A small scintimammography detector based on a 5" PSPMT and a crystal scintillator array

Steinbach, D.; Cherry, Simon R.; Doshi, N.; Goode, Allen R.; Kross, B.; Majewski, S.; Weisenberger, A.G.; Williams, Mark B.; Wojcik, R.

doi:10.1109/nssmic.1997.670537

Cited by 14 publications

(6 citation statements)

References 7 publications

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“…YAP:Ce in particular has many attractive properties, such as reasonably high density, fast decay, negligible afterglow, high light yield, and very good energy resolution [6]. These have made it a material of choice for many devices [7], including a small animal PET camera [8], a prototype gamma camera based on a position sensitive photomultiplier tube (high resolution single photon emission computed tomography or HIRESPECT) [9,10], dosimeters [11], scintimammography cameras [12], and pulse-shape discrimination for the Astro-E Hard X-ray Detector [13]. Consequently, significant efforts have been put into technological development of the material [14,15], as well as characterization of its optical [16][17][18] and scintillation properties [19][20][21][22].…”

Section: Introductionmentioning

confidence: 99%

Recombination and scintillation processes in

Wojtowicz

Głodo

Łempicki

et al. 1998

J. Phys.: Condens. Matter

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This paper reports spectroscopic and scintillation studies of the well established scintillator material . Standard measurements of luminescence emission and excitation spectra have been accompanied by investigations of thermoluminescence and scintillation light yield over a wide temperature range, and by decay measurements under pulsed gamma and VUV excitations at various temperatures. These measurements are interpreted in the framework of a model that includes a recombination centre and a number of electron traps. We demonstrate that some unusual and largely unexplained features of the scintillator, such as a substantial disparity between scintillation and radiative decay times, the presence of slow components in scintillation decays, and a strong temperature variation of scintillation light yield between 150 and 300 K, have their origin in the processes of charge carrier capture and emission by electron traps. Although the nature of these traps remains elusive, most of the trap parameters, such as frequency factors, energy depths, and relative populations, have been estimated. This makes it possible to predict the characteristics of trap-free material and thereby the potential improvements that could be achieved.

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Section: Introductionmentioning

confidence: 99%

Recombination and scintillation processes in

Wojtowicz

Głodo

Łempicki

et al. 1998

J. Phys.: Condens. Matter

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“…Since this first scanner was introduced, systems utilizing rotating planar detectors and rings of detectors have been developed . In addition to positron‐emitter based scanners, several based on the use of single‐photon emitting radionuclides have been also constructed …”

Section: Introductionmentioning

confidence: 99%

“…[12][13][14][15][16][17][18][19][20][21][22] In addition to positron-emitter based scanners, several based on the use of single-photon emitting radionuclides have been also constructed. [23][24][25][26][27][28] Dedicated breast imaging has extended beyond Nuclear Medicine methods to include the creation of x ray computed tomography (CT) systems. The first cone beam, breast-CT system was developed in 2001 by Boone, et al 29 Subsequently, additional academic researchers have created similar devices, [30][31][32] including one combined with a SPECT scanner, 33 the first commercially available, FDA-approved scanner 34 and phase-contrast-based systems.…”

Section: Introductionmentioning

confidence: 99%

A dedicated breast‐PET/CT scanner: Evaluation of basic performance characteristics

et al. 2018

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The basic performance characteristics of a new dedicated breast-PET/CT scanner are good, demonstrating that its performance is similar to current dedicated PET and CT scanners. The potential value of this system is the capability to produce combined duality-modality images that could improve detection of breast disease. The next stage in development of this system is testing with more advanced phantoms and human subjects.

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“…comparable to the X-ray ones ( cranio-caudal projection), also under compression [1]- [4]. The introduction of small field of view camera, based on scintillation array and position sensitive photomultiplier (PSPMT), allowed to enhance geometric spatial resolution and contrast of the images.…”

mentioning

confidence: 99%

Custom Breast Phantom for an Accurate Tumor SNR Analysis

Cinti

Pani

Garibaldi³

et al. 2004

IEEE Trans. Nucl. Sci.

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The capability of the scintimammography to diagnose subcentimeters sized tumors was increased by the employment of a dedicated gamma camera. The introduction of small field of view camera, based on pixellated scintillation array and position sensitive photomultiplier, allowed to enhance the geometric spatial resolution and contrast of the images due to reduced collimator-tumor distance.The aim of this paper is to investigate the realistic possibility of T1a tumors detection ( 5 mm size) by comparing the signal-to-noise ratio (SNR) values obtained by different imagers.To this end, we have utilized a self-designed solid breast phantom with different sized hot spots (tumors). The phantom consists of seven disks with different thickness, molded from resin epoxy activated with Co 57 isotope. The overlapped disks represent a pendula breast with about 800 cc volume. Hot spots have not wall. One disk has holes to fit the hot spots representing the different sized lesions. The imagers utilized were: a standard Anger Camera and three different cameras based on scintillator array, CsI(Tl) or NaI(Tl), coupled to position sensitive photomultiplier with different technologies, to make detectors with field of view of 3 and 5 inch. The experimental results are supported by Monte Carlo simulation. It was highlighted how spatial resolution is a predominant element in tumor visibility and how background causes a reduction of the image contrast. All gamma cameras show close results at SNR values less than 10 and a full detectability of 8 mm tumor size. However, the results show the 5 mm tumor size is lower detection limit for all cameras.

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A small scintimammography detector based on a 5" PSPMT and a crystal scintillator array

Cited by 14 publications

References 7 publications

Recombination and scintillation processes in

Recombination and scintillation processes in

A dedicated breast‐PET/CT scanner: Evaluation of basic performance characteristics

Custom Breast Phantom for an Accurate Tumor SNR Analysis

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