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The sensitivity reduction or ghosting mechanism of x-ray photoconductor is studied based on Monte Carlo simulation techniques. We have calculated the sensitivity reduction for different detector operating conditions (applied electric field, x-ray spectrum and photoconductor thickness) and for different levels of carrier trapping. We have analyzed the effect of photoconductor biasing (positive or negative) on ghosting. The following effects are taken into account in modeling the ghosting phenomena: (i) recombination between trapped and oppositely charged drifting carriers, (ii) trap filling, (iii) nonuniform electric field, (iv) detrapping of trapped holes, and (v) x-ray induced trap generation. Our calculation shows that not only the recombination between trapped and oppositely charged drifting carriers but the x-ray induced trap generation is also responsible for ghosting in photoconductor based x-ray image detectors. Moreover not all the trapped carriers take part in recombination; rather only a fraction of the trapped carriers are involved in recombination. Electric field also plays an important role in ghosting calculations via the electron hole pair generation mechanism. Trap filling has also non trivial effects on ghosting. The simulation results show that the amount of ghosting strongly depends on the applied electric field. Ghosting increases with decreasing applied electric field and vice versa. It is observed that ghosting is higher at high carrier trapping level than at low trapping level. Again ghosting is more pronounced in chest radiographic detector than mammographic detector. In chest radiographic detector, carrier trapping is high due to greater thickness hence recombination and electric field effects are prominent in chest radiographic detector. Biasing dependent ghosting depends on the carrier mobility lifetime product. For positively biased detectors, ghosting is less if the mobility lifetime product of hole is higher than that of electron and vice versa for negatively biased detectors. It also appears that the use of only recombination to calculate ghosting, as believed the primary source of ghosting in some literatures, will lead to significant error in the calculation of ghosting.

The sensitivity reduction or ghosting mechanism of x-ray photoconductor is studied based on Monte Carlo simulation techniques. We have calculated the sensitivity reduction for different detector operating conditions (applied electric field, x-ray spectrum and photoconductor thickness) and for different levels of carrier trapping. We have analyzed the effect of photoconductor biasing (positive or negative) on ghosting. The following effects are taken into account in modeling the ghosting phenomena: (i) recombination between trapped and oppositely charged drifting carriers, (ii) trap filling, (iii) nonuniform electric field, (iv) detrapping of trapped holes, and (v) x-ray induced trap generation. Our calculation shows that not only the recombination between trapped and oppositely charged drifting carriers but the x-ray induced trap generation is also responsible for ghosting in photoconductor based x-ray image detectors. Moreover not all the trapped carriers take part in recombination; rather only a fraction of the trapped carriers are involved in recombination. Electric field also plays an important role in ghosting calculations via the electron hole pair generation mechanism. Trap filling has also non trivial effects on ghosting. The simulation results show that the amount of ghosting strongly depends on the applied electric field. Ghosting increases with decreasing applied electric field and vice versa. It is observed that ghosting is higher at high carrier trapping level than at low trapping level. Again ghosting is more pronounced in chest radiographic detector than mammographic detector. In chest radiographic detector, carrier trapping is high due to greater thickness hence recombination and electric field effects are prominent in chest radiographic detector. Biasing dependent ghosting depends on the carrier mobility lifetime product. For positively biased detectors, ghosting is less if the mobility lifetime product of hole is higher than that of electron and vice versa for negatively biased detectors. It also appears that the use of only recombination to calculate ghosting, as believed the primary source of ghosting in some literatures, will lead to significant error in the calculation of ghosting.

Energy calibration of CdTe detectors is usually done using known reference sources disregarding the exact amount of charge that is collected in the pixels. However, to compare detector and detector model the quantity of charge collected is needed. We characterize the charge collection in a CdTe detector comparing test pulses, measured data and an improved TCAD simulation model [1]. The 1 mm thick detector is bump-bonded to a TIMEPIX chip and operating in Time-over-Threshold (ToT) mode. The resistivity in the simulation was adjusted to match the detector properties setting a deep intrinsic donor level [2]. This way it is possible to adjust properties like trap concentration, electron/hole lifetime and mobility in the simulation characterizing the detector close to measured data cite [3].

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For all medical imaging systems using X-rays or γ-rays, radiation detector development in general and scintillator development in particular are in full progress. There is a strong interest in the introduction of new dense, high-atomic-number inorganic scintillation crystals with a high light yield and a fast response, especially for PET and SPECT. Powder scintillators are of interest for projection X-ray imaging. For PET, research is focused on CeP3+P doped scintillators, employing the 5d → 4f transitions. A high light yield is expected in the visible region. The time response in PET/CT applications will be in the 25–100 ns range. Improved energy resolution will also be a point of interest. For CT, time response requirements are at the microsecond level for decay time and the afterglow should be well below 10P−4Ps. For X-ray screens light spreading should be kept under control, e.g. by denser material like LSO:Ce, or columnar phosphors (CsI:TI) and by shorter luminescence emission wavelength which shows higher light attenuation of laterally directed photons. In this study we examine, both in powder and in crystal form, the detection efficiency of LuB2BSiOB5B:Ce, the absolute luminescence efficiency, the X-ray to luminescence efficiency, the spectral compatibility and the effective efficiency using various optical detectors. All these measurements were conducted in the X-ray energy range from 22 to 140 kVp used in medical X-ray imaging. In conclusion the X-ray quantum detection efficiency and the X-ray energy absorption efficiency of a LSO:Ce powder scintillator screen of 25 mg/cmP2 Pcoating thickness were found higher than currently employed materials (e.g. GdB2BOB2BS: Tb and CsI:Tl) for detection of X-rays used in mammographic applications. The absolute luminescence efficiency of this screen maintains high values, within the mammographic energy range and the intrinsic conversion efficiency was found close to that of CsI:Tl but lower than that of GdB2BOB2BS:Tb. In ragiographic energy range the screen of 172.5 mg/cmP2P exchibit the higher values of ALE and XLE. The emission spectrum of LSO:Ce screens showed excellent spectral compatibility with currently used digital detectors and taking also into account its very fast response it could be considered for applications in digital X-ray imaging systems. The LSO:Ce scintillator crystal shows higher absolute luminescence efficiency values (17,86 at 140kVp) than the corresponding of BGO crystal (3,40 at 140 kVp). LSO:Ce X-ray luminescence efficiency was found higher than the corresponding of BGO crystal in the whole range of energies used in our study. The higher value of DOG, 2430 gain units, showed at 140 kVp X-ray tube voltage for the LSO:Ce scintillator when the corresponding value at the same energy of the BGO is 1670 units. In the mammographic energy range the difference between the above measured values was smaller than the ones obtained in the radiographic energy region. This lead us to the assumption that LSO:Ce crystal can be efficiently used for X-ray energy imaging (under 100 kVp) as those used in CT applications. The intrinsic conversion efficiency was estimated to be significantly higher for LSO:Ce, which in addition is higher than more of the currently employed scintillators. The light emission spectrum of the LSO:Ce scintillator, peaking at about 420 nm, was found compatible to many currently employed optical photon detectors. Its very short scintillation decay time and its high detection efficiency, both in terms of QDE and EAE, they can be crucial for the applications of this scintillator in modern fast image producing X-ray computed tomography systems, especially those employed in combined PET/CT devices. 12/−−⋅⋅smRmWμ12/−−⋅⋅smRmWμ The comparison of the ALE and the XLE of the LSO:Ce single crystal scintillator with that of the efficient powder LSO:Ce scintillator shows that the LSO:Ce screens can be used: i) in modern scinti-mammography/ X-ray mammography systems in which one common fast scintillator in powder form may satisfy the requirements of both modalities and the strict requirements in spatial resolution and ii) in applications where single crystals have to be replaced by powder or ceramic scintillators in order to improve spatial resolution (eg. in ring type SPECT detectors and in combined SPECT/CT detectors). In addition, this comparison may be of interest since powder scintillators are of lower cost than the corresponding single crystals. / -

Luminóforos inorgânicos contendo Terras Raras (TR) apresentam um papel importante como detectores de radiação ionizante, aplicados em diagnósticos médicos por imagem, como radiologia e tomografia. A função dos luminóforos é transformar os fótons da radiação de alta energia absorvidos (raios X ou ?) em fótons de luz visível, promovendo melhor qualidade de imagem e, conseqüentemente menor tempo de exposição do paciente à radiação. Os luminóforos de TR consistem de uma matriz hospedeira onde estão presentes íons de TR como Lu, La, Y ou Gd e de um íon ativador (que emite luz na região visível do espectro) como Eu3+, Tb3+, Tm3+ ou Ce3+, por exemplo. Luminóforos contendo íons Ce3+ como ativador são alvo de várias pesquisas relacionadas com detecção de radiação ionizante, devido às rápidas transições 5 d ? 4 f (tempo de resposta de ~ 10 a 100 ns) e emissão de luz na região do azul ou verde, requisitos esperados para um eficiente luminóforo para tal aplicação. Este trabalho apresenta a preparação de luminóforos de TR, dopados com Ce3+ ou Tm3+, na forma de pó, por diferentes métodos de síntese, como os métodos de combustão e Pechini e também por processo sol-gel. Aluminatos de TR (Lu3Al5O12 e Y3Al5O12) dopados com cério ou túlio foram obtidos pela reação de combustão entre precursores nitrato com uréia ou glicina sob aquecimento, ou pela síntese de polímeros de ácido cítrico com etilenoglicol contendo íons TR e alumínio (método Pechini). Em ambos os métodos os compostos foram obtidos por calcinação a temperaturas baixas quando comparadas às dos métodos convencionais. Silicatos de TR (Gd2SiO5, Lu2SiO5 e Y2SiO5) dopados com cério ou túlio foram preparados pelo método sol-gel convencional, por reação entre tetraetóxisilano (TEOS), etanol, água e nitratos metálicos, sob catálise básica, e por um método sol-gel modificado utilizando um polímero precursor. Neste último procedimento, TEOS, etanol e água reagiram juntamente com um sal orgânico de TR, álcool polivinílico (PVA) e uréia como combustível, produzindo um gel. Posterior calcinação levou à formação do silicato. A caracterização dos compostos foi realizada por análises de difratometria de raios X pelo método do pó (DRX), microscopia de eletrônica de varredura (MEV) ou de transmissão (MET), EDX, excitação e emissão no UV-Vis e tempo de vida de luminescência. Para os aluminatos dopados com cério foram ainda realizados espectros de emissão sob excitação por raios X. Os métodos de síntese utilizados se mostraram eficientes para obtenção de luminóforos na forma de pó nanométrico, com exceção do método sol-gel modificado, pois para algumas amostras observou-se a formação de mistura de fases. Os compostos dopados com cério apresentaram excitação e emissão características desse íon na região do verde ou azul do espectro visível, dependendo da matriz, com tempos de vida menores que 100 ns. Já aqueles dopados com túlio apresentaram emissão característica do íon, na região do azul, porém com tempos de vida da ordem de microssegundos. / Rare Earth (RE) inorganic phosphors play an important role as ionizing radiation detectors when applied to medical imaging techniques like radiology and tomography. These phosphors is to convert the high energy radiation absorbed photons (X or ?-rays) into visible photons, leading to better quality images and reducing the time the patient is exposed to radiation. RE phosphors consist of a host lattice where RE ions such as Lu, La, Y, or Gd are present, as well as activator ions (which emit light in the visible range of the spectrum) such as Eu3+, Tb3+, Tm3+, or Ce3+. Cerium-doped phosphors have been the target of several researches related with ionizing radiation detection due to their 5d - 4 f fast transitions (decay time in the ~ 10 to 100 ns range) and due to the fact that they emit light in the blue or green region of the spectrum, which is required for to the efficient phosphors to be applied in the detection of X or ?-rays. This work presents the synthesis of RE phosphor powders doped with Ce3+ or Tm3+, through different synthetic methods: combustion, Pechini, and sol-gel. RE aluminates (Lu3Al5O12 and Y3Al5O12) doped with Ce or Tm were prepared by combustion reaction between nitrate precursors and urea or glycine under heating. They were also obtained via the synthesis of polymers using citric acid, ethileneglycol, RE3+ and Al3+ ions (Pechini method). In both cases, the compounds were obtained by calcination at lower temperatures than those used inconventional methods. RE silicates (Gd2SiO5, Lu2SiO5 e Y2SiO5) doped with Ce or Tm were synthesized by the conventional sol-gel method using tetraethoxisylane (TEOS), ethanol and water, under basic catalysis, and also by a modified sol-gel route that uses a polymeric precursor. In the latter one, TEOS, ethanol and water were reacted with an organic RE salt, polyvinyl alcohol (PVA), and urea was used as fuel, thus yielding a gel. After calcination, we observed silicate formation. Characterization of the compounds was performed by X-ray diffractometry (XRD ? powder method), scanning or transmission electron microscopy (SEM or TEM), energy dispersive X-ray (EDX), luminescence spectroscopy in the UV-Vis range and lifetime analyses. For the cerium doped aluminates, emission spectra under X-ray excitation were also obtained. The synthetic methods used here showed to be efficient for the preparation of nanometric phosphor powders except for the modified sol-gel route, because in this case formation of a mixture of phases was observed for some samples. The Ce-doped compounds exhibited excitation and emission features of this ion in either the green or blue region of the visible spectrum, depending on the matrix, with lifetime values lower than 100 ns. However, the Tm-doped compounds displayed the blue emission typical of Tm ions, but the lifetime values were in the range of microseconds.

Contrast-enhanced mammography (CEM) relies on visualizing the growth of new blood vessels (i.e. tumor angiogenesis) to provide sufficient materials for cell proliferation during the development of cancer. Since cancers will accumulate an injected contrast agent more than other tissues, it is possible to use one of several methods to enhance the area of lesions in the x-ray image and remove the contrast of normal tissue. Large area flat panel detectors may be used for CEM wherein the subtraction of two acquired images is used to create the resulting enhanced image. There exist several methods to acquire the images to be subtracted, which include temporal subtraction (pre- and post-contrast images) and dual-energy subtraction (low- and high-energy images), however these methods suffer from artifacts due to patient motion between image acquisitions. In this research the use of a multilayer flat panel detector is examined for CEM that is designed to acquire both (low- and high-energy) images simultaneously, thus avoiding motion artifacts in the resulting subtracted image. For comparison, a dual-energy technique prone to motion artifacts that uses a single-layer detector is also investigated. Both detectors are evaluated and optimized using amorphous selenium as the x-ray to charge conversion material, however the theoretical analysis could be extended to other conversion materials. Experimental results of single pixel prototypes of both multilayer and single-layer detectors are also discussed and compared to theoretical results. For a more comprehensive analysis, the motion artifacts present in dual-exposure techniques are modeled and the performance degradation due to motion artifacts is estimated. The effects of noise reduction techniques are also evaluated to determine potential image quality improvements in CEM images.

Contrast-enhanced mammography (CEM) relies on visualizing the growth of new blood vessels (i.e. tumor angiogenesis) to provide sufficient materials for cell proliferation during the development of cancer. Since cancers will accumulate an injected contrast agent more than other tissues, it is possible to use one of several methods to enhance the area of lesions in the x-ray image and remove the contrast of normal tissue. Large area flat panel detectors may be used for CEM wherein the subtraction of two acquired images is used to create the resulting enhanced image. There exist several methods to acquire the images to be subtracted, which include temporal subtraction (pre- and post-contrast images) and dual-energy subtraction (low- and high-energy images), however these methods suffer from artifacts due to patient motion between image acquisitions. In this research the use of a multilayer flat panel detector is examined for CEM that is designed to acquire both (low- and high-energy) images simultaneously, thus avoiding motion artifacts in the resulting subtracted image. For comparison, a dual-energy technique prone to motion artifacts that uses a single-layer detector is also investigated. Both detectors are evaluated and optimized using amorphous selenium as the x-ray to charge conversion material, however the theoretical analysis could be extended to other conversion materials. Experimental results of single pixel prototypes of both multilayer and single-layer detectors are also discussed and compared to theoretical results. For a more comprehensive analysis, the motion artifacts present in dual-exposure techniques are modeled and the performance degradation due to motion artifacts is estimated. The effects of noise reduction techniques are also evaluated to determine potential image quality improvements in CEM images.

An inspection system was required in order to eliminate the difficulties which appear during the inspection of the vehicles according to specific criteria at Turkish Custom Border in a short time and effectively. In this thesis, we performed experiments on such a system to obtain the overall performance of its inspection quality. We firstly give with reasons, why the source of beam is selected as X-ray source. The subsystems of the main system are the accelerator subsystem and detector subsystem. Their structures and working principles are studied in detail by comparing them with their alternatives. Series of experiments are carried out to verify the general performance of system in terms of radiation security and quality of images produced by the system. These experiments were classified as general scan experiment, inspection performance experiment, image quality indicator experiment, radiation safety experiment and general performance experiment. The container inspection system studied and experimented in this thesis is now used effectively in Turkish Customs Boarder, Edirne Kapikule and Edirne ipsala.