bound to the electrode surfaces via bonding groups. The bonding groups can anchor or immobilize the aptamers to the solid phase / electrode via monothiol bonds or multithiol bonds, through RSSR' groups, RSR' groups, R-NH2 groups, R-CS2 groups, R-CN groups, where R and R' are any linear aliphatic or aromatic molecules with a chain length of less than 100 nm, preferably with a chain length of less than 10 nm, where R can be different from R', methyl carbodithioate esters, or via other covalent bonds. They can also be anchored to the solid phase, in particular the electrode, via oligonucleotides or high-affinity groups (biotin-streptavidin coupling). The coupling of the aptamers can also occur via amide bonds, carbonyl-like formation of carbamides and amides, or ester groups. The binding can occur via click reactions (e.g.,Azide-alkyne cycloaddition, Huisgen cycloaddition, Diels-Alder reaction, epoxidation reactions).

[0040] HS-(CH2)6 groups are particularly favored, especially those coupled at the 5' end of the aptamer (making the aptamer a modified one).

[0041] According to the invention, polyethylene glycol thiol solution is particularly preferred as a blocking molecule to prevent biofouling by other molecules present in the samples (non-specific binding of matrix components). However, the present invention is not limited to polyethylene glycol thiol solution. Other blocking molecules that can be used include, for example, 6-mercapto-1-hexanol, bovine serum albumin or albumins from other animals, betaines, zwitterionic phenyl layers such as phenylphosphorylcholine (PPC), phenylbutyric acid, poly(sulfobetaine-3,4-ethyl-ene-dioxythiophene), polysulfobetaine methacrylates, polycarboxybetaine methacrylates, or mixtures thereof, proteoglycans such as Lubricin, hydrogels, and 2-methacryloyloxyethyl phosphorylcholine. Other known blocking molecules can also be used.

[0042] In preferred embodiments, polyethylene glycol thiol, 6-mercapto-1-hexanol or longer-chain molecules of the same structure as well as bovine serum albumin are used.

[0043] In some embodiments of the present invention, conductive polymers such as poly(3,4-ethylenedioxythiophene)-polystyrenesulfonate can be used as an aptamer-embedding electrode coating to increase the density of aptamers on the electrode surface. It is also possible to use conductive 3D scaffolds, i.e., micro- and nanoframeworks made of metals, carbon, and conductive polymers, such as nanomaterials like nanoporous gold, platinum black, nanostructured gold, MOFs, dendritic molecules, and polyvalent molecules (see also above).

[0044] When the biosensors according to the invention are used in conjunction with or on multi-electrode arrays, further receptors (for example, antibodies or aptamers) can be bound to the solid phase or to the individual electrodes, which bind further relevant biomarkers. These biomarkers can be biomarkers for dementia, specifically for Alzheimer's disease, or also neurotransmitters, other neurochemicals, hormones, or energy carrier molecules.

[0045] If the sensors used are OECT devices, in some preferred embodiments each transistor can be assigned a receptor that binds and thus detects the corresponding biomarker. The same applies if the detection is electrochemical and the sensors consist of electrode arrays. In this case, in some preferred embodiments each electrode can be assigned a receptor that binds and thus detects the corresponding biomarker.

[0046] If detection is performed via optical determination or methods and the (modified) aptamers, especially aptamers modified with fluorophores, are present in solution, further receptors (e.g., antibodies or aptamers) that bind further relevant biomarkers can also be added to the analyte solution if they have been modified with further fluorophores and are excited at other wavelengths or emit fluorescence radiation.The biomarkers can include tau proteins, amyloid peptides, glial fibrillary acid protein (GFAP), apolipoprotein E, synaptosomal-associated protein 25 kDa (SNAP-25), growth-associated protein 43 (GAP-43), beta-secretase (BACE1), Alzheimer's-associated neuronal thread protein (AD7C-NTP), alpha-1 antitrypsin (AAT), amyloid precursor protein (APP), neurogranin, growth differentiation factor 15 (GDF15), neuron-specific enolase (NSE), insulin growth factor binding protein 7 (IGFBP 7), TDP-43 protein (transactive response DNA binding protein 43 kDa), neuronal pentraxin 2 (NPTX2), and soluble triggering. Receptor expressed on myeloid cells 2 (sTREM2), interleukin-6, chitinase-3-like protein 1 (CHI3L1 / YKL-40), the APOE4 gene or others.

[0047] In a preferred embodiment of the present invention, when used in assays or, in other words, when used in the form of electrode arrays, it is also possible to apply molecules other than passivation molecules or receptors without binding affinity to one or more individual electrodes instead of the desired aptamers or other analytically active aptamers or biomarkers. Electrodes modified with these molecules can then be used as control sensors.

[0048] Other optical assays include enzyme-linked oligonucleotide assays (ELONA), surface plasmon resonance assays, lateral flow assays, and ALPHAScreen. ® Assays, ALPHALisa ® These could be assays, microscale thermophoresis assays, or electrophoretic mobility-displacement assays.

[0049] The present invention provides methods for detecting NFL as an Alzheimer's disease (AD) biomarker in blood samples using an electrochemical biosensor. These methods are based on the fact that the NFL concentration in the blood, serum, or cerebrospinal fluid (CSF) of AD patients increases even before cognitive impairments become evident. These detection methods (tests) according to the invention are inexpensive and minimally invasive, as only a small amount (<10 ml) of blood, serum, or CSF is required. The detection methods (tests) according to the invention can be performed preventively and locally in a broad population at the point of care (physician's office) before cognitive impairments are detected.

[0050] The biosensors according to the invention use single-stranded deoxyribonucleic acid (ssDNA) molecules as aptamer receptors that selectively bind NFL. These aptamers are preferably generated by in vitro selection (systematic evolution of ligands by exponential enrichment - SELEX). DNA aptamers offer significant advantages over antibodies for use as receptors in biosensors. They are smaller, more thermally stable, easily chemically modifiable, and can be synthesized inexpensively. Within the scope of the present invention, the aptamers are immobilized on electrodes, transistors, or other signal transducers, together with molecules that suppress the non-specific binding of sample components (blood, serum, CSF). The biosensor thus generated is exposed to the sample, causing the NFL contained therein to bind to the aptamers bound to the signal transducer.The signal transducer registers this binding process and converts it into a quantifiable electrical signal. This signal can be used automatically or by a user, preferably a physician, for diagnosis. In embodiments of the present invention, the signal transducer can also be a multi-channel (electrode) system (array) on which various aptamer receptors for NFL or other AD biomarkers, such as amyloid-beta oligomers, tau protein, or others, can be immobilized and detected.

[0051] Within the scope of the present invention, it is assumed that at least one aptamer receptor for NFL, also referred to simply as an aptamer within the scope of the present invention, which is determined by SELEX and which selectively binds to NFL, is used. Within the scope of the present invention, the aptamer receptors (aptamers) are combined with at least one signal transducer that can detect the binding of the aptamer to NFL molecules and convert it into an electrical signal. Within the scope of the present invention, the signal transducer must not be influenced by matrix components of the sample.

[0052] The aptamers according to the invention can also be used in or for the production of biosensors according to the invention that are not based on electrochemical principles, but rather on optical, magnetic, gravimetric, or other transducer principles (transducer = signal converter). Furthermore, the aptamers according to the invention can be used for essentially all forms of application that have already been established for antibodies, e.g., as therapeutics or as affinity tags.

[0053] The present invention relates, in one aspect, to aptamer molecules, in particular those based on single-stranded deoxyribonucleic acid, for binding to neurofilament light (NFL), and to the use of these aptamer molecules as receptors in biosensors. These biosensors can be used for the detection of neuronal tissue degradation, particularly in the early detection of neurodegenerative processes such as those occurring in Alzheimer's disease and other dementias, by detecting neurofilament light as a biomarker. The detection of the biomarkers can be carried out in body fluids, in particular in blood, serum, or cerebrospinal fluid (CSF).This application describes the detection of NFL as an AD biomarker in body fluids, particularly blood samples, using a biosensor. This is because the NFL concentration in body fluids, preferably blood, serum, or cerebrospinal fluid (CSF), increases in AD patients even before cognitive impairments become evident. The biosensor according to the invention uses single-stranded deoxyribonucleic acid (ssDNA) molecules that selectively bind NFL as aptamer receptors. These aptamers are generated within the scope of the present invention by in vitro selection (systematic evolution of ligands by exponential enrichment - SELEX). DNA aptamers offer significant advantages over antibodies for their use as receptors in the development of biosensors. They are smaller, more thermally stable, easily chemically modifiable, and can be synthesized inexpensively.Because aptamers are produced through chemical synthesis rather than biological processes like cell culture expression, bacterial and viral contamination can be avoided, large synthesis volumes can be achieved, and batch variations can be reduced. Aptamers elicit weaker immune responses, and their small size (<30 kDa compared to ~150 kDa for antibodies) makes them accessible to epitopes on the target molecule to which antibodies cannot bind for steric reasons. Conformal changes in the structure of aptamers resulting from prolonged storage can be reversed by simple warming and cooling protocols, thereby improving their shelf life and reducing storage and transportation costs.

[0054] Despite their robust and simple structure, aptamers can bind to their target molecules with high specificity, selectivity, and affinity. According to the invention, the aptamers or modified aptamers can be freely present in the sample solution (in the binding assay) or immobilized on electrodes, transistors, nanomaterials, or other signal transducers. Each is combined with molecules that suppress the non-specific binding of sample components (blood, serum, CSF). Furthermore, the aptamers can be modified with probe molecules, such as fluorophores, nanomaterials, enzymes, or redox molecules, to enable or enhance signal transduction. Additionally, binding groups or other functional groups can be conjugated to the aptamers. The biosensor thus generated according to the invention is then exposed to the sample, causing the NFL contained therein to bind to the aptamers, which may be immobilized on a signal transducer.

[0055] Detection of the NFL biomarker in body fluids using the inventive method (test) is inexpensive and minimally invasive, as only a small amount (<10 ml) of body fluid, preferably blood, serum, or CSF, is required (for the assay). The inventive method (test) can potentially be performed preventively and decentrally in a broad population at the point of care (physician) before cognitive impairments are detected.

[0056] The aptamers according to the invention can be used, among other things and preferably, for the electrochemical, optical, electrical, magnetic, gravimetric biosensors according to the invention, or sensors based on other transducer principles (transducer = signal converter). Optical, electrochemical, and electrical (OECT) transducers are preferred within the scope of the present invention.

[0057] Furthermore, the aptamers according to the invention can potentially be used for all forms of application already established for antibodies, e.g., as therapeutics, as affinity tags, for labeling systems containing NFL, or for quality control. As oligonucleotides, the ssDNA aptamers can be used as reagents for technologies based on nucleic acid systems, such as DNA nanotechnology, DNA pharmaceuticals, DNA computing, or others.

[0058] Electrochemical biosensors are superior to other sensor systems due to their high sensitivity, ease of handling and manufacturing, the possibility of miniaturizing electrodes, and their ability to be parallelized for the simultaneous (or multiplexed) detection of redundant or complementary sensor signals. They are therefore particularly suitable for point-of-care applications. Similar advantages apply to sensors based on OECTs, except that these contain three electrodes as a component and offer lower detection limits.

[0059] Accordingly, optical sensors, electrochemical biosensors, and sensors based on OECT are particularly preferred according to the invention. However, the present invention is not limited to these.

[0060] The sensors or biosensors according to the invention, with the exception of the optical sensor, are based on metal electrodes, which can be configured as individual components or as component arrays. According to the invention, aptamer molecules that bind NFL are immobilized on these electrodes. In the case of component arrays, further receptors (for example, antibodies or aptamers) can be bound to the individual components, which bind further relevant biomarkers; see, for example, but not exclusively, the examples. In preferred embodiments, in addition to the aptamers, blocking molecules are bound to the electrodes, which suppress non-specific binding of matrix molecules. Upon contact of the sensor with the sample to be examined (body fluid, for example, CSF, blood, or serum, in particular blood), the binding of NFL to the aptamer molecules is measured electrochemically / electrically.

[0061] The present invention relates to specific ssDNA molecules in an article, which are used as aptamers and have a defined sequence of deoxyribonucleotides capable of binding neurofilament light with high specificity and affinity. These molecules were selected from an ssDNA library by incubating the library with NFL. The binding ssDNA molecules were separated from non-binding ssDNA molecules by capillary electrophoresis. The binding ssDNA molecules were then isolated and amplified. The sequence of the aptamers was derived from the binding ssDNA molecules by sequencing and subsequent in silico analysis.

[0062] Aptamers are composed of the nucleotides adenine (A), guanine (G), cytosine (C), uracil (U) and thymine (T) or derivatives of these nucleotides with chemical modifications such as methylations, mirror nucleotides or other sugar-modified nucleotides, nucleobase-modified nucleotides and backbone-modified nucleotides.

[0063] In the context of the present invention, the term "derivative" in some preferred embodiments refers to an aptamer that is chemically modified at the nucleobase, the pentose, or the phosphate backbone and that has a chemical structure not found in natural DNA or RNA. In particular, the term "derivative" refers to an aptamer that contains a chemical structure different from deoxyribose, ribose, phosphate, adenine, guanine, cytosine, thymine, or uracil. An aptamer derivative may be modified at the nucleobase, the pentose, or the phosphate backbone.Within the scope of the present invention, the term “derivative” may refer to an aptamer in which nucleotides naturally occurring in DNA and RNA are partially or completely replaced by chemically different nucleotides, so-called modified nucleotides, and / or whose molecular structure is otherwise modified, in particular by the attachment of structures not naturally occurring in RNA or DNA, and / or which has a modified backbone.

[0064] Some non-limiting, specific examples of derivatives within the scope of the present invention are: - Aptamers that have an alkylation, arylation or acetylation, alkoxylation, halogenation, an amino group or another functional group on at least one nucleotide; - Aptamers that exhibit a base modification, such as bromouridine, especially modifications that increase hydrophobicity; - Labeled aptamers, also referred to as labeled aptamers, wherein preferred labels are visually, optically, photonically, electronically, acoustically, opto-acoustically, by mass, electrochemically, electro-optically, spectrometrically, enzymatically, or otherwise chemically, biochemically, or physically detectable, and wherein labels can be, for example, attached reporter, marker, or adapter molecules; examples of which are labeled aptamers whose labeling can be detected by luminescence, UVNIS staining, enzymatically, electrochemically, immunologically, or radioactively (examples of labeling substances preferably used according to the invention can be found elsewhere in the description); - Aptamers that have enantiomeric nucleotides; - Aptamers that are wholly or partially composed of phosphorus thioate RNA or DNA, phosphorus dithioate RNA or DNA, phosphorus selenoate RNA or DNA, phosphorus diselenoate RNA or DNA, phosphoroamidate RNA or DNA, locked nucleic acid (LNA), peptide nucleic acid (PNA), N3'-P5' phosphoramidate RNA / DNA, cyclohexene nucleic acid (CeNA), tricyclo-DNA (tcDNA) or mirror mer, or that contain phosphoramidate morpholine (PMO) components. - Aptamers that exhibit wholly or partially modified ribose, such as 2'-fluoro nucleic acids, 2'-fluoro arabino nucleic acids, 2',2'-difluorocytidines, closed nucleic acids, open nucleic acids, xenogenic nucleic acids. - Aptamers consisting wholly or partly of artificial nucleotides such as (7- (2-Thienyl) Imidazo [4, 5-b] Pyridine), 6-Amino-5-Nitro-3- (1'-β-D-2'-Deoxyribofuranosyl)-2 (1H)-Pyridone, 2-Amino-8- (1'-β-D-2'-Deoxy-ribofuranosyl)-Imidazo-[1,2-a]-1,3,5-Triazine-4.

[0065] The following Table 1 lists the optimized aptamers according to the invention: Table 1 Aptamers SEQIDNO: sequence Rank 1R Quantity.1R RPM.1R Rank 3R Number.3R RPM.3R Enrichment_3R&1R log2E_3R&1R 1 GCATACTTGGCGAGTCCTAACAGGTATTGGTCAAGGTACGATTG 228038 2 1.8 1 1189 1773.83 985.461 9.945 2 TCCCTCCATCTAAGCCTTTATTTCGTATGTCGTCGAAGGTGTG 502225 1 0.9 9 299 446.07 495.633 8.953 3 CATAGCCCGCGCAATCTACGTAGACACACCTAACGAAACCAAC 192297 2 1.8 8 329 490.82 272.678 8.091

[0066] Aptamer sequences: Aptamer FZJ-NFL_1 (Aptamer 1), GCA TAC TTG CGA GTC CTA ACA GGT ATT GGT CAA GGT ACG ATT G Aptamer FZJ-NFL_2 (Aptamer 2), TCC CTC CAT CTA AGC. CTT TAT TTC GTA TGT CGT CGA AGG TGT G Aptamer FZJ-NFL_3 (Aptamer 3), CAT AGC CCG CGC AAT CTA CGT AGA CAC ACC TAA CGA AAC CAA C

[0067] These aptamers can have 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, or 19 modifications in the sequence to increase their specificity or affinity. These modifications can include the removal, substitution, and / or extension of the original sequence, or substitution, deletion, and / or insertion. This can result in sequences that exhibit 95%, 90%, 85%, 80%, 75%, 70%, 65%, 60%, or 50% sequence similarity with the original aptamers.

[0068] Stem-loop structures (secondary stem-loop structures occurring in single-stranded DNA or RNA with a double-stranded stem and a short single-stranded loop; also called hairpin structures) are particularly protected, as they are crucially involved in binding to NFL.

[0069] Aptamer FZJ-NFL_1 features three stem-loop structures. The numbering starts at the 5' end and continues to the 3' end. Accordingly, nucleotides 1 to 10 (GCATACTTGC), nucleotides 15 to 23 (CCTAACAGG), and nucleotides 31 to 43 (CAAGGTACGATTG) are particularly crucial for the aptamer's functionality; see [reference]. Fig. 24.

[0070] The stem-loop structures of FZJ-NFL_2 comprise nucleotides 14 to 40, but nucleotides 18 to 22 lack base pairing and are particularly protected, see Fig. 25.

[0071] The stem-loop structures of aptamer FZJ-NFL_3 can form two stem-loop structures, which include nucleotides 5 to 12 (GCCCGCGC) and nucleotides 19 to 35 (CGTAGACACACCTAACG), which are particularly protected, see Fig. 26.

[0072] These aptamers according to the invention can contain further functional groups, which are preferably attached to the 3' or 5' end of the aptamer or can be located on or between (intercalated) the nucleotides. These molecules can be probe molecules such as fluorophores, nanomaterials (silver nanoparticles, platinum nanoparticles, quantum dots, magnetic nanoparticles, etc.), enzymes (horseradish peroxidase, glucose oxidase, and others), or redox molecules (ferrocene, methylene blue, anthraquinone, etc.) that indicate the presence of the aptamer, enable signal transduction, or amplify or attenuate the signal.

[0073] Examples of fluorophores preferably used according to the invention are those selected from the group consisting of cyanine 5 (Cy5), green fluorescent protein (GFP), the group of xanthene dyes, Texas Red, fluorescein and its derivatives, G-Dye100, Nile blue, and mixtures thereof, particularly preferably cyanine 5.

[0074] Examples of nanomaterials preferably used according to the invention are those selected from the group consisting of silver nanoparticles, nanoparticles with catalytic properties consisting of platinum, iridium, cobalt, ruthenium, nickel, cerium, quantum dots, magnetic nanoparticles, photon upconverting nanoparticles such as NaYF4:Yb / Er and NaYF4:Yb / Tm and mixtures thereof, preferably magnetic nanoparticles of Fe3O4 or other stoichiometry, MeFe2O4 (Me=Co, Cu, Mn, Zn, Ni), metal nanoparticles of Fe, Ni, Co, Pd, or one of these particles decorated with each of a metal of Fe, Ni, Co, Pd, or one of these particles decorated with organic molecules, biomolecules, polymers or inorganic films such as SiOx, AlOx, TiOx.

[0075] Examples of enzymes preferably used according to the invention are those selected from the group consisting of horseradish peroxidase, glucose oxidase, phosphatase, ferredoxin, hydrogenase, and mixtures thereof, preferably horseradish peroxidase. Examples of redox molecules preferably used according to the invention are those selected from the group consisting of ferrocene, methylene blue, anthraquinone, Nile blue, phenazine ethosulfate, organometallic complexes such as porphyrins, cyanines, [Os(4,4'-dimethyl-2,2-dipyridil)2Cl(4-(aminomethyl)pyridine)], tetrathiafulvalene, and mixtures thereof, preferably methylene blue.

[0076] Examples of bonding groups that can be preferably used according to the invention are monothiols (e.g. alkanethiols HS-(CH2) n-), disulfides RSS-R', R-NH2 groups, R-CS2 groups, R-CN groups, wherein R and R' = any linear aliphatic or aromatic molecules with a chain length of less than 100 nm, particularly preferably with a chain length of less than 10 nm, wherein R can be different from R', methyl carbodithioate esters, preferably multithiol bonds such as bis-dithiolphosphoramidite or tris-dithiolphosphoramidite.

[0077] Furthermore, these binding groups can be attached to the sensor surface by single-stranded DNA molecules that are complementary or partially complementary to the aptamer sequence and hybridize with it, thus enabling immobilization of the aptamer. This hybridization can be designed to be broken and the aptamer separated when the target molecule binds. Hybridization of complementary or partially complementary single-stranded DNA molecules can also occur when the aptamer is directly hybridized to the sensor surface.

[0078] Furthermore, the present invention relates to sensors for the detection of NFL. The sensors according to the invention contain aptamers FZJ-NFL_1, 2, or 3, or combinations thereof. When NFL is bound, a signal is generated which can be evaluated qualitatively or additionally or alternatively quantified.

[0079] The biomarker sensors according to the invention can be used in automated multititer plates.

[0080] The samples, preferably body fluids, particularly preferably blood, serum or CSF, especially blood, can be processed or prepared before use in the method of the present invention in accordance with methods customary in the trade.

[0081] It should be noted that the method of the present invention is particularly suitable and intended for examining body fluid samples, especially blood, which are already available as such; i.e., the taking of body fluids is not part of the method of the present invention.

[0082] Some, but not all, advantages of the present invention are the following: - The method according to the invention is minimally invasive. The body fluid required for the test can, for example, also be obtained during a fluid withdrawal (blood draw) performed for another reason. - The method according to the invention is inexpensive. - The method according to the invention can be carried out preventively. - The method according to the invention can be carried out decentrally, even at the doctor's office (point-of-care), for a broad segment of the population. - The aptamers according to the invention exhibited a high specificity and affinity for Neufilament Light. - The aptamers according to the invention are highly selective towards neurofilament light. - The aptamers according to the invention exhibit high chemical stability. - The aptamers according to the invention exhibit low immunogenicity. - The aptamers according to the invention

[0083] Within the scope of the present invention, in addition to the inventive method, both aptamer molecules that bind selectively and with high affinity to neurofilament light, as well as sensors and assays for the detection of neurofilament light, are provided. These inventive aptamer molecules, sensors, and assays, as well as the inventive method itself, are usable at the point of care, cost-effective to produce, exhibit high stability, are easy to use, and have high test accuracy; they are therefore particularly advantageous.

[0084] The invention is explained in more detail below with reference to the figures. The figures are not necessarily to scale and are simplified. For example, common measures and device elements familiar to those skilled in the art (circuitry, walls, precise molecular structure, etc.) are not necessarily shown to improve the readability of the figures. Character description: Fig. Figure 1 shows a schematic for an optical assay according to the present invention and the associated components consisting of aptamer 1 with fluorophore 2 and analyte NFL 3. When the aptamer 1 binds to the NFL 3, the polarization of the fluorescence of the fluorophore 2 changes, which is detectable and serves as a measurement signal.

[0085] This figure shows that a fluorophore binds to the 3' end of the aptamer and, via binding to NFL, fluoresces. A possible connection between the aptamer and the electrode surface via the 5' end is illustrated in other figures.

[0086] Fig. Figure 2 shows a calibration curve of the optical assay for the modified Aptamer_FZJ-NFL_opt1 according to Example 3, recorded by fluorescence polarization as a function of concentration. The linear detection range of the optical assay starts from about 17 nM and extends to 1000 nM. D The value is 181.73 nM ( Fig. 2, upper curve). The modified aptamer_FZJ-NFL_opt1 shows no binding affinity to human serum albumin, which underlines the high specificity of the aptamers ( Fig. 2 lower curve).

[0087] Calibration is achieved by first measuring the polarization of the fluorescence light for different analyte concentrations (NFL) and fitting it using the Hill equation. Subsequently, by measuring the polarization of the fluorescence light from a solution of unknown concentration, the concentration can be determined using the fitted function.

[0088] K D The dissociation constant is obtained by fitting the curve using a suitable model, preferably the Hill equation. The plotted mP value is a dimensionless measure of the polarization of the fluorescence light and is also referred to as millipolarization. The results demonstrate the high affinity and specificity of the optical assay.

[0089] Fig. Figure 3 shows a calibration curve of the optical assay for the modified aptamer_FZJ-NFL_opt2 according to Example 3, recorded by fluorescence polarization as a function of concentration. The linear detection range of the optical assay starts from about 30 nM and extends to 1000 nM. D The value is 100.25 nM for Aptamer_FZJ-NFL_opt2 ( Fig. 3 upper curve). The modified aptamer_ FZJ-NFL_opt2 shows no binding affinity to human serum albumin, which underlines the high specificity of the aptamers ( Fig. 3 lower curve). The results demonstrate the high affinity and specificity of the optical assay.

[0090] Fig.Figure 4 shows a calibration curve of the optical assay for the modified aptamer_FZJ-NFL_opt3 according to Example 3, recorded by fluorescence polarization as a function of concentration. The linear detection range of the optical assay starts from about 30 nM and extends to 1000 nM; the K D The value is 124.80 nM for Aptamer_FZJ-NFL_opt3 ( Fig. 4 upper curve). The modified Aptamer_FZJ-NFL_opt3 shows no binding affinity to human serum albumin, which underlines the high specificity of the aptamers ( Fig. 4 lower curve). The results demonstrate the high affinity and specificity of the optical assay.

[0091] Fig.Figure 5 shows a schematic representation of chemical components of the electrochemical assay that can be used and are preferred within the scope of the present invention. On the left is the aptamer 1 including bonding group parts 4, 5 attached to the 5' end (HS-SH-C6 aptamer), in the middle a blocking molecule (thiol-PEG 2000) 6 and on the right a redox probe ([Fe(CN)6] 3- / 4- / 7. Although not shown in this figure, in the present invention a fluorophore is preferably attached to the 3' end of the aptamer in order to indicate the presence of the analyte by changing the fluorescence behavior (see also Fig. 1) Where the term aptamer is used below in relation to the figure descriptions, the possibility of a fluorophore bound to the 3' end is always implied, at least as an alternative.

[0092] Fig.Figure 6 schematically illustrates the individual modification steps for functionalizing an electrode for an electrochemical assay according to the inventive method using a microelectrode onto which a microelectrode 8 is first applied. A receptor layer comprising the aptamer 1 is then deposited. The aptamer 1 shown here is a modified aptamer (HS-SH-C6 aptamer) 1, 4, 5 and, in addition to the aptamer 1 itself, also comprises binding group components 4 and 5. The next step shows how blocking molecules (for example, thiol-PEG 2000) 6 are immobilized on the electrode surface. Finally, the process of applying redox probes 7 is shown. The detection of NFL can then be performed using the electrodes / assays thus produced.

[0093] Fig.Figure 7 shows electrochemical impedance spectra recorded in a Nyquist plot using an electrochemical assay based on Aptamer_FZJ-NFL_EC1 according to Example 1 for different NFL concentrations. Test buffer 1 (50 mM Tris-acetate buffer, 50 mM tris(hydroxymethyl)aminomethane buffer and acetic acid to pH 8.2, 5 mM [Fe(CN)6]) was used as the buffer. 3- / 4- The real part of the impedance is plotted on the abscissa and the imaginary part on the ordinate. With increasing NFL concentration (see legend), the charge transfer resistance (minimum on the right side of the semicircle) increases due to the binding of NFL to the aptamer-coated electrode surface.

[0094] Fig. Figure 8 shows the calibration curve. Fig. 7 recorded with the electrochemical assay based on Aptamer_FZJ-NFL_EC1. The K DThe aptamer's ΔR value is 0.34 nM. The change in charge transfer resistance (minimum on the right side of the semicircle) was used as the signal ΔR. Fig. 7) used when changing NFL concentration.

[0095] Fig. Figure 9 shows the electrochemical impedance spectra recorded in a Nyquist diagram using an electrochemical assay based on Aptamer_FZJ-NFL_EC2 according to Example 1 for different NFL concentrations. Test buffer 1 (50 mM Tris-acetate buffer, 50 mM tris(hydroxymethyl)aminomethane buffer and acetic acid to pH 8.2, 5 mM [Fe(CN)6]) was used as the buffer. 3- / 4- The real part of the impedance is plotted on the abscissa and the imaginary part on the ordinate. With increasing NFL concentration (see legend), the charge transfer resistance (minimum on the right side of the semicircle) increases due to the binding of NFL to the aptamer-covered electrode surface.

[0096] Fig.10 shows the calibration curve. Fig. 9 recorded with the electrochemical assay based on Aptamer_FZJ-NFL_EC2. The K D The aptamer's ΔR value is 0.41 nM. The change in charge transfer resistance (minimum on the right side of the semicircle) was used as the signal ΔR. Fig. 9) used when changing NFL concentration.

[0097] Fig. Figure 11 shows the electrochemical impedance spectra recorded in a Nyquist diagram using an electrochemical assay based on Aptamer_FZJ-NFL_EC3 according to Example 1 for different NFL concentrations. Test buffer 1 (50 mM Tris-acetate buffer, 50 mM tris(hydroxymethyl)aminomethane buffer and acetic acid to pH 8.2, 5 mM [Fe(CN)6]) was used as the buffer. 3- / 4-The real part of the impedance is plotted on the abscissa and the imaginary part on the ordinate. With increasing NFL concentration (see legend), the charge transfer resistance (minimum on the right side of the semicircle) increases due to the binding of NFL to the aptamer-covered electrode surface.

[0098] Fig. 12 shows the calibration curve. Fig. 11 recorded with the electrochemical assay based on Aptamer_ FZJ-NFL_EC3. The K D The aptamer's ΔR value is 0.18 nM. The change in charge transfer resistance (minimum on the right side of the semicircle) was used as the signal ΔR. Fig. 11) used when changing NFL concentration.

[0099] Fig.Figure 13 shows in a Nyquist diagram the electrochemical impedance spectra recorded with an electrochemical assay based on Aptamer_FZJ-NFL_EC1 for different NFL concentrations in phosphate buffer with a high salt concentration and an extended concentration range. Test buffer 2 (10 mM PBS, pH 7.4, 137 mM NaCl, 2.7 mM KCl, 5 mM [Fe(CN)6]) was used as the buffer. 3- / 4- The real part of the impedance is plotted on the abscissa and the imaginary part on the ordinate. With increasing NFL concentration (see legend), the charge transfer resistance (minimum on the right side of the semicircle) increases due to the binding of NFL to the aptamer-covered electrode surface.

[0100] Fig. 14 shows the calibration curve. Fig. 13 recorded with the electrochemical assay based on Aptamer_ FZJ-NFL_EC1. The K DThe ΔR value of the aptamer in high-salt phosphate buffer is 0.23 nM. The change in charge transfer resistance (minimum on the right side of the semicircle) was used as the signal ΔR. Fig. 13) used when changing NFL concentration.

[0101] Fig. Figure 15 shows a Nyquist plot of the electrochemical impedance spectra recorded with an electrochemical assay based on Aptamer_FZJ-NFL_EC1 for different NFL concentrations. Human serum was used as the buffer (diluted 10-fold with test buffer 2). The real part of the impedance is plotted on the abscissa and the imaginary part on the ordinate. With increasing NFL concentration (see legend), the charge transfer resistance (minimum on the right side of the semicircle) decreases due to the binding of NFL to the aptamer-covered electrode surface.

[0102] Fig. 16 shows the calibration curve. Fig.15 recorded using the electrochemical assay based on Aptamer_FZJ-NFL_EC1 in artificial blood. The K D The aptamer value in artificial blood is 0.48 nM. The change in charge transfer resistance (minimum on the right side of the semicircle) was used as the signal ΔR. Fig. 15) used when changing NFL concentration.

[0103] Fig. Figure 17 schematically shows an interdigitating electrode pair (in the present invention, this means a pair of electrodes with interlocking and opposing electrode fingers) of a transistor usable according to the invention, wherein one electrode functions as the source electrode 12 and the other as the drain electrode 13 (the left / right arrangement is arbitrary). The electrodes have fingers 9, which increase the width of the electrode channel. The conductive polymer 11, which forms the channel of the OECT 10, is located on the electrode pair.

[0104] The source and drain electrodes consist of interdigitating electrodes, where a number of electrode fingers increase the width W of the OECT channel. f represents the length of each individual electrode finger. W f defines the width of the electrode fingers and L ch This specifies the length of the OECT channel (distance between the source and drain electrodes). The number of fingers is two in the example shown here, but can be increased within the scope of the present invention to increase the amplification factor. The number of fingers is optimized against the area requirement of the OECT. L f For example, 25 micrometers and W 30 micrometers. W f This corresponds to 5 micrometers, which is the channel length L ch This corresponds to the gate electrode, for example, having a diameter of 0.5 millimeters and a distance to the channel of, for example, 50 micrometers.

[0105] Fig.Figure 18 schematically shows an interdigitating electrode pair according to Fig. 17 with associated leads and contact surfaces, as well as the conductive polymer 11 located on channel 10. Additionally, the gate electrode 8 of the transistor usable according to the invention is shown, located 50 µm away from the interdigitating electrode pair 12, 13 with 10 and 11. The gate electrode is shown arranged laterally in this figure. However, the present invention is not limited to this; for example, it is equally possible to arrange the gate electrode on the opposite side or above or below (which may be more complex to implement). Likewise, the distance of the gate electrode is not limited to the specified value. It should be noted that the metal electrodes are produced first, and then the polymer is deposited on them; to illustrate this, in Fig. 18 and Fig. 19 Polymer 11 is shown with an arrow, which means that it is deposited later, not that polymer 11 lies on the electrodes 12, 13.

[0106] Fig. 19 illustrates the arrangement according to Fig. 18, wherein a modified aptamer consisting of 1, 4 and 5 and a blocking molecule (for example, Thiol-PEG 2000) 6 are additionally present on the gate electrode 8.

[0107] Fig. Figure 20 shows the transfer curves of an OECT according to Example 2 and correspondingly Fig.19. Based on Aptamer_FZJ-NFL_EC1 in PBS buffer (PBS = phosphate-buffered saline) with varying NFL concentrations. The abscissa represents the voltage between the source and gate electrodes, and the ordinate represents the current flowing between the source and drain electrodes. Measurements were taken with a source-drain voltage of -0.1 V and a gate voltage ranging from -0.2 V to 1.0 V. The step size was 10 mV and the voltage scaling rate was 137 mV / s.

[0108] Fig. 21 shows the calibration curve. Fig. 20 samples were recorded using the assay based on an OECT in combination with aptamer FZJ-NFL EC1 in PBS buffer with varying NFL concentrations. Signal ΔV T The change to the K was D The aptamer's value is 0.003 nM.

[0109] Fig. Figure 22 shows the transfer curves of an OECT according to Example 2 and correspondingly Fig.19. Based on Aptamer_FZJ-NFL_EC1 in human serum with varying NFL concentrations. The abscissa represents the voltage between the source and gate electrodes, and the ordinate represents the current flowing between the source and drain electrodes. Measurements were taken with a source-drain voltage of -0.1 V and a gate voltage ranging from -0.2 V to 1.0 V. The step size was 10 mV and the voltage scaling rate was 137 mV / s.

[0110] Fig. 23 shows the calibration curve. Fig. 22 samples were recorded using the assay based on an OECT in combination with aptamer_FZJ-NFL_EC1 in human serum diluted 10-fold with test buffer 2 at different NFL concentrations. Signal ΔV T The change in threshold voltage (the voltage at which current just begins to flow) was used in response to changes in NFL concentration. The K D The aptamer's value is 0.003 nM.

[0111] Fig. Figure 24 illustrates the two-dimensional structure of the aptamer FZJ-NFL_1 according to the invention, which can have three stem-loop structures. The numbering starts at the 5' end and continues to the 3' end. Accordingly, nucleotides 1 to 10 (GCATACTTGC), nucleotides 15 to 23 (CCTAACAGG), and nucleotides 31 to 43 (CAAGGTACGATTG) are particularly crucial for the functionality of the aptamer.

[0112] Fig. Figure 25 illustrates the two-dimensional structure of the aptamer FZJ-NFL_2 according to the invention. The stem-loop structures comprise nucleotides 14 to 40 (GCCTTTATTTCGTATGTCGTCGAAGGT), wherein nucleotides 18 to 22 (TTATT) do not have base pairing.

[0113] Fig. Figure 26 illustrates the two-dimensional structure of the aptamer FZJ-NFL_3 according to the invention. The structure can form two stem-loop structures, which comprise nucleotides 5 to 12 (GCCCGCGC) and nucleotides 19 to 35 (CGTAGACACACCTAACG). Reference symbol list:

[0114] In the figures, the same reference symbols signify the same materials, fabrics, etc. 1 Aptamer 2 Fluorophore 3 Analyte (Neurofilament Light - NFL) 4 Bond group part (for example HS-SH group (disulfide bridge) 5 bond group part (for example, -(CH2)6 chain) 6 Blocking molecule (for example, thiol-PEG 2000) 7 Redox probe (for example [Fe(CN)6] 3- / 4- / ) 8 Microelectrode (Gate electrode) 9 electrode fingers 10 OECT channel (organic electrochemical transistor channel with interdigitating electrode fingers) 11 conductive polymer 12 Microelectrode (source electrode) 13 Microelectrode (drain electrode) W Width of the OECT channel W f Width of an electrode finger L f Length of an electrode finger L chLength of the OECT channel

[0115] The present invention will now be explained in more detail with reference to the following non-limiting examples. These non-limiting examples serve to illustrate the embodiments described therein. It is known to those skilled in the art that variations of these examples are possible within the scope of the present invention. Examples:

[0116] The functionality of the following three embodiments was demonstrated by the detection of human neurofilament light polypeptide (NFL) expressed in E. coli (Biozol Biovender, molecular weight 62.5 kDa). Example 1: Electrochemical Assay

[0117] This embodiment describes a sensor based on an electrochemical transducer that enables a quantifiable correlation between the measurement signal and the net magnetic field (NFL) in the sample. The sensor uses metal electrodes, which can be implemented as single electrodes or as multi-electrode arrays. In this embodiment, gold electrodes were used. For the fabrication of the sensor, the electrodes were cleaned by rinsing for 5 minutes each in acetone and isopropanol, followed by rinsing with highly purified deionized water (from a Milli-Q® system (18.2 megaohms resistivity)) and drying in a nitrogen flow. The electrochemical cleaning of the electrodes was performed by cyclic voltammetry (CV) in 0.1 M NaOH in a potential range of -1.35 V to -0.35 V for 10 scans at 2 V s⁻¹, followed by scanning in 0.05 M H₂SO₄ in a potential range of 0 V to 1.5 V for 20 scans at 1 V s⁻¹.The electrochemical surface area (ESA) was determined by CV in 0.05 M H₂SO₄ in a potential range of 0 V to 1.5 V at 0.1 V s⁻¹. It should be noted that the exact cleaning procedure is highly dependent on the electrode material used and may include, for example, plasma cleaning steps or other methods; only the cleaning procedure performed in this example is described here.

[0118] After cleaning (activating) the electrode, the aptamers were bound to the electrode surfaces via bonding groups (in this case, thiol bonds).

[0119] In this embodiment, the aptamers were modified with an HS-SH-(CH2)6 binding group at the 5' end of the ssDNA, resulting in the following sequences: Aptamer_ FZJ-NFL_EC1, HS-SH-(CH2)6- GCA TAC TTG CGA GTC CTA ACA GGT ATT GGT CAA GGT ACG ATT G Aptamer_ FZJ-NFLEC2, HS-SH-(CH2)6- TCC CTC CAT CTA AGC CTT TAT TTC GTA TGT CGT CGA AGG TGT G Aptamer_ FZJ-NFL_EC3, HS-SH-(CH2)6- CAT AGC CCG CGC AAT CTA CGT AGA CAC ACC TAA CGA AAC CAA C

[0120] These modified aptamers were used in this example at a concentration of 0.05 µM each. All aptamers were incubated with 10 mM tris(2-carboxyethyl)phosphine hydrochloride (TCEP) solution for one hour at room temperature to cleave the disulfide protective bond and enable immobilization on the electrodes via a thiol-gold self-assembling monolayer. The aptamer solutions were mixed in 50 mM tris-acetate buffer (50 mM tris(hydroxymethyl)aminomethane, 1 M NaCl, 1 mM MgCl₂, pH 8.20). The electrodes were then incubated with the respective aptamer solution for 16 hours in the absence of light. The aptamer-modified electrodes were first rinsed with tris-acetate buffer and then with deionized water (Milli-Q). ® -water), to remove non-specifically adsorbed molecules.

[0121] The electrodes were incubated for 1 hour with a 5 mg / ml monofunctional methoxy polyethylene glycol thiol solution (1.5 mg / mL thiol-PEG 2000). The PEG served as a blocking molecule to prevent biofouling by other molecules present in the samples (non-specific binding of matrix components). The Apta sensor was incubated with 50 mM Tris acetate buffer (pH 8.2) and Milli-Q. ® -washed with water to remove excess non-specifically adsorbed PEG molecules.

[0122] Electrochemical impedance spectroscopy (EIS) measurements were performed to determine the detection of NFL in the samples by the aptamer sensors. For this purpose, the sensor was immersed for 30 minutes in 50 mM Tris acetate buffer (50 mM tris(hydroxymethyl)aminomethane and acetic acid at pH 8.2, 5 mM [Fe(CN)6] 3- / 4- ; Test buffer 1) or in 10m M PBS (pH 7.4, 137 mM NaCl, 2.7 mM KCl, 5 mM [Fe(CN)6] 3- / 4-; test buffer 2) or incubated in human serum diluted 10-fold with test buffer 2, the solutions containing different but defined concentrations of NFL.

[0123] EIS measurements were performed using an Autolab potentiostat (Metrohm) with a three-electrode system. A platinum wire served as the counter electrode (CE), an Ag / AgCl electrode as the reference electrode (RE), and the aptamer-modified electrodes as the working electrodes (WE). EIS measurements were conducted at a potential of 0.22 V, with an AC voltage amplitude of 0.01 V and a frequency range of 0.1–10 kHz. Statistical analysis of the detection with the different electrodes and aptamers was performed and evaluated using statistical analysis software.

[0124] The measurement results are in Fig. Numbers 7 to 16 are shown.

[0125] For the implementation of the electrochemical sensor, the electrode containing the receptor layer was exposed to a solution containing the analyte in different, but known, concentrations (see legend for concentrations, indicated by different symbols). The corresponding impedance spectra were then measured, see Fig. 7, Fig. 9, Fig.11 (a different aptamer was used for each figure, see legend). The buffers used were Tris buffers (test buffer 1). From the resulting Nyquist plots, the charge transfer resistance (minimum on the right side of the semicircle) can be determined, which increases due to the binding of NFL to the aptamer-covered electrode surface. This increase in charge transfer resistance is caused by the impaired charge transfer between the electrode and the redox probe (ferric / ferrocyanide) in the solution. The charge transfer is caused by steric and electrostatic shielding effects of the NFL molecules bound to the aptamer receptors, making it difficult for the redox probes to reach the electrode. This is reflected in the increase in the diameter of the semicircle in the impedance spectrum.

[0126] Subsequently, the change in charge transfer resistance obtained when a specific concentration of NFL is exposed to the sensor was calculated from the determined values ​​of the charge transfer resistance (ΔR=R). ohne NFL -R mit NFL ). This change in charge transfer resistance was then plotted against the respective concentration of NFL, yielding the calibration curve ( Fig. 8, Fig. 10, Fig. 12) This curve indicates the change in charge transfer resistance that can be measured at a specific concentration. If a solution of unknown NFL concentration is exposed to the sensor, the NFL concentration can be determined from the change in charge transfer resistance.

[0127] For further implementation of the electrochemical sensor, the electrode containing the receptor layer was exposed to a solution containing the analyte in different, but known, concentrations (see legend for concentrations, indicated by different symbols). The impedance spectra were then measured, see Fig. 13, (Aptamer_FZJ-NFL_EC1). The buffer consisted of PDS buffer (test buffer 2). The figure shows an increase in charge transfer resistance, caused by the impaired charge transfer between the electrode and the redox probe (ferric / ferrocyanide) in the solution. The charge transfer is caused by steric and electrostatic shielding effects of the NFL molecules bound to the aptamer receptors, making it difficult for the redox probes to reach the electrode. This is evident from the increase in the diameter of the semicircle in the impedance spectrum.

[0128] Subsequently, the change in charge transfer resistance was calculated from the determined values. This change in charge transfer resistance was then plotted against the respective concentration of NFL, resulting in the calibration curve ( Fig. 14). This curve indicates the change in charge transfer resistance that can be measured at a specific concentration in test buffer 2.

[0129] To implement the electrochemical sensor in real samples, the electrode containing the receptor layer was exposed to a solution of diluted human serum containing the analyte in different, but known, concentrations (see legend for concentrations, indicated by different symbols). The impedance spectra were then measured, see Fig.15 (Aptamer_FZJ-NFL_EC1). From the obtained Nyquist plots, the charge transfer resistance could again be determined, which in this case decreased due to the binding of NFL to the aptamer-coated electrode surface. This reduction in charge transfer resistance is caused by the easier charge transfer between the electrode and the redox probe (ferric / ferrocyanide) in the solution. This easier charge transfer is caused by a change in NFL in human serum, which leads to a more positive net charge but does not affect the affinity for the aptamer. This positive charge shift reduces the electrostatic repulsion between the receptor film and the negatively charged redox probe, thus facilitating charge transfer. The reduction in charge transfer resistance is evident from the decrease in the diameter of the semicircle in the impedance spectrum.

[0130] Subsequently, the change in charge transfer resistance obtained when a specific concentration of NFL is exposed to the sensor was calculated from the determined values ​​of the charge transfer resistance (ΔR=R). ohne NFL -R mit NFL Since the charge transfer resistance decreases with increasing NFL concentration, the ΔR values ​​are negative. This change in charge transfer resistance was then plotted against the respective NFL concentration, resulting in the calibration curve ( Fig. 16). This curve indicates the change in charge transfer resistance that can be measured at a specific concentration.

[0131] Example 2: Assay using an organic electrochemical transistor. This embodiment describes a sensor based on an organic electrochemical transistor (OECT) or arrays of OECTs as transducers, enabling a quantifiable correlation between the measurement signal and the net magnetic field (NFL) in the sample. The organic electrochemical transistor used here comprised three electrodes, one serving as the source electrode, one as the drain electrode, and one as the gate electrode (see also...). Fig. 17) Between the source and drain electrodes there is a channel made of a conductive polymer, Fig.18. The electrodes used here were made of gold, and the conductive polymer was poly-3,4-ethylenedioxythiophene / poly(styrenesulfonic acid) (PEDOT / PSS). In this configuration, the OECT was operated as an amplifier to enable very low detection limits for NFL. For this purpose, the gate electrodes were modified with the aptamer FZJ-NFL_EC1, as described above in Example 1 for the electrochemical assay. The aptamer can also be bound to or within the channel material. During immobilization of the aptamers on the gate electrodes, they were incubated for 1 hour in blocking molecules of a 1.5 mg / mL monofunctional methoxy polyethylene glycol thiol solution (1.5 mg / mL Thiol-PEG 2000). NFL was detected using PBS buffer (see also...). Fig. 20 and Fig. 21 - 10 mM PBS pH 7.4, 137 mM NaCl, 2.7 mM NaCl)) and on the other hand diluted 10-fold in human serum with test buffer 2 ( Fig. 22 and Fig.23). The incubation period was 30 minutes.

[0132] The channel consisted of a mixture of poly(3,4-ethylenedioxythiophene) / polystyrenesulfonate (PEDOT:PSS) with 20 wt% D-sorbitol, 1 vol% (3-glycidyloxypropyl)trimethoxysilane (GOPS), and 0.1 vol% 4-dodecylbenzenesulfonic acid (DBSA). The weight and volume ratios are relative to the weight and volume of PEDOT:PSS. This mixture was spin-deposited onto the chip surface at 1000 rpm for 10 seconds and at 4000 rpm for 30 seconds. The polymer film was then heated to 120°C and annealed for 20 minutes. Fig. Figure 17 (see above) shows details of the channel geometry of the transistor used in this example.

[0133] The measurement results are in Fig. 20, Fig. 21, Fig. 22 and Fig. 23 shown.

[0134] Fig. Figure 20 shows the transfer curves of an OECT according to Fig.19 based on Aptamer_FZJ-NFL_EC1 in PBS buffer (PBS = phosphate-buffered saline) with different but known concentrations of NFL. For this purpose, Aptamer FZJ-NFL_EC1 and Thiol-PEG 2000 were immobilized on the gate electrode. On the abscissa of Fig. Figure 20 shows the voltage between the source and gate electrodes of the OECT, and the ordinate shows the current flowing between the source and drain electrodes. Measurements were taken with a constant source-drain voltage of -0.1 V and a gate voltage ranging from -0.2 V to 1.0 V. Applying the source / drain voltage causes a defined source / drain current (I) to flow. ds ) through the PEDOT:PSS channel, which is a function of the channel resistance. The channel resistance, and therefore I ds However, it also depends on the voltage between the gate and source electrode (V). gs ) dependent. Increases V gsPositively charged ions migrate from the electrolyte into the conductive polymer of the OECT channel, compensating for the negatively charged sulfonate groups of the PSS and reducing the doping of the polymer, thereby increasing the channel resistance and I ds If the gate electrode is modified with the receptor layer and exposed to an NFL-containing solution, the binding of these molecules induces a variation in the gate-source voltage V. gs , which led to a change in I ds leads to this. Thus, the change in the transfer curve (I) corresponds to ds vs V gs ) with the NFL coverage at the aptamer-modified gate electrode and consequently also the NFL concentration in the solution.

[0135] The threshold voltage (V) can be determined from the transfer curve. T ) by V gs to be determined, in which there is a significant increase in I dsThis occurs (at this voltage the channel becomes conductive, here determined by the intersection point of the tangent (with maximum slope) with the abscissa). If one plots the change in the threshold voltage (ΔV) T By comparing the values ​​obtained when changing the NFL concentration against the NFL concentration, the calibration curve is obtained. Fig. 21 corresponding to Fig. 20. This curve indicates the change in signal ΔV T This can be measured at a specific concentration. If a solution of unknown NFL concentration is exposed to the sensor, the change in V can be used to determine the concentration. T determine the concentration on NFL.

[0136] Analogous to the measurements in PBS buffer, the same experiments were carried out with OECTs in diluted human serum samples, in which the gate electrode was modified with FZJ-NFL_EC1 and Thiol-PEG 2000. Fig.Figure 22 shows the corresponding transfer curves of an OECT at different NFL concentrations in human serum diluted 10-fold with test buffer 2. Here too, the increasing immobilization of the NFL at the gate electrode leads to a shift of the transfer curve to higher V. gs Values ​​which also includes V T increases. Is this concentration-dependent change in the threshold voltage (ΔV) T ) applied against the NFL concentration in diluted human serum, the calibration curve is obtained, which can be used to determine the NFL concentration of an unknown solution. Example 3: Optical Assay

[0137] This embodiment describes an optical assay based on fluorescence polarization measurements. This sensor also allowed a quantifiable correlation between the measurement signal and the NFL in the sample.

[0138] For this purpose, the aptamers were modified with cy5 fluorescent molecules at the 5' end. Since this assay is performed in solution without immobilization of the aptamer, a bonding group was omitted.

[0139] The modified aptamers used in this example were the following: Aptamer_ FZJ-NFL_opt1, cy5- GCA TAC TTG CGA GTC CTA ACA GGT ATT GGT CAA GGT ACG ATT G Aptamer FZJ-NFL_opt2, cy5- TCC CTC CAT CTA AGC CTT TAT TTC GTA TGT CGT CGA AGG TGT G Aptamer_ FZJ-NFL_opt3,- cy5- CAT AGC CCG CGC AAT CTA CGT AGA CAC ACC TAA CGA AAC CAA C

[0140] For the optical assay, NFL was dissolved in 50 mM Tris-acetate buffer (pH 8.2). Corning ® 384 multiwell plates were coated with protein-blocking buffer (Pierce™ Protein-Free (TBS) Blocking Buffer, Thermal Fisher Scientific) for 1 hour. The blocking buffer was then removed and the multiwell plates were dried in an inert gas stream.

[0141] The Cy5-modified aptamers (10 nM) were mixed with increasing concentrations of NFL-containing human serum solution and incubated for 30 minutes. The fluorescence polarization signal was then measured. The excitation wavelength was set to 650 nm, and the emission was measured at a wavelength of 670 nm.

[0142] The measurement results are in Fig. 2, Fig. 3 and Fig. 4 shown.

[0143] In these experiments, an optical assay based on fluorescence polarization measurements was implemented. This sensor allowed for a quantifiable correlation between the measurement signal (fluorescence polarization) and the NFL (fluorescence-labeled molecule) in the sample. These measurements measured the change in fluorescence polarization caused by the binding of a fluorescently labeled aptamer to its target molecule. For this purpose, the aptamer solution was illuminated with linearly polarized light, thus exciting the fluorophore. The emitted fluorescence light is typically also linearly polarized but is influenced by the rotational diffusion of the dissolved aptamer molecules. To determine the polarization P of the fluorescence light, the intensity (I) is measured. ∥ The parallel radiation is measured when the polarizer (in front of the sample) and the analyzer (behind the sample) are parallel to each other. In addition, the intensity (I) is measured. ⊥The polarization is measured when the polarizer and analyzer are perpendicular to each other. The polarization is calculated as the difference between the intensity measured parallel to the intensity measured perpendicularly, divided by the sum of both P=(I ∥ -I ⊥ ) / (I ∥ +I ⊥ For the investigations, the aptamers were modified with cy5 fluorescent molecules at the 5' end, since cy5 has a suitable fluorescence lifetime for fluorescence polarization studies. Fig.In step 2, an FZJ-NFL_opt1 solution was incubated with NFL solutions of different but known NFL concentrations. With increasing association between the aptamer and NFL, the fluorescence polarization values ​​increased because the mass of the protein is much greater than that of the aptamer, thus reducing the rotational diffusion of the NFL-aptamer complex. This resulted in little change in the orientation of the fluorophores and a stronger retention of the polarization of the excitation light in the emission light.

[0144] A calibration curve can be determined from the dependence of the fluorescence polarization on the NFL concentration. If the fluorescence polarization of a solution of unknown concentration is then measured, the concentration can be determined using the fitted function. The fit can be performed, as shown here, for example, using a Hill equation.

[0145] In addition to NFL, a comparable binding test was also performed with albumin, which is present in high concentrations in the blood. In contrast to NFL, the fluorescence polarization did not change with increasing albumin concentrations, demonstrating that the aptamer does not bind to albumin and thus exhibits high specificity for NFL.

[0146] Similar to the experiments conducted with the aptamer FZJ-NFL_opt1 for Fig. Experiments with the aptamer FZJ-NFL_opt2 were conducted and recorded in 2 Fig. 3 shown, as well as with aptamer FZJ-NFL_opt3, whose results in Fig. Figure 4 shows that all three aptamers can bind NFL in solution and exhibit high selectivity towards albumin. The following is a sequence protocol as an electronic document. This can be accessed in both DEPATISnet and the DPMA register.

Claims

[1] Aptamer that binds to neurofilament light and is selected from the group consisting of a) comprising or consisting of an aptamer, a nucleic acid sequence selected from the group consisting of SEQ ID NO: 1, 2 and 3, b) an aptamer whose nucleic acid sequence has a similarity of at least 50%, 60%, 65%, 70%, 75%, 80%, 85%, 90%, 95% or 98% with the nucleic acid sequence of an aptamer from a), c) an aptamer in which, compared to an aptamer from a), up to 19 nucleotides are removed, substituted and / or extended in the sequence with SEQ ID NO: 1, or SEQ ID NO: 2, or SEQ ID NO:

3. [2] Aptamer according to claim 1, characterized by , that - the aptamer is modified by binding to a probe molecule; or - the aptamer used is modified by binding to a probe molecule and the aptamer used is additionally modified at its other end by binding to a bonding group. [3] Aptamer probe for the detection of neurofilament light comprising one or more different aptamers according to claim 1 or 2 and a labeling agent. [4] Biosensor encompassing - an aptamer binding to neurofilament light according to claim 1 or 2, wherein the aptamer is either a) is freely present in a sample solution, or b) is immobilized at a fixed phase. [5] Biosensor according to claim 4, characterized by , that in variant a) the aptamer used is modified by binding to a probe molecule; or in variant b) the aptamer used is modified by binding to a probe molecule and the aptamer used is additionally modified at its other end by binding to a bonding group. [6] Biosensor according to one of claims 4 or 5, characterized by , that in variant b) additionally molecules which suppress the non-specific binding of components of the sample are immobilized on a solid phase. [7] Method for determining neurofilament light in body fluids comprising the steps: a) Providing an aptamer that binds to neurofilament light; b) Bringing the aptamer into contact with a sample of body fluid; c) Detecting the binding of neurofilament light to the aptamer. [8] Method according to claim 7, characterized by , that the aptamer is provided in the form of a biosensor according to one of claims 4 to 6. [9] Method according to claim 7 or 8, characterized by that the detection by means of - optical methods, preferably fluorescence spectroscopy, or - electrical methods, preferably measuring voltage changes, are used. [10] Method for producing the biosensors according to any one of claims 4 to 6 comprising the steps - Providing an aptamer that binds to neurofilament light; - optional modification of the aptamer; - optional provision of an electrode, a transistor electrode, a microbalance, or another signal converter; - Immobilizing the aptamer on the electrode, microbalance or other signal transducer; - optionally immobilizing blocking molecules on the electrode, the microbalance or the other signal transducer. [11] Use of the aptamers according to claim 1 or 2, the aptamer probes according to claim 3, the biosensors according to any one of claims 4 to 6, the method according to any one of claims 7 to 9, - for the detection of neurofilament light in samples; - for the enrichment, separation and / or isolation of neurofilament light from samples; - for potentially preventive and decentralized testing, especially of broad population groups. [12] Use of the aptamers according to claim 1 or 2 or the aptamer probes according to claim 3 as therapeutics, as affinity tags, as reagents, for labeling systems containing neurofilament light, for or in biosensors, for quality control.

Images