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WO2004095069A1 - Element detecteur pour la detection combinee de rayons x et de rayons gamma - Google Patents

Element detecteur pour la detection combinee de rayons x et de rayons gamma Download PDF

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Publication number
WO2004095069A1
WO2004095069A1 PCT/IB2004/050418 IB2004050418W WO2004095069A1 WO 2004095069 A1 WO2004095069 A1 WO 2004095069A1 IB 2004050418 W IB2004050418 W IB 2004050418W WO 2004095069 A1 WO2004095069 A1 WO 2004095069A1
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WO
WIPO (PCT)
Prior art keywords
amplifier
pulse
detector
ray
quanta
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/IB2004/050418
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English (en)
Inventor
Michael Overdick
Herfried Karl Wieczorek
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 WO2004095069A1 publication Critical patent/WO2004095069A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • 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
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G01T1/1615—Applications in the field of nuclear medicine, e.g. in vivo counting using both transmission and emission sources simultaneously
    • 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
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G01T1/164—Scintigraphy
    • G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
    • G01T1/1648—Ancillary equipment for scintillation cameras, e.g. reference markers, devices for removing motion artifacts, calibration devices
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
    • G01T1/2914—Measurement of spatial distribution of radiation
    • G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)

Definitions

  • Detector element for combined detection of x-radiation and gamma radiation
  • the invention relates to a detector element for combined detection of x- radiation and gamma radiation, which can be used in a device capable of producing x-ray images and PET images. It also relates to a method for producing an x-ray image and a PET image in parallel.
  • US 6449 331 Bl discloses a combined CT (Computed Tomography) and PET scanner (PET: Positron Emission Tomography), which has detector elements for sequentially performed detection of x-ray quanta and gamma quanta. The detection of x-ray quanta is
  • the detector elements described in US 6 449 331 Bl contain a conversion element, which absorbs the quanta to be detected and provides a corresponding charge signal at its output. This charge signal is delivered to a circuit for analyzing individual pulses in which, on the one hand, the energy of
  • an absorbed (gamma) photon can be ascertained using a charge amplifier and, on the other hand, the arrival time of the photon can be ascertained using a fast amplifier. Said information is used in order to carry out a PET coincidence check.
  • the charge signal from the conversion element is sent to an integration circuit, in order to determine an average radiation dose or number of detected quanta.
  • the detector element according to the invention is used for combined detection of x-radiation and gamma radiation. It can be used, in particular, in a device for (simultaneously or sequentially) producing both x-ray images and PET images, and contains the following components: a) a conversion element for converting x-ray quanta and gamma quanta into an electrical signal dependent on the quantum energy, which is preferably a charge signal; b) an amplifier, coupled to the conversion element, for converting and amplifying the aforementioned electrical signal (for example a charge signal) into an amplifier pulse, the amplitude and time integral of the amplifier pulse having a known relation with the electrical signal.
  • the amplifier pulse may, in particular, be an electrical voltage pulse.
  • the value of the electrical signal can be inferred from both the amplitude and the time integral of the amplifier pulse.
  • a single-pulse analyzer coupled to the output of the amplifier, which is designed for analyzing individual amplifier pulses with respect to their value and the time of their occurrence ("event time").
  • the single-pulse analyzer therefore provides, in particular, the basis for the coincidence detection of gamma quanta which originate from an annihilation process of a positron and an electron.
  • a pulse-sequence analyzer also coupled to the output of the amplifier, which is designed for determining characteristic features of the sequence of amplifier pulses. These characteristic features may, for example, be a running average of the time integral and/or a running average of the rate of the amplifier pulses, or corresponding values starting from a fixed reference time.
  • the electrical signals (referred to below as "charge signals" by way of example and without restriction of generality) delivered by the conversion element are first converted or amplified in a single amplifier to form a pulse.
  • the amplifier pulses are then analyzed individually in a first branch and collectively in a second branch.
  • the central amplification has the advantage that all of the charge signal is recorded, and the subsequent analysis is only carried out with the resulting amplifier pulse. High accuracy of the detector element is achieved in this way, which requires comparatively few components overall for the central amplifier.
  • the one-off amplification of the charge signal downstream of the conversion element has the further advantage that it is possible to use conversion elements that provide only a comparatively weak charge signal.
  • Examples include a photodiode or a conversion element, which contains a directly converting material or consists thereof.
  • a directly converting element is characterized in that it converts absorbed x-ray or gamma quanta directly into a charge signal. With indirectly converting materials, conversely, the absorbed quanta are first converted into visible light, which is then converted into a charge signal by a downstream photodetector.
  • the dependency between the charge signal produced by the conversion element and the absorbed x-ray or gamma quanta is preferably such that the energy deposited by the quanta can be inferred from the value of the charge signal.
  • the amplitude or time integral of the amplifier pulse on the one hand, and the value of the associated charge signal, on the other hand.
  • the value of the charge signal can be inferred in a particularly straightforward way from the amplitude or time integral.
  • the relation is furthermore linear in this case, so that the sum of the amplitudes/time integrals of the amplifier pulses of two different charge signals is equal to the amplitude/time integral of the amplifier pulse of the superimposed charge signal.
  • the single-pulse analyzer is used to detect gamma quanta for a PET image. Two items of information about an absorbed quantum are required for this, namely its quantum energy and the time of its arrival. The latter is needed to check for coincidence with a second gamma quantum created by the same annihilation process.
  • the single-pulse analyzer contains two parallel branches, namely: a) an amplitude-determination branch, the input of which receives the amplifier pulse, and which is designed to provide a signal at its output which is proportional to the amplitude or time integral of the amplifier pulse.
  • a timestamp branch the input of which receives the amplifier pulse, and which is designed to indicate the event time of the amplifier pulse at its output.
  • the event time is in this case preferably defined by a unique characteristic position in the amplifier pulse, for example by particular points on its leading edge such as the 50% amplitude value.
  • the single-pulse analyzer has a discriminator as the input stage, which receives the amplifier pulses at its input and which is designed to provide further processing stages only with amplifier pulses above a predetermined amplitude threshold value. Since the gamma quanta on which a PET image is based have a higher energy (about 511 keV) than typical x-ray quanta (about 30 - 140 keV), the discriminator can be used to distinguish "normal" x-radiation from gamma quanta which potentially originate from an annihilation process. The subsequent processing can then be restricted to the relevant gamma quanta.
  • the pulse-sequence analyzer is used to determine time-averaged properties of the sequence of amplifier pulses. Such features are of prime importance for the production of an x-ray image, which is typically based on the detection of a comparatively large number of x-ray quanta.
  • the pulse-sequence analyzer has a counter circuit, the output of which indicates the number of amplifier pulses detected since a reference time, and/or the current rate of the amplifier pulses.
  • the pulse-sequence analyzer may have a dose circuit, which receives the amplifier pulse at its input and which is designed to indicate the integral of the amplifier pulses since a predetermined reference time at its output.
  • the reference time may in this case vary with time, so that the integral effectively indicates a running average of the time integral over the amplifier pulses. From the integral, it is possible to infer the value of the charge signals at the output of the conversion element, and therefore the energy deposited by the x-ray and gamma quanta.
  • the invention also relates to an instrument for producing both x-ray images and PET images, which contains the following components: a) an x-ray source for emitting x-radiation. b) a detector for detecting x-radiation and gamma radiation, which consists of detector elements of the type explained above. This means that each of the detector elements has a conversion element, an amplifier connected thereto, as well as a single-pulse analyzer and a pulse-sequence analyzer arranged in parallel downstream of the amplifier, c) a data-processing unit, which is coupled to the detector and is designed to reconstruct an x-ray image and a PET image from signals provided by the detector elements.
  • the invention furthermore relates to a method for producing an x-ray image and a PET image in parallel, which contains the following steps: a) the x-ray quanta and the gamma quanta are converted into an electrical signal, preferably a charge signal. b) the electrical signal (charge signal) is converted and amplified to form an amplifier pulse, the amplitude and time integral of the amplifier pulse being related to the electrical signal so that the value of the electrical signal can be inferred from their values. c) the values and the times of individual amplifier pulses are determined, so that it is possible to detect coincident gamma quanta from an annihilation process. d) for the chronological sequence of amplifier pulses, their rate and/or their time integral are determined so as to provide the information necessary for producing an x-ray image.
  • the charge signal is converted only once, centrally, into an amplifier pulse which is then available as a value accurately and unequivocally related to the charge signal for the subsequent analysis of the individual pulses and the pulse sequence.
  • Fig. 1 shows the general structure of a detector element according to the invention for x-radiation and gamma radiation
  • Fig. 2 shows a first possible embodiment of the amplifier
  • Fig. 3 shows a second possible embodiment of the amplifier
  • Fig. 4 shows the detailed structure of a special embodiment of the detector element in Fig. 1 ;
  • Fig. 5 shows a variant of the PET channel in a detector element according to Fig. 1;
  • Figs 6 - 9 show various possible arrangements of a detector and an x-radiation source in a device for combined production of CT and PET images.
  • CT images and PET images are commonly recorded in medical diagnosis, it being very helpful to have both types of image of the same body part available in parallel for various diagnostic tasks. While CT images provide morphological information about the body part, information about functional aspects can be derived from PET images. The two types of image should ideally be produced at exactly the same position in the patient, in order to ensure diagnostic interpretability. In this context, machines in which CT and PET systems are combined in a
  • CT systems are essentially characterized by the following features: - a geometry in which an x-radiation source is provided, with a detector extending over about 50° facing it, the two components rotating about the patient axis; an x-ray quantum energy of typically 30 - 140 keV; very high quantum fluxes of typically 3 x 10 9 photons/s mm 2 ; large dynamic range with very good linearity.
  • PET systems are characterized by: a geometry with an immobile 360° detector;
  • the invention proposes a detector element for the combined detection of x-radiation for x-ray images and gamma radiation for PET images, which has the structure outlined in figure 1.
  • the first stage of this detector element is a conversion element 1, which converts incident x-ray quanta X or gamma quanta ⁇ into electrical signals.
  • the electrical signals are preferably charge signals Q, the charge being proportional to the energy deposited by an absorbed quantum.
  • the conversion element 1 is preferably configured so that it has an absorption probability of at least 95% in the energy range of the x-ray quanta (30 - 140 keV) and an absorption probability of at least 80% in the range of the PET gamma quanta (511 keV).
  • This absorption property is achieved, for example, by a 2.0 cm thick GOS scintillator (GOS: gadolinium oxysulfide Gd 2 ⁇ 2 S).
  • GOS gadolinium oxysulfide
  • the conversion element 1 may be fonned in two parts by a scintillator/photodetector combination, or in one part by a directly converting sensor.
  • the charge signal Q produced by the conversion element 1 is delivered to an evaluation unit 2 electrically connected to the conversion element 1.
  • the evaluation unit 2 is generally characterized in that it processes the electrical signals from the conversion element 1 and provides the information necessary for the CT operation and PET operation at its output (or its outputs).
  • CT operation this involves a signal Y CT (analog, digital or mixed) which corresponds to the radiation dose detected by the conversion element during a time interval. This may involve the number of quanta detected and/or the energy deposited in the conversion element 1 by the quanta.
  • the evaluation unit 2 delivers information about the energy Y PET deposited for each detected gamma quantum, as well as information either implicitly or explicitly about the time of the detection, which is necessary for the coincidence detennination.
  • the charge signal Q from the conversion element 1 is first sent to an (input) amplifier 3 which, in a way which will be explained in more detail, produces an amplifier pulse U therefrom and provides it via its output to a coupling element 4.
  • the coupling element delivers the amplifier pulse, on the one hand, to a "PET channel” with a single-pulse analyzer 50, the output of which provides the infonnation Y PET necessary for the PET images and, on the other hand, to a "CT channel” with a pulse-sequence analyzer 60, which provides the information Y CT necessary for the CT images at its output.
  • the coupling element 4 may be permanent electrical coupling between the amplifier 30 and the single-pulse analyzer 50 or the pulse-sequence analyzer 60, respectively.
  • the element 4 may also be a selector switch by which the amplifier signal U can be appropriately directed to the PET channel or the CT channel, according to the operating mode (CT or PET).
  • CT or PET operating mode
  • figure 2 shows a first variant with a so-called CR-RC "pulse shaper".
  • this consists of a series circuit containing: a first operational amplifier 31 , the input and output of which are coupled through a capacitor 32; a second capacitor 33 downstream of the output of the operational amplifier; a second operational amplifier 35, the connection between its input and the second capacitor 33 being routed via a grounded resistor 34; a resistor 36, the output of which is grounded through a capacitor 37.
  • the output signal of such an amplifier has the form:
  • FIG. 3 shows another possible embodiment of the amplifier 30. It is formed by an operational amplifier 31, the input and output of which are coupled in parallel, on the one hand through a capacitor 32 and, on the other hand, through a resistor 38. For a (fast) charge signal Q at the input, this circuit produces a profile of the output voltage U according to:
  • Figure 4 shows possible embodiments of the single-pulse analyzer 50 and the pulse-sequence analyzer 60 of figure 1 in more detail.
  • the coupling element 4 of figure 1 is a simple electrical connection in this case.
  • the pulse-sequence analyzer 60 (CT channel) is constructed in tandem, the information from one of these two channels being in principle sufficient to produce an x-ray image.
  • the pulse-sequence analyzer 60 has, on the one hand, an integrating channel consisting of an integrator 63 and a sample-and-hold circuit 64. Owing to property (E3) of the amplifier 30, its output signals U can be readily integrated in order to obtain the total charge in a particular time window (cf. also DE 199 45 757 Al). A signal E tot which indicates the total deposited energy is therefore provided at the output of the sample-and-hold circuit 64.
  • the CT channel 60 also has a channel that counts the voltage pulses U. It consists of a CT event discriminator 61 which, owing to property (E2) of the amplifier 30, may be a simple voltage discriminator (W.R. Leo, op. cit, p.
  • n of events since a predetermined time can therefore be obtained from the output of the counter. As an alternative, this number may also no ⁇ nalized with respect to time, in order to provide a time-averaged rate.
  • the PET channel 50 firstly consists of a PET event discriminator 51, which only processes events above a predetermined energy. For example, it may be set to an energy above about 150 keV or above about 450 keV.
  • the energy info ⁇ nation is recorded on the output side by a sample-and-hold element 52, and is provided as a signal of the single-pulse energy Ep at the output of the evaluation unit 2.
  • the time Tp at which the voltage pulse U occurred is recorded and signaled out by a timestamp unit 53, connected to the discriminator 51 on the output side. For each potential PET event, its energy and information about the time of this event are therefore available at the output of the PET channel.
  • FIG. 5 shows an alternative embodiment of the single-pulse analyzer or PET channel 50.
  • the PET channel 50 must deliver the energy (corresponding to the quantity of charge Q) of an event, as well as a timestamp that is as accurate as possible. Owing to property (E2), the energy can be obtained from the amplitude information of the amplifier pulse U.
  • the series circuit containing a pulse stretcher 54 (cf. W.R. Leo, op. cit., p. 284) and a sample-and-hold element 52 may be used for this.
  • a differentiating element may also be interconnected at the input of the pulse stretcher 54, so that the correct amplitude information is actually measured when there are closely consecutive signals.
  • a signal representing the energy Ep of an individual event is therefore available at the output of the sample-and-hold element 52.
  • a timestamp Tp is produced according to figure 5 using a leading-edge discriminator 55 with a downstream timestamp generator 56.
  • This and other methods for producing time information for example a constant-fraction discriminator (CFD), are described in the literature (W.R. Leo, op. cit., pp. 326 ffi).
  • a simplified time-recording method consists in first recording time information with the leading-edge discriminator 55, and then correcting it with the aid of the amplitude information (so-called "Amplitude based Time Walk Correction", cf. G.H. Sanders et al., A high performance timing discriminator, Nuclear Instruments and Methods, 180 (1981), pp. 603 - 614). Such a correction is advantageously carried out in downstream logic (not shown) or in software.
  • the PET and CT channels of the detector elements are preferably contained in integrated circuits (for example CMOS) inside a pixel area.
  • CMOS complementary metal-oxide-semiconductor
  • a bump-bond technology for example, may be used for connecting the conversion elements 1 to the evaluation units 2.
  • figures 6 to 9 represent schematic longitudinal sections of various alternative arrangements of a detector 100, which is formed by the detector elements, for example arranged in rows and columns, and an x-radiation source (x-ray tube) 110.
  • the detector 100 is fonned as a static cylinder, or tunnel.
  • the x-ray tube 110 is arranged axially alongside the detector 100, and irradiates it at least partially. During imaging, the x-ray tube 100 rotates about the patient (not shown) who is in the middle of the detector tunnel 100.
  • the x-ray tube 110 is arranged inside the detector 100. It again rotates about the patient during imaging.
  • the x-ray tube 110 is rigidly connected to the cylindrical detector 100, and it can irradiate the opposite inner surface of the detector through a gap in the detector wall.
  • the x-ray tube 110 and the detector rotate together about the patient during imaging.
  • Figure 9 shows another variant, in which the inner part of the device comprises the rotating x-ray tube 110 and a co-rotating detector 100' opposite it, the outer parts of the device being formed by static cylindrical detector sections 100.
  • the CT channel 60 of the detector elements is used for the CT operation
  • the PET channel 50 is used for the PET operation.
  • Either the CT channel or the PET channel, or both simultaneously, may be used for the attenuation recording with a radioactive source.
  • the attenuation recording with a radioactive source may be omitted entirely, if the attenuation for the PET operation can also be determined reliably from the CT data.
  • the CT operation and the PET operation take place in parallel, in which case the PET channel 50 and the CT channel 60 are used simultaneously.
  • the PET channel is not affected by the x-ray quanta of the CT imaging, while, on the other hand, the infrequent gamma rays from PET events also cannot compromise the imaging in the CT channel.
  • the single- pulse signals are being used in CT operation, the beam hardening in the patient is simultaneously measured by the CT imaging.
  • the detector elements may also be switched over between the single-pulse analyzer 50 and the pulse-sequence analyzer 60 automatically inside the evaluation units 2. This may be controlled by information about the signal level, for example from immediately preceding measurements or from the count rate in the single-pulse analyzer 50.
  • the area of the detector elements should be approximately lxl mm 2 . While this is a typical pixel size for computer tomography, very much larger pixels are normally used for PET. Owing to Compton scattering during PET operation of the combined device with pixels that are so small, the energy (511 keV) of a PET gamma quantum may not remain in one pixel but instead be distributed over two pixels lying not far apart.
  • suitable configuration of the PET channel 50 for example as in figure 4, with an energy threshold of about 150 keV in the PET event discriminator 51), in such a case the two pixels lying not far apart would each register an event with the same timestamp.

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  • Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Molecular Biology (AREA)
  • High Energy & Nuclear Physics (AREA)
  • General Physics & Mathematics (AREA)
  • Biomedical Technology (AREA)
  • Optics & Photonics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Medical Informatics (AREA)
  • General Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Measurement Of Radiation (AREA)
  • Nuclear Medicine (AREA)

Abstract

La présente invention se rapporte à un élément détecteur d'un instrument de production combinée d'une image radiologique obtenue par tomographie assistée par ordinateur (CT) et d'une image obtenue par tomographie par émission de positrons (PET). L'élément détecteur renferme un élément convertisseur (1) qui produit un signal de charge (Q) proportionnel à l'énergie des quanta de rayons X incidents (X) et des quanta gamma (η). Le signal de charge (Q) est transformé en impulsion de tension (U) par un amplificateur (30) dans une unité d'évaluation, cette impulsion de tension (U) étant ensuite traitée séparément par un analyseur monoimpulsion (50) afin de déterminer les informations de CT (YCT). L'emploi d'un amplificateur commun permet à l'élément détecteur d'assurer une grande précision même en cas d'éléments convertisseurs (1) ayant un faible signal de charge.
PCT/IB2004/050418 2003-04-24 2004-04-13 Element detecteur pour la detection combinee de rayons x et de rayons gamma Ceased WO2004095069A1 (fr)

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Application Number Priority Date Filing Date Title
EP03101125 2003-04-24
EP03101125.7 2003-04-24

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WO2004095069A1 true WO2004095069A1 (fr) 2004-11-04

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Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102005053994A1 (de) * 2005-11-10 2007-05-24 Siemens Ag Diagnosevorrichtung für kombinierte und/oder kombinierbare radiographische und nuklearmedizinische Untersuchungen sowie entsprechendes Diagnoseverfahren
DE102005053993A1 (de) * 2005-11-10 2007-05-24 Siemens Ag Diagnosevorrichtung und Diagnoseverfahren für kombinierte und/oder kombinierbare radiographische und nuklearmedizinische Untersuchungen
DE102015217617A1 (de) * 2015-09-15 2017-03-16 Siemens Healthcare Gmbh Verfahren zum Korrigieren von Röntgenbilddaten umfassend Information bezüglich eines Zerfallsprozesses eines radioaktiven Materials
US10231678B2 (en) 2010-11-18 2019-03-19 Koninklijke Philips N.V. PET-CT system with single detector
US10371830B2 (en) 2015-10-21 2019-08-06 Koninklijke Philips N.V. Radiation detector for combined detection of low-energy radiation quanta and high-energy radiation quanta
EP4235226A1 (fr) 2022-02-24 2023-08-30 Koninklijke Philips N.V. Détecteur de radiation et procédé de détection

Citations (1)

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US20020090050A1 (en) * 2001-01-09 2002-07-11 Nutt Robert E. Combined PET and CT detector and method for using same

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US20020090050A1 (en) * 2001-01-09 2002-07-11 Nutt Robert E. Combined PET and CT detector and method for using same

Non-Patent Citations (1)

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Title
W TOWNSEND ET AL: "The smart scanner: A combined pet/ct tomograph for clinical oncology", 1998 IEEE NUCLEAR SCIENCE SYMPOSIUM AND MEDICAL IMAGING CONFERENCE, vol. 2, 12 November 1998 (1998-11-12) - 14 November 1998 (1998-11-14), TORONTO,CANADA, pages 1170 - 1174, XP002297414 *

Cited By (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102005053994A1 (de) * 2005-11-10 2007-05-24 Siemens Ag Diagnosevorrichtung für kombinierte und/oder kombinierbare radiographische und nuklearmedizinische Untersuchungen sowie entsprechendes Diagnoseverfahren
DE102005053993A1 (de) * 2005-11-10 2007-05-24 Siemens Ag Diagnosevorrichtung und Diagnoseverfahren für kombinierte und/oder kombinierbare radiographische und nuklearmedizinische Untersuchungen
US7550728B2 (en) 2005-11-10 2009-06-23 Siemens Aktiengesellschaft Diagnosis device and diagnosis method for radiographic and nuclear medical examinations
US7592600B2 (en) 2005-11-10 2009-09-22 Siemens Aktiengesellschaft Diagnosis device for radiographic and nuclear medical examinations
US7755058B2 (en) 2005-11-10 2010-07-13 Siemens Aktiengesellschaft Patient treatment using a hybrid imaging system
US10231678B2 (en) 2010-11-18 2019-03-19 Koninklijke Philips N.V. PET-CT system with single detector
DE102015217617A1 (de) * 2015-09-15 2017-03-16 Siemens Healthcare Gmbh Verfahren zum Korrigieren von Röntgenbilddaten umfassend Information bezüglich eines Zerfallsprozesses eines radioaktiven Materials
US10307127B2 (en) 2015-09-15 2019-06-04 Siemens Healthcare Gmbh Correcting X-ray image data relating to a decay process of a radioactive material
US10371830B2 (en) 2015-10-21 2019-08-06 Koninklijke Philips N.V. Radiation detector for combined detection of low-energy radiation quanta and high-energy radiation quanta
EP4235226A1 (fr) 2022-02-24 2023-08-30 Koninklijke Philips N.V. Détecteur de radiation et procédé de détection
WO2023161030A1 (fr) 2022-02-24 2023-08-31 Koninklijke Philips N.V. Détecteur de rayonnement et procédé de détection

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