Introduction
By the age of 10, up to 46 in 100,000 children are diagnosed with epilepsy [
1,
2]. Approximately one-third of these children do not respond to appropriately chosen and well-tolerated anti-seizure medications and are hence classified as having drug-resistant epilepsy (DRE) [
3]. A significant predictor of DRE is the presence of a structural lesion, which refers to any brain abnormality known to increase the risk of epilepsy [
4]. Epilepsy surgery is a safe and effective procedure in children whose focal onset DRE arises from a non-eloquent brain region [
5,
6]. The mainstays of presurgical evaluation include video-electroencephalography (EEG), magnetic resonance (MR) imaging, and neuropsychological testing [
7]. Children with a solitary, discrete lesion have higher chances of achieving postsurgical seizure freedom, provided that the lesion is completely removed [
5,
8]. However, over the last two decades, surgical indications have expanded to include more complex cases of extensive or even bilateral lesions and MR-negative cases [
5,
9], often necessitating auxiliary tests [
7].
Nuclear medicine techniques, specifically interictal positron emission tomography (PET) and ictal single-photon emission tomography (SPECT), are crucial in complex cases, confirming the lateralization or lobar localization of the presumed epileptogenic zone (EZ), which can then be targeted for resection or further investigated by invasive EEG [
7]. Past studies have indicated that 2-[
18F]fluoro-2-deoxy-D-glucose ([
18F]FDG)-PET is instrumental in decision-making for nearly 50% of patients with incongruent findings between EEG and MR [
10]. Most importantly, [
18F]FDG-PET demonstrates lower rates of false negatives compared to SPECT [
11] and helps in predicting surgical outcomes [
10,
12‐
14].
Despite its advantages, the use of hybrid imaging techniques, particularly [
18F]FDG-PET/computed tomography (CT), in children undergoing presurgical evaluation for DRE raises safety concerns due to the dual sources of radiation involved [
15,
16]. Given the significant number of children with DRE affected by this issue, there is a notable gap in research regarding radiation trends associated with hybrid imaging techniques like [
18F]FDG-PET/CT and [
18F]FDG-PET/MR. Thus, this study aimed to evaluate the trends in [
18F]FDG doses administered and the radiation doses from CT over the study period in children with DRE who underwent hybrid [
18F]FDG-PET scans. Additionally, we assessed how these changes impacted image quality.
Material and methods
In this retrospective, single-center study, we selected children with DRE who underwent hybrid brain [18F]FDG-PET scans at the Department of Nuclear Medicine, University Hospital of Zurich, for presurgical evaluation between January 1, 2005, and May 31, 2021. Inclusion criteria were: 1) DRE diagnosis, 2) hybrid [18F]FDG-PET brain scan, and 3) age ≤ 18 years at the time of the scan. Exclusion criteria were: 1) missing CT dose scan report, 2) congenital or acquired pathologies affecting the basal ganglia or thalamus that could interfere with image analysis (e.g., basal ganglia stroke, metabolic diseases), and 3) image artifacts that precluded evaluation.
We extracted epidemiological and epileptological data from medical records. A detailed description of these parameters is provided in the Supplementary Table
1. DRE structural etiology was classified according to Blümke et al. [
17] (Table
1). For children who underwent epilepsy surgery, the structural etiology was determined based on histological analysis; those not operated were classified based on unequivocal imaging patterns on structural MR alone. Lateralization and lobar localization of the presumed EZ were determined based on seizure semiology, EEG, structural MR, PET findings, or surgical outcomes (Supplementary Table
2). Lesion lateralization was subdivided into right, left, bilateral, or negative; lobar localization was classified as frontal, temporal, posterior, deep, infratentorial, or bilateral (Supplementary Table
2) [
18‐
20]. In cases of unilateral lesions involving multiple lobes, the most affected lobe was identified for classification.
Table 1
Structural classification based on Blümke et al. [
17]
Structural | | | 42 (76%) |
| Focal cortical dysplasia | | 12 (22%) | |
| Hippocampal sclerosis$ | | 9 (16%) | |
| Low-grade glioma$ | | 7 (13%) | |
| MCD-other | | 6 (11%) | |
| | Grey matter heterotopia | | 2 |
| | Tuberous sclerosis | | 2 |
| | Hypothalamic hamartoma | | 1 |
| | Polymicrogyria | | 1 |
| Non-low-grade glioma | | 1 (2%) | |
| | High-grade glioma | | 1 |
| Vascular malformations | | 3 (5%) | |
| | Sturge-Weber Syndrome | | 3 |
| Encephalitis | | 3 (5%) | |
| | Rasmussen’s encephalitis | | 3 |
| Glial scarring | | 1 (2%) | |
| | Hypoxic-ischemic encephalopathy | | 1 |
Non-structural | | | 13 (24%) |
| Genetic | | 7 (13%) | |
| Unknown* | | 6 (11%) | |
The local ethics committee approved the study (Number: 2020–03067). Written informed consent was waived for patients scanned before January 2016. After January 2016, only patients whose caretakers provided documented consent for the use of their medical data were included in the study.
Image acquisition
The [
18F]FDG-PET scans were acquired using various PET/CT and PET/MR scanners (Supplementary Table
3 and Supplementary image 1). Additional scanner information is detailed in a previous publication [
21]. CT and MR were used for PET attenuation correction and anatomical co-localization of [
18F]FDG-PET findings.
[18F]FDG-PET acquisition parameters
Children were asked to fast for at least 4 to 6 h before [
18F]FDG injection to maximize its uptake. The injected dose (MBq) was calculated according to our in-house developed protocol (Supplementary image
2). Briefly, in children weighing < 15 kg, a standard dose of 43.1 MBq was administered, which was limited by the minimum dose provided by the automatic injection system. In children with a body weight of 15–60 kg, the prepared dose was tailored to the patient’s weight and then refined using a calibration factor, with a maximal dose of 80 MBq. Finally, in children heavier than 60 kg, a standard dose of 100 MBq was administered. Minimal changes in the protocol on a per-patient basis were tolerated. If clinically indicated, children underwent sedation for image acquisition. The [
18F]FDG uptake time was set to 50–60 min. The uptake period was spent either in the scanner (sedated children) or the waiting room (non-sedated children). In children undergoing PET/CT, CT images were acquired after PET. In children undergoing PET/MR, the MR protocol was simultaneous with PET image acquisition. The scan coverage was limited to the patient’s head. PET images were reconstructed with different reconstruction algorithms (Supplementary Table
3).
CT acquisition parameters
The CT scan coverage was identical to the PET coverage. The CT technical parameters used are detailed in Supplementary Table
4. Standard-dose (x-ray tube voltage: 120-140 kV) or low-dose (x-ray tube voltage: 80–100 kV) protocols were adopted according to scanner generation and patient characteristics. Data on mAs and image reconstruction algorithms used throughout the study were not consistently retrievable from patients’ images or Digital Imaging and Communications in Medicine (DICOM) metadata. Therefore, they were not included in the analysis.
MR acquisition parameters
All scans included at least 3D T1-weighted and 2D T2-weighted MR sequences of the brain. Additional sequences, such as 2D and 3D fluid-attenuated inversion recovery (FLAIR) or 3D T2-weighted sequences were acquired if needed. Sequence parameters are detailed in the Supplementary Table
5.
Administered activity per body weight and CT dose value
The injected [18F]FDG dose was derived from scan reports, while administered activity per body weight was calculated by dividing the injected dose by the patient body weight (MBq/kg).
CT dose index volume (CTDIvol) and dose length product (DLP) were derived from dose reports or DICOM metadata and used to estimate the absorbed radiation dose in each patient. CTDIvol (mGy) represents the output dose of a specific scanner for a specific protocol, while DLP measures the ionizing radiation exposure during the entire acquisition (mGy*cm).
Image quality analysis
All readings were performed on a Picture Archiving and Communication System integrated station (24-inch display, 1920 × 1080 resolution). The readers were allowed to use post-processing tools such as windowing, gradation adjustment, and magnification. Image analysis was performed as follows:
-
PET scans: Four fully trained raters (two board-certified radiologists [AGG and AR] and two double board-certified radiologists and nuclear medicine physicians [AM and MWH]) qualitatively evaluated the image quality and noise of all [
18F]FDG-PET scans using a four-point Likert scale as reported in Liberini et al. [
22] (Table
2, and Supplementary image 3). Three locations were evaluated: centrum semiovale (defined as the first slice in which the corpus of the caudate nucleus is no longer visible), basal ganglia (defined as the slice in which both the head of the caudate nucleus and the putamen nuclei are visible), and cerebellum (defined as the slice in which the dentate nuclei are visible). The raters were blinded to epidemiological and epileptological information and other raters’ scores.
-
CT scans: A fully trained, board-certified radiologist (AGG) drew a circular 100 mm
2 region of interest (ROI) in the following locations: right and left thalamus, evaluated in an axial plane encompassing the genu and the splenium of the corpus callosum, as well as in the vitreous humor of the right ocular globe. The ROI’s mean density (Hounsfield units) and standard deviation (SD) were derived. Signal-to-noise ratio (SNR) and contrast-to-noise ratio (CNR) were calculated as follows:
-
SNRCT = mean density values of the thalami divided by the mean value of their SDs.
-
CNRCT = difference between the mean density values of the thalami and the mean density value calculated in the vitreous humor of the right ocular globe, divided by the mean value of the SDs calculated in the thalami.
Table 2
[18F]FDG-PET image quality assessment
Description | Score |
Overall image quality |
Inadequate image quality with marked blurring of grey-white matter junction and cortical gyri | 1 |
Fair image quality with diagnostically relevant blurring of grey-white matter junction and cortical gyri | 2 |
Good image quality with diagnostically irrelevant blurring of grey-white matter junction and adequate distinction of cortical gyri | 3 |
Very good image quality with almost any blurring of grey-white matter junction and good distinction of cortical gyri | 4 |
Image noise |
Almost any | 1 |
Diagnostically irrelevant | 2 |
Diagnostically relevant | 3 |
Marked noise | 4 |
Statistical analysis
The statistical analysis was performed using R software version
4.0.5 (
https://www.r-project.org). The D’Agostino-Pearson test was used to check data distribution. Mean ± SD, median (interquartile range, IQR), frequencies, and percentages were used for descriptive statistics as appropriate. Parametric, non-parametric, Fisher’s, and Chi-square tests were used for group-wise comparisons, while Pearson and Spearman correlation tests were used to calculate the relationship between variables. Specifically, the association between epidemiological data (e.g., age at scan, weight, etc.) and the date of scan, defined as a numeric variable, were tested using Spearman’s correlation.
Quasi-Poisson regression was used to investigate the changes in injected [
18F]FDG dose, administered activity per body weight, CTDIvol, DLP, and CT and PET image parameters from 2005 to 2021, adopting calendar year as the independent variable. Quasi-Poisson regression analysis was preferred over Poisson due to the overdispersion encountered with the latter. Age, sex, and injected [
18F]FDG dose were included as covariates in models evaluating [
18F]FDG-PET image quality. Only age and sex were retained in those analyzing CT dose and image quality. Age and sex were incorporated as covariates based on previous research highlighting variations in the brain according to sex and age ranges [
23‐
25]. Models’ residuals were checked for signs of autocorrelation using the Breusch-Godfrey test. Regression coefficients were exponentially transformed and presented with their 95% confidence intervals (CIs), expressing variables’ changes over calendar years as percentages to improve the readability of the results.
To account for the foreseeable radiation dose reduction associated with a more extensive implementation of PET/MR scanners, a sensitivity analysis including both CT and MR dose values was performed. For this purpose, the CTDIvol and DLP values of MR were fictitiously set to 0.
The two-way random effect model intraclass correlation coefficient (ICC) was used to assess the inter-rater agreement on [18F]FDG-PET image quality and noise. Poor agreement was defined by ICC values of 0.49 and below, moderate agreement by those between 0.5 and 0.74, good agreement by those between 0.75 and 0.89, and excellent agreement by those of 0.9 and above.
All statistical analyses were two-tailed; Holm’s correction was used for multiple comparisons, with statistical significance set at p < 0.05.
Discussion
Our study demonstrated that [
18F]FDG-PET image quality improved annually by 9%, while CT-associated radiation dose decreased annually by 15–16%, and [
18F]FDG administered activity per body weight remained stable over the last 15 years. Given that medical imaging is the most significant man-made source of ionizing radiation, our findings highlight the importance of the “As Low As Reasonably Achievable” principle [
26,
27], particularly in children due to their long life expectancy and rapidly dividing cells [
26,
27].
Compared to traditional radiological exams, [
18F]FDG-PET/CT typically delivers higher radiation doses [
28] due to its dual sources of radiation: radiopharmaceuticals and anatomical imaging [
29]. Therefore, its use in children is approached with caution. Interestingly, our study detected a reduction in the injected [
18F]FDG dose between 2005 and 2021. However, since we reported no variation in our injection protocol throughout the study period, we attribute this finding to the reduction in the age at scan, consistent with the idea of expedited epilepsy surgery in children with DRE [
30]. During the study period, the European Association of Nuclear Medicine (EANM) issued several guidelines [
31‐
34], which formed the basis for international consensus documents [
35]. While the study period spans almost two decades, our [
18F]FDG injection strategy, as well as that suggested by international guidelines and consensus documents, did not vary. This proves the generalizability of our results even if our in-house protocol differed from the EANM one. Conversely, the higher administered activity per body weight in females was explainable with random patient-based deviation from the injection protocol. Of note, the radiation concerns differ between children with oncological diseases – who require multiple scans covering broad anatomical areas, including radiosensitive structures, such as the bone marrow, thyroid, and reproductive system [
36] – and those with epilepsy, who typically need a single scan. This is reflected in our findings, where 93% of patients were scanned only once. Despite the global trend of shifting from PET/CT to PET/MR, PET/CT continues to be widely used in presurgical protocols of children with DRE [
10,
11,
37‐
39], hence, validating the ongoing tendency to reduce radiation CT-associated and/or FDG-associated doses observed in oncological scanning [
21,
40] in these patients is of paramount importance.
The role of various ancillary diagnostic tools for children with DRE remains a subject of debate [
7]. Different experts have favored distinct approaches based on the varying levels of confidence in these techniques. The need for an additional sedation session has been seen as a drawback, deterring pediatric neurologists and epileptologists from recommending [
18F]FDG-PET scans for children with DRE. Nonetheless, [
18F]FDG-PET is highly recommended for specific DRE cohorts, including those with extensive hemispheric lesions, inconclusive EEG or MR findings, or conflicting results from these modalities. These categories were well-represented in our study population, underlining the generalizability of our findings. Additionally, our results, which demonstrate substantial improvements in [
18F]FDG-PET image quality, may bolster the credibility of this technique. Of note, literature shows that [
18F]FDG-PET successfully localized the EZ in 72% of children deemed negative at 3T MR [
41]. Further, a recent multicenter study demonstrated that short-term surgical outcomes were similar between MR-positive temporal lobe epilepsy patients with MR-EEG concordance and MR-negative patients with [
18F]FDG-PET-EEG concordance (68% vs. 65%), underscoring the vital role of [
18F]FDG-PET in presurgical evaluation of patients with DRE [
10]. Additionally, the introduction of receptor radiotracers has proven to be more sensitive and accurate than [
18F]FDG in localizing the EZ and is expected to yield additional improvements [
36,
42].
Our study offers fresh insights into the perceived safety of hybrid scans, particularly [
18F]FDG-PET/CT, among pediatric neurologists and epileptologists. Both standardized measures of radiation dose metrics, DLP and CTDIvol, have significantly decreased – a crucial finding for centers lacking PET/MR scanners. Notably, the CT-associated radiation doses in our study were much lower than those typically reported for traditional brain CT scans in the radiological literature [
43,
44]. This reduction is increasingly relevant given the rising awareness of radiation's potential harm, making it an essential consideration for physicians and parents deciding on [
18F]FDG-PET scans for children with DRE. In addition, ongoing technological advancements are expected to further enhance dose reduction, with newer and more efficient scanners [
45].
Finally, the dissemination of PET/MR scanners could significantly reduce radiation concerns, providing a comprehensive “one-stop-shop” approach for children with DRE. The superior contrast resolution and the multiparametric capabilities of MR offer additional benefits. However, the widespread availability of such systems remains limited: currently, PET/MRs account for only ~ 1% [
46] and 7% [
47] of the hybrid scanners in the United States and Europe, respectively.
Limitations
Our study's retrospective, single-center design presents certain limitations. Although conducted at one of the largest tertiary care hospitals in Switzerland, our results may not be universally applicable due to differences in healthcare systems in various countries, nor do they translate to other radiotracers. Nonetheless, our detailed technical characterization could be beneficial for other centers aiming to implement dose-reduction strategies. The lack of data on CT image acquisition (mAs) and reconstruction algorithms limited our ability to thoroughly analyze the evolution of CT image quality over time or to explore the relationship between image quality and different tube voltages (kVs). Finally, it is important to note that CTDIvol and DLP do not represent the actual or effective radiation dose absorbed by a patient, and these values can vary with different patient sizes, particularly in pediatric cases [
48]. Nonetheless, these metrics are commonly used to compare scan performance across vendors and patients.
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