US20070116376A1

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Publication number: US20070116376A1
Application number: US11/283,365
Authority: US
Inventors: James Kolterman; Eric Shain; Robert Gray; Shihai Huang; Gavin Cloherty
Original assignee: Abbott Laboratories
Current assignee: Abbott Laboratories
Priority date: 2005-11-18
Filing date: 2005-11-18
Publication date: 2007-05-24
Also published as: EP1788523B1; US20100142848A1; EP2947624A1; US8249381B2; EP1788523B8; EP1788523A1; ES2537109T3

Abstract

Description

BACKGROUND OF THE INVENTION

1. Field of the Invention

This invention relates to a method for correcting signals detected by a detection system in a diagnostic instrument.

2. Discussion of the Art

Raw images generated by a diagnostic instrument having a digital image sensor as a detector, such as, for example, the Applied Biosystems Prism 7000 diagnostic instrument, can exhibit an anomaly known as “cross-talk.” Cross-talk refers to the situation where a signal from a given location in the image (for example, a given well in a plate having a plurality of wells, e.g., a 96-well PCR plate), causes a variation in the signal at a different location in the image (for example, a different well in the plate having a plurality of wells). A specific region within an image associated with an independent signal is often referred to as a region of interest (alternatively referred to herein as ROI). Each ROI defines the specific pixels within the image associated with a specific reaction. Variations in signal due to cross-talk, although typically small, can induce variations in reaction quantification of one or more regions of interest within the image. In some cases, sensitivity of the reaction is reduced by requiring an increase in signal threshold in order to avoid false positive results due to cross-talk.

The areas in the image between the regions of interest of the image contain optical information that can be used to compensate for sources of variation in signal. These sources of signal variation can result from a specific geometric optical reflection, scattered light from optical components, light leakage, changes in intensity of the source of light, and the like. All of these sources of variation can contribute to a dynamically changing error in the optical signal in a given region of interest of the image.

It is desired to monitor a region of interest associated with a reaction and ultimately correct for varying anomalous signals over the course of a testing run in a diagnostic instrument.

SUMMARY OF THE INVENTION

In one aspect, this invention provides a method for correcting the signal in an image having a plurality of regions of interest, the method comprising the steps of:

- (a) providing an image having a plurality of regions of interest, these regions of interest having areas between them;
- (b) determining a region of correction between at least two regions of interest;
- (c) calculating a correction signal from the region of correction; and
- (d) using the correction signal to correct a measured signal from one or more regions of interest.

In another aspect, this invention provides a method for defining a region of correction for use in a method for correcting the signal in an image having a plurality of regions of interest, the defining method comprising the steps of:

- (a) providing an image having a plurality of regions of interest;
- (b) extracting geometric information for a plurality of regions of interest;
- (c) selecting a location between at least two regions of interest;
- (d) selecting at least one parameter to describe regions of correction; and
- (e) constructing regions of correction between the at least two regions of interest.
  The regions of correction defined in the forgoing method can be stored for further use to correct signals measured from one or more regions of interest.

The specified regions of correction can have various shapes, such as, for example, circles, squares, diamonds, rectangles, or other geometric figures. Storing of the regions of correction involves determining the definition of the location and the shape of the geometric areas and specifying the pixels contained within each area.

The method of this invention can be used to measure a dynamically changing signal and the effect of the dynamically changing signal on a region of interest of a specific reaction. Correcting for the cross-talk inherent in a dynamically changing signal will greatly increase the sensitivity of the method of detection used in an assay employing such signals. The method of this invention does not affect the optical path of the light collected by a detector. The method can be applied directly to an image that is collected for all the regions of interest

By measuring the signals in the regions of correction, the signal anomaly due to cross-talk can be significantly reduced.

The sizes and shapes of the regions of correction can vary and depend primarily on the orientation of the existing regions of interest and any image distortions that may be present.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a flow chart that defines the placement of diamond-shaped regions of correction about circular reaction regions of interest.

FIG. 2A illustrates one embodiment of reaction regions of interest and regions of correction. The reaction regions of interest are circular and the regions of correction are circular.FIG. 2B illustrates another embodiment of reaction regions of interest and regions of correction. The reaction regions of interest are circular and the correction regions of interest are rectangular.FIG. 2C illustrates still another embodiment of reaction regions of interest and regions of correction. The reaction regions of interest are circular and the regions of correction are shaped like diamonds.

FIG. 3 is a flow chart illustrating the application of the image-based correction algorithm of this invention.

FIG. 4 is a map of a 96-well plate illustrating the location of each positive response and each negative response.

FIG. 5 is a sample of an image at the end of a run.

FIG. 6 is a sample of an image showing reaction regions of interest and regions of correction.

FIG. 7 shows fluorescence responses in a PCR assay without image-based correction applied.

FIG. 8 shows fluorescence responses in a PCR assay without image-based correction applied. In this figure, the Y scale is expanded.

FIG. 9 shows fluorescence responses in a PCR assay with image-based correction. In this figure, the Y scale is expanded.

FIG. 10 shows the fluorescence response in a PCR assay for well F-11 fromFIG. 4 with and without assay-based correction.

DETAILED DESCRIPTION

As used herein, the expression “region of interest” means the collection of pixels within an image that define the location of a specific optical signal. The expression “reaction region of interest” means the region of interest associated with a specific reaction in an assay. The expressions “region of correction” and “correction region of interest” mean the area associated with the background portion of the image adjacent to a reaction region of interest. The expression “reaction pixel sum” means the sum of all the pixel intensity values within a reaction region of interest. The expression “reaction pixel count” means the number of pixels within a reaction region of interest. The expression “reaction region of interest pixel average” means the value obtained by dividing the reaction pixel sum by the reaction pixel count. The expression “correction pixel sum” means the sum of all the pixel intensity values within a region of correction. The expression “correction pixel count” means the number of pixels with a region of correction. The expression “region of correction pixel average” means the value obtained by dividing the correction pixel sum by the correction pixel count. The term “scale” means a multiplicative factor applied to the correction calculation. The term “centroid” means the geometric center of a region of interest. As used herein, the terms “circular”, “rectangular”, “annular”, and other terms relating to shape referred to herein are intended to include shapes that are substantially circular, substantially rectangular, substantially annular, and shapes that are substantially similar to the other shapes referred to herein, respectively.

In one aspect, this invention provides a method for correcting an image having a plurality of reaction regions of interest and a plurality of regions of correction, the method involving the steps of:

- (a) providing an image having a plurality of regions of interest, these regions of interest having areas between them;
- (b) determining a region of correction between at least two regions of interest;
- (c) calculating a correction signal from the region of correction; and
- (d) using the correction signal to correct a signal measurement from one or more regions of interest.
  Prior to carrying out the method of this invention, certain steps must be taken to calibrate the imaging system, which is typically a digital imaging system.FIG. 3 shows a flow chart that illustrates steps for defining regions of correction between adjacent reaction regions of interest for the calibration step of the method of this invention. In this flow chart, generic regions of correction are described.

According to the calibration method of this invention, the centroid of each reaction region of interest is determined. The reaction regions of interest are typically determined by using a calibration where signals in a device having a plurality of reaction sites are measured. A signal is measured at each reaction site. In the case of 96-well reaction plates, the signals in a calibration plate containing fluorescent dye at each reaction site can be measured by an imaging sensor. A calibration plate is a 96-well reaction plate used for calibrating the instrument used. The reaction regions of interest can be determined by locating the contiguous pixels at each reaction site within the image. The geometric centroid of each set of centroids from four adjacent reaction regions of interest can be used to determine a center point for a region of correction. A region of correction using that center point and a specific geometric shape can be defined. As shown inFIGS. 2A, 2B, and2C, the reaction regions of interest are circular in shape. A region of correction can be circular-shaped, as shown inFIG. 2A, rectangular-shaped, as shown inFIG. 2B, or diamond-shaped, as shown inFIG. 2C. Other shapes, such as, for example, closed polygons, are suitable for both the reaction regions of interest and the regions of correction. The parameters of the regions of correction are typically radii of rings for circular-shaped regions of correction, length and width for rectangular-shaped regions of correction, and length of sides for diamond-shaped regions of correction. Dimensions for the particular geometric shape selected are specified. An alternative to defining regions of correction by means of geometric shapes involves the use of an arbitrary bitmap. Such a bitmap could, for example, be a 9 by 9 array of values specifying which pixels would be included in the region of correction and which pixels would be excluded from the region of correction. The center points of the regions of correction can be mirrored to create regions of correction on the periphery of the plate for the outer rows and columns of the reaction regions of interest in the image. Thus, in the case of diamond-shaped regions of correction in an image having 96 reaction regions of interest, there are 117 diamond-shaped regions of correction of interest in total, i.e., four (4) diamond-shaped regions of correction per reaction region of interest. The use of diamond-shaped regions of correction is shown inFIG. 2C. The regions of interest associated with specific wells can be determined and stored, such as, for example, by means of a computer. In this embodiment, each reaction region of interest has the four adjacent regions of correction associated with it.

After the region of correction calibration is performed, the correction based upon from the region of correction can be applied by using the following method. Once the region of correction calibration is performed, a background offset value needs to be generated. This value can be generated in at least two ways. According to a first alternative, a background calibration can be performed. In this method, an image is taken of a plate without any fluorescent dye. During the background calibration, the average pixel value for each region of correction is calculated by dividing the pixel sum by the pixel count in that region of correction to obtain an average pixel value. This average pixel value is indicative of the background light level and is referred to as the background offset value. The background offset values are stored for use in future runs, e.g., PCR runs. Alternatively, the background offset value can be determined on a run-by-run basis by calculating the average pixel value for each region of correction for the first reading of a run, e.g., a PCR run. Because the first (or first few) readings of a PCR run occur before a significant reaction signal is produced, this alternative method provides a good representation of the background.

The signal correction is performed in the following manner. Performance of signal correction is depicted inFIGS. 1 and 3. For each reaction, the reaction pixel sum and the reaction pixel count are calculated by using the reaction region of interest. The average pixel value for the four regions of correction associated with a given reaction region of interest is calculated. Although four regions of correction are shown inFIG. 1 and diamond-shaped regions of correction are shown inFIG. 1, the method is not limited to four regions of correction nor is the invention limited to diamond-shaped regions of correction. The background offset value is subtracted from the region of correction pixel average. Then, this difference is multiplied by the reaction region of interest pixel count and, if necessary, by a scale factor, to generate a correction value. The correction value is then subtracted from the reaction region of interest pixel sum to generate a corrected reaction region of interest pixel sum. The scale factor is typically dependent upon the detection system. An example of a scale factor is 1.15. In some instrument systems, multiple exposures are made at each reading to increase the dynamic range of measurement. In this case, a corresponding background offset and region of correction pixel average needs to be generated for each exposure. The correction to the reaction pixel sum is then made for the exposure of longest duration that does not exhibit significant saturation of the image sensor.

This invention can also be applied to an assay system based on array or a microarray, such as, for example, the Vysis GenoSensor genomic DNA microarray system (Abbott Laboratories, Abbott Park, Ill.). Such systems can measure a plurality of genomic targets through hybridization to an array of capture targets placed on a surface, such as, for example, a glass “chip” or a microscope slide. The product of the hybridization is typically measured by means of fluorescent dyes and an electronic imaging system.

The following non-limiting example further explains the method of this invention.

EXAMPLE

A real time PCR run for HIV was performed on an ABI Prism 7500 instrument (Applied Biosystems, Foster City, Calif.). This instrument utilizes a 96-well plate format with wells arranged in a 12×8 array. The run was configured so that there were 84 wells containing positive samples with a concentration of 1×10⁶copies/mL and 12 wells not containing positive samples, i.e., negative wells. The negative wells were distributed on the plate to maximize the potential cross-talk from the wells containing positive samples.FIG. 4 illustrates the layout of the plate.

The ABI Prism 7500 instrument uses a CCD camera and measures fluorescence in five wavelength bands.FIG. 5 shows one image from the end of the PCR run.FIG. 6 shows the same image with the reaction regions of interest and the regions of correction superimposed. In this example, a diagonal array of diamond-shaped regions of correction, each of which contained of 25 pixels, were used. The first reading in the PCR run was used to establish the background offset values for each subsequent reading. The scaling factor used was 1.15.

FIG. 7 shows the raw fluorescence signals for all 96 samples without any image-based correction applied. As can be seen, the 84 positive samples generated signals significantly above the background fluorescence bycycle15 and approached their maximum fluorescence bycycle25.FIG. 8 shows the same responses with the Y-axis scaled to focus on the responses in wells not containing positive samples. All of the negative responses showed a small but significant rise fromcycles15 through25, which is caused by cross-talk from the responses of the positive samples.FIG. 9 shows the effect of the image-based correction on the negative responses. As can be seen, the cross-talk signal has been effectively eliminated.FIG. 10 shows the response for well F-11 with and without the image-based correction applied.

The method is also applicable to images that contain a fewer or a greater number of regions of interest.

Various modifications and alterations of this invention will become apparent to those skilled in the art without departing from the scope and spirit of this invention, and it should be understood that this invention is not to be unduly limited to the illustrative embodiments set forth herein.