[go: up one dir, main page]

WO2008146230A2 - Comptage de photons avec détection d'un maximum local - Google Patents

Comptage de photons avec détection d'un maximum local Download PDF

Info

Publication number
WO2008146230A2
WO2008146230A2 PCT/IB2008/052058 IB2008052058W WO2008146230A2 WO 2008146230 A2 WO2008146230 A2 WO 2008146230A2 IB 2008052058 W IB2008052058 W IB 2008052058W WO 2008146230 A2 WO2008146230 A2 WO 2008146230A2
Authority
WO
WIPO (PCT)
Prior art keywords
photon
detector
pulses
counter
pulse train
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/IB2008/052058
Other languages
English (en)
Other versions
WO2008146230A3 (fr
Inventor
Roger Steadman Booker
Cristoph Herrmann
Christian Baeumer
Guenter Zeitler
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Philips Intellectual Property and Standards GmbH
Koninklijke Philips NV
Original Assignee
Philips Intellectual Property and Standards GmbH
Koninklijke Philips Electronics NV
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Philips Intellectual Property and Standards GmbH, Koninklijke Philips Electronics NV filed Critical Philips Intellectual Property and Standards GmbH
Publication of WO2008146230A2 publication Critical patent/WO2008146230A2/fr
Publication of WO2008146230A3 publication Critical patent/WO2008146230A3/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N23/00—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00
    • G01N23/02—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material
    • G01N23/04—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material
    • G01N23/046—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material using tomography, e.g. computed tomography [CT]
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/17—Circuit arrangements not adapted to a particular type of detector
    • G01T1/171—Compensation of dead-time counting losses
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N25/00—Circuitry of solid-state image sensors [SSIS]; Control thereof
    • H04N25/70—SSIS architectures; Circuits associated therewith
    • H04N25/76—Addressed sensors, e.g. MOS or CMOS sensors
    • H04N25/77—Pixel circuitry, e.g. memories, A/D converters, pixel amplifiers, shared circuits or shared components
    • H04N25/772—Pixel circuitry, e.g. memories, A/D converters, pixel amplifiers, shared circuits or shared components comprising A/D, V/T, V/F, I/T or I/F converters
    • H04N25/773—Pixel circuitry, e.g. memories, A/D converters, pixel amplifiers, shared circuits or shared components comprising A/D, V/T, V/F, I/T or I/F converters comprising photon counting circuits, e.g. single photon detection [SPD] or single photon avalanche diodes [SPAD]
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2223/00—Investigating materials by wave or particle radiation
    • G01N2223/40—Imaging
    • G01N2223/419—Imaging computed tomograph

Definitions

  • the following relates to photon counting radiation detectors. While it finds particular application to spectral and other computed tomography (CT) systems, it also relates to other applications in which pulse counting radiation detectors can be affected by pulse pileup.
  • CT computed tomography
  • CT scanners provide useful information about the internal characteristics of an object under examination.
  • CT scanners provide medical professionals with valuable information regarding the physiology of patients.
  • CT scanners have also been used in security inspection to examine the contents of items such as baggage, and in industrial applications such as non-destructive inspection and testing. While CT scanners have proven to be beneficial in these and other applications, the development of CT scanners having spectral capabilities promises to provide still additional benefits, such as an improved ability to provide information on the material composition of an object under examination.
  • Spectral information can be obtained using photon counting detectors.
  • pulses generated by a detector pixel in response to incoming photons have been processed by pulse shaping circuitry that integrates and amplifies the current produced by the pixel to generate voltage pulses, the heights of which are proportional to the energy of the detected photons.
  • the signal chain has also included a number of discriminators, each having a threshold. For each discriminator, a counter has been used to count the number of pulses that exceed the discriminator's threshold.
  • circuits are typically paralyzable at the count rates typically encountered in CT applications, and thus may not provide an output indicative of the true photon count rate. While non-paralyzable detector circuitry can also be implemented, such circuitry tends to be relatively complex, especially in the case of energy resolving detectors. Moreover, such circuits may not accurately characterize the energy of the detected radiation. Aspects of the present application address these matters and others.
  • a photon counting apparatus includes first circuitry that produces a pulse train in response to photons received by a radiation sensitive detector, a first photon counter that counts pulses of the pulse train, a local maximum detector that detects local maxima of the pulse train, a second photon counter that counts detected local maxima, and a pileup detector.
  • the first photon counter is operatively connected to the pileup detector so as to disregard pileup pulses.
  • a method includes producing a pulse train indicative of radiation received by a radiation sensitive detector, counting the pulses of the pulse train, detecting local maxima of the pulse train, counting the detected local maxima, and detecting pulse pileups in the pulse train.
  • the step of counting the pulses includes disregarding pileup pulses.
  • the invention may take form in various components and arrangements of components, and in various steps and arrangements of steps.
  • the drawings are only for purposes of illustrating the preferred embodiments and are not to be construed as limiting the invention.
  • Figure 1 depicts a CT scanner.
  • Figure 2 depicts a detector transfer function.
  • Figure 3 depicts a detector channel.
  • Figures 4A, 4B, and 4C depict electrical signals.
  • Figure 5 depicts a method.
  • a CT scanner 10 includes a rotating gantry 18 that rotates about an examination region 14.
  • the gantry 18 supports an x-ray source 12 such as an x-ray tube.
  • the gantry 18 also supports an x-ray sensitive detector 20 that subtends an arc on the opposite side of the examination region 14.
  • X-rays produced by the x-ray source 12 traverse the examination region 14 and are detected by the detector 20.
  • An object support 16 such as a couch supports a patient or other object in the examination region 14.
  • the support 16 is preferably movable in coordination with a scan in order to provide a helical, axial, circle and line, or other desired scanning trajectory. Accordingly, the scanner 10 generates projection data indicative of the radiation attenuation along a plurality of projections or rays through the object.
  • the detector 20 includes a plurality of detector elements 100 disposed in an arcuate array extending in the transverse and longitudinal directions.
  • the detector elements 100 produce electrical pulses or signals indicative of detected photons.
  • suitable detector elements include direct conversion detectors (e.g. , cadmium zinc telluride (CZT) based detectors) and scintillator-based detectors that include a scintillator in optical communication with a photosensor. Relatively faster detectors suitable for use in photon counting at the count rates likely to be encountered during operation of the CT scanner 10 are preferred.
  • An amplif ⁇ er/shaper circuit 102 receives the signal produced by a detector element 100 and produces a train of pulses having amplitudes that are proportional or otherwise a function of the energies of the photons detected by the detector element 100.
  • a local maximum detector 104 detects local maxima in the pulse train produced by the amplif ⁇ er/shaper 102.
  • a pileup detector 108 detects pulse pileups.
  • the signals from the amplif ⁇ er/shaper 102 and the pileup detector 108 are also received by one or more photon counters 110i_ n .
  • the photon counter 11Oi is configured to count those pulses indicative of photons having an energy that exceeds an energy minimum or floor.
  • the additional counters are preferably configured to count pulses indicative of photons having increasingly higher energies and hence provide photon spectral information.
  • the counters 110 are operatively connected to the pileup detector 108 so as to disregard pileup pulses.
  • a photon rate counter 106 counts the local maxima detected by the local maximum detector 104.
  • the first photon rate counter 106 counts the local maxima detected by the local maximum detector 104 and hence produces a count value indicative of the total number of photons received by the detector element 100.
  • the first photon rate counter 106 may be triggered by the pileup detector 108 and hence produce a count value indicative of the number of pileup pulses disregarded by the counters 110.
  • the photon rate counter 106 should not be paralyzable over the photon count rate expected to be encountered during the operation of the scanner 10, although the photon counters 110i_ n may be paralyzable.
  • FIGURE2 the transfer functions of an ideal photon counter 200, an example non-ideal, non-paralyzable counter 204, and an example paralyzable counter 206 are presented in graphical form, where the x-axis represents the true count rate and the y-axis represents the count rate observed by the detector channel.
  • the observed count rate equals the true count rate.
  • the non-paralyzable detector 204 the observed count rate may deviate from the true count rate, with the slope of the transfer function typically decreasing as the true count rate increases.
  • the slope of the transfer function becomes zero and/or negative in the range of count rates at which the detector is expected to operate.
  • a corrector 112 uses the count information from the photon rate counter 106 to correct the values from the photon counters 110i_ n .
  • the corrector 112 uses the count information from the first photon rate counter 106 to uniquely identify the actual count rate encountered by the photon counters 11O 1 -J 1 .
  • Other suitable correction techniques may also be contemplated.
  • a reconstructor 22 reconstructs the projection data from the various detector channels 101 to generate volumetric data indicative of the interior characteristics of the object.
  • the data from the various energy ranges may be processed (before reconstruction, after reconstruction, or both) to provide information about the material composition of the object under examination.
  • a controller 28 coordinates the x-ray source 12 parameters such as tube voltage and current, movement of the object support 16, operation of the data acquisition system 23, and/or other operating parameters as necessary to carry out a desired scan protocol.
  • a general purpose computer serves an operator console 44.
  • the console 44 includes a human-readable output device such as a monitor or display and an input device such as a keyboard and/or mouse.
  • Software resident on the console allows the operator to control the operation of the scanner by establishing desired scan protocols, initiating and terminating scans, viewing and otherwise manipulating the volumetric image data, and otherwise interacting with the scanner 10.
  • the channel includes a CZT based radiation detector 302.
  • the detector 302 produces output current pulses in response to detected photons, with the total charge being proportional to or otherwise a function of the photon energy.
  • FIGURE4A depicts a simulated pulse train produced by the detector 302 in response to photons received at an incoming count rate of 10 million counts per second (Mcps) according to a Poissonian distribution, with pileup neglected.
  • a charge sensitive amplifier (CSA) and signal shaper circuit 304 integrates and amplifies the current produced by the detector to form output voltage pulses, the amplitude of which is proportional to or otherwise a function of the charge pulses produced by the detector 302 and hence the energy of the detected photons.
  • a pulse train 404 produced by the circuit 304 in response to the pulse train 402 is depicted in FIGURE4B. As can be seen, the pulses of the pulse train 404 are characterized by rapid rise time, a peak amplitude that is a function of the energy of the received photon, and a somewhat slower fall time. Depending on the time period between the receipt of successive photons, a pulse produced in response to a first photon may not decay to the baseline level before a subsequent photon is received.
  • a differentiator 306 differentiates the voltage pulses to generate a differentiator output signal of the form: Equation 1 dV
  • FIGURE4C A signal 406 produced by the differentiator 306 in response to the pulse train 404 is shown in FIGURE4C. As can be seen, differentiator output signal 406 increases rapidly in response to a received photon and crosses a zero or baseline level as the signal 404 reaches its peak.
  • a baseline crossing detector 307 detects positive-to-negative baseline crossings of the differentiator signal 406 and hence the local maxima of the pulse train 404. It will be understood that positive-to-negative refers to the baseline crossings that indicate the local maxima of the pulse train 404, and not necessarily the actual electrical polarity or level of the differentiator signal 406. Note that the baseline crossings are substantially independent of the height of their corresponding local maxima. Detection of the baseline crossing can be complicated by noise in the vicinity of the baseline. Thus, the baseline crossing detector may include a discriminator that compares the differentiator signal 406 to a threshold that is offset from (e.g., slightly below) the baseline. Noise effects can be further reduced by introducing hysteresis.
  • One technique for implementing hysteresis is to limit the speed of the discriminator so that, once the discriminator has been activated, it takes some time until the discriminator can be again be activated by a subsequent falling edge.
  • Other techniques for implementing hysteresis are also contemplated.
  • the output of the baseline crossing detector 307 is used to increment a counter 308. Provided that pulse pileups are not caused by speed limitations of the detector 302, the output of the counter provides an output indicative of the total number of photons received by the detector element 100 during a reading period.
  • the baseline crossing detector 307 may be omitted.
  • a discriminator may be used to compare the slope of the signal 404 to a threshold value, again indicating the presence of a local maximum.
  • the counter 308 is implemented as an edge triggered counter 308 and is triggered by the rising or falling edge of the signal 404, as desired.
  • the detector channel also includes one or more discriminators 310i_ n and counters 312 1-n .
  • Each discriminator 310 compares the pulse train 404 against a threshold value.
  • the threshold value is selected to detect those pulses indicative of photons having energies greater than a minimum value.
  • the threshold values are preferably selected to detect those pulses indicative of photons having increasingly higher energies and hence provide photon spectral information.
  • the counters 312i_ n are triggered by the discriminators 310i_ n , thus providing an indication of the number of photons and their respective energies.
  • the pileup detector 314 detects the presence of pulse pileups in the pulse train 404, for example by determining if successive local maxima are detected within a relatively short time window. Such a situation is depicted generally in FIGURE4B, where subsequent or pileup pulses 408, 410 are detected shortly after pulses 412, 414. Depending on factors such as the decay time of the pulses, the thresholds established for the discriminators 3101 _ n , and the energy of and time between successive pulses, the pileup pulses 408, 410 may be missed by one or more of the counters 312 1-n . Also as illustrated in FIGURE4B, the height of the pulses 408, 410 may also be substantially over-represented, potentially leading to errors in the measured energy of the photons.
  • the counters 312i_ n are operatively connected to the pileup detector 314 so as to disregard the pileup pulses.
  • the counters 312 are decremented or otherwise adjusted to account for counted pileup pulses.
  • triggering of the counters 312 is delayed for a period of time sufficient to ensure that the detected pulse is not a pileup pulse.
  • Received radiation is detected at 502.
  • a pulse train is produced at 504.
  • Local maxima of the pulse train are detected at step 506.
  • the true counts are estimated at 508, for example by counting the local maxima. In one technique, the total number of maxima are counted. In another, the maxima indicative of pulse pileups are counted.
  • Pulse pileups are detected at 510.
  • the various pulses of the pulse train are counted at 510, with pileup pulses being disregarded.
  • the pileup pulses may be disregarded, for example, by decrementing or otherwise adjusting the count value(s) to account for counted pileup pulses or by counting only non-pileup pulses in the first instance. Note that separate counts may be obtained for each of a plurality of energy ranges or bins.
  • the desired count corrections are applied at 516.
  • An image of the object is reconstructed at 518.
  • data from the various energy ranges or bins may be processed to provide material composition information.
  • the image data is displayed in human readable form at 520.
  • fourth generation or other CT scanner configurations may be implemented.
  • the x-ray source 12 and detector 20 may also remain stationary while the object support is rotated or otherwise moved, especially in the case of inanimate objects.
  • the disclosed techniques can also be used to detect ionizing and other radiation in applications other than CT.
  • the invention has been described with reference to the preferred embodiments. Modifications and alterations may occur to others upon reading and understanding the preceding detailed description. It is intended that the invention be construed as including all such modifications and alterations insofar as they come within the scope of the appended claims or the equivalents thereof.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • General Physics & Mathematics (AREA)
  • Physics & Mathematics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Chemical & Material Sciences (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Molecular Biology (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Multimedia (AREA)
  • Pulmonology (AREA)
  • Radiology & Medical Imaging (AREA)
  • Theoretical Computer Science (AREA)
  • Signal Processing (AREA)
  • Analytical Chemistry (AREA)
  • Biochemistry (AREA)
  • General Health & Medical Sciences (AREA)
  • Immunology (AREA)
  • Pathology (AREA)
  • Measurement Of Radiation (AREA)
  • Apparatus For Radiation Diagnosis (AREA)

Abstract

L'invention concerne un appareil de comptage de photons qui comprend un détecteur de rayonnement (100) et des éléments de circuit de conditionnement de signal (102). Un compteur de vitesse de photon (106) produit une valeur de compte indicative d'un nombre total de photons reçus par le détecteur (100). Un ou plusieurs compteurs de photons (1101+N) produisent des valeurs de compte indicatives de photons ayant des caractéristiques énergétiques variables. Les compteurs (1101+n) négligent les impulsions d'empilement.
PCT/IB2008/052058 2007-05-29 2008-05-26 Comptage de photons avec détection d'un maximum local Ceased WO2008146230A2 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
EP07109082.3 2007-05-29
EP07109082 2007-05-29

Publications (2)

Publication Number Publication Date
WO2008146230A2 true WO2008146230A2 (fr) 2008-12-04
WO2008146230A3 WO2008146230A3 (fr) 2009-07-23

Family

ID=40075616

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/IB2008/052058 Ceased WO2008146230A2 (fr) 2007-05-29 2008-05-26 Comptage de photons avec détection d'un maximum local

Country Status (1)

Country Link
WO (1) WO2008146230A2 (fr)

Cited By (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2010142848A1 (fr) * 2009-06-09 2010-12-16 Planmeca Oy Capteur pour radiographie numérique, et procédé d'imagerie radiographique numérique
JP2013143980A (ja) * 2012-01-13 2013-07-25 Toshiba Corp Ｘ線ｃｔ装置
WO2013144754A3 (fr) * 2012-03-27 2014-01-23 Koninklijke Philips N.V. Électronique de détecteur comptant les photons à haut flux
EP2438429A4 (fr) * 2009-06-05 2014-04-30 Sentinel Scanning Corp Système et procédé d'inspection d'un conteneur de transport
CN104024886A (zh) * 2011-12-21 2014-09-03 皇家飞利浦有限公司 用于考虑堆积事件来探测光子的探测装置
US9029748B2 (en) 2013-03-15 2015-05-12 Her Majesty The Queen In Right Of Canada, As Represented By The Minister Of National Defence Method and apparatus for photon counting with optical space spreading
JP2017136342A (ja) * 2016-02-05 2017-08-10 東芝メディカルシステムズ株式会社 Ｘ線ｃｔ装置
WO2017178745A1 (fr) 2016-04-14 2017-10-19 Commissariat A L'energie Atomique Et Aux Energies Alternatives Dispositif de comptage de particules pour détecteur de rayonnement
WO2017216378A1 (fr) * 2016-06-16 2017-12-21 Koninklijke Philips N.V. Comptage amélioré de photons dans un détecteur de rayonnement spectral
US10078009B2 (en) 2013-04-24 2018-09-18 Koninklijke Philips N.V. Pulse processing circuit with correction means
EP3610231A2 (fr) * 2017-04-13 2020-02-19 Captl LLC Comptage et spectroscopie de photons
EP3709059A1 (fr) * 2019-03-14 2020-09-16 Koninklijke Philips N.V. Compensation de partage de charge à l'aide de discriminateurs échantillonnés
CN113933885A (zh) * 2020-06-29 2022-01-14 西门子医疗有限公司 光子计数x射线探测器、医疗成像设备和方法

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5873054A (en) * 1995-08-14 1999-02-16 William K. Warburton Method and apparatus for combinatorial logic signal processor in a digitally based high speed x-ray spectrometer
CN101297221B (zh) * 2005-10-28 2012-01-11 皇家飞利浦电子股份有限公司 用于谱计算机断层摄影的方法和设备

Cited By (30)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2438429A4 (fr) * 2009-06-05 2014-04-30 Sentinel Scanning Corp Système et procédé d'inspection d'un conteneur de transport
EP2441091A4 (fr) * 2009-06-09 2013-07-31 Planmeca Oy Capteur pour radiographie numérique, et procédé d'imagerie radiographique numérique
US8712010B2 (en) 2009-06-09 2014-04-29 Planmeca Oy Digital X-ray detector arrangement and digital X-ray imaging method
WO2010142848A1 (fr) * 2009-06-09 2010-12-16 Planmeca Oy Capteur pour radiographie numérique, et procédé d'imagerie radiographique numérique
US9801605B2 (en) 2011-12-21 2017-10-31 Koninklijke Philips N.V. Detection apparatus for detecting photons taking pile-up events into account
CN104024886A (zh) * 2011-12-21 2014-09-03 皇家飞利浦有限公司 用于考虑堆积事件来探测光子的探测装置
CN104024886B (zh) * 2011-12-21 2017-12-26 皇家飞利浦有限公司 用于考虑堆积事件来探测光子的探测装置
JP2013143980A (ja) * 2012-01-13 2013-07-25 Toshiba Corp Ｘ線ｃｔ装置
WO2013144754A3 (fr) * 2012-03-27 2014-01-23 Koninklijke Philips N.V. Électronique de détecteur comptant les photons à haut flux
US9535167B2 (en) 2012-03-27 2017-01-03 Koninklijke Philips N.V. High flux photon counting detector electronics
US9029748B2 (en) 2013-03-15 2015-05-12 Her Majesty The Queen In Right Of Canada, As Represented By The Minister Of National Defence Method and apparatus for photon counting with optical space spreading
US10078009B2 (en) 2013-04-24 2018-09-18 Koninklijke Philips N.V. Pulse processing circuit with correction means
JP2017136342A (ja) * 2016-02-05 2017-08-10 東芝メディカルシステムズ株式会社 Ｘ線ｃｔ装置
JP7123521B2 (ja) 2016-02-05 2022-08-23 キヤノンメディカルシステムズ株式会社 Ｘ線ｃｔ装置
US10627531B2 (en) 2016-04-14 2020-04-21 Commissariat à l'énergie atomique et aux énergies alternatives Device for counting particles for a radiation detector
FR3050282A1 (fr) * 2016-04-14 2017-10-20 Commissariat Energie Atomique Dispositif de comptage de particules pour detecteur de rayonnement
WO2017178745A1 (fr) 2016-04-14 2017-10-19 Commissariat A L'energie Atomique Et Aux Energies Alternatives Dispositif de comptage de particules pour détecteur de rayonnement
JP7041079B2 (ja) 2016-06-16 2022-03-23 コーニンクレッカ フィリップス エヌ ヴェ スペクトル放射線ディテクターにおける改善された光子カウント
CN109477903A (zh) * 2016-06-16 2019-03-15 皇家飞利浦有限公司 光谱辐射探测器中的改进的光子计数
JP2019521335A (ja) * 2016-06-16 2019-07-25 コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． スペクトル放射線ディテクターにおける改善された光子カウント
CN109477903B (zh) * 2016-06-16 2023-08-04 皇家飞利浦有限公司 光谱辐射探测器中的改进的光子计数
WO2017216378A1 (fr) * 2016-06-16 2017-12-21 Koninklijke Philips N.V. Comptage amélioré de photons dans un détecteur de rayonnement spectral
US11029425B2 (en) 2016-06-16 2021-06-08 Koninklijke Philips N.V. Photon-counting in a spectral radiation detector
JP7041079B6 (ja) 2016-06-16 2022-05-30 コーニンクレッカ フィリップス エヌ ヴェ スペクトル放射線ディテクターにおける改善された光子カウント
EP3610231A2 (fr) * 2017-04-13 2020-02-19 Captl LLC Comptage et spectroscopie de photons
WO2020182555A1 (fr) 2019-03-14 2020-09-17 Koninklijke Philips N.V. Compensation de partage de charge avec discriminateurs échantillonnés
CN113711084A (zh) * 2019-03-14 2021-11-26 皇家飞利浦有限公司 具有采样的区分器的电荷共享补偿
EP3709059A1 (fr) * 2019-03-14 2020-09-16 Koninklijke Philips N.V. Compensation de partage de charge à l'aide de discriminateurs échantillonnés
US11988785B2 (en) 2019-03-14 2024-05-21 Koninklijke Philips N.V. Charge sharing compensation with sampled discriminators
CN113933885A (zh) * 2020-06-29 2022-01-14 西门子医疗有限公司 光子计数x射线探测器、医疗成像设备和方法

Also Published As

Publication number Publication date
WO2008146230A3 (fr) 2009-07-23

Similar Documents

Publication Publication Date Title
WO2008146230A2 (fr) Comptage de photons avec détection d'un maximum local
US7480362B2 (en) Method and apparatus for spectral computed tomography
EP2225587B1 (fr) Detecteur de rayonnement pour compter ou integrer des signaux
EP2745143B1 (fr) Détecteur de comptage de photons
CN101680956B (zh) 用于多谱光子计数读出电路的数字脉冲处理
US9335424B2 (en) Spectral photon counting detector
US7894576B2 (en) Spectral computed tomography using correlated photon number and energy measurements
EP2092369B1 (fr) Appareil et procédé pour compter les photons de rayons x
JP6335120B2 (ja) 検出器アレイ及び光子を検出する方法
EP2052279B1 (fr) Dispositif et procede pour tomographie spectrale informatisee
US9801605B2 (en) Detection apparatus for detecting photons taking pile-up events into account
WO2008146218A2 (fr) Détecteur de comptage de photon spectral
US9588239B2 (en) Data acquisition system of photon counting detector array
US9952333B2 (en) Hybrid photon counting data acquisition system
EP2748594B1 (fr) Appareil radiographique de détection de photons avec correction de décalage
WO2013144812A2 (fr) Imagerie classique à l'aide d'un système d'imagerie comportant des détecteurs de comptage de photons
US9645260B2 (en) Photon counting system and method
CN102681001A (zh) 探测x射线辐射的方法和直接转换探测器的探测器系统

Legal Events

Date Code Title Description
NENP Non-entry into the national phase

Ref country code: DE

121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 08763105

Country of ref document: EP

Kind code of ref document: A2