Abstract
This is the first part of a two-part study in benchmarking the performance of fixed digital radiographic general X-ray systems. This paper concentrates on reporting findings related to quantitative analysis techniques used to establish comparative image quality metrics. A systematic technical comparison of the evaluated systems is presented in part two of this study. A novel quantitative image quality analysis method is presented with technical considerations addressed for peer review. The novel method was applied to seven general radiographic systems with four different makes of radiographic image receptor (12 image receptors in total). For the System Modulation Transfer Function (sMTF), the use of grid was found to reduce veiling glare and decrease roll-off. The major contributor in sMTF degradation was found to be focal spot blurring. For the System Normalised Noise Power Spectrum (sNNPS), it was found that all systems examined had similar sNNPS responses. A mathematical model is presented to explain how the use of stationary grid may cause a difference between horizontal and vertical sNNPS responses.
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References
International Electrotechnical Commission (2015) Medical electrical equipment—characteristics of digital X-ray imaging devices—Part 1–1: determination of the detective quantum efficiency—detectors used in radiographic imaging IEC 62220-1-1. IEC, Geneva
Samei E, Ranger NT, Dobbins JT III, Chen Y (2006) Intercomparison of methods for image quality characterization. I. Modulation transfer function. Med Phys 33(5):1454–1465. doi:10.1118/1.2188816
Dobbins JT III, Samei E, Ranger NT, Chen Y (2006) Intercomparison of methods for image quality characterization. II. Noise power spectrum. Med Phys 33(5):1466–1475. doi:10.1118/1.2188819
Ranger NT, Samei E, Dobbins JT III, Ravin CE (2007) Assessment of detective quantum efficience: intercomparison of a recently introduced international standard with prior methods. Radiology 243(3):785–795
Bertolini M, Nitrosi A, Rivetti S, Lanconelli N, Pattacini P, Ginocchi V, Iori M (2012) A comparison of digital radiography systems in terms of effective detective quantum efficiency. Med Phys 39(5):2617–2627. doi:10.1118/1.4704500
Samei E, Ranger NT, Mackenzie A, Honey ID, Dobbins JT III, Ravin CE (2008) Detector or system? extending the concept of detective quantum efficiency to characterize the performance of digital radiographic imaging systems. Radiology 249:926–937
Ranger NT, Mackenzie A, Honey ID, Dobbins JT III, Ravin CE, Samei E (2009) Extension of DQE to include scatter, grid, magnification and focal spot blur: a new experimental technique and metric. Proc SPIE 7258:7258A-1–7258A-12. doi:10.1117/12.813779
Donini B, Rivetti S, Lanconelli N, Bertolini M (2014) Free software for performing physical analysis of systems for digital radiography and mammography. Med Phys 41(5):051903-1–051903-10. doi:10.1118/1.4870955
Siemens (2011) Fluorospot compact operator manual imaging system for Ysio System Version VC10 or Higher. Siemens AG Healthcare Secto, Erlangen
Siemens (2009) Ysio as individual as your routine datasheet. Siemens AG Healthcare Sector, Erlangen
Electric General (2005) Definium 8000 System Schematics and Drawings, Revision 5. General Electric Company, Wisconsin
Carestream (2007) Kodak DirectView DR 9500 System Brochure. Carestream Health Inc, Rochester
Carestream (2008) Kodak DirectView DR 9500 system hardware guide. Carestream Health Inc, Rochester
Gallet J The concept of exposure index for Carestream DirectView Systems. Technical Brief Series. Carestream Health Inc, Rochester
Siewerdsen JH, Waese AM, Moseley DJ, Richard S, Jaffray DA (2004) Spektr: a computational tool for X-ray spectral analysis and imaging system optimization. Med Phys 31(11):3057–3067. doi:10.1118/1.1758350
Samei E, Ranger NT, Mackenzie A, Honey ID, Dobbins JT III, Ravin CE (2009) Effective DQE (eDQE) and speed of digital radiographic systems: an experimental methodology. Med Phys 36(8):3806–3817. doi:10.1118/1.3171690
Institute of Physics and Engineering in Medicine (2010) Measurement of the performance characteristics of diagnostic X-ray systems: digital Imaging systems IPEM Report 32 Part VII. IPEM, New York
Samei E (2003) Performance of digital radiographic detectors: quantification and assessment methods. RSNA Categorical Course in Diagnostic Physics, pp 37–47
Lee KL, Bernardo M, Ireland TA (2016) Benchmarking the performance of fixed-image receptor digital radiography systems. Part 2: system performance metric. Australas Phys Eng Sci Med. doi:10.1007/s13246-016-0439-9
Dobbins JT III (2000) Image Quality Metric for Digital Systems. In: van Metter RL, Beutel J, Kundel H (eds) Handbook of Medical Imaging, vol 1., Physics and PsychophysicsSPIE Press, Washington, pp 161–222
International Electrotechnical Commission (2008) Medical electrical equipment—exposure index of digital X-ray imaging systems—Part 1: definitions and requirements for general radiography IEC 62494-1. IEC, Geneva
Acknowledgments
We would like to thank Biomedical Technology Services Mater Workshop in manufacturing the tungsten edge phantom. We would also like to express our gratitude to Leah Biffin (Sunshine Hospital, St Albans, Victoria) in allowing us to use the GE equipment and assisting us in collecting the data.
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Appendix: stationary grid noise
Appendix: stationary grid noise
Using the definition of NPS [20], the NNPS is given by
where C is a normalising constant, I(x,y) is the image. Assume
where G(x,y) is the radiation perturbation under the grid and S(x,y) is the image without perturbation.
Orthogonal case
If the Fourier line integral, say in the x direction, is orthogonal to the perturbation, then this perturbation can be modelled as: For \(- \frac{T}{4} \le x \le \frac{3T}{4}\)
where P is the perturbation amplitude, T = 1/f0 and f0 is the grid frequency. Substituting (2) into (1) and re-arranging gives
Denoting N′(u) as the 1D noise spectrum and \(G_{n}^{{\prime }}\) as the complex Fourier coefficients of G(x), then (4) becomes
where δ(y) is the Dirac delta function and
Since G(x,y) is real, only the positive side of the spectrum \(G_{n}^{'}\) is needed. The subtraction of G′(0) removes the zero frequency component in the spectrum of \(G_{n}^{{\prime }}\). Hence the resultant noise spectrum is the sum of the original noise spectrum and the fundamental and second harmonic frequency components of \(G_{n}^{{\prime }}\) as higher frequency components are negligible.
Parallel case
If the Fourier line integral, say in the y direction, is parallel to the perturbation and is over the non-perturbed area, then (1) applies. If the line integral is over the perturbation, then this perturbation can be modelled as
where P is the perturbation amplitude. Since \(G\left( y \right) = \bar{G}(y)\), (4) reduces to (1). Hence when the line integral direction is parallel to the grid lines, there is no grid aliasing peaks in the NNPS.
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Lee, K.L., Ireland, T.A. & Bernardo, M. Benchmarking the performance of fixed-image receptor digital radiographic systems part 1: a novel method for image quality analysis. Australas Phys Eng Sci Med 39, 453–462 (2016). https://doi.org/10.1007/s13246-016-0440-3
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DOI: https://doi.org/10.1007/s13246-016-0440-3