Patent Application
20180172587
The present invention relates to the field of sensors, more particularly for instance biosensors. More specifically it relates to sensors making use of luminescence for quantifying a component in a solution.
Affinity based bio-sensors use an affinity probe which specifically binds to a target molecule. The target molecule is the molecule which comprises or consists of the analyte molecule that needs to be quantified. In affinity based bio-sensors the binding event is detected by a transduction scheme. This can be a direct detection of the binding event (e.g. in a label free sensor), or it may be an indirect chain of interactions that can be detected. In the last case a second probe with a label allows to obtain e.g. an optical or electrochemical signal representative for the amount of analyte being present. The label may for example be a fluorophore or an enzyme that catalyzes still another reaction that for example provides an optical or electrochemical signal.
In affinity based bio-sensors with fluorescence signal transduction, a bulk sample is sent over a surface, and the target molecule (analyte) is bound by an affinity probe on the surface. The presence of target molecules on the surface is thereby correlated with the presence of labels on the surface. These labels may for example be fluorescent. In such bio-sensors the fluorescent light is captured and its intensity is a measure for the amount of analyte molecules present in the original bulk sample. The affinity probe may for example be an antibody, an antigen, an aptamer, complementary DNA or a molecularly imprinted surface. In the affinity based fluorescent bio-sensor with evanescent excitation fluorescence, total internal reflection may be used to create an evanescent field very close to the sensor surface, to excite only those fluorophores which are present very close to the surface, and of a large fraction of which can be expected that they are bound to an affinity probe on the surface.
Despite the already existing affinity based sensors there is still room for building improved affinity based sensors.
It is an object of embodiments of the present invention to provide optical detection systems with a good, e.g. an improved, signal to noise ratio. It is an objective of embodiments of the present invention to be able to separate the desired signal from background signal(s).
The above objective is accomplished by a method and device according to embodiments of the present invention.
The above objective is accomplished by a method and device according to the present invention.
In a first aspect, the present invention provides a sensor device for quantifying luminescent targets. The sensor device comprises:
It is an advantage of embodiments of the present invention that a change in the number of luminescent targets in the observed cell results in a change in the detected signal caused by a change of the desired signal which can be distinguished over the background signal. It is an advantage of embodiments of the present invention that the cell size is so small that the total background level (and the fluctuations/uncertainty on this) drops, and the discrete events become distinguishable after processing by the processor. It is an advantage of embodiments of the present invention that the background signal stays stable over a longer period of time than the time resolution of the detector. Luminescent targets adding to the observed cell in between two sample moments will increase the desired signal with a discrete step. It is an advantage of embodiments of the present invention that drift of the background signal which extends over the sampling moments can be cancelled out. It is an advantage of embodiments of the present invention that by reducing the cell size the background signal decreases or that by reducing the time period between consecutive measurements the difference in background signal between the consecutive measurements decreases.
In embodiments of the present invention the spatial cell resolution is so high that only a small number of luminescent targets will be present in the cell when measuring at low target concentration and that the uncertainty on the desired signal when a luminescent target is present is smaller than the change in desired signal for a change in number of targets by one target.
It is an advantage of embodiments of the present invention that when decreasing the cell size, below the size in which only one luminescent target can be present in the cell, the background signal decreases while the desired signal in the presence of one luminescent target remains the same.
In embodiments of the present invention the processor is configured to compare the measured signal of an observed cell with at least one adjustable threshold such that the exact number of luminescent targets present in the observed cell can be concluded.
It is an advantage of embodiments of the present invention that a simple comparison is sufficient to decide on the presence of one or no luminescent target and/or to decide on the exact number of luminescent target(s) in a cell. By counting the number of cells in which a luminescent target is present, and by knowing the number of luminescent target(s) in a cell, the number of luminescent targets or the concentration of the luminescent targets in the original sample can be quantified. It is therefore an advantage of embodiments of the present invention that the presence of a luminescent target is digitized and/or that the absolute number of luminescent target(s) in a cell is digitized, and that also the measurement signal representative for the quantification of luminescent targets is digitized (counting the number of positive cells).
A sensor device according to embodiments of the present invention may comprise a surface or a three dimensional volume wherein the surface or the three dimensional volume comprises affinity probes for capturing the luminescent targets.
It is an advantage of embodiments of the present invention that the eventual position of the luminescent targets is well defined. This allows to position the detector such that the monitored cells are on places where luminescent targets are expected. It is an advantage of embodiments of the present invention that one binding event in a cell is sufficient to be detected by the detector for this cell.
A sensor device according to embodiments of the present invention may comprise an evanescent field generating structure, wherein the light source is coupled to the evanescent field generating structure and wherein the evanescent field generating structure is adapted for generating an evanescent field at the surface or in the three dimensional volume.
It is an advantage of embodiments of the present invention that the illuminated volume is concentrated towards the luminescent targets and that therefore the background signal decreases whereas the desired signal remains the same when comparing with devices with free space illumination.
A sensor device according to embodiments of the present invention may be adapted for use with fluorescent targets.
It is an advantage of embodiments of the present invention that the radiative lifetime of a fluorescent target is limited (e.g. around 5 ns or less). This allows to decrease the measurement time or to increase the number of measurements after which averaging can be applied.
In a second aspect, the present invention provides a method for quantifying luminescent targets. The method comprises:
A method according to embodiments of the present invention may comprise statistical methods which are applied to the obtained target numbers over a plurality of cells and/or wherein the exciting, detecting, and discretizing steps are executed at a plurality of time points and wherein statistical methods are applied to the obtained target numbers at the plurality of time points so as to quantify the concentration of the luminescent targets in the original sample.
It is an advantage of embodiments of the present invention that by applying statistical methods (e.g. Poisson statistics) the concentration of the luminescent targets in the original sample can be quantified.
A method according to embodiments of the present invention may comprise an averaging and/or smoothing step after the detection step wherein the averaging and/or smoothing step is applied on the data obtained by the at least ones executed excitation and detection step.
Particular and preferred aspects of the invention are set out in the accompanying independent and dependent claims. Features from the dependent claims may be combined with features of the independent claims and with features of other dependent claims as appropriate and not merely as explicitly set out in the claims.
These and other aspects of the invention will be apparent from and elucidated with reference to the embodiment(s) described hereinafter.
The drawings are only schematic and are non-limiting. In the drawings, the size of some of the elements may be exaggerated and not drawn on scale for illustrative purposes.
Any reference signs in the claims shall not be construed as limiting the scope. In the different drawings, the same reference signs refer to the same or analogous elements.
The present invention will be described with respect to particular embodiments and with reference to certain drawings but the invention is not limited thereto but only by the claims. The drawings described are only schematic and are non-limiting. In the drawings, the size of some of the elements may be exaggerated and not drawn on scale for illustrative purposes. The dimensions and the relative dimensions do not correspond to actual reductions to practice of the invention.
The terms first, second and the like in the description and in the claims, are used for distinguishing between similar elements and not necessarily for describing a sequence, either temporally, spatially, in ranking or in any other manner. It is to be understood that the terms so used are interchangeable under appropriate circumstances and that the embodiments of the invention described herein are capable of operation in other sequences than described or illustrated herein.
Moreover, the terms top, under and the like in the description and the claims are used for descriptive purposes and not necessarily for describing relative positions. It is to be understood that the terms so used are interchangeable under appropriate circumstances and that the embodiments of the invention described herein are capable of operation in other orientations than described or illustrated herein.
It is to be noticed that the term “comprising”, used in the claims, should not be interpreted as being restricted to the means listed thereafter; it does not exclude other elements or steps. It is thus to be interpreted as specifying the presence of the stated features, integers, steps or components as referred to, but does not preclude the presence or addition of one or more other features, integers, steps or components, or groups thereof. Thus, the scope of the expression “a device comprising means A and B” should not be limited to devices consisting only of components A and B. It means that with respect to the present invention, the only relevant components of the device are A and B.
Reference throughout this specification to “one embodiment” or “an embodiment” means that a particular feature, structure or characteristic described in connection with the embodiment is included in at least one embodiment of the present invention. Thus, appearances of the phrases “in one embodiment” or “in an embodiment” in various places throughout this specification are not necessarily all referring to the same embodiment, but may. Furthermore, the particular features, structures or characteristics may be combined in any suitable manner, as would be apparent to one of ordinary skill in the art from this disclosure, in one or more embodiments.
Similarly it should be appreciated that in the description of exemplary embodiments of the invention, various features of the invention are sometimes grouped together in a single embodiment, figure, or description thereof for the purpose of streamlining the disclosure and aiding in the understanding of one or more of the various inventive aspects. This method of disclosure, however, is not to be interpreted as reflecting an intention that the claimed invention requires more features than are expressly recited in each claim. Rather, as the following claims reflect, inventive aspects lie in less than all features of a single foregoing disclosed embodiment. Thus, the claims following the detailed description are hereby expressly incorporated into this detailed description, with each claim standing on its own as a separate embodiment of this invention.
Furthermore, while some embodiments described herein include some but not other features included in other embodiments, combinations of features of different embodiments are meant to be within the scope of the invention, and form different embodiments, as would be understood by those in the art. For example, in the following claims, any of the claimed embodiments can be used in any combination.
In the description provided herein, numerous specific details are set forth. However, it is understood that embodiments of the invention may be practiced without these specific details. In other instances, well-known methods, structures and techniques have not been shown in detail in order not to obscure an understanding of this description.
As used herein and unless provided otherwise, the term “analyte” or “target” refers to the substance to be measured, the substance having or not having a biological origin. By the expression “substance having a biological origin”, we intend to mean a substance that is present or produced in a living organism. Particularly, the substance may be a biomolecule. For instance, the analyte may be a protein or an antigen. The analyte may or may not be labeled for detection. In the context of the present invention, the terms target and analyte are considered to be synonyms.
By the term “biomolecule” is meant any molecule that is present in living organisms, including large macromolecules such as proteins, polysaccharides, lipids, and nucleic acids, as well as small molecules, such as primary metabolites, secondary metabolites, and natural products. The term “biomolecule” also encompasses molecules with similar properties and/or structure and/or composition, but that have been manufactured artificially rather than in a living organism.
Where in embodiments of the present invention reference is made to “luminescence of a target”, reference is made to emission of light by the target, not resulting from thermal emission. Typically, in the context of the present invention, luminescence will be photoluminescence, generated by absorption of photons; such as fluorescence or phosphorescence. The present invention, however, is not limited to this type of luminescence, and can also be applied in case of, for instance, bioluminescence or chemiluminescence (emission as a result of a (bio)chemical reaction by an organism) or electroluminescence (a result of an electric current passed through the target).
Where in embodiments of the present invention reference is made to the “background signal”, reference is made to any signal which is disturbing the measurement of the desired signal. This may comprise background signals from luminescent sources which do not form part of the target under study. This may comprise luminescence which is scattered by scattering centers in the device. This may comprise any other noise source which is present in the device.
Where in embodiments of the present invention reference is made to “quantifying luminescent targets”, reference is made to either determining the presence of luminescent targets, or determining the amount of luminescent targets, or determining the concentration of luminescent targets.
Where in embodiments of the present invention reference is made to “a cell” reference is made to a subdivision of the monitored volume or area of the sensor device.
Where in embodiments of the present invention reference is made to “an event”, reference is made to a luminescent target which enters a cell observed by the detector. In embodiments of the present invention this may be caused by a luminescent target that binds with a surface of the sensor device.
Where in embodiments of the present invention reference is made to “an area unit” reference is made to the size of an observed cell. In embodiments of the present invention the size of the observed cell is so small that individual (discrete) binding events are expected to occur after a given incubation time. This may be at equilibrium or at a fixed time before equilibrium. This may mean that at low target concentration, e.g. at or around the limit of detection, and/or for a specific accumulation time only a small fraction of the capture sites will be occupied.
Where in embodiments of the present invention reference is made to “a limited number of luminescent targets”, reference is made to a number of targets that is small enough such that they can be assigned absolutely/digitally. The limited number may be smaller than or equal to 20, or even smaller than or equal to 10, or even smaller than or equal to 3, or even smaller than or equal to 1
In a first aspect, the present invention provides a device 100 for quantifying targets (analyte) which may be present in a fluid sample, e.g. in a biological fluid such as a blood sample, a urine sample, a drop of saliva, sperm. One embodiment of such device 100 is schematically illustrated in
In embodiments of the present invention the sample may be injected in the device as a one-time event (e.g. filling a reservoir) or the injection may be a continuous event (e.g. triggered by starting a flow) that continues during the subsequent steps when quantifying the targets.
In embodiments of the present invention the luminescent targets may be illuminated through (regular) free space illumination or through evanescent illumination. In free space illumination light source 111 is illuminating at least the surface 190 with the affinity probes. The light source 111 may be located at the top (the top wall 172 and any other layer between the light source 111 and the cavity 180 should be transparent) or bottom (the substrate 160 and any other layer between the light source 111 and the cavity 180 should be transparent) of the sensor device 100. The light source 111 may be, amongst others, a laser, a laser diode, a VCSEL, a LED, a lamp, a Tungsten lamp, a Halogen lamp, a Mercury lamp, a Xenon lamp, a Metal Halide lamp. In embodiments of the present invention the light coming from the light source 111 may be projected or focused by lenses or mirrors or a microscope or optical fibers on the surface 190. (In this case no evanescent field generating structure 110 is present).
In case of evanescent illumination, devices according to embodiments of the present invention comprise an evanescent field generating structure 110 for generating an evanescent field at the surface 190.
The evanescent field generating structure 110 may be integrated in or on the substrate 160 or it may be separate from the substrate 160 (e.g. against the microfluidic channel top 172 or sidewalls 171). In embodiments of the present invention the light of the light source 111 may be guided towards the cavity 180 using a connecting structure such as an optical waveguide. The light may be coupled to the evanescent field generating structure 110 or to the connecting structure using any suitable optical device, such as for instance a grating coupler or a butt coupler.
In embodiments of the present invention the light source 111 may be integrated in the substrate 160. In case of close integration with the rest of the device 100, the light source 111 may be, amongst others, a laser, a laser diode, a VCSEL, a LED. These light sources may be applied in the case of evanescent excitation.
In case the light source 111 is not necessarily closely integrated with the rest of the device 100 it may also be a laser, a lamp, a Tungsten lamp, a Halogen lamp, a Mercury lamp, a Xenon lamp, a Metal Halide lamp. This type of light source can also be applied in the case of evanescent excitation.
Devices 100 according to embodiments of the present invention moreover comprise a detector 120 which can detect the luminescence of the luminescent target after the target has been excited with the evanescent field generating structure 110 or light source 111. The measured signal is composed of a desired signal which originates from the luminescent targets and a background signal emanating from other luminescent sources present in the system. The detector 120 may be located external to the cavity 180 (not integrated in/in physical contact with either substrate 160 or top 172). In that case at least one top or bottom wall (e.g. walls from the microfluidic channel 171, 172, substrate 160, any other layer) should be transparent such that the luminescence signals from the luminescent targets can exit from the cavity through this wall. In case the detector is located external to the cavity additional lenses, as used in classical optics, may be applied for guiding the luminescence signals towards the detector.
In embodiments of the present invention the detector 120 may be integrated with the cavity 180. It may be present at the top or at the bottom of the cavity. The bottom side is the side where the target molecules bind to the affinity probes, the top side is the opposite side thereof. The detector 120 may be present on the inside or the outside of the cavity. When on the outside a transparent wall of the cavity is required.
In embodiments of the present invention luminescence from the luminescent targets may be collected by a waveguide connected to the detector 120. This waveguide may be the same as the excitation waveguide, or it may be a different waveguide. The luminescent light may be coupled from the waveguide into the detector 120 the same way as the light coming from the light source is coupled into the waveguide (e.g. through a grating coupler, butt coupling etc.). This may be the same coupler as the input coupler, if it has enough bandwidth and if incoming and outgoing light is handled appropriately, or it may be a different coupler. In embodiments of the present invention the input coupler and the output coupler are different. In embodiments of the present invention diffraction and/or reflection optics may be present between the waveguide and the detector. This may for example be a lens to project the output couplers onto the detector. Filters may be present, in, on or before the detector, for attenuating light which is outside the frequency range of the light generated by the luminescent targets. The detector 120 may be a CMOS imager.
In embodiments of the present invention the area or volume observed by the detector is subdivided in a number of observed cells 310. In embodiments of the present invention the measured signal is composed of a desired signal which originates from the luminescent targets which are present in an observed cell 310 and a background signal emanating from other luminescent sources present in the system. In embodiments of the present invention the cell size is so small that only a limited number of luminescent targets are expected to be present in the observed cell. In embodiments of the present invention the cell size is thereby decreased so much that the desired signal (after processing) becomes larger than the background signal.
Embodiments of the present invention comprise a surface 190 provided with affinity probes for binding the luminescent targets.
In embodiments of the present invention, mainly the surface 190 of the substrate 160 or a three dimensional volume is illuminated. In these embodiments the bulk of the sample is not illuminated using free space light but using an evanescent light near the surface 190. The evanescent field region may have a thickness of a few nm-thick or even 10 nm thick or even between 10 nm and 100 nm thick. This may be done by evanescent excitation. Such evanescent illumination is also referred to as TIRF (total internal reflection fluorescence). This can be achieved by having a beam of light, coming from the evanescent field generating structure 110, incident on the interface between the evanescent field generating structure 110 and the cavity 180 at an incident angle below the critical angle, resulting in a total internal reflection. It can also be achieved by confining the light in a guiding structure such as a waveguide. It is an advantage that TIRF can be applied in embodiments of the present invention. Only the luminescent labels (e.g. fluorophores) which are immobilized at the surface 190 of the substrate evanescent field generating structure 110, or which are in its immediate neighbourhood (i.e., within the range of the evanescent field) will be illuminated this way. The substrate 160, on which evanescent field generating structure 110 is fabricated may be a semiconductor substrate, a glass substrate, or any other suitable type of substrate. It may be a quartz substrate. Luminescent labels which are in the bulk solution are thereby not measured. When these luminescent labels in the bulk solution are not excited they will also not generate a background signal.
Embodiments of the present invention comprise a waveguide for guiding the excitation light towards the evanescent excitation plane. It is thereby an advantage of embodiments of the present invention that the luminescent labels (e.g. fluorophores) in the bulk solution will not be excited. Only the luminescent labels which are in the evanescent field volume will be illuminated. These luminescent labels are mainly the surface immobilized luminescent labels. The labels in the bulk, which are not illuminated or which are less illuminated than the immobilized labels at the surface, will therefore generate a smaller luminescent signal than the immobilized labels at the surface. It is therefore an advantage of embodiments of the present invention that by only illuminating the evanescent excitation plane, the signal to noise ratio can be increased.
In embodiments of the present invention the surface 190 may be divided into a plurality of cells, and/or the time between consecutive measurements may be made so small such that the number of binding events in a cell is discrete, for example smaller than 20, preferably smaller than 10, preferably smaller than 3, or even digital (0 or 1). Such a cell may have size below 10 μm2, preferably below 1 μm2 or even down to 0.3 μm2. It is an advantage of embodiments of the present invention that the number of bound luminescent targets can be absolutely (and hence very accurately) determined.
Each of the cells 310 is observed by a detector 120. In embodiments of the present invention, the detector 120 may be a single detector. In embodiments of the present invention the detector may also be a (group of) pixel(s) of a line detector or a (group of) pixel(s) of an imager comprising multiple pixels. The detector may be a CMOS detector, a CCD detector, a(n array of) photodiode(s), an (array of) avalanche photodiode(s), a(n array of) photomultiplier tube(s) PMT(s).
In embodiments of the present invention the time between two consecutive measurements, performed by the detector, of an observed cell is significantly smaller than the average time between the capture of two consecutive (labelled) targets. This can be achieved by reducing the time between successive measurements and/or decreasing the size of each cell (which increases the average time between the capture of two consecutive (labelled) targets in said cell). In embodiments of the present invention the time between two consecutive measurements is decreased so much that a change in the desired signal caused by adding a labelled target to the cell becomes larger than the uncertainty on the signal level in between the binding events. In embodiments of the present invention the uncertainty on the signal level in between the binding events is reduced by averaging or smoothing or other data analysis techniques including wavelet-based techniques.
Embodiments of the present invention comprise a processor 140 which is configured to process the detected signals, thereby increasing the signal to noise ratio so much that the desired signal originating from individual luminescent targets can be distinguished.
The term processor 140 should be interpreted widely. It can be a microprocessor but it can for example also be an ASIC (application specific integrated circuit) or an FPGA (field programmable gate array), or an analog or digital signal processing device. The processing may be distributed. It may for example be partly or completely running on an external device (e.g. a smartphone). The external device, e.g. smartphone, may for example receive raw data (digitized output of the detector) or it may receive already pretreated data.
In embodiments of the present invention the detected signal is averaged or smoothed to distinguish the desired signal from the background signal. It is thereby an advantage of embodiments of the present invention that the desired signal can be distinguished from the averaged detected signal by looking at the discrete offsets in the averaged or smoothed detected signal. When averaging or smoothing the detected signal, the uncertainty on the averaged or smoothed background signal will decrease. It is sufficient to continue averaging until the discrete steps of the desired signal become visible. The baseline (the desired signal) per cell is therefore reduced to a discrete number of signal levels. Averaging or smoothing the detected signal will result in an averaged or smoothed signal which changes in discretely discernible steps corresponding to the number of binding events in the concerned cell.
A device 100 according to embodiments of the present invention may be present on a printed circuit board 150. It may comprise a needle or a suction element like a cotton strip (not illustrated) and a microfluidic channel 170 for taking or receiving a fluid sample and guiding it to the surface 190. It is thereby an advantage of embodiments of the present invention that the different features required for executing the steps for analyzing a fluid sample may be integrated in one and the same device 100.
Depending on the embodiment, the fluidics of the device 100 can be different. They can for example be capillary and/or they can be pressure driven, e.g. pumped. Pumps can for example control the pressure or the volumetric flow rate. The microfluidic channel 170 can be an open channel or a closed channel. A schematic drawing of a device 100 in accordance with embodiments of the present invention and comprising the features as described above is shown in
The size of the device 100, in accordance with embodiments of the present invention, is limited. The size may for example be comparable to the size of an SD-card or of a micro-SD card or of a USB-stick.
Embodiments of the present invention can for example be used to check if certain biomarkers are present in the fluid (e.g. presence of antibodies against HIV in a blood sample).
In embodiments of the present invention the background signal may have different origins. Luminescent sources may be present which are not linked with the analyte, hence which do not form part of target molecules. These will, nevertheless, be detected by the detector 120 and will increase the background signal of the device 100.
In an exemplary embodiment of the present invention, illustrated in
These background signals increase the noise and therefore decrease the signal to noise ratio, while it is desired to have the signal to noise ratio as large as possible.
Instead of pre-incubation, another approach would be to first send over the analyte, wash to remove any unbound particles, then send over the labelled detection probe, and wash again. In that case, some background sources are different/absent (e.g. the combination 220 would not be present, and some centers 240 would not be present in the detection probe). However, in this approach we cannot do real-time measurements, so the time-to-response is longer)
Embodiments of the present invention are not limited to the standardized enzyme-linked immunosorbent assay (ELISA) as illustrated in
The cells in
In embodiments of the present invention the number of bound molecules is statistically distributed (a typical distribution is the Poisson distribution). Statistical analysis may then be applied to the detected signals coming from the large number of sub-areas (cells) to determine the unknown target concentration that was applied to the sensor device.
For each of the different figures ten independent time traces were simulated. For each time trace the number of bound luminescent targets was chosen randomly (Poisson), but remained constant within the trace. These measurements can for example represent:
On average ten background molecules were present per unit area. The exact number was chosen randomly at every time step according to a Poisson distribution. This simulation can for example represent bulk fluorophores moving in and out of the sensing volume or non-specifically bound molecules binding to and unbinding from the sensor surface 190 where the integration time is shorter than the characteristic time scale at which the background events fluctuate. At longer integration times the background events are (partially) averaged out, such that the random changes would be smaller than in the present simulations.
The left graphs of
In
In
In
In
For the large cell sizes (with large desired signal counts, e.g. with a desired signal count of 100 or 10), the uncertainty on the average values is much larger than 1. As a consequence, the average value cannot be accurately determined.
For the small cell sizes (with small desired signal counts, e.g. in this exemplary embodiment of the present invention with a desired signal count below 1, for instance about 0.3), the uncertainty on the average values becomes comparable to or smaller than 1. Since the total number of bound molecules is an integer, the average can be assigned to a discrete level without any remaining uncertainty.
For example in
It will be noticed that these counts correspond to a (variable) number of bound molecules, and a number of background events that is unknown but that is equal for all time traces within an uncertainty of less than 1 count. However, the relative number of cells with 0, 1, 2, 3, . . . bound molecules follow a Poisson distribution. If a sufficiently large number of cells is measured, this distribution can be used to determine the level of the desired signal and the level of the background signal that corresponds to zero bound molecules (in many cases, this will be simply the lowest of the discrete levels), and hence also the averaged background count number and the exact number of bound target molecules in each cell.
It is therefore an advantage of embodiments of the present invention that this leaves only the statistical variation of the number of bound molecules on every small cell, which is the result of the random nature of the capturing of the targets. It is known that the behavior of this random process is well described by Poisson statistics. It is an advantage of embodiments of the present invention that by measuring a sufficient number of small cells the unknown target concentration giving rise to these capturing events can be determined by using the appropriate statistical models based on a Poisson process. Moreover, the smaller the cell size, the larger the number of cells on the surface 190, the more accurate extraction of the target concentration using the Poisson statistical model becomes.
In embodiments of the present invention the surface 190 (i.e. the sensing area) comprises about 20000 capture sites per μm2. When a prior art detector with a cell size of 1 μm2 is provided, and when the target concentration and the incubation time are large such that a large fraction of the capture sites are occupied, this would result in a “continuous” signal (up to 20000 bindings possible), and the approach described above would not work. However, under these conditions the signal itself is large, and the signal-to-noise ratio may already be large enough to get an accurate concentration value without recourse to the technique described above. On the other hand, when the target concentration and/or the incubation time are smaller, the signal decreases and the signal-to-noise ratio becomes worse. However, it is precisely in this regime that the described technique becomes applicable. In order to obtain a digital result in the concentration range of interest (e.g. determined by the known concentration range of the target in healthy or ill patients, or the concentration range of the target in a bioreactor), the cell size of the detector can be chosen according to embodiments of the present invention.
In an exemplary embodiment of the present invention the sensor device 100 is an immunological sensor (antibody-based protein sensor). The typical density of capture sites on the surface 190 is Γcapture probes=10 000 to 20 000 μm−2. In the following numerical example 104 μm−2 is taken.
A typical association rate constant is:
k
on=105 M−1s−1.
A typical concentration for a low-abundant target molecule is:
[target]=1 pM=10−12 M.
The association rate in this case is:
In other words, 0.001 binding events per second on a 1×1 μm2 capture area, or 0.1 binding events per second on a 10×10 μm2 capture area.
The order of magnitude of the detection antibody concentration in a sandwich ELISA assay is ˜10 nM=10−8 M. Assuming a transducer which is sensitive to the first 100 nm above its surface, then the number of background molecules in the detection volume above a 1 μm2 detector area is:
The characteristic time scale for these background events is the time to diffuse over 100 nm=100 10−7 cm (i.e. in or out of the detection volume). A typical diffusion coefficient for proteins in water is D=10−5 cm2 s−1. With a diffusion length given by LD=sqrt(D t), the time required to diffuse over length LD is t=LD2/D=(100 10−7 cm)2/(10−5 cm2 s−1)=10−5 s.
In other words, for integration times much longer than 10 us, the background intensity of 600 μm−2 would be significantly averaged out. In this particular case, discrete events can be distinguished for detection areas roughly around 1 μm2 (10−3 events per second per detector), or in the approximate range of (0.1 μm)2 (10−5 events per second per detector) to (10 μm)2 (0.1 events per second per detector).
In embodiments of the present invention luminescent targets with large labels are used to increase the signal per binding event. These labels may be beads with a large number of fluorophores.
The signal per binding event may also be increased by increasing the number of fluorophores which can be bound with the secondary antibody. This may for example be larger than 10, or even larger than 20, or even around 100. It is an advantage of embodiments of the present invention that the luminescence of a target can be increased by increasing the number of luminescent molecules which can bind with the target.
In a second aspect, the present invention provides a method for quantifying luminescent targets, for instance for detecting presence, for determining an absolute value or for determining concentration.
In a first step 1010 the luminescent targets are excited. Thereby the luminescent targets generate a luminescence signal.
In a second step 1020 the luminescence signal generated by the luminescent targets is measured per cell, wherein the monitored volume may be subdivided in a number of cells. The measured luminescence signal for each cell comprises a desired signal emanating from the luminescent targets in that cell and a background signal. The detection is done on a space and/or time resolution which is so high that the total amount of luminescent targets/or the increase of luminescent targets compared to the previous detection is limited (e.g. less than 20, or even less than 10, or even less than 3, or even zero or 1).
In embodiments of the present invention the excitation 1010 and detection 1020 steps may be repeated in an optional loop (loop 1 in
The excitation 1010 and detection 1020 steps may be followed by an optional smoothing/averaging 1030 to reduce the uncertainty on the measurement. In the example illustrated in
Smoothing and averaging 1030 can be done at one timepoint along the accumulation curve (e.g. if endpoint measurements are done; i.e. when the accumulation has stopped) on an array of small cells. Then the smoothing and averaging is done for each cell. Smoothing and averaging 1030 may also be done at different timepoints along the accumulation curve. Then the averaging and smoothing can be done on successive sets of e.g. 10 or 100 repetitions of loop 1, or also using a sliding window of e.g. 10 or 100 repetitions of loop 1.
After the detection step 1020 or optionally after the smoothing and averaging step 1030, the following step is to discretise 1040 the events (in each spatial cell and/or along the time axis).
After discretisation 1040 the sequence may be started again with an excitation step 1010 thus forming a closed loop 2. This is an optional loop. Discretisation 1040 may also be an offline process. In that case loop 2 may coincide with loop 1 (first gathering the data, and next applying an offline discretization step on this data. Loops 1 and 2 may not be required in case only spatial statistics are to be provided, and if averaging is not required to reduce the noise (see for example the simulation results illustrated in
The discretisation step 1040 is followed by applying statistical methods (e.g. Poisson statistics) 1050 on the many cells and/or time points to deduce/determine the concentration of the target. This step may include finding out which measured signal level corresponds to zero specifically bound molecules.
Sensor devices 100 according to embodiments of the present invention may be used in bioreactors. Bioreactors are, for example, used in the pharmaceutical industry, in food and agriculture (e.g. beer), in cell and tissue culturing (e.g. stem cells, regenerative medicine). In those cases, (affinity-based) (bio)sensor devices 100, according to the present invention, can be used to monitor if the culture is performing fine (e.g. check nutrients, measure the concentration of a product the culture is fabricating, check for contaminations).
| Number | Date | Country | Kind |
|---|---|---|---|
| 15174680.7 | Jun 2015 | EP | regional |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/EP2016/064441 | 6/22/2016 | WO | 00 |
