Image Processing

Quantitative performance characterization of image quality and radiation dose for a CS 9300 dental cone beam computed tomography machine

[+] Author Affiliations
Elham Abouei

University of British Columbia, Department of Physics and Astronomy, 6224 Agricultural Road, Vancouver, B.C. V6T 1Z1, Canada

Sierra Lee

University of British Columbia, Department of Oral Biological and Medical Sciences, 2199 Webrook Mall, Vancouver, B.C. V6T 1Z3, Canada

Nancy L. Ford

University of British Columbia, Department of Physics and Astronomy, 6224 Agricultural Road, Vancouver, B.C. V6T 1Z1, Canada

University of British Columbia, Department of Oral Biological and Medical Sciences, 2199 Webrook Mall, Vancouver, B.C. V6T 1Z3, Canada

J. Med. Imag. 2(4), 044002 (Nov 18, 2015). doi:10.1117/1.JMI.2.4.044002
History: Received May 6, 2015; Accepted October 16, 2015
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Open Access Open Access

Abstract.  This paper aims to characterize the radiation dose and image quality (IQ) performance of a dental cone beam computed tomography (CBCT) unit over a range of fields of view (FOV). IQ and dose were measured using a Carestream 9300 dental CBCT. Phantoms were positioned in the FOV to imitate clinical positioning. IQ was assessed by scanning a SEDENTEXCT IQ phantom, and images were analyzed in ImageJ. Dose index 1 was obtained using a thimble ionization chamber and SEDENTEXCT DI phantom. Mean gray values agreed within 93.5% to 99.7% across the images, with pixel-to-pixel fluctuations of 6% to 12.5%, with poorer uniformity and increased noise for child protocols. CNR was fairly constant across FOVs, with higher CNR for larger patient settings. The measured limiting spatial resolution agreed well with 10% MTF and bar pattern measurements. Dose was reduced for smaller patient settings within a given FOV; however, smaller FOVs obtained with different acquisition settings did not necessarily result in reduced dose. The use of patient-specific acquisition settings decreased the radiation dose for smaller patients, with minimal impact on the IQ. The full set of IQ and dose measurements is reported to allow dental professionals to compare the different FOV settings for clinical use.

Figures in this Article

Cone beam computed tomography (CBCT) has been used in dentistry since the early 2000s in North America. Dental CBCT machines are primarily installed in private dental offices, but guidelines for the use and maintenance of these machines have not been widely adopted.1 Early investigations compared the image quality (IQ) of dental CBCT machines with multislice computed tomography (MSCT) to identify the utility of the dental devices. Subjective observer assessments of the IQ and visibility of structures have been reported, where the observers scored images of a dry skull obtained with both dental CBCT and MSCT scanners, showing that dental CBCT units provide adequate IQ for dentomaxillofacial radiology.2 Using a phantom provided by the dental CBCT vendor, Loubele et al.3 compared the contrast-to-noise ratio (CNR), mean gray values, and segmentation accuracy between CBCT and MSCT, with the conclusion that the dental unit proved better for bone segmentation and was less prone to artifacts resulting from metal appliances. The same researchers also investigated the dose efficiency of dental CBCT by correlating the segmentation efficacy with the measured dose.4 Suomalainen et al.5 measured the CNR and spatial resolution by placing test objects in a radiosurgery verification phantom and compared the IQ for two MSCT and four CBCT machines, determining that adequate images could be obtained but optimizing the acquisition parameters would be important. Dillenseger et al.6 compared three MSCT scanners with a dental system using a quality assurance phantom7 developed for microcomputed tomography and concluded that the IQ achieved was comparable between the machines, although the uniformity across the FOV was better for the MSCT scanners.

To create a quality assurance program that could be adopted into routine clinical practice requires standardized measurement tools and a framework for their use. Steiding et al.8 have developed a framework for quality assurance testing, including an IQ phantom and automated analysis software. The proposed phantom and software have been tested on a dental CBCT unit, although they are proposed for widespread use in CBCT machines in radiology, in addition to the dental units. In Europe, the Sedentex consortium developed a pair of phantoms, one for measuring the IQ and one to measure the dose to the patient.9 The Sedentex IQ phantom has been used to assess the correlation between objective IQ metrics and clinical diagnostic value using a skull phantom.10 To address the requirement that the dental professionals perform quality assurance testing during their regular clinic hours, a user-friendly and time-efficient system was developed, with setup, imaging, and automated software analysis completed in approximately 10 min.11

Having the standardized tools in place is a step toward an effective quality assurance program. However, criteria for the measured IQ must be developed to ensure that machines are operating within the recommended framework. To date, there is no large-scale audit reported for assessing the IQ over the full range of operating parameters for any of the installed CBCT models.1 To create appropriate IQ criteria for a quality assurance program, baseline values for the important IQ metrics must be measured for a variety of equipment models and imaging settings. In this study, we use the Sedentex phantoms to measure the IQ and dose for the full range of fields of views (FOVs) and imaging parameters for different patient demographics (child, small, average, and large adults) to characterize the Carestream 9300 system.

Phantoms and Image Acquisition

In this study, the IQ and radiation dose of a dental CBCT machine (CS 9300, Carestream Dental LLC, Atlanta, Georgia) were evaluated using IQ and dose index (DI) phantoms developed by Leeds Test Objects Ltd. (SEDENTEXCT, Boroughbridge, UK) for dental CBCT machines. Both phantoms are head-sized cylinders (160-mm diameter by 162-mm high) made of poly-methyl methacrylate (PMMA) with a density of 1.20±0.01g/cm3 to simulate the human tissue.9 Each phantom was placed on a tripod, leveled with a spirit level, and positioned using the lasers to align the phantom within the FOV, as shown in Fig. 1. IQ assessment was obtained using images of the IQ phantom scanned with the parameters listed in Table 1 and analyzed using ImageJ (National Institutes of Health, Bethesda, Maryland) software. To evaluate the radiation dose, the DI phantom was scanned with the same imaging parameters (Table 1). A calibrated thimble ionization chamber system, a 0.6-cm3 Farmer ionization chamber (10×6 0.6 CT, Radcal Corp., Monrovia, California) in conjunction with a Radcal electrometer (AccuDose, Radcal Corp., Monrovia, California), was used following the SEDENTEX dose index (DI1) methodology. XR-QA2® Gafchromic™ (ISP Technologies Inc., Wayne, New Jersey) films were used to visualize axial dose distribution.

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Fig. 1
F1 :

The Sedentex phantoms (a) IQ for measuring image quality, (b) DI for measuring dose, and (c) the IQ phantom positioned on the tripod in the Carestream 9300 CBCT machine. The lines on the exterior of the IQ phantom indicate the different layers containing test objects. The DI phantom has holes drilled through for ion chamber placement, and PMMA plugs to fill unused holes.

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Table 1Factory installed protocols on the CS 9300 CBCT machine. Each patient setting was preprogrammed by the manufacturer, varying the kVp, mA, and reconstructed voxel size for each patient size. These are the settings that are used clinically.

The dental CBCT machine is the Carestream 9300 (Carestream Dental LLC, Atlanta, Georgia), which uses a partial rotation about the patient during image acquisition. This machine has a variety of cylindrical imaging FOV that cover the craniofacial complex (17-cmdiameter×11-cmheight, 17-cmdiameter×6-cmheight), the maxillofacial area (10-cmdiameter×10-cmheight, 10-cmdiameter×5-cmheight), and for imaging individual teeth (8-cmdiameter×8-cmheight, 5-cmdiameter×5-cmheight). The machine comes with preinstalled imaging protocols for use with different patient demographics, including children, small adults, average adults, and large adults (Table 1), with the option of a high-resolution or low-resolution mode for each. The high-resolution modes offer improved resolution in the images, albeit with increased scan times and x-ray dose to the patient. For this paper, we investigate all patient sizes with voxel sizes of 180 to 250μm to enable comparisons between the protocols, although voxel sizes of 90μm are possible for the smallest FOV (5×5cm) and voxel sizes of 500μm are possible for the largest FOV (17×11cm).

Image Quality Measurements

The IQ phantom has seven vertical columns drilled through the PMMA, which are filled with different test objects to assess IQ. Each hole is 35 mm in diameter, with one in the center of the phantom and the others equally spaced around the periphery. The complete design of the phantom has been published by Pauwels et al.9 Each set of test objects is placed at a different height within the phantom to obtain all of the IQ data simultaneously. To assess the IQ, the center slice for each test object was located in the orthogonal view, and five adjacent slices were used for the measurements (two above, the central slice and two below). By using only the middle five slices of the test objects, the measurements were less sensitive to misalignment of the phantom, partial volume at the edges, or artifacts from adjacent test objects.

To measure the image noise, five circular ROIs were placed at the center (ROI 5) and periphery (ROIs 1, 2, 3, 4) of the FOV on the center slice of noise/uniformity layer oriented as shown in Fig. 2(a). ROIs were 40 mm in diameter for images obtained with the 17-cm diameter FOVs, and the ROI diameter was 20% of the FOV diameter for all other FOV sizes. Noise was defined as average SD of gray values of five ROIs. The SD was normalized to the difference of MGV between PMMA and air regions [Eq. (1)]12 to be comparable through different protocols, since the mean values for each protocol were different. Uniformity was defined as the difference between MGV of central and peripheral ROIs, as given by Eq. (2).12 MGV and SD were measured on images of the lower part of the IQ phantom that had uniform PMMA across the entire phantom diameter. Uniformity was also assessed by vertical and horizontal line profiles through the center of the central slice. Care was taken to ensure that the lines drawn were orthogonal to each other and passed through the center of the phantom (along the diameter) Display Formula

Noise=SD(MGVPMMAMGVAir),(1)
Display Formula
Uniformity=(1|MGVCenterMGVPeripheralMGVPMMAMGVAir|)×100.(2)

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Fig. 2
F2 :

(a) ROIs for noise/uniformity, (b) two perpendicular lines to measure line profiles for geometric distortion, and (c) rectangular ROIs around the artifact rods.

Periodicity of the evenly spaced voids in the geometric distortion layer was defined as the geometric distortion parameter. It is measured using line profiles drawn manually across two perpendicular lines on the center slice of geometric distortion layer shown in Fig. 2(b). The actual spacing between the voids in the phantom is 10.0 mm, with each void measuring 2.0 mm in diameter and 3.0-mm deep. The center-to-center distance between adjacent holes was calculated from the line profile and compared to the nominal value. The average center-to-center distance is reported.

For the quantitative evaluation of metal artifacts, the artifact added value (AAV) using two metal artifact inserts was calculated using Eq. (3).13 The AAV for each protocol was reported as the average of AAVs for the four ROIs shown in Fig. 2(c). Regions of interest near the metal inserts were chosen to extend the length of the three inserts but exclude the metal, and the mean gray value was obtained. Measurements of the mean gray value in PMMA and air were obtained in regions of interest in other layers and subtracted to yield the AAV Display Formula

AAV=MGVArtifactMGVPMMAMGVPMMAMGVAir.(3)
The CNR was defined as the ratio of the difference between the MGV of PMMA and a material (Al, PTFE, POM, LDPE, and Air) to the average of SD of both PMMA and the material [Eq. (4)].12MGVPMMA and SDPMMA are measured from the noise/uniformity layer, and MGVmaterial and SDmaterial are measured for 20-mm diameter circular ROI at each corresponding disk using the pixel intensity insert. The materials included in the phantom represent a range of densities consistent with human tissues, ranging between 0.90g/cm3 for LDPE, 1.18g/cm3 for PMMA, 1.41g/cm3 for POM, 2.2g/cm3 for PTFE, and 2.70g/cm3 for Al. Display Formula
CNR=|MGVMaterialMGVPMMA|1/2(SDMaterial+SDPMMA).(4)

The resolution (LP/mm) inserts were used to determine the spatial resolution of the image visually (Fig. 3). The smallest LP/mm was visually counted for both the xy-plane and z-axis inserts. The spatial resolution was also calculated quantitatively using the point spread function (PSF) insert, which contains a 0.25-mm diameter stainless steel wire suspended in air parallel to the z-axis, to calculate the modulation transfer function (MTF) using MATLAB (Mathworks, Natick, Massachusetts). Ten adjacent central axial slices were averaged to generate a low-noise PSF, ensuring that the location of the wire remained constant through all slices used. A rectangular ROI, 30×30pixels, was centrally placed at the PSF insert. Pixel values over this ROI were integrated in the longitudinal direction (integrating along either the x- or y-axis) to yield a one-dimensional (1-D) PSF. The resulting distribution was plotted, and full-width at half-maximum (FWHM) was calculated. The MTF was calculated from 1-D PSF using the fast Fourier transform method, and divided by the spatial frequency spectrum described by the steel wire.14,15 The frequency at 10% of the MTF was used to calculate the limiting spatial resolution (Fig. 4), as this provides the limiting resolution for a human observer that can be compared to the subjective measurement of the bar pattern insert. The limiting resolution is calculated using Eq. (5), where LP10%MTF is the frequency at 10% MTF Display Formula

resolution=12*LP10%MTF.(5)

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Fig. 3.
F3 :

The bar pattern insert imaged in the axial plane with voxel spacings (a) 250μm, (b) 200μm, and (c) 180μm. The images for z-axis are shown in (d), (e), and (f) respectively. The bar pattern spacing ranges from 1.0to5.0LP/mm.

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Fig. 4
F4 :

(a) The ROI on the central axial slice of the point spread function (PSF) insert. (b) Surface plot of the PSF insert over the ROI. (c) An integrated one-dimensional (1-D) profile of the PSF. (d) MTF obtained from the FFT of the 1-D PSF.

Dose Measurement

The SEDENTEXCT DI phantom, composed of a stack of six PMMA plates forming a cylinder of the size of an adult head, was scanned in the same configuration as a patient. Dose measurements were performed with the method adapted from the SEDENTEXCT project along a diameter of the phantom.16 The measuring diameter was determined from a dose distribution map generated using Gafchromic™ film placed on the center slice of the phantom. The film was scanned five times to accumulate sufficient dose to be in the sensitive range of the film, then it was scanned in a flatbed HP scanner (HP LJ 1536dnf MFP, Hewlett Packard Company, Palo Alto, California) and the dose distribution map obtained using MATLAB (Mathworks, Natick, Massachusetts). For asymmetric dose distributions, a line profile passing through the center of the phantom that exhibited the largest gradient in gray values was identified as the measurement diameter for the ion chamber placement. For symmetric dose distributions, any measurement along the diameter of the phantom should be sufficient. By determining the measuring diameter, dose measurements at five points along this line were performed using a thimble ionization chamber (Fig. 5), and then DI was defined as the average dose along this line [Eq. (6)]. Two scans at each point were taken to assess variation without overheating the x-ray tube; these two dose values reported in milligray were averaged to give the radiation dose at each point Display Formula

DI1=i=15Di5.(6)

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Fig. 5
F5 :

The dose measurement points for DI1 using DI phantom. Number 1 is located at interior/right side of the phantom.

Variability of Image Quality Measurements

For the largest (17×11cm2) and the smallest (5×5cm2) FOVs, intraobserver variability, interobserver variability, and interscan reproducibility of the images obtained from the CS 9300 machine were determined using the average adult settings to assess the consistency and reproducibility of the measurements. For interscan reproducibility, three phantom images were collected and analyzed by a single observer; the phantom was set up and taken down for each of the three phantom images. For intraobserver variability, a single observer analyzed the images on three different dates, 14 days apart. For interobserver variability, a second observer analyzed the same data. The standard deviation of measurements was calculated for the reproducibility and intraobserver variability consistency, and the difference between the measurements was recorded for the interobserver variability. For the remaining settings and FOVs, the phantom was imaged and analyzed once by a single observer.

Image Quality Parameters

The IQ results for noise, uniformity, geometric distortion, and artifacts are summarized in Table 2. As shown in Fig. 6, the 17×11cm2 FOV had the greatest noise value and the 8×8cm2 FOV had the lowest noise value. The 5×5cm2 FOV had noise values less than 17×11cm2 FOV and larger than other FOVs, likely due to reduced kVp settings for the 5×5cm2 FOV. For all FOV options, the child settings had the highest noise indicating that fewer photons were reaching the detector, likely due to a reduction in the dose to the patient.

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Table 2Noise, uniformity, geometric distortion, and AAV obtained for different protocols on CS 9300 CBCT.
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Fig. 6
F6 :

Noise values for all FOVs and patient settings on CS 9300 machine.

The uniformity of the images calculated with Eq. (2) was better than 93.5% for all protocols (Table 2), indicating the difference between the central and peripheral ROIs was less than 7%. Figure 7 shows that the line profiles were symmetric with reduced gray-scale values in the middle of the individual graphs for 17×11cm2 and 17×6cm2 FOVs. For the other FOVs, the uniformity graphs were asymmetric because the FOV includes less than the full phantom width, but showed reduced gray-scale values at the center of the phantom. A cupping artifact occurs at the center of an object due to beam hardening (x-rays with higher energies are more likely to pass through).

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Fig. 7
F7 :

The uniformity graphs including the noise in the image, which is not representing the actual noise in the image since it was smoothed for illustration purposes. (a) Uniformity profile at center of image representing symmetrical uniformity cupping at middle as an example for 17×11 (shown) and 17×6cm2 FOVs. (b) Uniformity profile at center of image is showing asymmetrical cupping uniformity at middle of image for 5×5, 8×8, 10×10, and 10×5cm2 (shown) FOVs.

The average periodicity in the voids was between 9.95 and 10.05 mm for each setting (Table 2), suggesting ±0.05mm error. The measurement error in each case is a fraction of the voxel spacing and agrees well with the actual spacing of 10.0 mm.

The AAV was calculated from four rectangular ROIs per image and averaged (Table 2). The AAVs were between 0.3 and 0.4 for all protocols, except one protocol that had the value of 0.2. No clear difference was seen between large/small FOVs or high-/low-dose protocols.

To investigate the contrast, the MGV for each material in the pixel intensity insert is presented in Table 3. Aluminum (Al) had the greatest MGV value and air with the lowest value, as expected. The MGV values decreased for PTFE, POM, and LDPE, respectively. The standard deviations were greatest for the Al inserts for all protocols and were generally similar for the PTFE, POM, LDPE, and air materials. The CNRs were fairly consistent for each material for all the scanning protocols with the same FOV except for the small FOV, 5×5cm2, which had the greatest range of CNR values over different mA and kVp settings. These differences may occur because the images for each insert were acquired separately, and the range of gray-scale values in the image may depend on the materials present in the FOV. Figure 8 shows the CNR value results for different protocols within each FOV. Al and air had the greatest and most similar CNR values, while there was a small difference between the CNR values of LDPE and POM values. The CNR was reduced for the smaller patient sizes (child, small adult), which was likely related to the increased noise for these acquisition settings.

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Table 3Mean gray values and standard deviations for the different materials in the pixel intensity insert are reported for different protocols on CS 9300 CBCT.
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Fig. 8
F8 :

The CNR values are plotted for the different materials in the phantom for each FOV: (a) 17×11cm2, (b) 17×6cm2, (c) 10×10cm2, (d) 10×5cm2, (e) 8×8cm2, and (f) 5×5cm2. Each graph shows four curves, which correspond to child (blue), small adult (red), average adult (green), and large adult (purple).

The spatial resolution results are presented in Table 4. The FWHM were almost the same within each FOV but did not correlate with the reconstructed voxel size. Although 8×8, 10×10, and 10×5cm2 FOVs have the smallest reported voxel size (180μm), the FWHM was more than double the actual width of the wire (250μm). The results of the visual analysis of the line pair inserts in the xy-plane and along the z-axis for each protocol were between 1 and 2LP/mm. Although the CBCT has isotropic voxels, the LP/mm was not exactly the same in the xy-plane and z-direction for most protocols, with better resolution observed in the axial (xy) plane. The limiting spatial resolution was calculated for each protocol from the LP/mm measured at the 10% of the MTF graph and agreed well with the bar pattern measurements. As an example, Fig. 9 shows MTF curves for the child setting for six FOVs.

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Table 4Spatial resolution obtained from the full-width at half-maximum (FWHM) of the point spread function (PSF), the limiting resolution calculated using Eq. (5) from 10% MTF and the bar pattern insert are reported for different protocols on CS 9300 CBCT.
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Fig. 9
F9 :

The MTF graphs for the child setting for all six FOVs.

Reproducibility of Image Quality Parameters

The reproducibility of IQ parameters assessed through interscan, intraobserver, and interobserver variability represents the reproducibility of the phantom positioning, the measurement method, and the observer’s analysis, respectively. Each IQ metric was measured as described earlier, and the standard deviation was taken of the repeated measurements to assess the variability. SD of the measurements obtained for interscan as well as intraobserver variability is shown in Table 5. The SD for CNR is the average SD of the CNRs of five materials.

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Table 5Reproducibility and intraobserver variability of measurements. For interscan variability, three images were obtained and compared for each FOV. For intraobserver variability, the same image was assessed three times by a single observer.

Percentage difference between measurements obtained by two observers was reported as the interobserver variability in Table 6. The percentage difference for CNR is the percentage difference of the CNRs of all five materials. For interobserver reproducibility, the variation was less for noise, CNR, and LP/mm for the 5×5 compared to 17×11cm2 FOV; however, it was larger for uniformity, geometric distortion, and AAV for 5×5 compared to 17×11cm2 FOV. The highest reproducibility was seen for uniformity and noise; on the other hand, metal artifact had the most deviation due to the large difference between gray values in the ROI, and sensitivity of the rectangular ROI’s positioning near the titanium rods [Fig. 2(c)].

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Table 6Interobserver variability.
Dose Measurement

Dose distributions for all six protocols are shown in Fig. 10, where the color map represents the percentage of the maximum dose, ranging from 0% shown as white to 100% shown as black. Different acquisition settings with the same FOV had very similar dose distributions on the axial slice. The measuring diameter for each FOV is shown by the line in Fig. 10, showing the location of the points shown in Fig. 3 used for the thimble ion chamber measurements. Point dose measurements along the measuring diameter are provided in Fig. 11 for the average adult protocol.

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Fig. 10
F10 :

Axial dose distribution for different FOVs. The dose distribution was obtained just for average adult and child settings. The red line represented the measuring diameter for DI1. The bottom and left side of the dose distribution correspond to the anterior and right side of the patient. The scale bar shows the distribution of dose as a percentage of maximum dose in each image.

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Fig. 11
F11 :

The average of two dose readings at each point along the measuring diameter for average protocols is plotted. Points 1–5 were placed anterior to posterior uniformly.

The DI1 ranged from 2.75 to 4.13 mGy for large adults, 1.82 to 3.23 mGy for average adults, 1.63 to 2.69 mGy for small adults, and 1.01 to 2.21 mGy for the child setting. Variability in the measurements was within 0.02 mGy for all ion chamber positions in all FOVs. DI1 for each protocol is shown in Fig. 12 as column bars. The error bars represent the variability across the phantom for each FOV, with the largest error bars corresponding to the FOVs with a linear gradient in the dose distributions (Fig. 10). In general, DI1 increased for larger FOVs, higher mA and kVp, smaller voxel sizes, and longer scan times, as expected. However, Fig. 12 also shows the 5×5cm2 FOV, large adult (8 mA, 84 kV, 12 s, and 200μm) in the far right column with a higher dose compared to the 17×11cm2 FOV, child (4 mA, 80 kV, 6.40 s, 250μm) shown in the left-most column, making dose trends more difficult to predict across different FOVs.

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Fig. 12
F12 :

The DI1 measured for different FOVs and different patient settings (child, small, average, and large adult).

Quality assurance in dental radiology is to ensure that consistently adequate diagnostic information is acquired, while the radiation dose is kept as low as reasonably achievable (ALARA). The SEDENTEXCT project recommended that the QA program be mainly composed of six subjects including performance of the x-ray tube and generator, quantitative assessment of IQ, display screen performance, patient dose assessment, clinical IQ assessment, and clinical audit.16 Image intensity values, uniformity, and artifacts are recommended for monthly testing, and the others are recommended for yearly testing.15 It is important to select the CBCT exposure parameters considering both the radiation dose, adhering to the ALARA principle, and IQ evaluation.

In this study, a CS 9300 machine for application in dental imaging (maxillofacial region) was assessed in terms of technical performance (dose and IQ including noise, uniformity, geometric distortion, metal artifact, contrast resolution, and spatial resolution) for all FOVs and patient demographics. Reproducibility of the measurements of IQ parameters was assessed, and all measurements of the IQ parameters were proven to be reproducible within a few percent for all metrics (up to 30% for artifacts) in consecutive scans (interscan), as well as for repeated measurements of identical scans (interobserver or intraobserver). It can be expected that consecutive scans differ slightly in terms of voxel values due to slight variability in tube output,9 detector operation, and phantom positioning. Our measurements showed that the interscan reproducibility exhibited more variability than interobserver/intraobserver reproducibility. For interscan reproducibility, the SDs for all IQ parameter values in the 5×5cm2 FOV were larger than the 17×11cm2 FOV, because more image acquisitions and more adjustments were required to image the entire phantom for the 5×5cm2 FOV. For intraobserver variability, the 5×5cm2 FOV had less variation than the 17×11cm2 FOV except for AAV parameter since the 5×5cm2 FOV was acquired with longer exposure time, which reduced the variability in the measurements performed by a single observer.

This study showed that image noise and uniformity values were not only affected by the exposure, but that the noise values for 17×6 FOV, 10×10 FOV, and 10×5cm2 FOV were comparable because they were all acquired with the same exposure times, kVp, mA, and voxel sizes. The location of the FOV and the amount of mass outside the volume were additional parameters leading to differences in performance; the “exo-mass” effect has been defined as the gradient of voxel values appearing for asymmetrical phantom positioning and causes a shift in density response throughout the entire volume, as well as a decrease in uniformity.9,17 Beam hardening and correction of projection data may also affect the image noise and uniformity.15

All protocols showed geometric distortion of less than 0.05 mm; the geometric distortion is generally required to be less than 1 mm for a measurement to be considered accurate.18 The measurement error could be due to geometric distortion or the partial volume effect.19 There may also be minor misalignment of the rows of voids and the positioning aids on the exterior of the phantom, causing the voids to cross axial planes. Geometric distortions can be caused by detector misalignment with the imaging plane during the gantry rotation or nonuniformities in the detector material. Geometric distortions are rare in modern equipment and are generally eliminated by calibration adjustments or corrected in software. Artifacts arising from photon starvation in the vicinity of the titanium rods appeared similar comparing different protocols and was quantified by calculating the AAV, similar to the methods established by Pauwels et al.13 The AAV provides a relevant description of the net effect of streaks on IQ at the vicinity of the titanium rods, but provides no information regarding extinction, beam hardening, or other artifacts. Artifacts around metallic restoration materials are problematic, as CBCT is used for follow up in these patients, and the important regions to visualize (soft tissues, such as oral mucosa, and the underlying bone) are often adjacent to the metal. Artifacts in this region may interfere with assessing the integration of the metallic post into the surrounding bone, which is an important predictor of implant survival. The AAV values measured in this study seem to agree with the range provided by Pauwels et al.,9 although the Carestream 9300 was not investigated in Pauwel’s study.

Soft-tissue contrast resolution was somewhat limited, especially for the large FOV (17×11cm2). CNR measurements showed the general poor contrast for materials of intermediate density; the noise is often similar or larger than the measured difference in mean voxel value between a low-density material and PMMA. Dental CBCT is optimized for imaging high-contrast material, such as the bone and tooth structure in the maxillofacial region, and is typically used for planning oral surgeries and in the field of orthodontics.20 During planning, the dentist or surgeon will need to see important soft tissues in addition to bone and tooth, such as facial nerves, ligaments, infected areas, and pathologies such as cysts and tumors. Therefore, the soft tissue contrast is important to investigate for treatment planning and assessment as well as for identifying any suspicious lesions that may be present. Assessing the CNR and contrast resolution for a variety of tissue-like materials may predict at what size different types of tissues will be visible in the images.

The bar pattern test exhibited limiting resolutions of 12LP/mm for all protocols, exhibiting acceptable resolution as suggested by Brullman and Schulze.21 The measured limiting spatial resolution did not correlate with reconstructed voxel size, which is consistent with the measurements of Pauwels et al.22 and Bamba et al.15 The images are resampled for display purposes at the voxel spacing reported in the acquisition parameters. Although a general consistency was observed between limiting spatial resolution measured by the 10% MTF and visual inspection of the bar patterns, it is clear that the reported voxel size (reconstructed voxel size) provides only a crude prediction of the spatial accuracy.9 It must be noted that the MTF measurement can be influenced by a number of factors, such as the difference in voxel values for the steel wire and the surrounding air, and the presence of small streak artifacts,9 as well as the selected ROI for PSF measurement.

The dose distributions were not uniform for all measurements, because the device does about a half rotation instead of a full rotation around the patient’s head. In addition, the center of the FOV does not align with the center of the patient’s head for FOVs with less than a 17-cm diameter. As seen in Fig. 10, a symmetric dose gradient is evident for 17×11cm2 and 17×6cm2 FOVs. The 10×10cm2, 10×5cm2, 8×8cm2, and 5×5cm2 FOVs have off-axis positioning of the FOV to image specific portions of the mandible or maxilla, leading to more localized dose within the FOV. The DI1 values differed with different protocols, with an increase in the measured DI1 for larger FOVs for a given patient setting. The DI1 was expected to increase from a child to a large adult for a given FOV; however, for 10×5 and 10×10cm2 FOVs, DI1s were larger for the small adult than the average adult. This anomaly can be due to positioning the ionization chamber slightly above or below the central plane in the z-axis for the different FOV acquisitions, which indicates that a range of acceptable values may be needed for dose measurements in a quality assurance program to account for small variations in ion chamber position within the phantom and within the FOV. The child settings did provide a reduction in the radiation dose to the patient, as suggested by Choi et al.23 and the Image Gently Campaign.24 Since the imaging technique changes (kVp, mA, exposure time) in addition to the FOV size between these two acquisition settings, the dose received by the patient can only be predicted by accounting for all factors and is not necessarily reduced by simply reducing the FOV size.

In this study, IQ metrics were compared for different patient imaging protocols. We found that the pediatric protocols did reduce the dose to the patient, with only small changes to the IQ—primarily an increase in image noise. This result suggests that using protocols that are specifically designed for smaller patients will reduce their radiation risk with no loss of image information. We also compared different imaging FOV, while maintaining similar reconstructed resolution settings (180 to 250μm). Using a smaller FOV will reduce the amount of tissue exposed to radiation, thereby decreasing the dose. Furthermore, improvements in the image noise and the CNR were measured in the smaller FOV images, which may lead to improved visualization of important structures. Since the smaller FOV also has a higher resolution setting (not used in this study), which would increase the dose to the patient considerably if used, careful consideration of the imaging task must be taken to determine if the improved CNR of the small FOV is sufficient for the diagnostic task or if higher resolution imaging would be required.

In this study, a complete characterization of the IQ and dose for a single dental CBCT unit was performed. All FOV and patient sizes were used to quantify the baseline values of a variety of IQ metrics that could be used in a quality assurance program. The measurement reproducibility and variability were investigated and found to be within 6% for the semiautomated methods used for all tests except artifact evaluation, which seems quite favorable for routine quality assurance. Images obtained with the child setting exhibited slightly reduced CNR and increased noise (3%) compared to the adult settings, although there was a corresponding decrease in radiation dose, ranging from 0.8 to 1.0 mGy compared to the average adult. In clinical practice, this degradation in IQ may not materialize, as the child and small adult settings would only be used with smaller patients.

The authors acknowledge Dr. Pierre Deman for assistance with the dosimetry measurements. Funding for this study was from an NSERC Discovery Grant (RGPIN 341581-10), CIHR Health Professional Student Research Award (2013), UBC Faculty of Dentistry S. Wah Leung Award (2013), and UBC Faculty of Dentistry Research Equipment Award (2012).

Horner  K., , Jacobs  R., and Schulze  R., “Dental CBCT equipment and performance issues,” Radiat. Prot. Dosim.. 153, (2 ), 212 –218 (2013).CrossRef
Liang  X.  et al., “A comparative evaluation of cone beam computed tomography (CBCT) and multi-slice CT (MSCT) Part I. On subjective image quality,” Eur. J. Radiol.. 75, (2 ), 265 –269 (2010).CrossRef
Loubele  M.  et al., “Comparative study of image quality for MSCT and CBCT scanners for dentomaxillofacial radiology applications,” Radiat. Prot. Dosim.. 129, (1–3 ), 222 –226 (2008).CrossRef
Loubele  M.  et al., “Image quality vs radiation dose of four cone beam computed tomography scanners,” Dentomaxillofac. Radiol.. 37, (6 ), 309 –318 (2008).CrossRef
Suomalainen  A.  et al., “Dosimetry and image quality of four dental cone beam computed tomography scanners compared with multislice computed tomography scanners,” Dentomaxillofac. Radiol.. 38, (6 ), 367 –378 (2009).CrossRef
Dillenseger  J. P.  et al., “MSCT versus CBCT: evaluation of high-resolution acquisition modes for dento-maxillary and skull-base imaging,” Eur. Radiol.. 25, (2 ), 505 –515 (2015).CrossRef
Du  L. Y.  et al., “A quality assurance phantom for the performance evaluation of volumetric micro-CT systems,” Phys. Med. Biol.. 52, (23 ), 7087 –7108 (2007).CrossRef
Steiding  C., , Kolditz  D., and Kalender  W. A., “A quality assurance framework for the fully automated and objective evaluation of image quality in cone-beam computed tomography,” Med. Phys.. 41, (3 ), 031901  (2014).CrossRef
Pauwels  R.  et al., “Development and applicability of a quality control phantom for dental cone-beam CT,” J. Appl. Clin. Med. Phys.. 12, (4 ), 3478  (2011).CrossRef
Choi  J. W.  et al., “Relationship between physical factors and subjective image quality of cone-beam computed tomography images according to diagnostic task,” Oral Surg. Oral Med. Oral Pathol. Oral Radiol.. 119, (3 ), 357 –365 (2015).CrossRef
Torgersen  G. R.  et al., “A phantom for simplified image quality control of dental cone beam computed tomography units,” Oral Surg. Oral Med. Oral Pathol. Oral Radiol.. 118, (5 ), 603 –611 (2014).CrossRef
Gayou  O., “Influence of acquisition parameters on MV-CBCT image quality,” J. Appl. Clin. Med. Phys.. 13, (1 ), 3638  (2012).CrossRef
Pauwels  R.  et al., “Quantification of metal artifacts on cone beam computed tomography images,” Clin. Oral Implants Res.. 24, (Suppl. A100 ), 94 –99 (2013).CrossRef
Jaffray  D. A., and Siewerdsen  J. H., “Cone-beam computed tomography with a flat-panel imager: initial performance characterization,” Med. Phys.. 27, (6 ), 1311 –1323 (2000).CrossRef
Bamba  J.  et al., “Image quality assessment of three cone beam CT machines using the SEDENTEXCT CT phantom,” Dentomaxillofac. Radiol.. 42, (8 ), 20120445  (2013).CrossRef
Sedentex Project, “Cone beam CT for dental and maxillofacial radiology,”  European Commission  (2012).
Bryant  J. A., , Drage  N. A., and Richmond  S., “Study of the scan uniformity from an i-CAT cone beam computed tomography dental imaging system,” Dentomaxillofac. Radiol.. 37, (7 ), 365 –374 (2008).CrossRef
Kobayashi  K.  et al., “Accuracy in measurement of distance using limited cone-beam computerized tomography,” Int. J. Oral Maxillofac. Implants. 19, (2 ), 228 –231 (2004).
Plewes  D. B., and Dean  P. B., “The influence of partial volume averaging on sphere detectability in computed tomography,” Phys. Med. Biol.. 26, (5 ), 913 –919 (1981).CrossRef
De Vos  W., , Casselman  J., and Swennen  G. R., “Cone-beam computerized tomography (CBCT) imaging of the oral and maxillofacial region: a systematic review of the literature,” Int. J. Oral Maxillofac. Surg.. 38, (6 ), 609 –625 (2009). 0901-5027 CrossRef
Brullmann  D., and Schulze  R. K., “Spatial resolution in CBCT machines for dental/maxillofacial applications-what do we know today?,” Dentomaxillofac. Radiol.. 44, (1 ), 20140204  (2015).CrossRef
Pauwels  R.  et al., “Comparison of spatial and contrast resolution for cone-beam computed tomography scanners,” Oral Surg. Oral Med. Oral Pathol. Oral Radiol.. 114, (1 ), 127 –135 (2012).CrossRef
Choi  E., and Ford  N. L., “Measuring absorbed dose for i-CAT CBCT exams in child, adolescent and adult phantoms,” Dentomaxillofac. Radiol.. 44, , 20150018  (2015).CrossRef
Goske  M. J.  et al., “The ‘image gently’ campaign: increasing CT radiation dose awareness through a national education and awareness program,” Pediatr. Radiol.. 38, (3 ), 265 –269 (2008).CrossRef

Elham Abouei received her BS degree in physics from the Sharif University of Technology, Iran, and her MS degree in physics in the field of medical physics from the University of British Columbia (UBC), Canada. She is a PhD candidate in the physics department at UBC. Her current research interests include medical image processing and optical cancer imaging.

Sierra Lee is an undergraduate student in the Doctor of Dental Medicine (DMD) program at the University of British Columbia. She received her BSc degree in mathematics from the University of British Columbia in 2010. Her current research interests include clinical applications of panoramic radiography and CBCT in dental practices.

Nancy L. Ford is an assistant professor in the Department of Oral Biological and Medical Sciences, and the director of the UBC Centre for High-Throughput Phenogenomics. She is an associate member of the Department of Physics and Astronomy at the University of British Columbia. She holds a PhD in medical biophysics from the University of Western Ontario. Her research interests include preclinical micro-CT and synchrotron imaging and clinical CBCT for medical and dental applications.

© The Authors. Published by SPIE under a Creative Commons Attribution 3.0 Unported License. Distribution or reproduction of this work in whole or in part requires full attribution of the original publication, including its DOI.

Citation

Elham Abouei ; Sierra Lee and Nancy L. Ford
"Quantitative performance characterization of image quality and radiation dose for a CS 9300 dental cone beam computed tomography machine", J. Med. Imag. 2(4), 044002 (Nov 18, 2015). ; http://dx.doi.org/10.1117/1.JMI.2.4.044002


Figures

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Fig. 1
F1 :

The Sedentex phantoms (a) IQ for measuring image quality, (b) DI for measuring dose, and (c) the IQ phantom positioned on the tripod in the Carestream 9300 CBCT machine. The lines on the exterior of the IQ phantom indicate the different layers containing test objects. The DI phantom has holes drilled through for ion chamber placement, and PMMA plugs to fill unused holes.

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Fig. 2
F2 :

(a) ROIs for noise/uniformity, (b) two perpendicular lines to measure line profiles for geometric distortion, and (c) rectangular ROIs around the artifact rods.

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Fig. 3.
F3 :

The bar pattern insert imaged in the axial plane with voxel spacings (a) 250μm, (b) 200μm, and (c) 180μm. The images for z-axis are shown in (d), (e), and (f) respectively. The bar pattern spacing ranges from 1.0to5.0LP/mm.

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Fig. 4
F4 :

(a) The ROI on the central axial slice of the point spread function (PSF) insert. (b) Surface plot of the PSF insert over the ROI. (c) An integrated one-dimensional (1-D) profile of the PSF. (d) MTF obtained from the FFT of the 1-D PSF.

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Fig. 5
F5 :

The dose measurement points for DI1 using DI phantom. Number 1 is located at interior/right side of the phantom.

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Fig. 12
F12 :

The DI1 measured for different FOVs and different patient settings (child, small, average, and large adult).

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Fig. 11
F11 :

The average of two dose readings at each point along the measuring diameter for average protocols is plotted. Points 1–5 were placed anterior to posterior uniformly.

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Fig. 10
F10 :

Axial dose distribution for different FOVs. The dose distribution was obtained just for average adult and child settings. The red line represented the measuring diameter for DI1. The bottom and left side of the dose distribution correspond to the anterior and right side of the patient. The scale bar shows the distribution of dose as a percentage of maximum dose in each image.

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Fig. 9
F9 :

The MTF graphs for the child setting for all six FOVs.

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Fig. 8
F8 :

The CNR values are plotted for the different materials in the phantom for each FOV: (a) 17×11cm2, (b) 17×6cm2, (c) 10×10cm2, (d) 10×5cm2, (e) 8×8cm2, and (f) 5×5cm2. Each graph shows four curves, which correspond to child (blue), small adult (red), average adult (green), and large adult (purple).

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Fig. 7
F7 :

The uniformity graphs including the noise in the image, which is not representing the actual noise in the image since it was smoothed for illustration purposes. (a) Uniformity profile at center of image representing symmetrical uniformity cupping at middle as an example for 17×11 (shown) and 17×6cm2 FOVs. (b) Uniformity profile at center of image is showing asymmetrical cupping uniformity at middle of image for 5×5, 8×8, 10×10, and 10×5cm2 (shown) FOVs.

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Fig. 6
F6 :

Noise values for all FOVs and patient settings on CS 9300 machine.

Tables

Table Grahic Jump Location
Table 1Factory installed protocols on the CS 9300 CBCT machine. Each patient setting was preprogrammed by the manufacturer, varying the kVp, mA, and reconstructed voxel size for each patient size. These are the settings that are used clinically.
Table Grahic Jump Location
Table 2Noise, uniformity, geometric distortion, and AAV obtained for different protocols on CS 9300 CBCT.
Table Grahic Jump Location
Table 6Interobserver variability.
Table Grahic Jump Location
Table 5Reproducibility and intraobserver variability of measurements. For interscan variability, three images were obtained and compared for each FOV. For intraobserver variability, the same image was assessed three times by a single observer.
Table Grahic Jump Location
Table 4Spatial resolution obtained from the full-width at half-maximum (FWHM) of the point spread function (PSF), the limiting resolution calculated using Eq. (5) from 10% MTF and the bar pattern insert are reported for different protocols on CS 9300 CBCT.
Table Grahic Jump Location
Table 3Mean gray values and standard deviations for the different materials in the pixel intensity insert are reported for different protocols on CS 9300 CBCT.

References

Horner  K., , Jacobs  R., and Schulze  R., “Dental CBCT equipment and performance issues,” Radiat. Prot. Dosim.. 153, (2 ), 212 –218 (2013).CrossRef
Liang  X.  et al., “A comparative evaluation of cone beam computed tomography (CBCT) and multi-slice CT (MSCT) Part I. On subjective image quality,” Eur. J. Radiol.. 75, (2 ), 265 –269 (2010).CrossRef
Loubele  M.  et al., “Comparative study of image quality for MSCT and CBCT scanners for dentomaxillofacial radiology applications,” Radiat. Prot. Dosim.. 129, (1–3 ), 222 –226 (2008).CrossRef
Loubele  M.  et al., “Image quality vs radiation dose of four cone beam computed tomography scanners,” Dentomaxillofac. Radiol.. 37, (6 ), 309 –318 (2008).CrossRef
Suomalainen  A.  et al., “Dosimetry and image quality of four dental cone beam computed tomography scanners compared with multislice computed tomography scanners,” Dentomaxillofac. Radiol.. 38, (6 ), 367 –378 (2009).CrossRef
Dillenseger  J. P.  et al., “MSCT versus CBCT: evaluation of high-resolution acquisition modes for dento-maxillary and skull-base imaging,” Eur. Radiol.. 25, (2 ), 505 –515 (2015).CrossRef
Du  L. Y.  et al., “A quality assurance phantom for the performance evaluation of volumetric micro-CT systems,” Phys. Med. Biol.. 52, (23 ), 7087 –7108 (2007).CrossRef
Steiding  C., , Kolditz  D., and Kalender  W. A., “A quality assurance framework for the fully automated and objective evaluation of image quality in cone-beam computed tomography,” Med. Phys.. 41, (3 ), 031901  (2014).CrossRef
Pauwels  R.  et al., “Development and applicability of a quality control phantom for dental cone-beam CT,” J. Appl. Clin. Med. Phys.. 12, (4 ), 3478  (2011).CrossRef
Choi  J. W.  et al., “Relationship between physical factors and subjective image quality of cone-beam computed tomography images according to diagnostic task,” Oral Surg. Oral Med. Oral Pathol. Oral Radiol.. 119, (3 ), 357 –365 (2015).CrossRef
Torgersen  G. R.  et al., “A phantom for simplified image quality control of dental cone beam computed tomography units,” Oral Surg. Oral Med. Oral Pathol. Oral Radiol.. 118, (5 ), 603 –611 (2014).CrossRef
Gayou  O., “Influence of acquisition parameters on MV-CBCT image quality,” J. Appl. Clin. Med. Phys.. 13, (1 ), 3638  (2012).CrossRef
Pauwels  R.  et al., “Quantification of metal artifacts on cone beam computed tomography images,” Clin. Oral Implants Res.. 24, (Suppl. A100 ), 94 –99 (2013).CrossRef
Jaffray  D. A., and Siewerdsen  J. H., “Cone-beam computed tomography with a flat-panel imager: initial performance characterization,” Med. Phys.. 27, (6 ), 1311 –1323 (2000).CrossRef
Bamba  J.  et al., “Image quality assessment of three cone beam CT machines using the SEDENTEXCT CT phantom,” Dentomaxillofac. Radiol.. 42, (8 ), 20120445  (2013).CrossRef
Sedentex Project, “Cone beam CT for dental and maxillofacial radiology,”  European Commission  (2012).
Bryant  J. A., , Drage  N. A., and Richmond  S., “Study of the scan uniformity from an i-CAT cone beam computed tomography dental imaging system,” Dentomaxillofac. Radiol.. 37, (7 ), 365 –374 (2008).CrossRef
Kobayashi  K.  et al., “Accuracy in measurement of distance using limited cone-beam computerized tomography,” Int. J. Oral Maxillofac. Implants. 19, (2 ), 228 –231 (2004).
Plewes  D. B., and Dean  P. B., “The influence of partial volume averaging on sphere detectability in computed tomography,” Phys. Med. Biol.. 26, (5 ), 913 –919 (1981).CrossRef
De Vos  W., , Casselman  J., and Swennen  G. R., “Cone-beam computerized tomography (CBCT) imaging of the oral and maxillofacial region: a systematic review of the literature,” Int. J. Oral Maxillofac. Surg.. 38, (6 ), 609 –625 (2009). 0901-5027 CrossRef
Brullmann  D., and Schulze  R. K., “Spatial resolution in CBCT machines for dental/maxillofacial applications-what do we know today?,” Dentomaxillofac. Radiol.. 44, (1 ), 20140204  (2015).CrossRef
Pauwels  R.  et al., “Comparison of spatial and contrast resolution for cone-beam computed tomography scanners,” Oral Surg. Oral Med. Oral Pathol. Oral Radiol.. 114, (1 ), 127 –135 (2012).CrossRef
Choi  E., and Ford  N. L., “Measuring absorbed dose for i-CAT CBCT exams in child, adolescent and adult phantoms,” Dentomaxillofac. Radiol.. 44, , 20150018  (2015).CrossRef
Goske  M. J.  et al., “The ‘image gently’ campaign: increasing CT radiation dose awareness through a national education and awareness program,” Pediatr. Radiol.. 38, (3 ), 265 –269 (2008).CrossRef

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