Nuclear Sciences

  

http://opn.to/a/jWrMM

The association of dosimetric quantities from computed tomography with operational factors: basis for optimization strategies

Asociación de magnitudes dosimétricas de tomografía computarizada con factores operacionales: bases para estrategias de optimización


Abstract

Clinical Computed Tomography (CT) imaging is supported by a patient - technology - observers system. Such system involves dosimetric quantities associated with image quality descriptors, where operational factors are predictors. Knowledge of quantitative association between CT dosimetric and image quality quantities with systemic factors, provides the basis to devise scanner-specific optimization strategies. Kerma indexes were measured with a pencil ionization chamber free in air C a,100 and in phantom C pmma,x (x changes into c and p for center and periphery respectively). Polymethyl Methacrylate (PMMA) standard phantoms were used (diameters of 16 and 32 cm). Several operational factors of a Siemens Sensation 64 Cardiac were considered: estimated spectrums, tube potential F 8 (80 - 140 kV), tube current x time product F 1 (40 - 350 mAs) and total collimation at isocenter F 3 (2,7 - 19,2 mm). The water equivalent radius R w , an important factor for patient Size Specific Dose Estimators (SSDE), was estimated by taking into account the spectrums in each phantom. Average pixel noise was measured from Regions of Interest (ROIs) in water phantoms with radius of 2,5; 3; 6; 8 and 11,5 cm. A linear association was found between C pmma,p and C pmma,c . A dose reduction of C pmma,c = 2 mGy per tube rotation can be obtained from data analysis (head mode), with F 1 = 50 mAs, F 3 = 19,2 mm, resulting in average pixel noise of 20 Hounsfield Units (HU). Knowledge of noise association with C pmma,c provides a straightforward tool for quantitative optimization, considering a systemic approach, which includes patient - technology - observer factors.

Key words: 

optimization; dosimetry; X-ray spectra; computerized tomography; image processing.

Resumen

La tomografía computarizada (TC) clínica se basa en un sistema paciente - tecnología - observador. Dicho sistema incluye magnitudes dosimétricas asociadas a descriptores de calidad, donde los factores operacionales son predictores. Conocer la asociación cuantitativa entre magnitudes dosimétricas y de calidad de imagen con factores sistémicos, provee la base para concebir estrategias de optimización específicas por tomógrafo. Se midieron índices de kerma en aire C a,100 y en maniquí C pmma,x (x cambia a c y p para centro y periferia respectivamente) con una cámara de ionización tipo lápiz. Se utilizaron maniquíes de Polimetil Metacrilato (PMMA) con diámetros de 16 y 32 cm. Se consideraron factores operacionales de un equipo Siemens Sensation 64 Cardiac: espectros estimados, tensión del tubo F 8 (80 - 140 kV), producto corriente x tiempo de exposición F 1 (40 - 350 mAs) y colimación total en isocentro F 3 (2,7 - 19,2 mm). El radio agua-equivalente R w es un factor importante para Estimadores de Dosis Específicos del paciente (SSDE), se estimó teniendo en cuenta el espectro en cada maniquí. El ruido promedio de píxel se midió en regiones de interés (ROIs) de imágenes de maniquíes de agua con radios de 2,5; 3; 6; 8 y 11,5 cm. Se encontró una asociación lineal entre C pmma,p y C pmma,c . Se describe una reducción de dosis a C pmma,c = 2 mGy por rotación del tubo mediante el análisis de datos (modo cabeza), con F 1 = 50 mAs, F 3 = 19,2 mm, resultando en un ruido promedio de píxel de 20 Unidades Hounsfield (UH).

Palabras clave: 

optimización; dosimetría; espectros de rayos X; tomografía computarizada; tratamiento de imágenes.


The operational process of clinical CT imaging is supported by a patient - technology - observers system with specific interactions of several factors (e.g. attributes of patient, x ray spectrum and its modulation, reconstruction algorithms and image quality perception) [1], affecting dosimetric and image quality quantities. Knowledge of quantitative association between CT dosimetric and image quality quantities with systemic factors, constitutes the basis to devise scanner-specific optimization strategies. Most of CT dosimetric quantities are derived from CT air kerma index (C pmma,c at the center and C pmma,p at the perifery) [2]. The aim was to analyze the association of the air kerma index with systemic factors and pixel noise, to get insight for specific optimization strategies.

Kerma indexes (C a,100 and C pmma,x ) [2] were measured with a pencil ionization chamber (PTW-Freiburg, model TN30009-0577, 3,14 cm3), and an electrometer Unidos E (PTW-Freiburg) on both standard circular cylindrical PMMA phantoms with radius of 8 and 16 cm. A systemic approach was considered [1], regarding the following factors from a CT unit Siemens Sensation 64 Cardiac:

  1. tube current x time product F 1 (40 - 350 mAs), total collimation projected at isocenter F 3 (2,7 - 19,2 mm), slice thickness F 7 (0,15 - 1 cm), tube potential F 8 (80 and 140 kV), and

  2. the impinging spectrum Φ 0 was estimated with SPEKTR 3.0 [3] at the exit of the x ray tube, with added thickness of 0,2; 0,25 and 0,3 mmCu, considering beam qualities as RQT 8 for measurements with 80 kV and 100 kV, RQT 9 for 120 kV and RQT 10 for 140 kV [2], respectively. The attenuated spectrum Φ was computed for every phantom diameters and combinations of operational factors used for measurements. Additionally, the Φo and Φ were attenuated with specific inherent filtration, the latter computed using the MATLAB function spektrTuner[3], in order to satisfy the measured C a,100 and C pmma,c . For the estimation of attenuated spectrums, the phantom radius was considered as a layer thickness, traversed by all incident photons summed during one rotation of the x ray tube, but with fixed position of the x ray tube.

As C pmma,c and C pmma,p were measured in PMMA phantoms, and pixel noise measured in water phantoms, it is convenient to estimate the water equivalent radius R w , which is here the thickness of a water layer that produces the same exposure attenuation that the PMMA layer under the same technical conditions (tube potential, tube current, collimation, and filtration).

It is very important that the uncertainty associated with the measurements be known and small. Through this work the measurement uncertainties express the 95 % confidence limits of the results, in case of used coverage factor k = 2 will be addressed.

Average pixel noise σ was estimated from measurements with ROIs of 30 x 30 pixels in five positions (center, 12h, 3h, 6h and 9h) inside images of water phantoms with radius of 2,5; 3; 6; 8 and 11,5 cm. The same water phantoms were used in a previous work [4].

Data analysis was the departure to get insight for optimization alternatives. The association between C pmma,c and C pmma,p was verified graphically and with linear regression analysis. The association of C pmma,c with F 1 , F 3 and σ was verified with nonlinear regression analysis, with fixed values of tube potential and phantom radius.

The expanded uncertainties of C a,100 and C pmma,c were 10,8 % and 12,4 % (k=2) respectively (see details in table 1).

Table 1. 

Uncertainty budget for direct measurement of C pmma,p and C pmma,c using the ionization chamber - electrometer system (i.c.- e)

Source of uncertaintySource for evaluationTypeUncertainty (k=1) [%]
Calibration factor of ionization chamber: u calib Calibration certificateB3,7
Differences of beam qualities between SSDL1 and measurements: u kQ Calibration certificateB0,3
Direction of radiation incidence: u dir From [1] B1,0
Air pressure: u pre From [1] B0,5
Temperature and humidity: u thu From [1] B0,5
Electromagnetic compatibility: u cel From [1] B2,9
Field size/field homogeneity: u hca From [1] B1,0
Operating voltage of the system i.c.- e: u vol From [1] B1,2
Long term stability of user’s instrument: u est From [1] B1,2
Precision of Reading in air: u Mai From [1] A1,0
Precision of tube loading indication: u car From [1] B1,0
Relative combined standard uncertainty (k = 1) for C a,100 5,4
Relative expanded uncertainty (k = 2) for C a,100 10,8
Precision of chamber/phantom positioning in the center of the gantry: u pos From [1] B0,3
Uncertainty of 1 mm in phantom diameter and 0.5 mm in depth of measurement bores: u php From [1] B0,4
Uncertainty in chamber response for in phantom measurements: u phm From [1] B3,0
Relative combined standard uncertainty (k = 1) for C pmma,c 6,2
Relative expanded uncertainty (k = 2) for Cpmma,c 12,4

1 SSDL - Secondary Standard Dosimetry Laboratory.

The total fluences were derived with spectrums obtained for all observations (see sample in figure 1 a), and each R w,i was computed, corresponding to combinations of PMMA phantom radius and scanning factors F 1 , F 3 and F 8 . For PMMA layers of 8 cm and 16 cm the R w were 8,3 ± 0,21 cm and 17,4 ± 0,26 cm respectively.

The quantity C vol [2], wich takes into account the helical pitch or axial scan spacing, is linearly associated with C pmma,c . Also a linear association was found here between measured C pmma,p and C pmma,c (see figure 1b).

2075-5635-nuc-65-28-gf1.jpg

Figure 1. 

(a) Computed tungsten 80kVp spectrum: incident Φ0 (which satisfies C a,100 ), spectrum Φ that satisfies measured C pmma,c , spectrum of primary radiation Φp (Φ0 attenuated with R pmma ) and spectrum of scattered radiation Φs (Φ - Φp ). (b) Linear association of C pmma,p with C pmma,c .

A good agreement between C pmma,p and C pmma,c was found for both phantom diameters of 8 cm and 16 cm, represented by the linear regression models y@8 and y@16 respectively in figure 1b.

The figure 2 a confirms that C pmma,c has a direct linear association with F 1 and is inversely proportional to F 3 . Specifically for this example, the steeped surface for R pmma = 8 cm allows to identify, quantitatively, the operational regions with lower doses for pediatric examinations at 80 kV (e.g., less than 100 mAs and more than 10 mm of total collimation). In figure 2 b is represented the association of mean pixel noise σ with kerma at the center of a water phantom C awc with R w = 11,5 cm. The C awc was simulated using the spectrums of 80 kVp. The σ corresponds with a Reconstruction Diameter F 6 = 30 cm and kernel H30s. A minimum C awc is feasible with a resulting average pixel noise of 20 HU (F 1 = 50 mAs and F 3 = 19,2 mm).

2075-5635-nuc-65-28-gf2.jpg

Figure 2. 

(a) Surfaces of C pmma,c associated with F 1 , F 3 and both diameters of standard PMMA phantoms and (b) the average pixel noise associated to C pmma,c (represented by C awc = C pmmac , which is associated with R w ) and the Slice Thickness F7.

The spectrums matched with C a,100 and C pmma,x allow to know quantitatively the contributions of primary and scattered radiation, and to estimate water equivalent radius adaptive to size specific quantities. This provides a basis for further modeling of dosimetric quantities and departure spectrums for in silico simulations when manufacturer data are not available. Knowledge of noise association with C pmma,c provides a straightforward tool for quantitative optimization, considering a systemic approach, including a patient - technology - observer system.

ACKNOWLEDGEMENT

This work was supported by the Centro de Biofisica Medica, as part of the project “Optimization of the image quality with respect to dose for pediatric Computed Tomography” (Code I 223 SC 904-002).

 

REFERENCES

[1] MILLER-CLEMENTE RA, PÉREZ-DÍAZ M, GUEVARA MVM. AMAR: a systemic approach for patient radiation protection in CT. INIS 43(2010). Available in: http://www.irpa12.org.ar/fullpapers/FP3389.pdf‎

[2] IAEA. Dosimetry in diagnostic radiology: an international code of practice. TRS 457. Vienna: IAEA, 2007.

[3] PUNNOOSE J, XU J, SISNIEGA A, ZBIJEWSKI W, et. al. Technical Note: spektr 3.0-A computational tool for x-ray spectrum modeling and analysis. Med Phys. 2016; 43: 4711-4717.

[4] MILLER-CLEMENTE RA, PEREZ-DIAZ M, ZAMORA-MATAMOROS L, EDYVEAN S. Nonlinear model of image noise: an application on computed tomography including beam hardening and image processing algorithms. Applied Mathematics 2014; 5: 1320-1331.

 

 

 

 


This is an open-access article distributed under the terms of the Creative Commons Attribution License