Patent Application
20180284112
The present invention relates to a method for detecting an analyte, and particularly to extending the dynamic range and/or sensitivity of an immunoassay.
Immunoassays are often used for measuring the concentration of an analyte in a sample. However, they can be limited in terms of the lower limit of detection, the upper limit of detection and the dynamic measurement range.
In a typical sandwich immunoassay, an antibody specific for an antigen of interest is attached to a polymeric support such as a sheet of polyvinylchloride or polystyrene. A drop of cell extract or a sample of serum or urine is laid on the sheet, which is washed after formation of the antibody-antigen complex. Antibody specific for a different site on the antigen is then added, and the sheet is again washed. This second antibody carries a label so that it can be detected with high sensitivity. The amount of second antibody bound to the sheet is proportional to the quantity of antigen in the sample. This assay and other variations on this type of assay are well known, see, for example, “The Immunoassay Handbook, 2nd Ed.” David Wild, Ed., Nature Publishing Group, 2001.
The upper limit of detection in an immunoassay is usually limited by the total amount of reagents used. The amount of antibody that can be immobilised on a support is limited by the finite surface area of the support. When excess analyte is present in the sample, the system becomes saturated, as all of the antibody binding sites are blocked with analyte (depending upon the affinity constant of the antibody used) and unbound analyte is washed away. Therefore, the system is unable to discriminate between concentrations of analyte above saturation, typically at concentrations between 1 μM and 100 mM. In lab analysers, this problem is addressed by diluting the sample and re-running the assay. However, sample dilution is impractical for point-of-care assays.
In a homogenous sandwich assay, the first antibody, the analyte and the second antibody are all incubated simultaneously and there are no wash steps. As the analyte concentration increases, the detected signal increases, until saturation is reached. At concentrations of analyte above saturation, the analyte binds separately to the first and second antibodies. Consequently, the amount of second antibody bound to the sheet is now no longer proportional to the quantity of antigen in the sample and the detected signal decreases—an effect known as “high-dose hook”. This effect can reduce the dynamic range of the assay.
Therefore, there exists a need for the provision of a solution to the problem of assay saturation and/or high-dose hook, in order to extend the dynamic range and/or sensitivity of a sandwich assay.
Accordingly, the present invention provides a method for detecting an analyte in a sample comprising:
(i) providing a labelled reagent, the labelled reagent having a binding site which is capable of binding the analyte or an analogue of the analyte and a label, wherein the label is capable of absorbing the electromagnetic radiation to generate energy by non-radiative decay;
(ii) providing a device having
a radiation source adapted to generate a series of pulses of electromagnetic radiation,
a transducer having a pyroelectric or piezoelectric element and electrodes, which is capable of transducing energy generated by non-radiative decay into an electrical signal,
a detector which is capable of detecting the electrical signal,
a controller for controlling the source of electromagnetic radiation and the detector,
wherein the device has a first and second chamber,
the first chamber containing a first reagent proximal to the transducer, wherein the first reagent is capable of binding to the analyte such that the binding of the labelled reagent to the first reagent via the analyte is directly proportional to the concentration of the analyte, and the second chamber containing a second reagent proximal to the transducer, wherein the second reagent mimics the analyte such that the binding of the labelled reagent to the second reagent is inversely proportional to the concentration of the analyte;
(iii) exposing the sample to the transducer;
(iv) irradiating the sample with electromagnetic radiation and detecting the electrical signal.
Thus, the present invention provides a method for performing a sandwich assay in which the dynamic range and/or sensitivity of the assay can be extended by running a competitive assay simultaneously and combining the results.
The present invention will now be described with reference to the drawings, in which:
The method of the present invention is used for detecting an analyte in a sample. The method provides a device having: a radiation source adapted to generate a series of pulses of electromagnetic radiation; a transducer having a pyroelectric or piezoelectric element and electrodes, which is capable of transducing energy generated by non-radiative decay into an electrical signal; and a detector which is capable of detecting the electrical signal generated by the transducer. The device of the present invention is based on the device described in WO 2004/090512.
The label 2 is held proximal to the transducer 3 by a binding event. A preferred feature of the present invention is that the label 2 generates heat when irradiated by a source of electromagnetic radiation (typically termed “light”) 6, preferably visible light. The light source may be, for example, an LED. The light source 6 illuminates the label 2 with light of the appropriate wavelength (e.g. a complementary colour). Although not wishing to be bound by theory, it is believed that the label 2 absorbs the light to generate an excited state which then undergoes non-radiative decay thereby generating energy, indicated by the curved lines in
The energy generated by the label 2 is detected by the transducer 3 and converted into an electrical signal. The electrical signal is detected by a detector 7. The light source 6 and the detector 7 are both under the control of the controller 8. The light source 6 generates a series of pulses of light (the term “light” used herein means any form of electromagnetic radiation unless a specific wavelength is mentioned) which is termed “chopped light”. In principle, a single flash of light, i.e. one pulse of electromagnetic radiation, would suffice to generate a signal from the transducer 3. However, in order to obtain a reproducible signal, a plurality of flashes of light are used which in practice requires chopped light. The frequency at which the pulses of electromagnetic radiation are applied may be varied. At the lower limit, the time delay between the pulses must be sufficient for the time delay between each pulse and the generation of an electrical signal to be determined. At the upper limit, the time delay between each pulse must not be so large that the period taken to record the data becomes unreasonably extended. Preferably, the frequency of the pulses is from 1-50 Hz, more preferably 1-10 Hz and most preferably 2 Hz. This corresponds to a time delay between pulses of 20-1,000 ms, 100-1,000 ms and 500 ms, respectively. In addition, the so-called “mark-space” ratio, i.e. the ratio of on signal to off signal is preferably one although other ratios may be used without deleterious effect. There are some benefits to using a shorter on pulse with a longer off signal, in order to allow the system to approach thermal equilibrium before the next pulse perturbs the system. In one embodiment, a light pulse of 1-50 ms, preferably 8 ms, followed by a relaxation time of 10-500 ms, preferably 250 ms allows a more precise measurement of particles bound directly to the surface. Sources of electromagnetic radiation which produce chopped light with different frequencies of chopping or different mark-space ratios are known in the art. The detector 7 determines the time delay between each pulse of light from light source 6 and the corresponding electrical signal detected by detector 7 from transducer 3. The applicant has found that this time delay is a function of the distance, d. The signal is preferably measured from 2-7 ms.
Any method for determining the time delay between each pulse of light and the corresponding electrical signal which provides reproducible results may be used. Preferably, the time delay is measured from the start of each pulse of light to the point at which a maximum in the electrical signal corresponding to the absorption of heat from bound label is detected as by detector 7.
The finding that the label 2 may be separated from the transducer surface and that a signal may still be detected was surprising since the skilled person would have expected the heat to be dispersed into the surrounding medium and hence be undetectable by the transducer 3 or at least for no meaningful signal to be received by the transducer. It was found, surprisingly, that not only was the signal detectable through an intervening medium capable of transmitting energy to the transducer 3, but that different distances, d, may be distinguished (this has been termed “depth profiling”) and that the intensity of the signal received is proportional to the concentration of the label 2 at the particular distance, d, from the surface of the transducer 3. Moreover, it was found that the nature of the medium itself influences the time delay and the magnitude of the signal at a given time delay. In the present invention, the detector is arranged to detect only the electrical signal corresponding to non-radiative decay occurring proximal to the transducer.
By way of an explanation of the principle underlying the present invention,
In use, the sample chamber is filled with liquid 10 (or any fluid) containing an analyte 11. The analyte 11 then binds to first reagent 12. Additional labelled reagent 13 is present in the liquid and a so-called “sandwich” complex is formed between the bound first reagent 12, the analyte 11 and the labelled reagent 13. An excess of labelled reagent 13 is included so that all of the bound antigen 11 forms a sandwich complex. The sample therefore contains bound labelled reagent 13a and unbound labelled reagent 13b free in solution.
During or following formation of the sandwich complex, the sample is irradiated using a series of pulses of electromagnetic radiation, such as light. The time delay between each pulse and the generation of an electrical signal by the transducer 3 is detected by a detector. The appropriate time delay is selected to measure primarily the heat generated by the bound labelled reagent 13a. Since the time delay is a function of the distance of the label from the transducer 3, the bound labelled reagent 13a may be distinguished from the unbound labelled reagent 13b. This provides a significant advantage over the conventional sandwich immunoassay in that it removes the need for washing steps. In a conventional sandwich immunoassay, the unbound labelled reagent must be separated from the bound labelled reagent before any measurement is taken since the unbound labelled reagent interferes with the signal generated by the bound labelled reagent. However, on account of the “depth profiling” provided by the present invention, bound and unbound labelled reagent may be distinguished. Indeed, the ability to distinguish between labels proximal to the transducer (i.e. bound) and labels in the bulk solution (i.e. unbound) is a particular advantage of the present invention.
The method of the present invention also comprises exposing the sample to the device as described herein, transducing the energy generated into an electrical signal and detecting the signal. Preferably, the method is carried out without removing the sample from the transducer between the steps of exposing the sample to the transducer and transducing the energy generated into an electrical signal, i.e. the method is a homogeneous assay.
The present invention provides controls which compensate for natural variability in the components of the measuring system (including the pyroelectric sensor material, the LED light sources and the amplifier circuits), variability in the samples that are measured, and variability in the environmental conditions during the measurement. This can be achieved by exposing the sample to reagents on the surface of the transducer. The different reagents are typically located at different areas of the transducer surface, these areas being coated in different reagents. These controls are defined as “negative” and “positive” controls, in the sense that the negative control should approximate the expected signal in the absence of analyte, and the positive control should approximate the expected signal when analyte has saturated the system. In a preferred embodiment, the device of the present invention is based on the device described in WO 2012/137009, and the controls which are described therein. WO 2012/137009 describes how the use of such controls improves the accuracy and precision of an assay carried out using the device described in WO 2004/090512.
To achieve detection with these controls, the device of the present invention comprises a first, second and third chamber, which contain a first, second and third reagent, respectively, proximal to the transducer.
The first reagent has a binding site which is capable of binding to the analyte. The labelled reagent then binds to the analyte such that the binding of the labelled reagent to the first reagent via the analyte is directly proportional to the concentration of the analyte. In this manner, the analyte has two differing epitopes. Accordingly, the first chamber comprises a sandwich immunoassay.
Determining the extent of binding of the labelled reagent to the first reagent provides a measurement of the concentration of the analyte in the sample.
The second reagent mimics the analyte and is an analogue of the analyte (it is an analogue because it is bound to the transducer surface either through covalent bonding or non-covalent interactions). The labelled reagent binds directly to the second reagent. The second reagent will compete with any free analyte in the sample for the binding of the labelled reagent such that the binding of the labelled reagent to the second reagent is inversely proportional to the concentration of the analyte in the sample. When no analyte is present in the sample, the labelled reagent binds exclusively to the second reagent and a high signal is detected. With increasing concentration of analyte present in the sample, binding of the labelled reagent to the second reagent proportionally decreases and a drop in signal is detected. Accordingly, the second chamber comprises a competitive immunoassay. The present invention is therefore a combination assay as both a sandwich and competitive immunoassay are used to detect an analyte in a sample.
The sensitivity of the competitive assay as a function of analyte concentration depends upon a number of factors, including the population of labelled reagent and the surface concentration of the second reagent. By adjusting these factors it is possible to “tune” the sensitivity of the competitive assay.
In one embodiment, the competitive assay is tuned so that it is less sensitive to the analyte concentration than the sandwich assay. In this manner, as the concentration of the analyte present in the sample increases, the signal from the first sample chamber rises sharply whereas the signal from the second chamber falls slowly. By combining these two outputs mathematically, it is possible to maintain the detection limit of the sandwich assay, whilst extending the dynamic range of the assay by use of the less sensitive competition assay that is taking place simultaneously.
In a second embodiment, the sandwich assay and the competitive assay have similar sensitivities, and hence they saturate at similar concentrations. In this instance, the dynamic range of the assay is not enhanced, but the detection limit is improved by combining two assays that are functioning in opposite modes.
Preferably, the device further comprises a third chamber comprising a third reagent proximal to the transducer, the third reagent having a lower affinity for the analyte or the labelled reagent under the conditions of the assay than the first reagent for the analyte. Accordingly, the third reagent provides the negative control. It is important that the affinity is considered under the conditions of the assay. The reason is that the affinity of the first reagent for the labelled reagent is mediated by the presence of the analyte. Thus, in the absence of the analyte, neither the first nor third reagent has any affinity for the labelled reagent. However, in the presence of the analyte, the third reagent has a lower affinity for the labelled reagent than the first reagent.
The third reagent is an inert surface which mimics the surface where the first and second reagents are immobilised. In one embodiment, the third reagent is a polysaccharide, for example dextran. In an alternative embodiment, the third reagent is an isotype control antibody. The third reagent typically has similar chemical and physical properties to the first reagent, but provides little or no affinity for the labelled reagent under the conditions of the assay. In a particularly preferred embodiment, the third reagent has essentially no affinity for the labelled reagent under the conditions of the assay. Preferably, the third reagent provides essentially no affinity for the analyte. That is, the binding of the labelled reagent, or, where applicable, the analyte, to the third reagent is non-specific. In this manner, the third reagent can compensate for non-specific binding of the labelled reagent to the first reagent, and can also compensate for unwanted movement of the labelled reagent relative to the transducer, e.g. by sedimentation under gravity, which can interfere with the measurement process.
The electrical signals from the sample chambers are manipulated mathematically. The mathematical manipulation of the electrical signals is the same as that described in WO 2012/137009. In a preferred embodiment, the method of the present invention further comprises subtracting the electrical signal of the third chamber from the electrical signals of the first and second chambers to obtain baseline corrected electrical signals and dividing the baseline corrected electrical signal of the first chamber by the baseline corrected electrical signal of the second chamber.
In the present invention, the first and second reagents can be considered as acting as “dynamic” controls for each other, whereas WO 2012/137009 uses a “static” positive control. When using such a static positive control, the algorithmic output is limited approximately to lie between 0.000 and 1.000.
In the present invention, at low concentrations of analyte, a ratiometric signal between 0.000 and 1.000 is obtained which defines the magnitude of the signal from binding to the first reagent (i.e. the measurement signal) relative to the binding of the second and third reagents (i.e. the positive and negative controls, respectively), by interrogating the output of the detector.
In one embodiment, at high concentrations of analyte, the ratiometric signal increases above 1.000 i.e. the signal from binding to the first reagent exceeds the signal from binding to the second reagent. This arises because the signal from binding to the second reagent (the positive control) decreases slowly whilst the signal from binding to the first reagent (the measurement signal) increases sharply. In this embodiment, the decrease in the signal from binding to the second reagent is steady owing to the use of a low sensitivity competitive assay. The ratiometric signal continues to increase above 1.000 until the signal from binding to the second reagent approaches 0.000 owing to saturation of the labelled reagent with analyte. In this manner, the first and second reagents are working in combination with each other to extend the dynamic range of the sandwich assay in the first sample chamber and delay the onset of saturation and/or high dose hook which would normally be observed at lower analyte concentrations. The first and second reagents can be thought of as acting as controls for each other. In combination with the third reagent, the first and second reagents are acting to increase the dynamic range of a sandwich assay without compromising the sensitivity of the assay.
In a preferred embodiment, the binding of the first and second reagents to the analyte or the labelled reagent is dependent on the analyte concentration and the binding of the third reagent to the analyte or the labelled reagent is independent of analyte concentration. The second reagent (the positive control) is therefore variable whereas the third reagent (the negative control) is constant. The present invention removes the requirement for a “static” positive control, although such a control may also be included without detriment.
The first, second and third reagents may be attached to the transducer using techniques known in the art. Preferably the attachment is via non-covalent bonding, for example, a primary layer such as streptavidin or polystreptavidin, is adsorbed on to the transducer and the reagents are attached to the primary layer by a binding event.
The assay also requires the presence of a labelled reagent. By “labelled” reagent is meant a reagent which is attached to a label, which label being capable of absorbing the electromagnetic radiation generated by the radiation source to generate energy by non-radiative decay. It is this non-radiative decay which is transduced into an electrical signal by the transducer.
The label may therefore be composed of any material which is capable of interacting with the electromagnetic radiation in this manner. Preferably the label is selected from, but not limited to, a carbon particle, a coloured-polymer particle (e.g. coloured latex), a dye molecule, an enzyme, a fluorescent molecule, a metal (e.g. gold) particle, a haemoglobin molecule, a red blood cell, a magnetic particle, a nanoparticle having a non-conducting core material and at least one metal shell layer, a particle composed of polypyrrole or a derivative thereof, and combinations thereof. Preferably, the label is a carbon particle or a gold particle and most preferably a carbon particle.
In the case of a magnetic particle, the electromagnetic radiation is radio frequency radiation. All of the other labels mentioned hereinabove employ light, which can include IR or UV radiation. Gold particles are commercially available or may be prepared using known methods (see for example G. Frens, Nature, 241, 20-22 (1973)). For a more detailed explanation of the nanoparticle label see U.S. Pat. No. 6,344,272 and WO 2007/141581.
Preferably, the present invention uses a particle having a particle size of 20 to 1,000 nm, more preferably 100 to 500 nm. By particle size is meant the diameter of the particle at its widest point. The density of the particle will depend on the type of assay. Where the assay is diffusion-controlled, the particle preferably has a density of 0.5 to 3.0 g/mL, more preferably 1.5-2.0 g/mL and most preferably 1.8 g/mL. In this assay type, the particle is a carbon particle having the aforementioned particle size and density. Where the assay is gravity-assisted, the particle preferably has a density of 1.5 to 23 g/mL, more preferably 15-20 g/mL and most preferably 19 g/mL. In this assay type, the particle is a gold particle having the aforementioned particle size and density.
The label is proximal to the transducer when the binding event has occurred. That is, the label is sufficiently close to the surface of the transducer for the transducer to be able to detect the energy generated by the label on irradiation of the sample. The actual distance between the label and the surface of the transducer will, however, depend on a number of variables, such as the size and nature of the label, the size and nature of the antibodies and the analyte, the nature of the sample medium, and the nature of the electromagnetic radiation and the corresponding settings of the detector. The device of the present invention may include a radiation source which is adapted to generate a series of pulses of electromagnetic radiation and the detector is adapted to determine the time delay between each pulse of electromagnetic radiation from the radiation source and the generation of the electric signal thereby allowing a precise determination of the position of the label with respect to the transducer as discussed with reference to
The nature of the first, second and third reagents, as well as the labelled reagent, will depend on the nature of the analyte. In a particularly preferred embodiment, the labelled reagent comprises an antibody raised to the analyte or the complex or derivative of the analyte, the first reagent is an antibody raised to the analyte or the complex or derivative of the analyte, the second reagent is an analogue of the analyte, and the third reagent is a neutral surface. In principle, a single molecule could be used for each reagent, but in practice, the first, second and third reagents, as well as the labelled reagent, are a population of molecules. The term “antibody” preferably includes within its scope a Fab fragment, a single-chain variable fragment (scFv), and a recombinant binding fragment.
As alternatives to antibody-antigen reactions, the reagents and analyte may be a first and second nucleic acid where the first and second nucleic acids are complementary, or a reagent containing avidin or derivatives thereof and an analyte containing biotin or derivatives thereof, or vice versa. The reagents may also be aptamers. The system is also not limited to biological assays and may be applied, for example, to the detection of heavy metals in water. The system also need not be limited to liquids and any fluid system may be used, e.g. the detection of enzymes, cells and viruses etc. in the air.
The maximum observable signal is the maximum signal that can be achieved when monitoring the label binding to a surface. In the absence of alternative mass transport phenomena (e.g. convection, magnetic movement, buoyancy, sedimentation, etc.), the binding of particles to the transducer is governed by the diffusion rate of the analyte and labelled reagent which is, in turn, governed largely by the hydrodynamic radius of these components and the viscosity/temperature of the sample. The negative control should give a signal that is independent of the absence or presence of the analyte to be measured.
It has been found that for immunometric (i.e. sandwich or reagent-excess) assays, improvements in performance can be achieved by using an analogue of an analyte as the positive control (that recognises an antibody on the labelled reagent), and a non-reactive surface as the negative control. When used in combination, these controls define the upper and lower limits of the measuring range of the system. Thus, the output from the system is defined as the ratio of where the measurement lies between these two limits. Surprisingly this combination can be used to account for variations in the system components (e.g. the material forming the transducer), the environmental conditions, the sample variability and unwanted particle movement (e.g. sedimentation) in combination. The controls provided by the present invention have been found to compensate for all these parameters at the same time.
Other methods can be used to increase the dynamic range of an assay by incorporating different reagent spots with different antibodies at different concentrations, or different affinities, and by using mixtures of different labels. However, this greatly increases the complexity of the system, and requires further reaction chambers and may require splitting of the sample in order to mix different parts of the sample with different reagents and/or labels.
The sample which is suspected of containing the analyte of interest will generally be a fluid sample, e.g. a liquid sample, and usually a biological sample, such as a bodily fluid, e.g. blood, plasma, saliva, serum or urine. The sample may contain suspended particles and may even be whole blood. An advantage of the method of the present invention is that the assay may be performed on a sample which does contain suspended particles without unduly influencing the results of the assay. The sample will typically be in the order of microliters (e.g. 1-100 μL, preferably 1-10 μL). In order to hold a fluid sample, the transducer is preferably located in a sample chamber having one or more side walls, an upper surface and a lower surface. Accordingly, the device of the present invention preferably further comprises a chamber for holding a liquid sample containing the analyte or the complex or derivative of the analyte in contact with the transducer. In a preferred embodiment, the transducer is integral with the chamber, i.e. it forms one of the side walls, or upper or lower surface which define the chamber. Preferably the transducer forms the upper surface as shown in
The device contains a first chamber containing the first reagent, a second chamber containing the second reagent and a third chamber containing the third reagent. The first, second and third reagents are proximal to the transducer. The first, second and third chambers are preferably in fluid communication, allowing the mixture of sample and labelled reagents to fill the three chambers in a sequential fashion. It should be noted that the sample and labelled reagents in each of the three chambers are identical in the present invention. The device preferably further contains a capillary channel having a sample receiving end which is contact with the outside of the device and a sample delivery end which is in fluid communication with the sample chamber(s), as shown in the core 21 in
The labelled reagent and optionally one or more additional reagents are preferably stored in a chamber incorporated into the device of the present invention. The labelled reagent may also be supplied as part of a kit incorporating the device and the labelled reagent. Accordingly, the present invention also provides a kit comprising the device as described herein and the labelled reagent. The labelled reagent may be deposited onto the surface of the transducer.
The device of the present invention is not restricted to detecting only one analyte and different analytes may be detected by employing different first reagents which selectively bind each analyte, or a derivative or complex of the analyte, being detected. Multiple tests can be carried out using only one electrical connection to the transducer, by illuminating different locations of the transducer sequentially and interrogating the outputs sequentially.
A potential additional source of background interference is the settling of suspended particles on to the surface of the piezo/pyroelectric transducer, including labelled reagent and cellular components of the sample. This source of interference may be reduced by positioning the transducer above the bulk solution, e.g. on the upper surface of the reaction chamber. Thus, if any settling occurs, it will not interfere with the transducer. Alternatively, the particles could be less dense than the medium and hence float to the surface of the bulk solution rather than settling on the surface of the transducer. This and other modifications are included in the scope of the present invention.
In a preferred embodiment, the device of the present invention consists essentially of the above-described features. By “essentially” is meant that no other features are required to perform the assay. The device may take the form of a separate reader and cartridge, or an integrated device. In the former, the device is formed of a reader and a cartridge, in which the cartridge is releasably engageable with the reader, and in which the reader incorporates the radiation source and the detector, and the cartridge incorporates the transducer and the first, second and third reagents. The reader is preferably a portable reader. The present invention also provides the cartridge comprising the transducer and the first, second and third reagents as defined herein. The cartridge is preferably a disposable cartridge.
The present invention will now be described with reference to the following examples which are not intended to be limiting.
PVDF Film
A poled piezo/pyroelectric polyvinylidene fluoride (PVDF) bimorph film, coated in indium tin oxide was used as the sensing device in the following examples. The indium tin oxide surface was coated with a layer of parylene (of approximate thickness 1 micron) by a vapour phase gas deposition process. This method involved the sublimation and subsequent pyrolysis of a paracyclophane precursor, followed by a free-radical polymerisation on the surface. See WO 2009/141637 for further details. The resulting parylene layer was then coated with a layer of biotinylated bovine serum albumin (10 μg/mL in 10 mM phosphate buffer) by passive adsorption over the course of two hours. The surface was washed and then coated in polystreptavidin solution (10 μg/mL in PBS-10 mmol/L phosphate buffer containing 2.7 mmol/L KCl, 137 mmol/L NaCl and 0.05% Tween) by incubation at room temperature overnight. Polystreptavidin was prepared as described by Tischer et al (U.S. Pat. No. 5,061,640).
Materials
Monoclonal antibodies were raised essentially as described in “Monoclonal Antibodies: Properties, Manufacture and Applications” by J. R. Birch and E. S. Lennox, Wiley-Blackwell, 1995, and biotinylated by methods known in the art. Carbon-labelled reporter conjugates were prepared essentially as described by Van Doom et al. (U.S. Pat. No. 5,641,689).
Preparation of the Cartridge
Strips of PVDF pyroelectric polymer film were coated in three separate areas with a universal streptavidin coating, as described above. The three areas were separated by an adhesive spacer attached to the surface of the sensor, allowing subsequent incubation of reagents onto each area without cross-contamination of the surfaces. The three surfaces (labelled spot 1, spot 2 and spot 3) were coated with three different biotinylated reagents, washed and then dried in the presence of sucrose stabiliser.
As shown in
Assays
Assays were carried out by charging the sample chambers with the sample through the capillary channel in the core 21. The sample was either pre-mixed with the labelled carbon particles prior to being loaded into the cartridge, or the carbon particles (and any additional reagents) were dried down in the channels of the cartridge. The sample was then mixed with the reagents by being pumped through the channels of the cartridge by a displacement pump in the instrument. After the measurement chambers had filled, they were then irradiated (through the holes in the top cover 19) sequentially with chopped LED light. For each LED pulse, a voltage was measured across the piezo/pyrofilm 15 using an amplifier and analogue to digital (ADC) converter. The change in the ADC signal is calculated over time. The final output from each spot is the rate of change of signal from the ADC as a function of time.
Two different types of assay for IgE were carried out. Each assay used three measurement chambers, denoted spot 1 (negative control), spot 2 (sandwich assay) and spot 3 (positive control). The coatings in spots 1 and 2 were identical for each assay. Spot 1 was coated with a biotin conjugated 70 kDa amino-dextran (Fleet Bioprocessing) at a concentration of 1 μg/ml and spot 2 was coated with a biotinylated anti-IgE Hytest mouse antibody (clone 4F4) at a concentration of 4 μg/ml. The coatings in spot 3 were specific to each assay. In Example 1 (comparative), with a fixed positive control, spot 3 was coated with biotinylated goat anti-mouse IgG. In Example 2 (invention), biotinylated IgE was coated onto spot 3 at a concentration of 10 μg/ml. Carbon particles coated in a matching anti-IgE antibody, Hytest 4F4, were used as the label in the system. For the avoidance of confusion, the surface of spot 2 (described as the first chamber above) is equivalent to the first reagent, the surface of spot 3 (described as the second chamber above) is equivalent to the second reagent and the surface of spot 1 (described as the third chamber above) is equivalent to the third reagent.
Repeat measurements (six at each concentration) were carried out on fresh blood samples at four different IgE concentrations (0, 156, 547, 1471 IU/mL). For each cartridge, the output from spot 1 was subtracted from the outputs in both spot 2 and spot 3 (i.e. both measurements were baseline corrected). Then the baseline corrected measurement in spot 2 was divided by the baseline corrected measurement in spot 3. The mean final assay count (and standard deviation) was then calculated from the cartridges run at each concentration.
The results are set out in Table 1.
| Number | Date | Country | Kind |
|---|---|---|---|
| 1508832.1 | May 2015 | GB | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/EP2016/061435 | 5/20/2016 | WO | 00 |
