Patent Application
20130052085
The present invention relates to microfluidic analysis systems where the emitted light of an emitting source is measured by optic detection, and where a transparent body separates the emitting source from the optic detector. The invention especially relates to optic calibration of the device, the calibration being related to changes in the transparency of the transparent body and/or changes in the temperature of the emitting source.
Microfluidic systems are widely used, for example to measure concentrations of a substance in fluid, such as a substance in a body fluid for example glucose.
One example of such a system is found in WO 2008/089764, describing a system based on the extraction of the substances from the medium by diffusion across a semi-permeable membrane to be collected by a sweeping fluid, or perfusion fluid. This substance enriched fluid is then fed to a microfluid system, especially being formed as a microfluidic chip, where different reactions with the substances emit light at an intensity to be correlated to the concentration of the substances in the medium. An optical detector forms part of an electrical part of the system connected to the microfluidic chip, where the optical detector is positioned so that it detects the light emitted from the reactions. The electrical part and the microfluidic chip are separated by a transparent medium or body such as glass.
The importance of being able to accurately and continuously measure substance concentrations within a medium, such as tissue or some fluid like bodily fluid, is well known in the field of medical art or science. For patients suffering from diabetes it is often vital to monitor the levels of glucose, since it is known that elevated levels of glucose in the blood are indicative of conditions such as hyperglycemia and glycosuria resulting from inadequate production or utilization of insulin. Alternatively, abnormally low glucose concentrations may be an indication of overproduction of insulin. Therefore measurement of blood glucose concentration is an important tool for diagnosing, treating or controlling a variety of disorders in which the glucose concentration is known to be an indicator of the existence or severity of the condition. Situations thus exist in which the amount of insulin present is either in excess of or less than that required to handle the specific blood glucose level at any given time. Such situations are especially severe when an individual with a diabetic condition is under stress conditions, such as surgery or during childbirth.
Not only diabetics, but also non-diabetic patients may have the need of having a surveillance of their blood glucose level, like acutely ill patients treated with a pharmacologic dose of corticosteroid.
Within biotechnology other interesting applications are to maintain and control specific concentration levels of nutrients, such as glucose, in cell culture reactors, where a long-term stability is needed in order to provide feedback information required to control computerized delivery systems so that a particular chemical can be maintained within preset limits.
In a system as the one disclosed in, for example WO 2008/089764, where a transparent medium separates the optical detector from the emitting source, the state of the transparency of the transparent medium will also influence the measurements, such as if the transparent medium gets covered with dirt and moieties or simply is scratched and gets cracks. The same may be the problem of a transparent cover of the channels of the microfluidic chip of the system.
Among examples are as also described in WO 2008/089764 and its references, the document disclosing that examples of measuring the concentration of a specific chemical, such as glucose, in a solution is described in a number of documents, such as WO9939629A1 and U.S. Pat. No. 4,452,887. The latter describes a determination method where a test material or the reaction product thereof is oxidized using an oxidase enzyme, and hydrogen peroxide formed simultaneously with the oxidation is determined by various means. This has recently become important. The reason for this is that the determination of hydrogen peroxide can be accurately performed by a colorimeteric determination after a dye-forming reaction using peroxidase or by means of an electrode reaction. According to U.S. Pat. No. 4,452,887 a colorimeteric method based on the foregoing principle using a Trinder reagent is well known. In this method, hydrogen peroxide formed by the action of an oxidase enzyme is reacted with peroxidase to catalyze the oxidative coupling reaction of aminoantipyrine and a phenol and the dye thus formed is colorimetrically determined. The merit of the reaction system is that the same detection system can be utilized for different kinds of oxidase enzymes and the application of the system for various kinds of analyses is being investigated. Among these oxidase enzymes, particularly important enzymes in clinical chemistry are glucose oxidase, cholesterol oxidase, uricase, glycerol oxidase, phosphoglucose oxidase, etc.
In order to improve the systems enhancers may be introduced such as described in WO9105872A1, describing an enhanced chemiluminescent assay, in which a dihydrophthalazinedione such as luminol, a peroxidase such as HRP and an oxidant such as H2O2 are co-reacted in the presence of an enhancer such as (p)-iodophenol. The enhancer is generated by enzyme-catalysed reaction of a pro-enhancer, e.g. (p)-iodophenol phosphate is cleaved by alkaline phosphatase, enabling this enzyme to be assayed instead of peroxidase. Alternatively, the enhancer is added, an anti-enhancer such as (p)-nitrophenol is generated by enzymatic reaction of a pro-anti-enhancer such as (p)-nitrophenol phosphate and the reduction in luminescent emission is measured.
The chemi-luminescent assays are described as “enhanced” in the sense that the total light emission of the reaction and/or the signal/background ratio is larger than that obtained in the same reaction carried out in the absence of an enhancer.
The present invention introduces a method of estimating present state of the system especially for calibration purposes. This is done by introducing a device with a fluidic part comprising,
The present invention is especially, but not exclusively, suitable for devices forming part of an analysis system, especially where the analysis is based on optical detection formed by reactions in fluids present in the fluid communicating network, the detector being an optic detector.
The reactions in the fluids may be related to a concentration of specific substances to be measured by the device.
In one more specific embodiment of the present invention, the transparent wall section and the electronic part are separated by a transparent body.
In a further embodiment, the light emitting device is used to estimate the transparency of the transparent body and/or the transparent wall section by reflection.
In another or additional embodiment, the light emitting device is used to estimate the temperature of the fluid(s) in the fluid communicating network.
The correlation of the system is in a preferred embodiment of the present invention based to the estimation of the transparency, the method being to detect light emitted from the light source being scattered and reflected in and by the transparent body, and comparing the detected value(s) or spectral distribution to reference value(s) or a reference spectral distribution.
To clearly separate the correlation light from the emitted light from the reactions in the system, the light emitting device emits light at a narrow spectral span being substantially different to the light formed by the reactions in the fluids.
In one preferred embodiment, the light emitting device is a light diode.
In another preferred embodiment of the present invention, a temperature responsive element characterized by having reflection characteristics related to its temperature is positioned into or in connection with the fluid communicating network, and in further embodiment; a heating element is positioned in contact with the fluid communicating network. These may be used to estimate the temperature of the fluids and the fluid communicating network, the method being to detect light emitted from the light source being reflected by the temperature responsive element, and comparing the detected value(s) or spectral distribution to reference value(s) or a reference spectral distribution.
The present invention thus further introduces a method of regulating the temperature of the fluid of the device, wherein the method is to regulate the temperature of the heating element in accordance with the estimated temperature.
In order to improve the reflection of the emitted light to an optical detector, the present invention in another embodiment introduces that the fluidic part further comprises at least one optically reflective surface.
In one specific embodiment, the reflective surface is formed at the internal surface(s) of the fluid communicating network at least where the wall section is transparent.
In another specific embodiment, the reflective surface is formed at the side opposite to the detector of the fluid communication network at least where the wall section is transparent.
To focus the emitted light, in yet another embodiment the reflective surface is shaped having a focus point roughly at the position of the detector.
In a further embodiment of the present invention the fluidic part is a fluidic chip where ridges are formed in the surface of at least a first body, the ridges formed into channels by covering the first body with a second body having at least a transparent area.
The present invention in general relates to calibrating a system where the emitted light of an emitting source is measured by optic detection, and where a transparent body separates the emitting source from the optic detector. The invention especially relates to optic calibration of the device, the calibration being related to changes in the transparency of the transparent body and/or changes in the temperature of the emitting source.
The fluid communicating network (2) may comprise any number of branches for feeding any number of different fluids (5, 6) into the system for mixing, and a mixing section (3) where the fluids gets time to mix sufficiently to give some reactions with an observable effect representative of the desired quantity to be measured. The fluid communicating network (2) may further comprise a detection section (4) where the observable effect may be measured or detected.
The reactions in the detection section (4) lead to an observable effect (11), where the effect non-limiting in the following description is an optical effect, such as emitting light at some spectral distribution. The cover (10) and any other optional second bodies covering the fluid communicating network (2) are transparent to the observable effect (11), at least where it/they cover(s) the detection section (4).
An electrical part (9) having an optical sensor or cell (12) is positioned on top of the fluidic part (1) such that the optical sensor (12) is at least partly aligned with the detection section (4).
One of the fluids, for example (5), may be a sample fluid, in the present context being defined as a carrier fluid enriched with substances of interest at some concentration representative of the concentration of the species in some medium. As non-limiting examples the medium may be the human tissue or waste water. The remaining of the fluids (6) may thus be reagent fluids to be mixed to the sample fluid to give some observable effect, in the following exampled as a optical effect.
The operation of this example setup could in one embodiment be that a sample fluid (5) is mixed with reagent fluid(s) (6) to emit light with an intensity corresponding to the concentration of substances. This intensity is then measured by the optical sensor (12) and the measurements are optionally processed in a computer to give an indication of the concentration of the substances of interest in the sample fluid. The fluids may finally leave the system (7) or be collected in a waste storage.
Since the measurements depend on an observable effect being correlated to the quantity to be measured, such as an optical reaction being related to the concentration of substances in a fluid, it is essential that no ‘external’ effects to the quantity affect the measurements, or at least, that they are correlated for by calibrating the system accordingly.
The light emitted by the light emitting device (15) will be scattered in the system of cover (11), channels (2, 3, 4) and the main body of the fluidic part (1), and a fraction of it will be measured by the optical sensor (12). Thus the light emitted by the light emitting device (15) will be affected in the same manner by ‘external’ effects like (13) and (14) as the light emitted by the reactions (11).
The idea of the invention therefore is from time to time to emit light by the light emitting device (15) and use the intensity measured by the optical sensor (12) to estimate the present transparency of the cover (10) (and other optional covers/second bodies), using this for calibration purposes. Optionally, a threshold limit could be introduced to give off a signal when the measured intensity gets below this threshold limit, indicating the system may no longer operate properly, and should be exchanged, repaired or cleaned.
A further aspect of the present invention illustrated in
With given intervals the light emitting device (16) emits light and the reflected light from the temperature responsive element (17) is measured by the optical sensor (12) and the temperature of the temperature responsive element (17), being in contact with and therefore related to the temperature of the fluids in the fluid communication network (2), is calculated.
In one preferred embodiment a heating and/or cooling element (18) is positioned in contact with the fluid communicating network (2), especially in contact with the detection section (4). This element will then be controlled in its heating and/or cooling in response to the temperature measurements, thereby making it possible to regulate the temperature of the fluids to a desired temperature.
The light emitting device (16) used for temperature measurements may be the same device as the light emitting device (15) used to measure the transparency of the cover (10), optionally able to emit light at two different spectral spans, one used to estimate the transparency of the cover (10), and one used for temperature measurements.
In another embodiment two separate light emitting devices (15) and (16) are introduced in the system.
In yet another embodiment of the present invention, the fluidic part (1) comprises at least one reflective surface (19). In one embodiment shown in
Further, in a preferred embodiment, the reflective surface (19) is shaped in such a manner that it comprises a focus point being located at the optical sensor (12). If, for example, the at least one reflective surface (19) is formed in the bottom surface of the channel(s) of the detection section (4) (or part of or the whole of the fluid communicating network (2)), this shaping with a focus point may be formed by shaping the heights (20) of the channel(s) by introducing varying heights (20) so that the bottoms of the channels would ‘fit’ to a parabolic surface.
The present invention may comprise one of or any combination of the embodiments described above.
Although the invention above has been described in connection with a preferred embodiment of the invention, it will be evident for a person skilled in the art that several modifications are conceivable without departing from the invention as defined by the following claims.
| Number | Date | Country | Kind |
|---|---|---|---|
| PA 2010 00023 | Jan 2010 | DK | national |
This application is entitled to the benefit of and incorporates by reference essential subject matter disclosed in International Patent Application No. PCT/DK2011/000001 filed on Jan. 12, 2011 and Danish Patent Application No. PA 2010 00023 filed Jan. 13, 2010.
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/DK2011/000001 | 1/12/2011 | WO | 00 | 10/2/2012 |
