Some studies of avalanche photodiode readout of fast scintillators

Holl, I.; Lorenz, E.; Natkaniez, S.; Renker, D.; Schmelz, C.; Schwartz, B.

doi:10.1109/23.467822

Cited by 42 publications

(8 citation statements)

References 14 publications

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“…The reason for still using PMTs in PET although they are bulky and relatively expensive is that they are reliable in operation and so far provide the best performance with respect to electronic noise and timing properties, when compared with all other light detectors. Avalanche photodiodes (APDs) have been the subject of intensive research for the last 15 y (3)(4)(5)40). The first evaluations of APDs in prototype smallanimal PET scanners proved their feasibility as light detectors.…”

Section: Pet Advances In Pet Detector Technologymentioning

confidence: 99%

“…However, signals can be enhanced by a technique called hyperpolarization, which involves polarizing certain nuclei, thus increasing their observed MRI signal by several orders of magnitude. For instance, 3 He and 129 Xe are polarized via optical pumping whereas 13 C can be polarized via parahydrogen-induced polarization (102,103) and dynamic nuclear polarization (104,105). Applications of 3 He and 127 Xe include lung perfusion studies (106,107).…”

Section: Beyond Anatomic Mri-toward Functional Imagingmentioning

confidence: 99%

“…The invention of PET dates back more than 30 y. However, the acceptance of PET as a routine clinical diagnostic tool has been hampered by the need for an on-site cyclotron and a radiochemistry unit for the production of the short-lived radiotracers (1)(2)(3)(4)(5)(6)(7). With the availability of commercial radiopharmacies that supply PET probes and with the relatively broad insurance coverage for a variety of clinical indications, the number of PET centers now totals more than 2,000 worldwide.…”

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confidence: 99%

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Latest Advances in Molecular Imaging Instrumentation

Pichler¹,

Wehrl²,

Judenhofer³

2008

J Nucl Med

193

110

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This review concentrates on the latest advances in molecular imaging technology, including PET, MRI, and optical imaging. In PET, significant improvements in tumor detection and image resolution have been achieved by introducing new scintillation materials, iterative image reconstruction, and correction methods. These advances enabled the first clinical scanners capable of time-of-flight detection and incorporating point-spread-function reconstruction to compensate for depth-of-interaction effects. In the field of MRI, the most important developments in recent years have mainly been MRI systems with higher field strengths and improved radiofrequency coil technology. Hyperpolarized imaging, functional MRI, and MR spectroscopy provide molecular information in vivo. A special focus of this review article is multimodality imaging and, in particular, the emerging field of combined PET/MRI. PETi s a high-performance imaging technology that can image the whole-body distribution of positron-emitting biomarkers with high sensitivity. The invention of PET dates back more than 30 y. However, the acceptance of PET as a routine clinical diagnostic tool has been hampered by the need for an on-site cyclotron and a radiochemistry unit for the production of the short-lived radiotracers (1-7). With the availability of commercial radiopharmacies that supply PET probes and with the relatively broad insurance coverage for a variety of clinical indications, the number of PET centers now totals more than 2,000 worldwide.Major technologic milestones in the development of PET include the discovery of faster and brighter scintillators such as lutetium oxyorthosilicate (LSO), gadolinium oxyorthosilicate, and lutetium yttrium oxyorthosilicate. Furthermore, the continuing development of the detectors, progressing from one-to-one scintillator-to-photomultiplier-tube (PMT) coupling (8,9) to advanced block and Anger readout schemes, helps to limit the costs of a PET scanner by providing a multiplexed readout and reduced electronic channels (10-13).The use of faster scintillators enabled the transition from 2-dimensional data acquisitions for whole-body PET, using lead or tungsten collimators as septa (14-16), to 3-dimensional (3D) acquisitions (17). However, approximately an 8-fold increase in detection sensitivity is accompanied by an increased fraction of random and scattered photon events leading to degradation of image quality if not corrected during image reconstruction (18). This degradation effectively reduces the increase in sensitivity from a factor of 8 to approximately 5-fold. To achieve high-quality and quantitative PET data, various image reconstruction techniques have evolved (19). One simple approach is filtered backprojection, which is computationally fast but results in poor image quality if the count statistics of the available PET data are inadequate. Better image quality and improved spatial resolution are achieved by iterative methods such as ordered-subset expectation maximization or maximumlikelihood expectation maximiza...

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Section: Pet Advances In Pet Detector Technologymentioning

confidence: 99%

Section: Beyond Anatomic Mri-toward Functional Imagingmentioning

confidence: 99%

mentioning

confidence: 99%

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Latest Advances in Molecular Imaging Instrumentation

Pichler¹,

Wehrl²,

Judenhofer³

2008

J Nucl Med

193

110

View full text Add to dashboard Cite

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“…The scintillation crystals are one-to-one coupled to the active APD surface, reducing dead time as compared to the Anger readout in bismuth germanate (BGO) block detectors [4]. The advantages of APDs over photomultipliers (PMs) are their compactness their insensitivity against high magnetic fields [5], their high quantum efficiency (75 ... 80 YO), their low bias voltage, potential mass production and low price [6]. LSO scintillators have a seven times shorter scintillation decay time (40 ns) and a 4-6 times higher light yield (28 000 photons/MeV) than BGO.…”

Section: Introductionmentioning

confidence: 99%

Studies with a prototype high resolution PET scanner based on LSO-APD modules

Pichler

Böning

Lorenz

et al. 1998

IEEE Trans. Nucl. Sci.

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Lutetium oxyorthosilicate (LSO) scintillation crystals coupled to avalanche photodiodes (APDs) have been proven to be an interesting detector module for high resolution positron emission tomography (PET). Compact detector modules were built to test their performance in a prototype tomograph. Each detector module consisted of sixteen 3.7 x 3.7 x 12.0 mm3 LSO crystals, which are one-to-one coupled to a two dimensional APD array (2 x 8 diodes, 3 mm 0, 4 mm spacing). The signals were read out by a low noise, fast, charge sensitive preamplifier, a 50 ns shaping amplifier and CAMAC electronic modules. Two detector modules were mounted on a rotatable gantry, to simulate a detector ring. Long term runs over 110 hours have shown that the detector remains stable over a long period of time. The energy resolution (FWHM) was 13.4 % for 51 1 keV gamma rays and the intrinsic spatial resolution was 2.2 mm (FWHM). The gain dependence of the APD on temperature had been determined as 3.5 %/K. The time resolution was 3.2k0.1 ns (FWHM). Phantom measurements showed the suitability of the new LSO/APD detector for high resolution animal PET.

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“…T HE advantages of avalanche photodiodes (APDs) compared to photomultiplier tubes (PMTs) are their compactness, high quantum efficiency, low bias voltage, and the potential of low cost due to mass production [1], [2]. On the other hand, APDs have a much lower gain than PMTs.…”

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confidence: 99%

Integrated low-noise low-power fast charge-sensitive preamplifier for avalanche photodiodes in JFET-CMOS technology

Pichler

Pimpl

Buttler³

et al. 2001

IEEE Trans. Nucl. Sci.

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To take advantage of the compactness of avalanche photodiode (APD) arrays, low-noise power-efficient fast charge-sensitive preamplifier chips with differential current drivers have been developed. A 16-channel and a single-channel version are available. The chips were adapted for low-capacitance 4 8 APD arrays produced by Hamamatsu, Japan. A mixed junction field-effect transistor (JFET)-CMOS production process yielded high-quality integrated JFETs for the input stage of the amplifier's folded cascode. Thus, the 1 -noise corner is kept at 4 kHz. The JFET has a transconductance of 11 mS at a drain current of 3 mA. The serial noise of the input transistor was found to be 0.8 nV Hz. The signal rise time of the driver outputs is 20 ns. The rms noise of the preamplifier was found to be 480 e with a 25-e pF noise slope for a shaping time of 50 ns. The serial input noise of the preamplifier is about 1.4 nV Hz from 200 kHz up to 40 MHz, and the 1 -noise corner is at 70 kHz. The power consumption is 30 mW per preamplifier, including the differential driver. The linearity is better than 1.3% over 48-dB dynamic range. For the 16-channel chip, the channel-to-channel gain variation is less than 3.5%. Performance similar to photomultiplier tubes can be achieved with APDs in combination with this integrated preamplifier chip.Index Terms-Aavalanche photodiode (APD), charge-sensitive preamplifier, junction field-effect transistor (JTET)-CMOS, lownoise preamplifier.

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Some studies of avalanche photodiode readout of fast scintillators

Cited by 42 publications

References 14 publications

Latest Advances in Molecular Imaging Instrumentation

Latest Advances in Molecular Imaging Instrumentation

Studies with a prototype high resolution PET scanner based on LSO-APD modules

Integrated low-noise low-power fast charge-sensitive preamplifier for avalanche photodiodes in JFET-CMOS technology

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