Position Sensitive Gamma Ray Detectors Using Resistive Charge Division Readout

Gerber, M. S.; Miller, Don W.; Schlosser, P. A.; Steidley, J. W.; Deutchman, Arnold H.

doi:10.1109/tns.1977.4328666

Cited by 19 publications

(5 citation statements)

References 8 publications

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“…In order to minimize the electronic hardware involved in the imaging chain, a simple charge division readout scheme [20,39,40] was developed and optimized for the imaging probe (Fig. 12).…”

Section: Positioning Readout Electronicsmentioning

confidence: 99%

Design considerations and initial performance of a 1.2 cm/sup 2/ beta imaging intra-operative probe

Tornai

MacDonald

Levin

et al. 1996

IEEE Trans. Nucl. Sci.

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A novel small area beta (p') detector is under development for nuclear emission imaging of surgically exposed, radiolabeled tumor beds. The imaging device front-end consists of a 0.5 mm thick by 1.25 cm diameter CaF,(Eu) scintillator disk coupled to a rigid bundle of 2 mm diameter double clad optical fibers through a polystyrene light diffuser. The detector area (1.2 cm2) was determined by the requirement of introducing the probe into small cavities, e.g. during neuro-surgical lesion resection, but large enough to produce images of clinical significance. Flexible back-end optical fibers (1.9 m long) were coupled to the front-end components allowing -75 photoelectrons to be detected for mean beta energies of 250 keV, indicating that sufficient signal can be obtained with clinical beta emitters (e.g. lSF, 1311). The long flexible fibers guide the scintillation light to a Philips XP1700 series, fiber optic faceplate, Multi-Channel PMT. The parallel MC-PMT outputs are fed into a variable gain, charge divider network and an i-V pre-amplifiedline driver network, whose resulting four outputs are digitized and histogrammed with standard Anger positioning logic. The various components in the imaging chain were evaluated and optimized by both simulations and measurements. Line spread functions measured in the 10.8 mm FOV were 0.50 mm f. 0.038 mm and 0.55 mm f 0.065 mm FWHM in X and Y, respectively. A 20% variation in pulse height and minimal variation in spatial resolution was observed. The differential image uniformity was measured to be rt15.6% with -150 ctdpixel. Preliminary images show excellent reproduction of phantom activity distributions. (A)FRONT-END BACK-END

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“…In order to minimize the electronic hardware involved in the imaging chain, a simple charge division readout scheme [20,39,40] was developed and optimized for the imaging probe (Fig. 12).…”

Section: Positioning Readout Electronicsmentioning

confidence: 99%

Design considerations and initial performance of a 1.2 cm/sup 2/ beta imaging intra-operative probe

Tornai

MacDonald

Levin

et al. 1996

IEEE Trans. Nucl. Sci.

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“…Very recently, capacitive multiplexing has been proposed for the SiPM-based PET detector development (Olcott et al 2009, Olcott and, in which detector signals were read out for each row and column individually. This concept has been originally designed for a cross-strip readout for germanium detectors (Gerber et al 1977). In essence, the scheme uses capacitor pairs of different capacitance values to divide charge.…”

Section: Introductionmentioning

confidence: 99%

Investigation of analog charge multiplexing schemes for SiPM based PET block detectors

2013

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Reducing the number of output channels in pixelated positron emission tomography (PET) detectors is an effective way to minimize cost and complexity while minimizing the impact on detector performance. This paper compares the system performance of two multiplexing schemes by using both simulation and experimental studies, with respect to spatial, time and energy resolutions. Simulations were performed using the SPICE environment to investigate differences in resulting flood histograms and rising edge slopes. Experiments were performed using lutetium-yttrium oxyorthosilicate (LYSO) crystals coupled to a SensL ArraySL-4 silicon photomultiplier (SiPM) connected to interchangeable circuit boards containing the two multiplexing schemes of interest. Three crystal configurations were tested: a single crystal element (3×3×20 mm(3)), 2×2 array (crystal pitch: 2×2) and 6×6 array (crystal pitch: 2.1×2.1×20 mm(3)). Good agreement was found between the simulations and experiment results. It is found that the capacitive multiplexing is able to achieve an improved time resolution of good uniformity (average of 1.11 ± 0.01 ns and 1.90 ± 0.03 ns for the arrays, respectively) and crystal separation, compared to the resistive multiplexing (average of 1.95 ± 0.03 ns and 3.33 ± 0.10 ns). On the other hand, the resistive multiplexing demonstrates slightly improved energy resolution (11 ± 0.1% and 22 ± 0.6%, compared to 12 ± 0.1% and 24 ± 0.4% for the capacitive array), which is believed to be caused by the RC circuit formed between the splitting capacitors and the input impedance of amplifiers. The relevancy of this work to the PET block detector design using SiPM arrays is also discussed, including light sharing, edge compression and gain variation among SiPM pixels.

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“…A segmentation method requiring fewer channels of pulse-processing electronics is the orthogonal-strip geometry shown in Figure 3 [13][14][15]. In this method, both electrodes are segmented into strips such that the strips on one detector side are orthogonal to the strips on the opposing detector surface.…”

Section: Introductionmentioning

confidence: 99%

Three-Dimensional Position-Sensitive Germanium Detectors

Amman¹,

Luke²

2001

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Position Sensitive Gamma Ray Detectors Using Resistive Charge Division Readout

Cited by 19 publications

References 8 publications

Design considerations and initial performance of a 1.2 cm/sup 2/ beta imaging intra-operative probe

Design considerations and initial performance of a 1.2 cm/sup 2/ beta imaging intra-operative probe

Investigation of analog charge multiplexing schemes for SiPM based PET block detectors

Three-Dimensional Position-Sensitive Germanium Detectors

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