|Year : 2017 | Volume
| Issue : 4 | Page : 266-272
A study to determine whether the volume-weighted computed tomography dose index gives reasonable estimates of organ doses for thai patients undergoing abdomen and pelvis computed tomography examinations
Supawitoo Sookpeng1, Colin J Martin2, Chitsanupong Butdee1
1 Department of Radiological Technology, Faculty of Allied Health Sciences, Naresuan University, Phitsanulok, Thailand
2 Department of Clinical Physics, University of Glasgow, Glasgow G12 8QQ, UK
|Date of Submission||29-Jul-2017|
|Date of Decision||13-Oct-2017|
|Date of Acceptance||13-Oct-2017|
|Date of Web Publication||5-Dec-2017|
Department of Radiological Technology, Faculty of Allied Health Sciences, Naresuan University, Phitsanulok 65000
Source of Support: None, Conflict of Interest: None
| Abstract|| |
Introduction: Values for the CTDIvol, which is displayed on scanner consoles, give doses relative to a phantom much larger than most Thai patients, and the CTDIvoldoes not take account of differences in patient size, which affect organ doses. Objective: The purpose of this study was to evaluate relationships for size specific dose estimate (SSDE) and volume weighted computed tomography (CT) dose index (CTDIvol) with patient size for CT scanners operating under automatic tube current modulation (ATCM). Methods: Retrospective data from 244 patients who had undergone abdomen and pelvis examination on GE and Siemens CT scanners were included in this study. The combination of anteroposterior (AP) and lateral dimensions at the level of the first lumbar vertebra (L1) was used to represent patient size. Image noise within the liver was measured, and values of the absorbed dose for organs covered by the primary beam such as the liver, stomach and kidney were calculated using methods described in the literature. Values of CTDIvolwere recorded and SSDE calculated according to the American Association of Physics in Medicine (AAPM) Report No.204. Linear regression models were used to evaluate the relationship between SSDE, CTDIvol, image noise and patient size. Results: SSDE is 20%-50% larger than the CTDIvol, with values for larger patients being more representative. Both the CTDIvoland image noise decreased with patient size for Siemens scanners, but the decline in SSDE was less significant. For the GE scanner, the CTDIvolwas a factor of 3-4 lower in small patients compared to larger ones, while the SSDE only decreased by a factor of two. Noise actually decreased slightly with patient size. Conclusion: Values of SSDE were similar to the doses calculated for the liver, stomach and kidney, which are covered by the primary beam, confirming that it provides a good estimate of organ-absorbed dose.
Keywords: Automatic exposure control, computed tomography dosimetry, size-specific dose estimate
|How to cite this article:|
Sookpeng S, Martin CJ, Butdee C. A study to determine whether the volume-weighted computed tomography dose index gives reasonable estimates of organ doses for thai patients undergoing abdomen and pelvis computed tomography examinations. J Med Phys 2017;42:266-72
|How to cite this URL:|
Sookpeng S, Martin CJ, Butdee C. A study to determine whether the volume-weighted computed tomography dose index gives reasonable estimates of organ doses for thai patients undergoing abdomen and pelvis computed tomography examinations. J Med Phys [serial online] 2017 [cited 2019 Apr 19];42:266-72. Available from: http://www.jmp.org.in/text.asp?2017/42/4/266/219937
| Introduction|| |
If staffs operating computed tomography (CT) scanners are aware of the level of doses delivered to patients, this can be helpful in optimizing scan protocols. Dose indices are displayed on CT scanner consoles in terms of the volume weighted CT dose index (CTDIvol) and the dose-length product that incorporates the CTDIvol. The CTDIvol is based on output measurements made in standard cylindrical polymethyl methacrylate phantoms ,, and so does not give an accurate indication of how dose varies with patient size. Therefore, the CTDIvol gives a false impression of doses to the organs and tissues of larger relative to smaller patients, because the incident X-rays are attenuated to a greater extent in overlying tissues. The American Association of Physics in Medicine (AAPM) introduced a concept termed the size-specific dose estimate (SSDE) in report No. 204. This is the CTDIvol adjusted for patient size giving a dose parameter that equates to the dose to tissues in the center of the scanned region for patients of any size. The SSDE is calculated by multiplying CTDIvol values from the scan by coefficients relating to patient size. The coefficients take account of the greater attenuation in the tissues of larger patients, so increase as patient size decreases.
Current CT scanners incorporate automatic tube current modulation (ATCM) systems to aid in maintaining consistent image quality throughout scans by optimizing the radiation level for tissue attenuation and patients of varying size. In principle, the tube current is adjusted automatically to that appropriate for the X-ray attenuation of the patient cross-section being scanned. The ATCM systems for different CT manufacturers vary in their modes of operation. Those used at present can be divided into two groups, based on different image quality criteria.,, The tube current is adjusted to achieve the reference image quality throughout each scan. The ATCM systems of Toshiba and GE scanners aim to maintain a constant image noise level selected by the operator through varying the tube current within minimum and maximum levels also set by the operator. In contrast, the ATCM systems of Philips and Siemens scanners use an image quality level selected by the operator that is linked to a reference mAs for parts of the patient that have a similar attenuation to that of a reference patient stored by the scanner. This system varies tube current with patient attenuation according to a predetermined relationship and accepts higher noise levels for more attenuating parts of the patient.
The objectives of this study were to investigate the relationships between SSDE, CTDIvol, and patient size for two CT scanners with different types of ATCM system, and demonstrate how variations in the displayed dosimetry parameters differ from the actual changes in magnitudes of patient organ doses. This is particularly significant for Asian populations since the stature of a typical adult is substantially different from that of an adult from a western population on which the dimensions of the standard dosimetry phantom is based. Values of the SSDE have been compared with mean absorbed doses for organs fully covered by the primary beam, derived using equations proposed by Turner et al. differences in the manner in which noise levels vary with a patient size between the two scanners have also been studied.
| Materials and Methods|| |
Ethical approval was gained from Naresuan University committee (IRB235/59). Two 128 slice CT scanners equipped with ATCM systems were used in the study, a Siemens Definition AS + software version Syngo CT 2012B (Siemens Healthcare) and a GE Optima 660 software version cj2_5 m3sp4.5 (GE Healthcare). Details of the abdomen and pelvis protocols used for all examinations are shown in [Table 1]. The start and stop positions of the scans were the carina and symphysis pubis, respectively. An Adaptive Statistical Iterative Reconstruction (ASIR) level of 20% was used for the GE scanner but only filtered back projection was available on the Siemens scanner. From a previous study on transferring of CT protocols for CT ATCM system, the protocols for both scanners were matched for noise in patients who had cross-sectional areas that approximated to that of the trunk for a large adult Thai patient. The minimum mAs for the GE scanner was set at 80 mAs to restrict modulation that can affect image quality for small patients, and this resulted in the mAs remaining constant throughout scans for some patients, so data for these individuals were excluded from the study. There is no option for users to select the mAs range for the Siemens scanner, because of the mode of operation, as described above.
|Table 1: Routine abdomen and pelvis protocols for each computed tomography scanner|
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Values of CTDIvol (mGy) were recorded from the scanner displays after the scans. It has been proved that calculation of patient dose using each of CTDIvol per slice along the scan length for ATCM system is quiet similar to that using the average CTDIvol for the whole scan. Tube current time products per image for the entire scan under ATCM control were read out using an Auto-mA plugin and values of average mAs were plotted against patient size. For the Siemens scanner, the mAs was calculated using a multiplication of effective mAs and pitch factor to allow the mAs values for both CT scanners to be compared. Values of SSDE (mGy) were calculated using the AAPM TG 204 conversion factors and the scanner reported CTDIvol from the equation 1.
Where is the displayed CTDIvol (mGy) from the scan, and is a factor to convert the CTDIvol for the 32 cm diameter reference phantom to that for a patient with dimension AP + lateral (LAT) (cm) as shown in equation 2. The relationship derived from the equation is shown in [Figure 1].
|Figure 1: Plot of conversion factor between volume-weighted computed tomography dose index and size-specific dose estimate against the summation of anteroposterior and lateral dimensions used for size-specific dose estimate calculation|
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Since the sum, AP + LAT has been shown to produce less variability in SSDE calculation with respect to measurement position,,, the present study used this to represent patient size. CT images were reviewed to measure the patient anteroposterior (AP) and LAT dimensions in centimeter at the reference level of L1. The slices with the smallest and largest LAT dimensions were used to assess the range in AP + LAT dimensions for each patient which was used to evaluate the percentage uncertainty in SSDE. Where the same anatomic region was scanned multiple times, for example, pre- and post-contrast injections, the CTDIvol was only recorded for the precontrast examination.
Image noise in terms of standard deviation in pixel value was measured by placing each of five circular regions of interest of 100 mm 2 within the liver at the level of the mid-point of the liver, and the relationship between the average value of the measured noise and patient size studied. Absorbed doses (mGy) for organs lying fully within the scan volume such as the liver, stomach, and kidney were calculated using equations proposed by Turner et al. These are based on Monte Carlo simulations and use CTDIvol-to-organ-dose conversion coefficients linked to the patient perimeter distance as shown in the equation 3.
Where x is the patient perimeter and values of the coefficient A0 are 3.824, 3.780, and 3.969, and of B0 are 0.012, 0.0113, and 0.0124 for the liver, stomach and kidney, respectively. The patient circumference was calculated from the equation 4.
Where a and b are the major and minor axes (cm) of the image of the cross-section. Statistical Package for the Social Sciences version 17 was used (SPSS Inc., Chicago, IL, USA) for the project. Relationships in the form of linear regressions between SSDE (mGy), CTDIvol (mGy), organ absorbed dose (mGy), and patient size (cm) were analyzed.
| Results|| |
Data from 244 patients who had undergone CT examinations of the abdomen and pelvis protocol from the two CT scanners were included in the study (106 patients for the GE scanner and 138 for the Siemens scanner). Descriptive statistics for patient sizes, CTDIvol, and SSDE are given in [Table 2].
|Table 2: Descriptive statistics (mean±standard deviation and range) for patient size, image noise, volume weighted computed tomography dose index and size-specific dose estimate (n=244)|
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Plots of the average mAs values against patient size for both CT scanners are shown in [Figure 2]. The mAs values increased substantially with patient size (r2 = 0.725, P= 0.001) for the GE scanner, while those for the Siemens scanner increased less, the range in mAs was smaller but the data were more scattered (r2 = 0.119, P= 0.001). Plots of CTDIvol and SSDE data against patient size for both CT scanners are shown in [Figure 3] with linear regression fits and since the CTDIvol data are lower this indicates that it underestimates organ dose for almost all patients in the study. The results show a stronger dependence of the CTDIvol and SSDE on patient size for the GE scanner, with both data, fits having similar gradients of 0.53–0.55 mGy/cm, P < 0.001, although the increase in SSDE with patient size will be proportionately less. For the Siemens scanner, the gradient for the CTDIvol was 0.3 mGy/cm (P < 0.001) and that for the SSDE was 0.13 mGy/cm, (P = 0.002), showing that the change in SSDE with patient size was substantially less than indicated by the CTDIvol. Comparing doses for patients with AP + LAT measurements of 65 cm with those for a 45 cm patient, the CTDIvol values increased by factors of 3.7 and 1.6 for the GE and Siemens scanner respectively, but this gives a false impression of the actual differences in dose to the patients' organs. The ratios of the SSDE values for patients with AP + LAT measurements of 65 cm and 45 cm are 2.4 and 1.2 for the GE and Siemens scanners, respectively, showing that the actual differences in doses to the organs of patients of different size are actually much lower as shown in [Table 3].
|Figure 2: Relationships between the average mAs and patient size for (a) GE and (b) Siemens computed tomography scanners|
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|Figure 3: Variation in the size-specific dose estimate and volume-weighted computed tomography dose index with patient size for (a) GE and (b) Siemens computed tomography scanners|
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|Table 3: Comparisons of image noise, volume weighted computed tomography dose index and size-specific dose estimate for small standard and large patients from both computed tomography scanners|
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Changes in the measured noise levels with patient size for both CT scanners are shown in [Figure 4]. For the GE scanner, the SD was 12.0 ± 1.4 HU and there was a small decrease in measured noise with patient size. The SD for the Siemens scanner increased slightly with the patient size and the average value was 10.8 ± 1.7 HU. The magnitudes of the changes in SD with size were similar to or less than the overall scatter in the results. Uncertainties in the SSDE based on differences in the AP + LAT measurement made at different positions within the scan fields were ± 6.2% for both CT scanners.
|Figure 4: Variations in measured noise with patient size for (a) GE and (b) Siemens computed tomography scanners|
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Plots of the absorbed dose for organs covered in the primary beam, which are the liver, the stomach and the kidney, are shown in [Figure 5]. There were strong relationships between the organ absorbed dose and the SSDE for all organs and both CT scanners (values of r2 > 0.99). Multiplication factors to calculate absorbed dose for the liver, the stomach and the kidney from SSDE were 1.03, 0.98, and 1.03 respectively for the GE scanner and 1.03, 0.99, and 0.99, respectively, for the Siemens one. Results suggest that the SSDE reflects doses to organs that lie entirely within the primary beam to within ± 3%.
|Figure 5: Relationships between organ dose and size-specific dose estimate for (a) liver, (b) stomach, and (c) kidney for Siemens and GE computed tomography scanners|
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| Discussion|| |
Results in this study were based on the routine protocol for both CT scanners. For the GE scanner, ASIR levels from 10% to 100% can be selected, with noise reduced to a minimum in the 100% ASIR. From literature review, up to 40%, ASIR is considered a good balance between reduced noise and a natural appearance of the image. Since there were over-smoothing, due to aggressive noise reduction, of images with higher strengths of iterative reconstruction, 20% ASIR was set as a default protocol for CT body scans for this GE scanner.
Since a minimum mA of 80 mA was set, the mAs remained constant throughout scans of smaller patients. If a higher value of ASIR had been selected, there would have been no change in mA for the group of slightly larger patients at the selected Noise Index (NI) level as shown in [Table 1], and the ASIR would reduce image quantum noise with no impact on radiation dose. If the operator-selected NI is increased, the patient dose may be decreased at the expense of greater image noise. The image contrast for slim patients tends to be lower because there is a limited fat delineation of organ structures. Higher dose levels are implemented for very small patients by capping the minimum mA to limit current modulation and achieve a lower level of image noise improving image quality.
Based on a comparison of SSDE and CTDIvol for patients undergoing CT abdomen and pelvis examinations as shown in [Table 2], the CTDIvol displayed on the scanner console underestimated the doses to the organs of the majority of patients by 20%-50%, with values for smaller patients being up to 50% less than the organ doses for both CT scanners. The discrepancies occur because the size of the standard dosimetry phantom that was developed for a European-North American population is substantially larger than almost all Thai patients; in fact, only three patients in each of the groups of 120 patients were larger than the phantom. The relative CTDIvol values suggested that large patients received 3-4 times the radiation dose given to small patients on the GE scanner, but the SSDE values showed that the actual ratio between the two was only just over two as shown in [Table 3]. Values of image noise for standard size patients with AP + LAT measurements of 55 cm were similar for both CT scanners. The variation in patient organ doses for the Siemens scanner was much less, but the actual doses were higher. The average CTDIvol for the GE scanner was 33% less than that for the Siemens scanner. This was largely due to the availability of iterative reconstruction on the GE scanner since this allowed the noise levels required by the image quality reference setting to be achieved with lower mAs values. Values of CTDIvol were 2.5, 1.4, and 1.1 times higher in small, standard, and large patients for the Siemens scanner compared to those of the GE one as shown in [Table 3]. The large difference between the two scanners for small patients occurs because the Siemens image reference requires a lower noise level to be achieved and limits the reduction in tube current. The setting of a minimum tube current performs a similar function in the GE scanner. The Siemens scanner accepts a higher noise level for large patients, and here dose levels for the two scanners are similar.
The ranges of tube current, CTDIvol and SSDE values with patient size were wider for the GE scanner than the Siemens scanner [Figure 2] and [Figure 3], as the CTDIvol increased with increasing patient size to maintain a constant noise level and image noise was actually found to decrease with patient size as shown in [Figure 4]. Thus, the GE ATCM system may overestimate the mAs required to maintain a constant noise level for larger patients. A higher target noise setting (NI 12.1–13.3) is now included in the optimized clinical scanning protocols for larger patients to avoid the higher dose levels. The mAs increased less for bigger patients, and the data were more scattered for the Siemens ATCM system since it aims to achieve an image noise level similar to that for a reference-stored image and maintain a similar level of image quality for all patients. This avoids the dose levels for large patients being substantially greater while enabling full use of current modulation for patients of all sizes and results in a smaller variation of tube current with patient size as shown in [Figure 2]b and lower doses for larger patients.
The study calculated the mean absorbed doses for organs covered by the primary beam such as the liver, stomach, and kidney. The results show strong relationships (r2 > 0.99) between SSDE and calculated organ doses as illustrated in [Figure 5], the ratios of the SSDE and the organ dose were close to 1:1, confirming that the SSDE can be used to predict the organ absorbed dose. However, there are uncertainties in the calculation of the SSDE, relating to the error in the measurement of patient size. The values of SSDE could vary by ± 6% with the range in AP + LAT dimension within the middle of the scan field. The AAPM recommend measuring patient dimensions at the center of the scan region, but the accuracy achieved will depend on the diligence of the technologist or radiologist performing the measurement.
There are some limitations to the study. First, data for only adult patients were evaluated, and the majority of the patients were small in size, representing a typical population group in Thailand. Second, data were collected from only one CT scanner of each manufacturer. Finally, there might be personal bias since all AP and LAT dimension measurements were made by one observer.
| Conclusion|| |
Results of the study show that there is a strong relationship between patient size and CTDIvol for both CT scanners. However, conversion of the CTDIvol to the SSDE shows that the actual doses to the organs of the patients are 20%–50% less than the CTDIvol values and do not decline to the same extent with patient size. This occurs because the standard phantom is not representative of individuals within the Thai population. The agreement is closer for larger patients, but becomes significant for smaller ones. When doses for patients with AP + LAT measurements of 45 cm and 65 cm were compared, the ratio of CTDIvol values for the GE scanner was 3.7, whereas the ratio of the SSDE values was only 2.4, so variations in the CTDIvol give a false impression of the actual differences in doses to the patients' organs. The differences for patients scanned on the Siemens scanner were substantially smaller, and SSDE values for larger patients were <20% higher than those for small patients. Image noise from the Siemens scanner increased with the patient size, but image quality was still maintained at an acceptable level. The ratio between SSDE and absorbed dose to various organs was about 1:1 for both CT scanners under investigation demonstrating that the SSDE provides a realistic assessment of doses to tissues lying within the primary beam.
The authors would like to thank Ms. Arunrak Surarit and Mr. Kanlapaphat Temphon for their help in data collection.
Financial support and sponsorship
Conflicts of interest
There are no conflicts of interest.
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[Figure 1], [Figure 2], [Figure 3], [Figure 4], [Figure 5]
[Table 1], [Table 2], [Table 3]