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 Table of Contents     
ORIGINAL ARTICLE
Year : 2022  |  Volume : 37  |  Issue : 3  |  Page : 209-216  

Contrast enhancement of scintigraphic image using fuzzy intensification


1 Department of Nuclear Medicine, All India Institute of Medical Sciences, New Delhi, India
2 Department of Computer Science, SGTB Khalsa College, University of Delhi, New Delhi, India

Date of Submission31-Dec-2021
Date of Decision04-Mar-2022
Date of Acceptance16-Mar-2022
Date of Web Publication02-Nov-2022

Correspondence Address:
Dr. Anil Kumar Pandey
Department of Nuclear Medicine, All India Institute of Medical Sciences, Ansari Nagar, New Delhi - 110 029
India
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Source of Support: None, Conflict of Interest: None


DOI: 10.4103/ijnm.ijnm_210_21

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   Abstract 


Introduction: The objective of this study was to see the effect of fuzzy intensification (INT) operator on enhancement of scintigraphic image. Materials and Methods: Nuclear medicine physician (NMP) provided 25 scintigraphic images that required enhancement. The image pixels value was converted into fuzzy plane and was subjected to contrast INT operator with parameters of INT operator i.e., cross-over = 0.5 and number of iterations = 1 and 2. The enhanced image was again brought back into spatial domain (de-fuzzification) whose intensity value was in the range 0–255. NMP compared the enhanced image with its input image and labeled it as acceptable or unacceptable. The quality of enhanced image was also accessed objectively using four different image metrics namely: Entropy, edge content, absolute mean brightness error and saturation metrics. Results: Most of the enhanced images (18 out of 25 images) obtained at cross-over = 0.5 and number of iterations = 1 are acceptable and found to have overall better contrast compared to the corresponding input image. Four images (two brain positron emission tomography scan and two I-131 scan) obtained at cross-over = 0.5 and with iteration = 2 are acceptable. Three input images (one dimercaptosuccinic acid (DMSA), one I-131 and one I-131- metaiodo-benzyl-guanidine (MIBG) scan) were better than their enhanced images. Conclusions: The enhancement produced by fuzzy INT operator was encouraging. Majority of enhanced images were acceptable at cross-over = 0.5 and number iterations = 1.

Keywords: Contrast enhancement, fuzzy intensification operator, scintigraphic image


How to cite this article:
Pandey AK, Dogra S, Sharma PD, Jaleel J, Patel C, Kumar R. Contrast enhancement of scintigraphic image using fuzzy intensification. Indian J Nucl Med 2022;37:209-16

How to cite this URL:
Pandey AK, Dogra S, Sharma PD, Jaleel J, Patel C, Kumar R. Contrast enhancement of scintigraphic image using fuzzy intensification. Indian J Nucl Med [serial online] 2022 [cited 2022 Nov 27];37:209-16. Available from: https://www.ijnm.in/text.asp?2022/37/3/209/360276




   Introduction Top


We aspire to see the true distribution of radioactivity inside the body in a scan. To be able to achieve this, the image must be sharp such that activity in each compartment (tissue or organ) can be easily perceived distinctly and each compartment should look as an independent entity in the image. However, such an ideal image is far from the real ones which we observe in routine nuclear medicine practice. Various types of images are observed: Images that have very high global contrast (difference in maximum and minimum count is very high but there is lack of local contrast so that the details in entire image canvas are not visible), blurry images having boundaries of one uptake region merged with another structure in the image so that tracing the accurate boundary of an object is difficult, images with uptake differences in target object and the background (structures other than the target object in the image) is too small to be viewed clearly and label the target object representing a disease confidently, images with target object blurred and embedded in the noisy background making the detectability of small lesions ambiguous and also lowering the confidence in making decision regarding the presence of a disease, and so on. Such images require some kind of mathematical manipulation of pixel values so that the relevant details get prominence in the image and irrelevant details are suppressed.

Several image processing techniques are used to enhance images starting from simple window-level contrast enhancement tool to state of the art algorithms which sharpen the image and also remove noise while preserving edges.[1],[2],[3] In particular, several image processing techniques have been explored for enhancing the quality of scintigraphic images[4],[5],[6],[7],[8] Fuzzy intensification (INT) operator has been used for image enhancement in fields other than nuclear medicine but has yet not been used by nuclear medicine community for contrast enhancement of images.[9],[10],[11]

In this pilot study, we have applied the fuzzy INT operator on a set of 25 nuclear medicine images to improve their quality. The quality of the enhanced images was evaluated by nuclear medicine physician (NMP) for acceptability. Here, we report the results of this investigation.


   Materials and Methods Top


The contrast INT operator on a fuzzy set A generates another fuzzy set A' = INT (A) in which the fuzzification is reduced by increasing the values of μA (xmn) which are above 0.5 and decreasing those which are below it. We define this INT operator[11] by a transformation T1 of the membership function μmn as



In general, each μmn modified to μ'mn to enhance the image X in the property domain by a transformation function Tr where



The transformation function Tr is defined as successive applications of T1by the recursive relationship



And T1(Pmn)represents the operator INT defined in eq. (1)

As r increases, the enhancement function in μmn - μ'mn plane tends to be stepper because of the successive application of INT. In the limiting case, as r → ∞, Tr produces a two level (binary) image. It is to be noted here that, corresponding to a particular operation of T, one can use any of the multiple operation of T” and vice-versa to attain a desired amount of enhancement. Similarly, some other enhancement functions can be used independently instead of these used in equation (1).

The membership plane μmn for enhancing contrast around a cross over point may be obtained from



Where the position of crossover points bandwidth and hence the symmetry of the curve are determined by the fuzzifiers Fe and Fd. when xˆ = xmn (maximum level in X), μmn represents an S-type function. When xˆ = any arbitrary level l, μmn represent a π-type function.

After enhancement in fuzzy property domain, x'mn the enhanced spatial domain may be obtained from



Where α is the μmn value of when xmn=0

The essence of above mathematical description of fuzzy INT operator and how this operator is helpful in improving the contrast of a given image can be explained graphically. [Figure 1] illustrates the nature of INT operator. The illustration is based on the assumption that input image has pixel counts ranging from 0 to 255 (which is shown as input image pixel counts on X-axis), and after application fuzzy INT operator the pixel counts ranges from 0 to 1 as output image pixel counts on Y-axis. For a cut-off value = 0.5, using equation (1) three different curves have been generated at number of iterations 1, 2, and 4.
Figure 1: Illustrating nature of fuzzy intensification operator

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The transition of pixel counts above and below the cut-off value = 0.5, (corresponds to 128 input image pixel counts) is symmetrical, the bright pixels (greater pixel counts) become brighter and dark pixels (smaller pixel counts) become darker. Thus, the nature of the operator to make bright pixel brighter and dark pixel darker creates the contrast in the image.

It is to be noted that with the increase in the number of iterations, slope of the curve becomes steeper (meaning that operator is going to create relatively increased contrast with increase in number of iterations, a time will come when the contrast will become maximum (i.e., the image will become a binary image having only two values: 0 and 1.). On visual inspection, it can be confirmed that the curve corresponding to number of iterations = 1 have lowest slope and curve corresponding to number of iterations = 4 has highest slope. Thus, the enhanced image obtained with number of iterations = 4 will have maximum contrast and the enhanced image obtained with number of iterations = 1 will have minimum contrast.

In this pilot study, the motivation for selecting the cutoff value as 0.5 is based on the article published by Pal and King,[11] in which they have demonstrated very good performance of fuzzy INT operator at this cutoff value.

Images in data set

The pilot study included 25 scintigraphic images two F-18 fluorodeoxyglucose (F-18-FDG) brain scan images, nine F-18-FDG liver scan images, three Tc-99 m dimercaptosuccinic acid (Tc-99 m DMSA) renal scan images, three Tc-99 m methylene diphosphonate (Tc-99 m MDP) bone scan images, one Tc-99 m pertechnetate thyroid scan images, one Tc-99 m sestamibi parathyroid scan images, and six I-131 metaiodobenzylguanidine (I-131 mIBG) scan images, [Figure 2] acquired between April 2021 and July 2021 during of routine investigation at our facility. The acquisition protocols used for these images are as follows:
Figure 2: All 25 images include in the study

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F-18-FDG positron emission tomography (PET) scan images (two brain and nine liver scan images) were acquired on integrated PET-computed tomography (CT) system (Biograph mCT, Siemens Medical Solutions, Erlangen, Germany). Patients had glucose level ≤7.7 mmol/l and had fasted for at 4 h underwent PET/CT scan 45–60 min after intravenous injection of 370 MBq of F-18-FDG.

Images acquired with covering the patient from skull apex to midthigh in the liver and in case of brain from apex of the skull to the base of the skull. PET bed size matched the CT FOV. PET acquisition was performed just after CT on covering the same field of view. The acquisition time per bed position for the liver and brain study was 2 min and 15 min, respectively.

The acquired images in 128 × 128 matrix were reconstructed using the order subset expectation maximization algorithm with 2 iterations and 8 subsets, and full width half maximum of 5 mm. CT-based attenuation correction of the PET images was applied. The attenuation corrected PET images have been included in the study.

Planar gamma camera images (three Tc-99 m-DMSA renal scan images, three Tc-99 m-MDP-bone scan images, one Tc-99 m-pertechnetate thyroid scan images, one Tc-99 m-MIBI-parathyroid scam image, six I-131-mIBG scans images): Tc-99 m-DMSA-renal scan was performed after 4–6 h of administration of radiopharmaceuticals on Siemens Symbia E Dual Head Gamma camera (Siemens Medical Solutions, Illinois, USA) equipped with low energy high resolution (LEHR) collimator Posterior, Right Posterior oblique and Left Posterior oblique views were acquired with a zoom 1.45 for 250 KiloCounts in 256 × 256 matrix. Whole body Tc-99 m-MDP bone scan image was performed on Symbia T6 single-photon emission computed tomography/CT (SPECT/CT) scanner (Siemens Medical Solutions, Illinois, USA) equipped with LEHR collimator. The scan speed was 20 cm/min and images were acquired in 1024 × 256 matrix. I-131-mIBG scan was performed on high energy collimator with the speed of 10 cm/min in continuous mode with 1024 × 256 matrix size on GE Discovery 670 NM/CT (General Electrical Healthcare, Illinois, USA).

Tc-99 m-MIBI parathyroid scan images were acquired using the following acquisition protocol: 15–20 mci-MIBI was administered intravenously to the patient, and planar images were acquired at 15 min, 50 min and 2-hr after the radiopharmaceutical administration on Siemens Symbia T6 Dual Head Gamma camera and SPECT/CT (Siemens Medical Solutions, Illinois, USA) equipped with LEHR collimator at zoom 2.0 and 700 Kilo counts. The images included in this study were the images acquired at 2-h.

The image enhancement using fuzzy INT operator involved the following steps: (1) read the image, (2) fuzzify the image data (all pixel values after fuzzification should be in the range 0–1), (3) modify the pixel values for contrast INT: If the pixel value is ≤0.5, then enhanced pixel value = 2 × (pixel value)^2 else enhanced pixel value = 1–2 × (1-pixel value)^2. Iterate this step for required number of iterations, (4) defuzzify (bring all the pixel values between 0 and 255), and (5) save the enhanced image.

Subjective assessment of image quality

Images were placed on PowerPoint slides. On each slide, there were three images: Input image, enhanced image at iteration 1 and enhanced image at iteration 2 [A representative slide is shown in [Figure 3]]. Enhanced images were categorized into two groups: Acceptable or unacceptable.
Figure 3: (a), Input image. (b), input image a after iteration 1. (c), input image a after iteration 2. (d), input image. (e), input image d after iteration 1. (f), input image d after iteration 2. Image (b) shows enhanced contrast, no loss of boundaries and details. Image (c) shows enhanced contrast but the boundaries missing and some details also missing. In image (e) no over enhancement of contrast and no missing details. In image (f), over enhanced contrast and details are also missing

Click here to view


The enhanced image [Figure 3]c and [Figure 3]f having any of the characteristics: (Outline/contour of the object, loss of object/structure, over enhancement), were categorized as unacceptable.

Objective assessment of image quality

Second order entropy (Entropy),[12] edge-based contrast metric (EBCM),[13] absolute mean brightness error (AMBE),[14] and saturation evaluation metrics (SEM)[15] were used for objective assessment of the contrast in the image. A good quality image has (i) low AMBE, (ii) low SEM, (iii) well preserved edges (i.e., change in EBCM should be zero), and (iv) decrease in entropy as a result of image enhancement algorithm. The formulas used for calculation of entropy, EBCM, AMBE, and SEM are given in [Table 1].
Table 1: The formulas used for calculating entropy, edge-based contrast metric, absolute mean brightness error, saturation evaluation metrics

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Statistical analysis

Test of normality (Shapiro–Wilk's test) was applied on the image quality metrics data. Those data sets which passed the test of normality were subjected for paired t-test. Paired t-test was conducted to determine whether the means of the two groups (image quality metrics [AMBE, EBCM, SEM, and Entropy] at iteration = 1 and iteration = 2) are equal to each other. The null hypothesis was that the two means are equal at. Those datasets that failed to pass the test of normality were subjected to Wilcoxon signed-rank test with continuity correction. We used open-source software R for statistical analysis (R Core team, R foundation for stastical computing, Vienna, Austria).[16]


   Results Top


The overall contrast in the enhanced image (obtained after 1st iteration) was found to be better than its corresponding input image. [Figure 3] shows a sample case of input and enhanced images (2a and 2d are input and 2b and 2e are their respective enhanced images). The global contrast was found to be better in enhanced image as compared to the corresponding input image. Further, at number of iterations = 2, the global contrast was better than that of the enhanced image obtained at iteration = 1. The radiopharmaceutical uptake became more prominent in enhanced images obtained either at iteration = 1 or iteration = 2, and signal to noise ratio is much better in the enhanced image at iteration = 2. However, at iteration = 2, loss of information was also observed because of saturation of pixels [Figure 3]c and [Figure 3]f.

Eighteen out of 25 images obtained with number of iterations = 1 were found to be acceptable to NMP [[Figure 4]a, [Figure 4]b, [Figure 4]c, [Figure 4]d, [Figure 4]e, [Figure 4]f, [Figure 4]g, [Figure 4]h, [Figure 4]i, Input images: [Figure 4]a, [Figure 4]d and [Figure 4]g, corresponding enhanced image at iteration = 1: [Figure 4]b, [Figure 4]e and [Figure 4]h].
Figure 4: (a) Input image. (b) input image a after iteration 1. (c) input image a after iteration 2. (d) input image. (e) input image d after iteration 1, (f) input image d after iteration 2. (g) input image, (h) input image g after iteration 1 (i) input image g after iteration 2

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Four images (two I-131-mIBG images and two F-18-FDG brain PET scan) obtained at iteration = 2 were found to be acceptable. One each representative image of I-131 and F-18-FDG PET scan obtained at iteration = 2 that were acceptable are shown in [Figure 5] (brain PET scan: [Figure 5]a (input image), [Figure 5]c (output images), I-131-mIBG scan: [Figure 5]d (input image), [Figure 5]f [output images]). [Figure 5]b and [Figure 5]e are the enhanced image at iteration = 1 is shown here to visually compare the enhanced images at iteration = 1 and iteration = 2.
Figure 5: (a) Input image. (b) input image a after iteration 1. (c) input image a after iteration 2.(d) input image. (e) input image d after iteration 1. (f) input image d after iteration 2

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In three images out of 25, input images were found to have better image quality compared to its enhanced images [[Figure 6]a, [Figure 6]d and [Figure 6]g are the input images].
Figure 6: (a) Input image. (b) input image a after iteration 1. (c) input image a after iteration 2. (d) input image. (e) input image d after iteration 1, (f) input image d after iteration 2. (g) input image, (h) input image g after iteration 1 (i) input image g after iteration 2

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In case of F-18-FDG brain scan images; enhanced image [Figure 5]c, has much better signal (i.e., lesion uptake) to noise (i.e., other structures) ratio compared to its input image [Figure 5]a. In case of liver scan image; overall enhancement (both local and global contrast) was noticed, and can be verified by inspecting images [Figure 3]b and [Figure 3]c, there is much better contrast in the inner structures [Figure 3]c compared to its input image [Figure 3]a.

In case of F-18-FDG liver scan images, the metabolic uptake is clearly visualized at both iteration 1 and 2, however, at iteration 2 the contrast is so enhanced that the enhanced image had missing boundaries and missing details which may be important while making diagnosis [[Figure 3]a: Input image, b: Enhanced image at iteration = 1 and c: Enhanced at iteration = 2].

Tc-99 m-MDP bone scan image and Tc-99 m-MIBI-parathyroid scan images show better uptake at iteration = 1 [Figure 4]a and [Figure 4]d and at iteration = 2 the uptake is much more clearly visible but the body outline is missing [Figure 4]c and [Figure 4]f. Similar types of results were also observed in case of Tc-99 m-DMSA images [Figure 4]g, [Figure 4]h, [Figure 4]i.

The mean AMBE value (13.97) of the enhanced images at iteration = 1 were smaller than that of mean AMBE value (20.53) of enhanced images at iteration = 2. The result of paired t-test indicates that there was statistically significant difference between the means of two groups (t = −4.55, df = 24, P < 0.0001, (95% confidence interval [CI]: −9.53–3.58), mean of the differences = −6.56).

The median EBCM value (28.632) of the enhanced images at iteration = 1 was smaller than that of median EBCM value (28.632) of the enhanced images at iteration = 2. The result of Wilcoxon signed rank test with continuity correction indicates that there was insignificant difference between the median of two groups the P value which is significantly less then (V = 27, df = 24, P = 0.234).

The mean Entropy value (7.44) of the enhanced images at iteration = 1 was greater than that of mean Entropy value (5.49) of enhanced images at iteration = 2. The result of paired t-test indicates that there was statistically significant difference between the means of two groups (t = 11.38, df = 24, P = 3.72e-11, 95% CI: 1.59, 2.29 mean of the differences = 1.94).

The median SEM value (0.57) of the enhanced images at iteration = 1 was greater than that of median SEM value (0.52) of enhanced images at iteration = 2. The result of Wilcoxon signed rank test with continuity correction indicates that there was statistically significant difference between the median of two groups (V = 76, P = 0.004). The results of objective evaluation of the image quality agree with the result of visual assessment. The value of image quality metrics of all images in the data set is given in [Table 2].
Table 2: Result of objective assessment of image quality for both the iterations (iteration-1, iteration-2) on the basis of absolute mean brightness error, edge-based contrast metric, entropy, saturation evaluation metrics

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   Discussion Top


In this plot study, we evaluated fuzzy INT operator for contrast enhancement of scintigraphic images. The experiment was conducted on a set of 25 scintigraphic images and on visual assessment we found that application of fuzzy INT operator (at number of iterations = 1) resulted in sharp image, with 18 out of 25 images generating acceptable or better image than that of the corresponding input images. Four images obtained at number of iterations = 2 was improved, while three input images were having much better contrast than their corresponding processed images The randomization of display of images or blinding the expert reading these images will influence the result. However, this has not been included in this pilot study, keeping in view the scarcity of time available from NMPs.

Due to the inclusion of penetration and scatter photons in the photo-peak energy window, in order to increase the number of counts per pixel in the limited duration of imaging, the observed images had low contrast and had appreciable noise. At times in the midst of the appreciable noise, the small important clinical details fall in a zone where the clinical confidence is low to about the presence of a disease [Figure 5]a. In such cases, we expected that the fuzzy INT operator could be useful for diagnosis [[Figure 5]c shows improvement in F-18-FDG brain scan image].

There were three input images in which fuzzy INT operator did not perform well as NMP preferred input images compared to its enhanced images [Figure 6]. The explanation for this might be the characteristic of input image itself. Visually we can observe that the information density (counts per square cm) in these input images is very low. If comparatively large number of pixels have very small value (nearly zero), then total counts/total number of pixels in the image or in a given area of the image is low. As the image (each pixel value in the range (0–255) in spatial domain is transformed into the fuzzy plane the pixel counts are in the range (0–1) with the cross-over point at 0.5. The application of fuzzy INT operator improves the contrast by widening the gap between the minimum and maximum value by increasing the pixel value (squaring the pixel value) above the cross-over point and decreasing the pixel value (by squaring the pixel value) below the cross-over point.

This study is unique in the sense that all experiments related to the study has been performed on personal computer, with the image dataset used in the study transferred from the costly nuclear medicine processing work stations provided by the vendor. This study will inspire the young researchers to carry out the research on their personal computers, using free open-source software (such as R, or Scilab), or economy versions of proprietary software (such as MATLAB), which are rather affordable.

In this study we, investigated the fuzzy INT operator proposed by Pal and King[11] cross over value 0.5 at two iterations. At iteration number = 1, the images have adequate contrast enhancement, and iteration number = 2 there was contrast enhancement as well as some loss of details. The contrast of images was found to be enhanced by both visual (by NM physician) and objective assessment (Entropy,[12] EBCM,[13] AMBE,[14] and SEM[15]). We applied statistical analysis on objective measures of enhancement (Shapiro–Wilk's test for normality). Data set which passed the test of normality were subjected to paired t-test to determine whether the means of two groups are equal to each other. Datasets which failed to pass the test of normality were subjected to Wilcoxon signed rank test.

On fuzzy image enhancement various studies have been performed.[17],[18],[19],[20],[21],[22] Yet, there are very few studies done on use of fuzzy logic in nuclear medicine.[10] Pandey et al. have explored the utility of two fuzzy filters (triangular fuzzy filter with the moving average (TMAV) and asymmetrical triangular fuzzy filter with the moving average (ATMAV) for reducing noise from Tc-99 m sestamibi parathyroid images.[10] They investigated the effect of window size small window width (n = 3) for small level of noise, and large window (n = 5) for width for the large level of noise. There are other works on fuzzy logic in contrast enhancement that have shown have good results.[22]


   Conclusions Top


The enhancement produced by fuzzy INT operator was encouraging. Majority of enhanced images were acceptable at cross-over = 0.5 and number iterations = 1.

Financial support and sponsorship

Nil.

Conflicts of interest

There are no conflicts of interest.



 
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    Figures

  [Figure 1], [Figure 2], [Figure 3], [Figure 4], [Figure 5], [Figure 6]
 
 
    Tables

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