- Research article
- Open Access
Evaluation of methods for detection of fluorescence labeled subcellular objects in microscope images
© Ruusuvuori et al; licensee BioMed Central Ltd. 2010
- Received: 17 September 2009
- Accepted: 13 May 2010
- Published: 13 May 2010
Several algorithms have been proposed for detecting fluorescently labeled subcellular objects in microscope images. Many of these algorithms have been designed for specific tasks and validated with limited image data. But despite the potential of using extensive comparisons between algorithms to provide useful information to guide method selection and thus more accurate results, relatively few studies have been performed.
To better understand algorithm performance under different conditions, we have carried out a comparative study including eleven spot detection or segmentation algorithms from various application fields. We used microscope images from well plate experiments with a human osteosarcoma cell line and frames from image stacks of yeast cells in different focal planes. These experimentally derived images permit a comparison of method performance in realistic situations where the number of objects varies within image set. We also used simulated microscope images in order to compare the methods and validate them against a ground truth reference result. Our study finds major differences in the performance of different algorithms, in terms of both object counts and segmentation accuracies.
These results suggest that the selection of detection algorithms for image based screens should be done carefully and take into account different conditions, such as the possibility of acquiring empty images or images with very few spots. Our inclusion of methods that have not been used before in this context broadens the set of available detection methods and compares them against the current state-of-the-art methods for subcellular particle detection.
- Kernel Density Estimation
- Simulated Image
- Spot Detection
- Reference Result
- Human Osteosarcoma Cell Line
Recent advances in cell imaging technologies include accurate stage controllers, improved optics, increased camera resolution, and, perhaps most importantly, fluorescent staining of specific cellular components. Together these advances enable automated image acquisition of small subcellular objects with the goal of providing insight into phenotypes and cellular functions [1–4]. With increased imaging throughput and large-scale data acquisition, the challenge of image interpretation and information extraction has also shifted from visual inspection or interactive analysis to more automated methods [5, 6].
Accurate and automated subcellular object segmentation is essential for a variety of applications. For example, interpreting complex cellular phenotypes is typically dependent on identifying and quantifying various parameters associated with small organelles, setting high requirements for the accuracy of the image analysis . Also the analysis of cellular structures based on 3D images obtained with fluorescence and confocal microscopes requires accurate detection. Advances in such methods will improve our ability to model small organelles in 3D . Further, live-cell imaging with specific molecular probes has brought image tracking to subcellular level, and thus reliable object detection over the course of the imaging period adds a temporal dimension to image analysis [9, 10].
Summary of methods.
Band-pass filtering (BPF)
Object intensity enhancement with bandpass FIR filtering
Feature point detection (FPD) 
Percentile detection with non-particle discrimination
h-dome detection (HD) 
h-dome morphological filtering
Kernel methods (KDE) 
Kernel density estimation with a family of kernels
Local comparison (LC)
Maximization between direction-specific image convolutions
Locally enhancing filtering (LEF)
Local signal enhancement and background suppression
Morphometry (MGI) 
Morphometry with granulometric analysis
Multiscale wavelets (MW) 
Multiscale product of wavelet coefficients
Source Extractor (SE) 
Convolution applied for background clipped image
Sub-pixel localization (SPL) 
Fitting of Gaussian kernels to local intensity maxima
Top-hat filtering (THE) 
Top-hat filtering and entropy-based thresholding
Evaluating the performance of image segmentation algorithms has been a long-standing challenge. Validating segmentation results usually requires a ground-truth reference, and in biomedical applications the task of generating such reference falls to an expert biologist. This burdensome and error-prone strategy becomes even more challenging when evaluating small, but numerous subcellular organelles, particularly in the context of high-throughput experiments. In these cases, common limitations in the focus, contrast and resolution of the images render reliable pixel-level outlining of objects nearly impossible. Alternative evaluation methods include the use of computer-generated images for direct comparisons to ground truth results, experimentally derived control vs. test samples, and evaluations that measure performance as a function of an input stimulus that enable indirect comparisons between different conditions. Recently, benchmark image collections of cells and other types of biological samples have been developed to facilitate comparison and validation of image analysis methods [12–14].
In this study, we compare the performance of several algorithms for finding subcellular objects (i.e. small, bright spots) in fluorescence microscopy images. The algorithms employ various approaches for segmenting small structures, all aimed at detecting spot-like local intensity peaks, as opposed to the general separation of signal from background that is common in cell segmentation. We also propose an objective and comprehensive approach for evaluating algorithms for small particle detection. We use indirect comparisons with high-throughput well plate data, comparisons against manually scored objects in frames of 3D image stacks, and pixel-level comparisons against ground truth results in simulated images.
Importantly, our comparison study takes into account various situations, such as cases where a part of spots are severely blurred, emulating the typical situations of out-of-focus and diffraction limited appearance. Our comparison also considered cell heterogeneity (in this case images with varying number of spots), a factor commonly encountered in high throughput screening assays. In such case, the detection algorithms must be able to cope both with a range of conditions, such as cells ranging from low to high spot concentration in cells. Especially in high-throughput settings, tuning of parameters needs to be done for the whole screen, not for individual images.
Recently, a comparative study of nine commonly used spot detection methods has been published [15, 16]. Here, we expand the set of methods evaluated while also taking into account the results in [15, 16] by including the top-performing unsupervised method in our study. Further, our study covers a wide set of usage scenarios by applying three different image sets, providing a set of methods tested in various conditions, including methods that have not been used in the context of subcellular object detection before. The set of methods serves also as a resource for developers of novel particle detection algorithms, enabling more reasonable and informative comparison than histogram thresholding of intensity values.
Methods for detecting subcellular objects
A set of eleven algorithms covering a wide range of techniques for spot detection was selected for this study. Our selection includes eight previously published methods that were initially developed for applications other than subcellular spot detection. In addition, we formulate three filtering-based methods that, to the best of our knowledge, have not been previously applied to subcellular object detection. The detection of small subcellular particles from images can be divided into three phases : First, an optional preprocessing phase can be used to reduce noise and to attenuate objects of a desired shape or size. Due to limitations in imaging technology, an accurate representation of the biological sample can be degraded by several error sources, resulting in a noisy observation of the underlying object. To decrease the effect of these errors, an optional low-pass filtering phase for noise suppression can be applied, and here the linear low pass filtering has been applied depending on whether the method has been observed to suffer from false detections due to background noise and the choice has been made through testing separately for each image set and method. We leave, however, experimenting with various preprocessing methods out of the scope of this article. Next, signal enhancement may be used to make the desired objects more easily detectable than they were in the original image. Many of the methods studied here involve user-definable parameters for controlling this phase. We use grid-search for tuning such parameters (described below). Finally, the actual detection is obtained by thresholding the enhanced signal. Because we do not consider segmentation threshold as a parameter for the detection methods unless it has been defined as such in method description, the presented methods derive the detection result automatically based on heuristics rather than stepping through multiple threshold levels. As a result, our comparison shows the results as given by the methods after tuning their parameters in a grid-search manner, not after fixing the operation point by tuning the segmentation threshold. In this way, the methods can be compared based on their performance when operating in a fully automated manner.
The large number and wide variety of methods designed for intensity detection in different image analysis applications preclude an analysis of all possible methods described in the literature. We chose to exclude methods relying on statistical learning, such as in , to avoid the problem of selecting training data. We also left of methods relying on pure intensity thresholding, since they are are likely to perform poorly due to non-uniform background and staining in the cell bodies. However, our selection does cover a variety of different approaches, which are relatively comparable in terms of accuracy and processing time. The selected algorithms are listed in Table 1 with a brief note on their operation principle and the abbreviations of their names used throughout the manuscript. Below is a more detailed description of each algorithm.
In this method we formalize a detection method based on band-pass filtering (BPF). Here the image is band-pass filtered using a filter with transfer function H in a frequency domain that produces an image in which the objects of interest are emphasized. In addition to emphasizing the objects, the band-pass filter can be used to suppress the presence of noise, e.g. shot noise can be taken out by filtering the high-frequency components.
The filter H is designed such that the normalized cut-off frequencies are . Because the choice of cut-off frequencies is not a straightforward task from the spatial domain, it is advisable to consider the spectrum while choosing the desired band-passes. After filtering, Otsu's method  is used to automatically obtain a threshold value th for binarizing the band-pass filtered image. Thus, the four cut-off frequencies are the only user-defined variables.
Feature point detection
where f(x, y) is the original image, (x, y) and (i, j) are pixel coordinates in the image and kernel, respectively.
The initial point locations are then estimated by finding local intensity maxima. A point is considered to be a local maximum if it has the highest intensity within a local window, and the intensity value falls within the r highest percentile. The algorithm then proceeds by refining the point locations. Finally, all detected points are subjected to non-particle discrimination in the zeroth and second order intensity moment space, where a user-defined threshold T s controls the discrimination. A detailed description of the discrimination step can be found in . Thus, the percentile threshold, the discrimination threshold, and the window size parameter (related to the particle size) are the three free parameters for FPD in this study. We note that one feature of the applied FPD implementation is that it was used for giving the object locations as an output instead of a segmentation result. As a result, detection of an object can be evaluated but direct comparison of the segmentation result is not done here.
The morphological h-dome transform (HD)  has been applied to subcellular object detection in a tracking context . Smal et al. [15, 16] reported the best results among unsupervised object detectors were achieved with the h-dome transform based detector. The h-dome detector, according to , assumes that the image is formed by N o objects of interest, heterogeneous background structures and intensity distribution B(i, j), and a noise term η(i, j). The aim of the method is to estimate the number of objects N o and the object locations in image.
where H σ contains the small objects, the grayscale reconstruction B σ represents larger background structures, and intensities of height h are cut-off from the top. The h-dome transformed image H σ , where the bright objects should all have an intensity value of h, is used as a probability map for sampling and where pixel values of H σ are raised to the power of s. The map reveals areas that are likely to contain spots. After sampling, the samples are divided into clusters using the mean-shift algorithm. Using the mean value and variance of each cluster, the samples are divided into real objects and other structures, while the parameter σ M controls the maximum allowed size for an object of interest. Details about sampling and object discrimination can be found in . Overall the h-dome transformation based method has several parameters that need to be tuned based on the data in order to obtain useful results. As reported in [15, 16], the method is a very powerful detector when the parameters are tuned reasonably and when the data supports the assumptions made by the model.
Kernel density estimation
A segmentation algorithm based on the use of kernel density estimation (KDE) is presented in detail in , this method is also known as the Parzen window method. Briefly, the method estimates the probability density function over the image by combining local information. The estimation step results in a smoothed version of the original image where the effect of noise is suppressed.
where h is the smoothing parameter, (k, l) denotes pixel coordinate inside kernel, card is the cardinality of the set, and the kernel K(u) could be, e.g., uniform K(u) = [|u| ≤ 1]. Other implemented kernels are Gaussian, Epanechnikov, triangle, quartic, triweight and cosine . Finally, Otsu's method  is used to obtain a binarized version of the original image. In this method there are three parameters that can be set by the user: the radius R, the smoothing parameter h and the kernel. However, the choice of the kernel used is not crucial  to the result.
Local comparison and selection
where is the image filtered with the kernel at direction NE (and similarly for the other directions). The filtering directions are illustrated in Figure 1. Hence, the user-definable parameters are the radius R which relates to the object size, and the scaling factor α which can be used for tuning the segmentation threshold. By using the aforementioned binarization method one can take into account the possibility of non-uniform background, i.e., object presence is decided based on the local features.
Local spot enhancement filtering
where the filtering provides a so-called spot likelihood image that needs to be thresholded. The thresholding, performed by the product of the sensitivity threshold and the standard deviation of the spot likelihood image (th s × ) provides the final detection result. The division of the kernel area into inner and outer areas is not limited and it could be done based on assumed objects shape, enabling adjustments based on prior knowledge about the objects of interest. In this study, we keep the kernel fixed in order to avoid additional parameter tuning. In this case, the weighting parameter th s for thresholding is the only free parameter.
Morphometry based on granulometric analysis
The morphometry method for spot detection, abbreviated here as MGI, is adapted from  where automated morphometry was proposed for the quantification of synaptic boutons in neurons. The automated morphometry is based on granulometric analysis. The method first calculates granulometry by using morphology with varying disc sizes d, yielding a so-called granulometric index, or size density, G(d) [23–25]. The granulometric index is then used to select the scale of interest, which in our case involved automatically choosing the two highest peaks in G(d), denoted as d low and d high . Choosing the scale of interest is critical for the outcome, but for compatibility with high-throughput analysis, we chose to automate the scale selection. The scale of interest is used for constructing the corresponding opening images I low = I ◦E(d low ) and I high = I ◦E(d high ), where ◦ means grayscale opening and E is the disk-shape structuring element. Subtracting I high and I low gives the image where the structures of the desired scale should be present. Further, the structures of interest are extracted by masking with binary image obtained with k-means clustering. Finally, integral thresholding  gives the particle detection result within the area that was masked with k-means clustering. Notably, we used our version of the automated morphometry algorithm with default parameters, requiring no parameter tuning.
Multiscale product of wavelet coefficients
where J denotes the scales. To repress noise, the wavelet coefficients are thresholded prior to multiplication. Here, we use the hard thresholding scheme proposed in , where the threshold is given as 3 × σ i , and σ i is estimated to be MAD(W i )/0.67. The heuristics for choosing the actual objects from the multiscale product include thresholding according to a user-specified detection level. In this study, we use the number of scales J and the detection level l d as free parameters.
Unlike most filtering methods examined in this study, SourceExtractor (SE)  estimates the background in blocks and removes it before filtering with a Gaussian kernel. Background removal is also performed in blocks, the size of which is controlled here by a user-definable parameter. The background estimate is achieved by clipping the intensity histogram at both ends until the histogram converges at three standard deviations around the median. When the standard deviation is changed by less than 20% during the clipping process, the mean is taken to be the background intensity. Otherwise, the background is estimated to be BG = 2.5 × Median - 1.5 × Mean. Pixelwise, the background estimate is then obtained by interpolating the blockwise background estimates.
where BG is the estimate for the background, σ is standard deviation of the intensity, f is the input image, and bw gives the binary detection result, each defined here in pixel location (i, j). By setting thBG = 0, the version given in  is obtained. The detected objects, i.e. the areas in the intensity image under the connected components in the binary image bw, are then processed further in the deblending phase, where possible overlapping sources are separated. Briefly, the deblending proceeds by splitting the detected object into 30 slices inside the intensity range (from the detection threshold to the highest intensity peak) of the object. Starting with the highest intensity peaks, the algorithm takes each slice and determines whether two branches originating from different intensity peaks within the same object should be separated as different objects. The deblending algorithm considers the integrated pixel intensity of the branch relative to the total integrated intensity of the detected object as a basis for determining the separation, as explained in .
The original application area of Source Extractor is as far from subcellular object detection as possible; it was designed for analysis of galaxy-survey data . Though the method has been widely applied across many disciplines, to the best of our knowledge, its use in subcellular spot detection has not been reported. The applicability of Source Extractor in the analysis of subcellular structures underscores the generality of the problem of finding bright spots within images.
Sub-pixel location detection
The detection method in  was used for defining sub-pixel locations (SPL) of single molecules in low SNR (signal-to-noise ratio) images. The detection, though originally intended to be used in tracking, can be used as an independent module for identifying spots. The algorithm detects local intensity maxima by comparing to neighboring pixel intensities and the standard deviation of the local background. In , temporal averaging is used to reduce intensity variation prior to detection. However, we omitted the time averaging step since it is only applicable in the context of time-lapse imaging.
The method proceeds as follows. Within a window, the central pixel is chosen to be a potential spot if it is brighter than its surrounding pixels. The initial detection is further controlled by testing against the standard deviation of the local background. A user-defined parameter α, the only free parameter for SPL used in this study, controls the local maxima detection. This parameter defines the limit for type I errors in the initial local maxima detection. Sub-pixel locations are estimated for the local maxima that pass the criteria by fitting a 2D Gaussian kernel iteratively as described in [10, 28]. Like the feature point detection method, we use SPL only for estimating the locations of detected spots, therefore it can be used to count the number of spots and for object-level comparisons, but not for pixel-level evaluation.
Top-hat filtering by grayscale morphological opening
The grayscale morphological top-hat filtering [25, 29] acts as a local background removal function, simultaneously enhancing round, spot-like structures. Here we combine top-hat filtering and automated thresholding to form a spot detection method, abbreviated as THE. Essentially, the filtering phase performs grayscale opening with a flat disk-shaped structuring element E of radius r and subtracts it from the original image f. More formally, the top-hat filtering result is given as fdiff = f - f ◦ E(r), where ◦ denotes grayscale opening. In the filtering result, the objects roughly of size determined by r should be enhanced, and background removed.
The resulting image fdiff needs to be thresholded in order to obtain a binary mask for spots. We tested several histogram-based segmentation methods [30, 31], and applied an entropy-based thresholding  which produced slightly more conservative values for images with spots than many other thresholding methods. Thus, instead of parameterizing the detection threshold or applying any post-segmentation constraints, we use top-hat filtering in a more automated manner, which requires considerably less parameter tuning.
The most natural way of comparing segmentation algorithms is by a pixelwise comparison. However, constructing a reference segmentation in which all of the pixels belong to biologically meaningful small spots would be difficult. Creating a reliable and representative reference result is difficult because, on the one hand, it is extremely tedious to manually analyze a large number of spots in a reliable manner, and on the other hand, analyzing a relatively small number of spots is statistically inadequate. Thus, to enable pixelwise comparisons against a reference result, we used simulated experiments published previously as a benchmark set in .
The simulated image set, generated by using the SIMCEP cell image simulation framework [33, 34], consists of 20 images with nuclei, cytoplasmic areas, and subcellular objects each having their own channel in the RGB image. Noise, i.e. intensity variations in cell texture, and blurring for out-of-focus objects are also introduced in the simulation process  in order to give the simulated images some level of error akin to that encountered in experimentally derived images. Prior to the analysis, the images are converted to grayscale using the standard conversion of 0.2989 × R + 0.5870 × G + 0.1140 × B. After this conversion, subcellular objects in the grayscale images have slightly higher intensities than their surroundings.
Frames from image stacks of yeast cells
The second data set contains frames from image stacks obtained with wide-field imaging. The objects are P-bodies, visualized by Edc3 protein fused to green fluorescent protein (using a strain created by Huh, et al., ). Stacks of 28 frames along the z-axis (every 0.3 μ m) were acquired using a Leica DMGI 6000B microscope equipped with motorized X-Y stage, a high quantum efficiency cooled back-illuminated Qimaging Rolera-MGi CCD camera, and integrated software control (BD Bioscience Bioimaging IPLab). The images were acquired under oil using a 63× objective/1.40 NA Plan APO oil lens.
Stacks usually consist of a set of frames starting with images in which the objects of interest are not yet in focus. As the microscope scans through the sample in the Z plane, objects come in focus, appear in a set of frames, and then vanish as the scanning proceeds past the object's focus area. The implication for the analysis task is that the spot detection methods must be able to detect objects only in the in-focus frames. We selected seven stacks of images and from each stack chose four frames such that one frame is empty (only out-of-focus objects are in the image and no P-bodies are marked in the reference result) and three frames with varying number of P-bodies that are present and in focus. In total, 28 frames are used in this study.
For the selected frames a reference result was manually determined by two observers. In order to limit the number of comparisons we chose to combine the results from two observers such that we included all spots in our reference. Due to the small spot size and the noisy appearance of the wide-field microscope image, the objects are marked with a fixed-size spot but the area is not outlined in detail. As a consequence, the manual reference result can be used for object level comparison, i.e. to assess whether an object is found or not, but not as a pixel-level ground truth result.
Well plate experiments of a human osteosarcoma cell line
A major application of bright spot detection of subcellular organelles is in high-throughput screening, where for example the effects of gene knock-outs or differences in responses to varying dose levels of a particular stimulus are of interest. To test the ability of the various methods to detect differences in populations of cells stimulated with different doses of a drug, we used the SBS CompuCyte Transfluor image set provided by Dr. Ilya Ravkin and available from the Broad Bioimage Benchmark Collection . The images are of a human osteosarcoma cell line. The image set consists of a portion of a 96-well plate containing 3 replica rows and 12 different concentrations of isoproterenol. Importantly, stimulation with different doses of isoproterenol affects the appearance of small vesicle-like spots. There are four acquired fields per well, resulting in 144 total images. The image set also contains specific staining for nuclei, which we used to determine the number of cells per image. Thus, the outcome of the analysis is an assessment of the average number of vesicles per cell in each image, with the images grouped by dose level. These results can be used for indirectly comparing different methods, since no ground truth information for the vesicles is available.
Performance evaluation metrics
Several metrics for performance evaluation exist when reference result, for example object number and locations are known [36, 37]. For measuring the accuracy of detection algorithms, we chose the following commonly applied metrics.
By intuition, detecting objects where no true objects exist is penalized in p, whereas failure to detect true objects is penalized in r.
The F-score combines precision and recall as a single measure of segmentation accuracy, making it a useful parameter for evaluation purposes.
Allowing the user to tune many parameters leads to a highly adaptable method, but also requires considerable effort to ensure reasonable (or ideally optimal) performance. Thus, the calculation times for the optimization procedures vary greatly between methods. While a detailed discussion of the effect of each parameter for the 11 methods is beyond the scope of this article, we offer a list of parameters for each method along with the applied ranges in the supplementary materials. Lastly, we note that by tuning different parameters than the ones in this study, and by adding more parameters to the methods, the methods may be further customized for analysis tasks.
Results for simulated images with pixel-level reference
First, we consider the validation of algorithm performance with simulated images in which the noise-level and other image characteristics are known. In this case, we calculated the number of objects detected in the 20 images by each method and determined whether the differences between object counts were significant, using the non-parametric Kruskal-Wallis test of whether the medians of multiple groups are equal. Our results suggest that detection results do infact differ significantly (p ~ 0 while p < 0.01 was considered statistically significant). Wilcoxon rank sum tests between result pairs further support this claim by showing that most of the results do not have the same median.
Results for yeast images with object level reference
Results for yeast image frames
Results for osteosarcoma well plate images
The dose responses in Figure 7 form a step-like pattern, with very few vesicles per cell in low-dose populations (dose levels I to VI), increasing vesicle numbers beginning with dose level VII and peak vesicle numbers at dose level XI. Increasing the dosage beyond that of level XI (i.e. level XII) does not appear to increase the average number of vesicle structures per cell. This behavior is consistent with saturation as the dose concentration increases.
Although there are differences in the absolute number of vesicles per cell in low dose images and the magnitude of the difference between the low and high dose images, all methods (except MGI and THE) produce this step-like dose response curve. For example, the step given by FPD, LC, and KDE is substantially lower than those by BPF, SE, and SPL. The result given by MGI and THE resemble the others for the high dose values where the images contain a large number of vesicles. When vesicles are few in number or not present at all, the methods give false detections. The clear differences in the dose responses obtained with different algorithms suggests that any downstream analysis, such as clustering or classification of populations based on the vesicle counts could produce significantly different results.
Comparison of relative similarities
Finally, we calculated the pairwise correlation coefficients between the object counts obtained for all images. The pairwise correlation values between methods are shown in Figure 9. These correlation results further support the clustering results, namely that results given by MGI and THE differ significantly from the others (low correlation with other results) whereas SE, SPL and MW performed similarly (correlation > 0.99). The object counts for all image sets that were used for constructing the dendrogram and calculating the correlations are available at the supplementary site.
We have studied the performance of eleven subcellular object detection algorithms under different analysis scenarios. Our study included real images of high-throughput well plate experiments for indirect comparison of the algorithms, as well as frames from image stacks of yeast P-bodies for which the object-level reference information was available. In addition, we used simulated images with small subcellular objects, thereby enabling a pixel-level comparison of algorithms against a computer-generated ground truth.
Results for the simulated images gave detailed insight into the performance of the methods. In the simulated image set all the images had the same number of subcellular objects. The object counts obtained for the image set revealed that statistically significant differences exist between the algorithms. The small spots proved to be rather difficult to detect, highest object level accuracy (in terms of F-score) being 0.8249 given by HD. Worth noting is that also MGI (0.7698), THE (0.7244), and FPD (0.6905) all perform well for the set where all images had spots, all of which had problems with the empty images. Simulation allowed also pixel-level comparison, where MW gave the most accurate segmentation by a slight difference when measured by F-score, but none of the methods provided outstanding accuracy. The pixel-level results confirm how challenging it is to accurately segment small particles in noisy and partially blurred images with heavy background fluorescence. Moreover, the limitations in segmentation performance on pixel-level raise a question about the reliability of shape, size or morphology features extracted from subcellular objects in standard fluorescence microscopy measurements.
Second, the high level of F-score values for the detection of GFP labeled P-bodies in wide-field microscope images proved that all methods can be used for accurate detection of bright spots when background intensity is on a moderate level. The highest F-scores between manually located reference result and automated analysis result were given by BPF (0.9459), LC (0.9450), and SE (0.9354). Furthermore, FPD, MGI, and THE had difficulties in the handling of empty frames of wide-field microscope images, which shows as a high number of false positives leading to low precision values. Excluding the empty frames, all these three algorithms were accurate for the frames with in-focus P-bodies, which is confirmed by the high recall values.
Third, results for the human osteosarcoma well plate measurement data further confirmed how some of the algorithms failed to cope with a large data set where images contain varying amount of small spots. Examples of poor handling of varying conditions were THE and MGI algorithms. Our implementation of MGI detects automatically the scale of interest, and in case of no or very few vesicles it fits to the scale of cells. The implementation of THE included automated thresholding, which in this case assumed the data to include two groups: objects and background. Thus, neither of these two algorithms was able to handle all images with same parameter settings when used in the way described here. However, including free parameters for tuning the segmentation or preprocessing steps could lead to better results. Also FPD and HD produced less obvious ramp as a dose response. FPD assumes certain level of spots to be present in all images (percentile-based detection), which explains why varying probability for spots within experiment may cause problems in detection. HD method, despite its heavy parametrization, seems to make a compromise where very few false objects are detected, but also part of true objects are missed. Apart from MGI and THE, all of the compared algorithms produced a step-like dose response, suggesting that the methods can be used for detecting differences between populations exposed under varying levels of stimulus. The results given by the 11 algorithms confirm that they all are very useful in spot detection tasks, but the results also show clear differences in terms of their ability to detect small, vesicle-like objects and to adjust to varying conditions. The handling of images containing very few, if any, small spots, in particular, brought out significant differences between the algorithms. Since handling such images can be fundamental for some applications, the algorithms should be chosen with care.
Finally, some remarks on the performance of the three detection algorithms originally developed for tracking purposes, i.e. FPD, HD, and SPL. Though developed for similar purposes, the methods have different approaches for detection. By definition, FPD tends to detect roughly the same number of objects for a set of images when used with fixed parameter settings. From a tracking point of view, this is a reasonable assumption if the number of particles is expected to be rather constant throughout the imaging sequence. The results for simulated image set support this conclusion, since the the number of particles stays constant in this set. On the other hand, when the number of particles present in the images changes dramatically over the course of the imaging period, the HD and SPL approaches are likely to give more accurate performance. This assertion is supported by our results. SPL adjusts well to varying conditions in well plate and wide-field images, and HD performs reasonably well in varying conditions, avoiding excessive false positive detections for empty yeast images (high precision value), though doing so at the cost of missing some spots (low recall value). We note that for the yeast stack images, even tuning the five free parameters of HD did not provide results as accurate as those with the single open parameter of SPL. For the simulated images, on the other hand, HD gave the most accurate results among all 11 algorithms, outperforming both FPD and SPL. Although detection accuracy does not directly predict subsequent tracking performance, choosing a method based on careful testing may be beneficial.
Thus, although detection algorithms are problem-specific, the systematic comparison of methods with a large set of test images can help choose the best method for the particular imaging challenge. Using a systematic approach, algorithms can be compared under varying conditions, providing useful information for various use cases. Our study also makes use of recently published benchmark datasets in order to evaluate algorithms. Importantly, evaluation based on a wide range of images tests the algorithms with an objective framework in which performance has not been tuned for a small set of images with specific characteristics. For example, subcellular object detection in modern high-throughput imaging experiments provides a challenge for image analysis because contrast, intensity, and number of spots may vary significantly within the same experiment. Systematic testing of algorithm performance with large image sets, as was done in this study, allows one to predict algorithm performance in such tasks. Supplementary material, including additional result figures and an algorithm toolbox as a CellProfiler  compatible module written in MATLAB (The MathWorks, Natick, MA) are available for download at http://www.cs.tut.fi/sgn/csb/subcell.
This work was supported by the Academy of Finland, (application number 129657, Finnish Programme for Centres of Excellence in Research 2006-2011) and by the National Technology Agency of Finland. PR was supported by Tampere Graduate School in Information Science and Engineering (TISE) and Nokia Foundation. CGT was supported by a grant from the NIH/NIGMS (P50GMO76547). AMD was supported by an NIH/NHGRI Genome Scholar/Faculty Transition Award (K22 HG002908). The authors would like to thank Dr. Prisca Liberali for her help. This work benefited from the Tampere Center for Scientific Computing (TCSC) and Techila Technologies's grid computing solution.
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