KEYWORDS: Sensors, Selenium, Photon counting, Electric field sensors, Spatial resolution, Time metrology, Surgery, Spectroscopy, Spectroscopes, Single photon
In this study, we fabricated a pixelated unipolar charge sensing detector based on amorphous selenium with a 20-μm pixel pitch using standard lithography process. A pulse-height spectroscopy (PHS) setup with a very low noise front-end electronics was designed, and experiments were performed to investigate the achievable energy resolution with the unipolar detector, as well as with a conventional detector for comparison purposes. PHS measurement results are presented that demonstrate, for the first time, a measured energy resolution of 8.3 keV at 59.5 keV is for the unipolar charge sensing device in contrast to 14.5 keV at 59.5 keV for conventional a-Se devices, indicating its promise for the contrast-enhanced photon counting imaging with an unsurpassed spatial resolution.
It has been reported and discussed that electrical current can be produced when an insulating material interacts with ionizing radiation. We have found that high-resolution images can be obtained from insulating materials if this current is guided by an electric field to the pixels of a TFT array. The charge production efficiency of insulators is much smaller than that of photoconductor materials such as selenium, silicon, or other conventional semiconductors. Nevertheless, when the intensity of the ionizing radiation is sufficiently high, a charge sensitive TFT imaging array with only dielectric material can produce high MTF images with contrast resolution proportional to the intensity of the radiation. The function of the dielectric in this new detector may be similar to that of an ionization chamber. Without the semiconductor charge generating material, the dielectric imaging detector does not exhibit charge generation fatigue or charge generation saturation. Prototype detectors have been tested using diagnostic x-ray beams with energy ranging from 25 kVp to 150 kVp, and therapeutic 2.5MV, 6MV, 10MV, and 15MV photon beams (with and without an electron built-up layer), electron beams, broad area proton beams, and proton pencil beams in the energy range of 150 MeV. High spatial resolution images up to the Nyquist frequency have been demonstrated. The physics, structure, and the imaging properties as well as the potential application of this detector will be presented and discussed.
Using electric field to partition the selenium layer into a low field charge drift region and a high field avalanche gain region was first proposed in 2005(1). Engineering and fabricating such a grid structure on a TFT array have been a challenge. High dielectric strength material (up to several hundred volts/um) is required. Furthermore, it is very difficult to achieve or control a stable and uniform avalanche gain for imaging without too much excess noise from the elevated grid structure about the pixel plane. Image charge gain is non-uniform depending on the distance from the center of the avalanche well. A novel coplanar detector structure is now being tested. All image charges collected on a dielectric pixel surface will transfer to the central pixel readout electrode along a converging field. Uniform gain via a stable avalanche process can be achieved. This new structure does not require a conventional TFT platform and higher temperature fabrication process can be used. Imaging charges generated from x‐ray are first directed to a dielectric charge collection interface surface. During the sequential rolling image readout, imaging charges in each line are re-directed to an orthogonal lines of central readout electrode by a convergent field with high electric field strength at the rim of each pixel central electrode. All accumulated image charges need to pass through the end point of this converging field and therefore undergo a uniform impact ionization charge gain. This gain mechanism is similar to a proportional counter in radiation detection.
A new and novel detector structure is now being investigated to minimize the readout noise of large area
TFT arrays. A conventional TFT panel consists of orthogonal arrays of gate lines and data lines. The
parasitic capacitance from the crossover of these lines results in a sizable data line capacitance. During
image readout, the thermal noise of the charge integrator is greatly magnified by the ratio of the data line
capacitance to the feedback capacitance of the charge amplifier. The swinging of the gate voltage will
also inject charges in and out of the imaging holding pixel capacitors and contribute to the switching noise
in the readout image. By redesigning the layout of the TFT arrays and by coupling linear light source to
the bottom side of the TFT array in the same direction as the gate lines, the crossover of gate lines and
data lines can be avoided and the data line capacitance can be greatly reduced. Instead of addressing
each row of transistors by the switching of the gate control voltage, linear light source with collimators are
used to optically switch on and off the amorphous silicon transistors. The transistor switching noise from
the swinging of the gate voltages is reduced. By minimizing the data line capacitance and avoiding the
swinging of the gate control voltage, the basic TFT readout noise is minimized and lower dose x-rays
images can be obtained. This design is applicable to both Direct Conversion and
Indirect Conversion panels.
Flat panel selenium detectors (1) have been commercially available since 1998 (2). The MTF of these detectors can
approach the theoretical SINC function for the pixel size (3). Detectors can be designed with selenium thickness
suitable for absorption of the range of x-ray energy for the modality (4, 5). For higher energy x rays, the thickness
of the selenium layer can be increased without greatly degrading the spatial resolution. The non-spreading nature of
the signal allows the detector to detect very weak x-ray signal in the vicinity of strong signal. Selenium detectors
can therefore be designed to produce very high dynamic range images when needed. However, as a photo-conducting material, selenium also comes with some less than ideal properties. For example, charge trapping, long settling time for with bias electric field, and interface charge injection (6). These adverse properties must be
included in detector design for optimal performance in each application. This paper describes a novel method for
interfacial charge removal using lateral conductivity of selenium.
Direct detection of x-ray using the technology of selenium on Thin Film Transistor (TFT) has been used in a number of medical imaging and other products for almost 10 years. The spatial resolution of this Direct Conversion Technology with MTF approaches the theoretical Sinc Function remains unsurpassed. However, there are rooms for improvement in several areas that may further advance the performance. This paper is to examine some of these areas and to explore potential solutions.
KEYWORDS: Selenium, X-rays, Sensors, Signal to noise ratio, Electrodes, X-ray imaging, Interference (communication), X-ray detectors, Medical imaging, Digital mammography
Amorphous selenium direct-conversion x-ray detectors have been used successfully for full field digital mammography (FFDM) and digital radiography (DR). Such detectors characteristically exhibit high spatial resolution and conversion efficiency that is a function of the applied electric field. At an electric field of 10 volts per micron, about 50 electron volts of photon energy are required to generate an electron-hole pair in a typical amorphous selenium x-ray conversion layer. At FFDM and DR imaging x-ray energies each absorbed photon can generate only about 250 to 1000 electron-hole pairs. Each absorbed x-ray photon is only contributing 4 x 10-17 to 1.6 x 10-16 coulombs of imaging charge. On the noise side, detectors operating at room temperature have a basic thermal (kTC) noise of 300 to 600 electrons per pixel from the image charge storage capacitor. Electronic noise from the front-end charge amplifier is also amplified by one plus the ratio of the TFT data line capacitance and the feedback capacitance of the charge amplifier. Medical imaging applications must therefore employ low noise thin film transistor (TFT) arrays, low data line capacitance and low noise charge integration amplifiers to achieve high signal-to-noise ratio (SNR) and detective quantum efficiency (DQE). To achieve quantum-noise limited imaging results with the lowest practical x-ray exposure dose, it is desirable to include an additional low-noise gain stage in the x-ray conversion layer. This is particularly important for the application of dynamic imaging or for tomosynthesis where x-ray dose per frame is very limited. A new structure for an amorphous selenium detector that employs an internal biased gain grid to cause avalanche-gain within the x-ray conversion layer is being proposed. A signal charge amplification of at least 10X can be achieved without introducing excessive noise. Quantum-limited image detection should then be attainable for even very low exposures.
The presampling modulation transfer function (MTF) of a digital imaging system is commonly determined by measuring the system’s line spread function (LSF) using a narrow slit or differentiating the detector’s edge spread function (ESF) with an edge device. The slit method requires precise fabrication and alignment of a slit as well as a high radiation exposure. The edge method [3] is a complicated image processing procedure, requiring determination of the edge angle, reprojection, sub-binning, smoothing and differentiating the ESF, and spectral estimation. In this paper, a simple method is employed to evaluate the MTF using an edge device. The image processing procedures required by this method involve simply the determination of the over-sampling rate and the Fourier transform of the modified ESF. Differentiation and signal to noise ratio (SNR) improvement are jointly applied in the Fourier domain. The MTFs obtained by this simple method are compared to the theoretical MTF and the previously proposed more complicated edge method. The experimental results show that the proposed method provides a simple, accurate and convenient measurement of the presampling MTF for digital imaging systems.
Amorphous selenium direct-conversion x-ray detectors have been used successfully for full field digital mammography (FFDM) and digital radiography (DR). Such detectors characteristically exhibit high spatial resolution and conversion efficiency that is a function of the applied electric field. About 50 electron volts of photon energy are required to generate each electron-hole pair in a typical amorphous selenium x-ray conversion layer biased at 10 volts per micron. At FFDM and DR imaging x-ray energies each absorbed photon can generate only about 250 to 1000 electron-hole pairs. Medical imaging applications must therefore employ low noise thin film transistor (TFT) arrays and charge integration amplifiers to achieve high signal-to-noise ratio (SNR) and detective quantum efficiency (DQE). To assure quantum-noise limited imaging results with the lowest practical x-ray exposure dose, it is desirable to include
an additional low-noise gain stage in the x-ray conversion layer. We have proposed and studied a new structure for an amorphous selenium detector that employs an internal biased gain grid to cause avalanche-gain within the x-ray conversion layer. An amplification of at least 10X can be achieved without introducing excessive noise. Quantum-limited image detection should then be attainable for even very low exposures.
In this paper, a fast, accurate and memory-saving Tomosynthesis algorithm is presented based on the Algebraic Reconstruction Technique (ART). In this approach, a one step ART iterative reconstruction takes the place of the commonly used two step Tomosynthesis reconstruction and deblurring processes. The weight matrix required by ART is calculated offline and saved in a look-up-table since the weight matrix will not change with the object if the acquisition geometries of the projections are fixed. This look-up-table speeds up the reconstruction procedure and the memory space is greatly reduced by using a compact weight matrix. A Bessel-Kaiser function is utilized in this algorithm as the pixel basis function, which improves the quality of the reconstruction over other commonly used basis functions. Simulation results show that the presented algorithm generates fast, accurate and memory-saving reconstructions of a three-dimensional object.
Traditional Tomosynthesis requires the X-ray source to be parallel beams or cone beams constrained to the same plane above the object of interest. Commonly, the X-ray sources are placed uniformly around a circle or along a line in the same plane, which demands fixed and high-precision equipment. To eliminate the constraints on the X-ray sources and obtain fast and efficient reconstruction with adequate quality, a fast and unconstrained cone beam Tomosynthesis reconstruction method as well as the corresponding deblurring method is presented in this paper. In this method, two reference balls, whose connecting line is parallel to the detector, are placed above the detector. According to the information provided by these two balls, the X-ray source position and its relative motion are readily calculated for the reconstruction and the corresponding deblurring processes. A layer-by-layer, rather than a voxel-by-voxel, reconstruction is utilized in order to speed up the calculation. This fast and unconstrained cone beam Tomosynthesis has a large commercial value, allowing unconstrained projection acquisition and making portable and relatively cheap Tomosynthesis equipment possible.
DirectRay direct-conversion digital x-ray-imaging detectors using selenium exhibit high sensitivity and resolution to x-ray energies just below the K-fluorescence edge compared to energies just above. Detector sensitivity and self-protected dynamic range can be manipulated by modifying dielectric thickness and selenium electric field. Replacing the dielectric layer with a charge-transport layer (CTL) allows a faster cycle time, lower residual-image charge, improved signal to noise ratio, and better operating stability. The new CTL structure allows fast multi-frame imaging, enabling applications such as dual-energy subtraction, tomosynthesis, and dynamic imaging (fluoroscopy).
Direct conversion imaging panels have pixels that need to be protected from excessive voltage across the FET switch resulting from excess X-ray exposure. Protection can be achieved by placing a dielectric layer between the charge generator and the high voltage bias electrode. The charges that accumulate at the interface create a counter electric field so that the electron-hole pairs recombine in the selenium, thus limiting the charge accumulated at the corresponding pixels. A variety of means have been used to neutralize the charges accumulated at the interface, a so called erase step. We have demonstrated a novel charge transport layer (CTL) that protects the FETs from transient overexposure and eliminates the need for a separate erase step. By selection of the time constant of the CTL, the panel can be used for static and dynamic imaging. The operating principle of this new structure and the performance of prototypes compared to conventional will be reported.
We describe a high-resolution digital x-ray detector suitable for producing high quality mammographic images. The detector consists of an array of 3584 by 4096 pixels on 70 micrometer centers covering an area of 25 cm by 29 cm. The conversion layer of the detector is 250 micrometer thick amorphous selenium. Each pixel of the array consists of a storage capacitor for collecting x-ray signals and an amorphous silicon switching transistor. The signal is read out by custom high-speed, low-noise electronics. The integration of this detector with a mammographic x-ray system and acquisition console is described, as well as algorithms for calibration of the full system. We review characterization of the imaging performance of our system based on quantitative analyses of MTF and DQE data, and compare experimental results with theoretical calculations. We compare the performance of our direct conversion system with that of screen/film analog systems and indirect conversion digital detectors, such as LORAD's CsI/CCD detector, operated under similar conditions. MTF degradation mechanisms and system noise sources and their effect on DQE are discussed. We review qualitative aspects of image quality from our detector and present preliminary observer performance characteristics on clinical studies run with our system.
Direct conversion of x-ray energy into electrical charge has been extensively developed into imaging products in the past few years. Applications include general radiography, mammography, x-ray crystallography, portal imaging, and non-destructive testing. Direct methods avoid intermediate conversion of x-rays into light prior to generating a measurable electrical charge. This eliminates light scattering effects on image sharpness, allowing detectors to be designed to the limit of the theoretical modulation transfer function for a discrete-pixel sensor. Working exposure range can be customized by adjusting bias and thickness of sensor layers in coordination with readout-electronics specifications. Mature amorphous selenium technology and recent progress on high-quality Thin-Film Transistor (TFT) arrays for computer displays have allowed development of practical large-area high-resolution flat-panel x-ray imaging systems. A variety of design optimizations enable direct-conversion technology to satisfy a wide range of applications.
This paper will describe details of and results for a frequency-dependent filtered gain calibration technique that optimizes DQE, yet does not reduce MTF performance which is important to both systems.
Professional and consumer digital photography cameras use either CCD or CMOS sensors. Both of these sensors are fabricated using crystalline silicon technology. The advantage of this technology is that the pixel sizes can be made relatively small with resolutions approaching that of conventional photographic film. The disadvantage is that the active area is limited by the size of the silicon wafers, thereby making large format photography difficult. A new class of sensor using amorphous silicon on glass has bene developed for the medical field of radiography, fluoroscopy, and mammography. These pixilated devices have a thin-film- transistor (TFT) switch coupled to a photodiode or storage capacitor located at each pixel. Devices with 70 micrometers pixel pitch and nominally 10 inch by 12 inch active area are under development. Results are presented on a 14 inch by 17 inch TFT-based large area sensor with a pixel pitch of 139 micrometers and a prototype 512 by 512 pixel device with a 70 micrometers pitch. Characterizations include linearity, dynamic range, input-output transfer characteristics and resolution. Advantages and limitations of this technology for large format photography will be discussed.
Digital imaging systems require offset and gain calibration to normalize the behavior of individual pixels. This normalization corrects for imperfections in the system and also external variables that have effects on uniformity. Imaging metrics like Detective Quantum Efficiency (DQE) and Modulation Transfer Function (MTF) define how sensitivity and resolution are transferred through the system. Gain calibration can result in a loss of DQE due to the noise associated with its application. The typical technique to minimize this noise is to average several gain calibration procedures so that the introduced noise is minimized. This paper discuses the effects of gain calibration on DQE. It measures DQE as a function of the number of gain calibration procedures averaged and contrasts it with a novel technique that uses a single filtered gain calibration. It demonstrates that noise filter techniques, applied to a single gain calibration, regains the loss in DQE without any degradation in resolution. This paper also compares imaging performance of a system using a filtered gain map against a system that has many gain calibrations averaged. The technique is demonstrated using a Thin-Film-Transistor (TFT)-based large area medical imaging system.
Large area flat panel solid-state detectors are being studied for digital radiography and fluoroscopy. Such systems use active matrix arrays to readout latent charge images created either by direct conversion of x-ray energy to charge in a photoconductor or indirectly using a phosphor and individual photodiodes on the active matrix array. Our work has utilized the direct conversion method because of its simplicity and the higher resolution possible due to the electrostatic collection of secondary quanta. Aliasing of noise occurs in current designs of direct detectors based on amorphous selenium ((alpha) -Se) because of its high intrinsic resolution. This aliasing leads to a decrease in detective quantum efficiency (DQE) as frequency increases. It has been predicted, using a previously developed model of the complete imaging system, that appropriately controlled spatial filtration can reduce this aliased noise and hence increase DQE at the Nyquist frequency, fNY. Our purpose is to experimentally verify this concept by implementing presampling filtration in a practical flat panel system. An (alpha) -Se based flat panel imager is modified by incorporating an insulating layer between the active matrix and the (alpha) -Se layer to introduce a predetermined amount of presampling burring. The modified imager is evaluated using standard linear analysis tools, modulation transfer function (MTF), noise power spectra (NPS) and DQE(f), and the results are compared to theoretical predictions.
The development of a new high spatial resolution x-ray detector system is described. The prototype detector is based on a patented detector technology that utilizes selenium for the x-ray conversion material, charge storage capacitors, and a thin film transistor (TFT) array for reading out the charge image. This experimental detector consists of a 512 X 512 matrix with a pixel pitch of 70 microns. The selenium layer deposited on the TFT array is 250 microns thick. With a low absorption entrance window the system is optimized for an energy range of 10 - 30 keV, and is designed for applications that require high spatial resolution and low noise. This presentation describes the imaging performance of the detector using the DQE and MTF metrics. Example images of phantoms are shown. Previously, we demonstrated a practical flat-panel self-scanned digital radiography system based on amorphous selenium and TFT technology. This system is being used clinically for chest radiography and general musculoskeletal imaging, and in industrial applications. The current work demonstrates the feasibility of adapting this technology for applications requiring higher spatial resolution.
Efforts to integrate projection radiography into the digital environment have, to date, required signal degrading steps. The purpose of this study was to compare new directly acquired digital projection radiographic images to conventional film screen images. Fifty paired images (25 chest and 25 abdomen) were obtained under identical conditions and at comparable exposures using a new digital system and a conventional 200 speed film-screen system. This new direct x-ray converting full field 14 X 17 inch detector (Sterling Imaging) uses selenium coupled to a 2560 X 3072 thin film transistor array with a pixel pitch of 139 microns. The detector was easily retrofitted to existing radiographic equipment. After applying appropriate algorithms to obtain images that were comparable in gray scale appearance to conventional film, the 14 bit digital images were printed at full resolution (8 bit) on laser film. Detail evaluation of these paired images under identical viewing conditions, using standardized protocols that were formulated prior to imaging, was performed by three experienced radiologists for each body area. The hard copy clinical digital images were judged by all of the expert panel of radiologists to be superior or equivalent to their paired conventional film screen study (t-value confidence level of 10-6 for chest and .03 for abdomen).
Thin Film Transistor (TFT) array technology is presented for Digital X-ray Sensors in Direct Radiography applications. Circuit simulations were performed to optimize the design of the TFT array. The sensor array uses a combination of a mushroom electrode with a high fill factor of 86% and a polymer passivation dielectric to minimize column capacitance and improve signal-to-noise ratio. A 14 in. X 8.5 in. sensor array with 1536 X 2560 pixels was developed using this technology. The TFT arrays are processed entirely in Class 1 clean room environments to eliminate line defects and minimize pixel defects. The best 14 in. X 8.5 in. panels have exhibited fewer than 0.001% pixel defects, as detected during in process testing prior to Se coating. In typical image quality comparisons with conventional X-ray film/screen combinations, the digital X-ray sensor exhibited equal or better performance than film-screens. Clinical studies were also conducted. Radiologists concluded that diagnostically significant projection radiographic images can be produced with the new digital X-ray sensor that are equivalent or superior to conventional film/screen images at the same X-ray exposures. The detector recently received FDA approval.
Progress is discussed on the improvement of a Direct RadiographyTM solid state, flat panel, digital detector designed for use in general radiographic applications. This detector, now known as DirectRayTM, operates on the principle of direct detection of X-ray photons with a selenium photoconductor and consists of 500 micrometer thick amorphous selenium coupled to an amorphous silicon thin-film-transistor (TFT) readout array. This device is fabricated with a 14 X 17-inch (35 X 43-cm) active imaging area, corresponding to 2560 X 3072 pixels having dimensions of 139 micrometer X 139 micrometer and a geometrical fill factor of 86%. Improvements include a TFT array design upgrade with reduced noise characteristic, lower-noise readout electronics, and improved interfaces. Clinical radiographic images are currently being generated with the DirectRay detector using an X-ray exposure level equivalent to that of a 400 speed screen- film combination while maintaining the superior spatial resolution that is inherent in the direct conversion method. An effective sensor restoration technique has been implemented that eliminates the potential for selenium memory artifacts after a high dose. New results on NPS, MTF, DQE and signal linearity are presented. Detectability of low contrast objects using FAXiL test objects as well as the results of clinical studies are discussed.
A Selenium thin film transistor (STFT) array-based rotational volume tomographic digital angiography (VTDA) imaging system has been constructed. The system consists of an x-ray tube and a STFT detector that are separately mounted on a gantry. This system uses the STFT array as a two-dimensional (2D) detector so that a set of 2D projections can be acquired for a direct three-dimensional (3D) reconstruction. This paper presents the results of the preliminary phantom studies using the STFT- based volume tomographic angiography imaging system. This research work demonstrates through phantom studies that the STFT array introduces no distortion and the STFT-based VTDA imaging system has a higher spatial resolution and better contrast resolution than an image intensifier(II)-based system.
KEYWORDS: Digital imaging, Image processing, X-ray detectors, Digital image processing, Detection and tracking algorithms, X-rays, Absorbance, Sensors, Diagnostics, Algorithm development
Typical digital x-ray image detectors in current use, or under development, provide a dynamic range of digital values which significantly exceed the actual range of useful diagnostic data for any given exposure condition. It becomes a task of the digital detection system to provide recognition of the useful data values and to provide appropriate post processing to produce diagnostically useful display image. In this paper we describe a technique which was developed to automatically useful display image. In this paper we describe a technique which was developed to automatically define the range of useful image data values. Reference values are derived from a histogram, and it is integral, of the detector's output. These reference values, along with exam specific parameters, are used in exam specific algorithms to define the range of digital values to be included in a diagnostic display image.The display image values are gray scale processed to produce an optimized soft or hard copy image data set. Using the described algorithms we have demonstrated the automated production of hard copy images from a digital detector system which are comparable to properly exposed conventional radiographs. These algorithms automatically compensates for exposure technique and subject contrast characteristics. The algorithms were developed for the Sterling Direct Radiography digital x-ray detector system; however, they are applicable to any digital x-ray image detector system. The technique described is based on the digital input values which represent log exposure values. If linear values are provided, a log conversion must be made preceding the described technique.
Progress on the development of a semiconductor-based, direct-detection, flat-panel digital radiographic imaging device will be discussed. The device consists of a 500 micrometers thick amorphous selenium sensor coupled to an amorphous silicon thin-film-transistor (TFT) readout matrix. This detector has an active imaging area of 14 inches X 17 inches, 3072 X 2560 pixels with dimensions 139 micrometers X 139 micrometers and a geometrical fill factor of 86 percent. Charges generated primarily as a consequence of photoelectric interaction between the incoming x-rays and Se are integrated on storage capacitors that are located at each pixel. The high electric field applied across the Se minimizes the lateral spreading of the signal resulting in a significantly higher spatial resolution when compared to conventional film/screen systems used for general radiography. The sensor array is read out one pixel line at a time by manipulating the source and gate lines of the TFT matrix. Data are digitized to 14 bits. This paper will discuss the statistical photon counting analysis performed on an early prototype device. Measurements will include modulation transfer function, detector quantum efficiency, linearity, and noise analysis. Image analysis will include small contrast object visibility studies using a Faxil x-ray test object T016. Advantages of this flat-panel electronic sensor over conventional systems are discussed.
The productivity-improving features of a direct digital radiography system for projection radiography are introduced and the integration of the system with PACS is discussed. A flat panel digital array, an array controller, and a system controller with video monitor and standard interface to a local or wide area communications network are the main components of the direct digital radiography system of which prototypes have been built and tested in laboratory settings. When used in radiology room for projection radiography, the digital array converts x-ray photons into digital image data and makes the data available immediately for display on a video monitor for the technologist's review. Upon the technologist's acceptance of the image, an industry-standard network allows the transmission of the image to a workstation where additional image processing can be performed and where the image can be viewed on a high resolution display by the radiologist. If so desired, the image may be routed to a laser printer, digital mass storage medium, or to a PACS communication interface. By connecting the direct digital radiography system with a PACS network, radiographs may be shared electronically like images of other digital modalities. In this scenario, productivity improvements would come mainly from shorter patient exams as a result of the immediate availability of the review images, wider exposure latitude and ease of handling of the digital array, and from the electronic transport, storage and retrieval of image files and patient data in a PACS environment.
The imaging performance of a new direct digital radiographic detector based on amorphous selenium and amorphous silicon TFT array which is under development is discussed. Progress has been made on the development of a multilayer digital x-ray detector panel with a structure consisting of a thin-film transistor pixel array, selenium x-ray photoconductor, dielectric layer and top electrode. An electronic system allows the rapid readout of image data which produces high resolution and wide dynamic range images. Using a straight edge, small wires and low contrast small holes targets, we have studied the spatial resolution, contrast detectability, and dynamic range of this new detector. Digital signals obtained from each pixel of this detector are almost linear with the total x-ray energy absorbed within the pixel area over a wide range of x-ray exposures. The resultant wide dynamic range allows extended latitude of exposure conditions and the enhancement or emphasis of different gray level regions from a single set of image data. For example, from one single exposure of the head, the soft tissue of the nose, detail structure of the teeth, as well as the bone structure of the neck can be examined by displaying and emphasizing selective gray levels of the image data. Image information obtained from this detector appears to be more evenly distributed over a wide dynamic range which is different from digital data obtained from other digital modalities such as the electrometer sensing of discharged potentials on photoconductors or from film digitization. Examples of images are shown. The discrete pixel structure of this detector and the higher intrinsic spatial resolution of selenium combine to produce image sharpness greater than those produced from digital detectors of similar pixel pitch using indirect conversion method or from digitizing film-screen images. The applicability of mathematical tools, such as the MTF which was developed primarily for analog images on a continuous imaging medium, is discussed with respect to our new discrete element detector.
Surgeons often need to localize foreign objects in wounded patients in facilities where computed tomography (CT) may not be present or is contraindicated by anticipation of massive CT artifacts associated with imaging radiopaque materials such as shrapnel. A skull phantom was placed on top of a 22 by 18 cm radiographic imaging panel developed by Du Pont Diagnostic Imaging Systems in both posterior-anterior (PA) and lateral orientations. A radiopaque reference sphere (2 mm dia.) was attached to the phantom and a set of eight, two- dimensional radiographic projections was obtained for each of the two orientations. This was done by laterally displacing the x-ray head in a plane parallel to the projection panel to eight different positions well distributed around the periphery of a solid angle approximating 25 degrees. An operator identified the reference shadow on each digital projection. This information was used by the TACT system to compute tomographic slices based on the reference sphere's relative displacement in the field. These TACT slices were compared directly with tomographs of the same region of the skull made with a Phillips Model BTS4 tomographic machine. Both methods appeared to yield clinically interpretable images of comparable diagnostic quality.
The operational principle of a new, patented digital radiographic system using a multi-layer structure consisting of a thin-film pixel array, selenium x-ray photoconductor, dielectric layer and top electrode is described. Under an applied electric field, a diagnostic x-ray signal is obtained by the direct conversion of x-ray energy to electron-hole pairs which are collected as electrical charges by individual storage capacitor associated with each pixel element. The electronic readout sequence is initiated immediately after the x-ray exposure, and in several seconds, the image data is available for display on a video monitor, for data storage, data transmission, and hard copy generation. Signal strength of this direct conversion method is estimated to be significantly higher than that of other indirect conversion methods where light is first generated using a scintillator or phosphor and then detected by charge-coupled devices (CCDs) or thin-film-transistor (TFT) arrays in conjunction with photodiodes. In addition, since charges generated by x-ray photons move mostly along the direction of the bias electric field, images of very high spatial resolution can be obtained. The resolution limits are principally defined by the smallest pixel that can be manufactured. Recent x-ray images obtained from experimental detector panels are presented. X-ray sensitivity, dynamic range, signal-to-noise ratio, and spatial resolution are discussed.
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